system and method for measuring a quantity of a first type of cells in a blood fluid sample

专利摘要:
DYNAMIC RANGE EXTENSION SYSTEMS AND METHODS FOR PARTICLE ANALYSIS IN BLOOD SAMPLES. For the analysis of a sample containing particles from at least two categories, such as a sample containing blood cells, a particle counter subject to a detection limit is coupled to an analyzer capable of differentiating the ratios between the particle numbers, such as a visual analyzer, and a processor. The first category of particles can be present beyond the limits of the detection range, while a second category of particles is present within the respective limits of the detection range. The concentration of the second category of particles is determined by the particle counter. A ratio between the counts of the first category and the second category is determined with the analyzer. The concentration of particles in the first category is calculated on the processor based on the ratio and count or concentration of particles in the second category.
公开号:BR112015021800B1
申请号:R112015021800-8
申请日:2014-03-18
公开日:2021-01-26
发明作者:Thomas H. Adams；Bart J. Wanders；John Roche；Harvey L. Kasdan
申请人:Iris International, Inc.；
IPC主号:

专利说明:

CROSS REFERENCES TO RELATED ORDERS
[0001] This application is a non-provisional patent application for, and claims priority benefit for, US Provisional Patent Application No. 61 / 799,152 filed on March 15, 2013, the content of which is incorporated herein by reference. This application is also related to US Patent Applications Nos. 14 / 215,834, 14 / 216,533, 14 / 216,339, 14 / 216,811 and 14 / 217,034; and International Patent Applications in (automatic focus, flow cell, coating fluid, contrast agent, hematology), all filed on March 17, 2014. The content of each of these deposits is incorporated herein by reference. BACKGROUND OF THE INVENTION
[0002] This description refers to the field of equipment, systems, compositions and methods for particle analysis, including particle imaging in fluid samples, using fully or partially automated devices to discriminate and quantify particles like blood cells in the sample. The present description also relates to an intracellular organelle and / or particle alignment liquid (PIOAL) useful for analyzing particles in a sample from an individual, methods for producing the liquid, and methods for using the liquid to detect and analyze the particles. Compositions, systems, devices and methods useful for conducting image-based biological fluid sample analysis are also disclosed. The compositions, systems, devices and methods of the present description are also useful for the detection, counting and characterization of particles in biological fluids, such as erythrocytes, reticulocytes, nucleated erythrocytes, platelets, and for differential counting, categorization, subcategorization, characterization and / or leukocyte analysis based on image and morphologically.
[0003] Blood cell analysis is one of the most commonly performed medical tests to provide an overview of a patient's health condition. A blood sample can be drawn from a patient's body and stored in a test tube containing an anticoagulant to prevent clotting. A whole blood sample is usually composed of three main classes of blood cells, including red blood cells (erythrocytes), white blood cells (leukocytes) and platelets (thrombocytes). Each class can be divided into subclasses of members. For example, five main types or subclasses of white blood cells (WBCs) have different shapes and functions. White blood cells can include neutrophils, lymphocytes, monocytes, eosinophils and basophils. There are also subclasses of red blood cell types. The appearance of particles in a sample can be different according to pathological conditions, cell maturity and other causes. Subclasses of red blood cells can include reticulocytes and nucleated red blood cells.
[0004] A blood cell count that estimates the concentration of red blood cells, white blood cells or platelets can be done manually or using an automatic analyzer. When blood cell counts are done manually, a drop of blood is applied to a microscope slide, like a thin smear. Traditionally, manual examination of a stained, dried blood smear on a microscope slide has been used to determine the number or relative quantities of the five types of white blood cells. Histological dyes and stains have been used to stain cells or cell structures. For example, Wright's dye is a histological dye that has been used to stain blood smears for examination under a light microscope. A Complete Blood Count (CBC) can be obtained using an automated analyzer, a type that counts the number of different particles or cells in a blood sample based on the impedance or dynamic dispersion of light as the particles or cells pass through a detection area along a small tube. Automated CBC can use instruments or methods to differentiate between different cell types that include RBCs, WBCs and platelets (PLTs), which can be counted separately. For example, a counting technique that requires a minimum particle size or volume can be used to count only large cells. Certain cells, such as abnormal cells in the blood, cannot be counted or identified correctly. Small cells that adhere to each other may be mistakenly counted as one large cell. When erroneous counts are suspected, manual review of the instrument's results may be necessary to verify and identify the cells.
[0005] Automated techniques for counting blood cells may involve flow cytometry. Flow cytometry involves providing a narrow flow path, and detecting and counting the passage of individual blood cells. Flow cytometry methods have been used to detect particles suspended in a fluid, such as cells in a blood sample, and to analyze particles for particle type, size, and volume distribution in order to deduce concentration of the respective particle type or particle volume in the blood sample. Examples of suitable methods for analyzing particles suspended in a fluid include sedimentation, microscopic characterization, impedance-based counting, and dynamic light scattering. These tools are subject to test errors. On the other hand, the precise characterization of the types and concentration of particles can be critical in applications such as medical diagnosis.
[0006] In imaging-based counting techniques, pixel data images of a prepared sample that may be passing through a viewing area are captured using a microscopic objective lens attached to a digital camera. The pixel image data can be analyzed using data processing techniques, and also displayed on a monitor.
[0007] Aspects of automated diagnostic systems with flow cells are disclosed in US Patent No. 6,825,926 issued to Turner et al. and in US Patents No. 6,184,978; 6,424,415; and 6,590,646, all of which are granted to Kasdan et al., which are hereby incorporated by reference as if fully disclosed in the present invention.
[0008] Automated systems that use impedance or light dynamic scattering have been used to obtain a complete blood count (CBC): total leukocyte count (WBC), total erythrocyte cell volume (RBC distribution), hemoglobin HGB ( the amount of hemoglobin in the blood); mean cell volume (MCV) (mean red cell volume); MPV (average volume of PLT); hematocrit (HCT); MCH (HGB / RBC) (the average amount of hemoglobin per erythrocyte); and MCHC (HGB / HCT) (the average hemoglobin concentration in cells). Automated or partially automated processes have been used to facilitate differential counting in five parts of white blood cells (leukocytes) and blood sample analyzes.
[0009] While such systems and methods of particle analysis known today, together with related medical diagnostic techniques, can provide real benefits for physicians, clinicians and patients, further improvements are desirable. The embodiments of the present invention provide solutions to at least some of these pending needs. BRIEF SUMMARY OF THE INVENTION
[00010] The modalities of the present invention encompass systems and methods for the quantification of cells or particles present in a blood fluid sample, using exemplary detection range or dynamics extension techniques.
[00011] For example, the exemplifying modalities comprise techniques for the correction of inaccurate particle counts associated with at least one detection range, based on a parameter such as the volume of the particles. When operating the equipment as described in the present invention, particles outside the detection range for concentration and / or by volume can be detected and measured accurately.
[00012] For use in the present invention, the term "detection limit" or "outside the detection range" associated with a particle counter produced in this description will be understood to cover a range, within which the particle count is more accurate. and / or outside which the particle count is less accurate or even inoperable. A detection range can include an upper and / or lower detection limit, typically expressed as a maximum or minimum concentration, but also possibly expressed as a maximum or minimum frequency at which particles are counted within a given tolerance. precision. Consequently, the embodiments of the present invention encompass systems and methods for parallel analysis of flow cells and impedance of blood fluid samples for quantification of abundant and / or sparse species counts.
[00013] A detection range can be based on the concentration, which can include a local concentration, and / or other specified criteria or criteria. For example, it can be difficult to accurately detect and count in a particle counter a particle such as a fragment or blood cell smaller than a normal PLT (that is, having a diameter of less than 2 μm). It can be difficult to detect and count accurately on a particle counter an abnormal cell larger than a regular white cell (that is, having a diameter greater than 15 μm). In addition, at high concentrations, RBCs and PLTs can be difficult to count accurately. Even after dilution, RBCs and PLTs can aggregate to form agglomerations, resulting in false readings of the particle counts obtained using a particle counter. Furthermore, it is difficult to provide an accurate count of some immature or abnormal blood cells present in the sample at low concentrations.
[00014] As an example, when using the equipment described here, the measurement detection range, the upper detection limit for WBCs, can be extended up to 300,000, 400,000, 500,000, 600,000, 700,000, 800,000, 900,000, or 1,000. 000 per (volume unit) in some modalities. The lower detection limit for PLTs can be extended to minus 20,000, 19,000, 18,000, 17,000, 16,000, 15,000, 14,000, 13,000, 12,000, 11,000, 10,000, 9,500, 9,000, 8,500, 8,000, 7,500, 7,000, 6,500, 6,000, 5,500, 5,000, 4,500, 4,000, 3,500, 3,000, 2,500, 2,000, 1,500 or 1,000, or 500 per μl in some modalities.
[00015] Similarly, the exemplifying modalities include techniques for correcting inaccurate results obtained in a particle counter by differentiating different classes (including members of each class) of particles detected in a channel. As described here, some particles have similar morphology or volume and can be detected in one channel. For example, "giant" PLTs, aggregates or clusters of PLT and nucleated RBCs can be counted as "WBCs" in a channel designed to detect WBCs. In addition, other species, such as non-lysed cells, cryoglobulin, heinz bodies, and malaria parasite, can be counted as "WBCs" to produce a greater WBC count than actually exists in the sample. Similarly, the high concentration of giant WNCs and PLTs can be counted as "RBCs" and result in a RBC count greater than the actual value. The presence of microcytic red cells, inclusions of red cells, fragments of white cells, dust particles, hemolysis / schistocytes and even electronic / electrical noise can result in a higher than real PLT count. On the other hand, nuclear shadow cells and coagulation within the same class or confusion of a class of cells with another class can result in inaccurate and inferior counting of the corresponding class of cells in the particle counter.
[00016] In some aspects of the methods of the present description, a first category and / or subcategory of particles is present in the sample in a concentration above a detection range applicable to the first category and / or subcategory of particles; and a second category and / or subcategory of particles is present in the sample within a detection range applicable to the second category and / or subcategory of particles. In other aspects of the methods of the present invention, the first category and / or subcategory of particles is present in the sample at a concentration below a detectable range applicable to the first category and / or subcategory of particles, and the second category and / or subcategory of particles. particles is present in the sample within a detection range applicable to the second category and / or subcategory of particles. In other respects, the first category and / or subcategory of particles comprises at least one type of abnormal blood cells, immature blood cells, aggregated blood cells, blood cells having a diameter greater than 15 microns, and blood cells having a diameter less than 2 microns; and the second category and / or subcategory of particles comprises white blood cells.
[00017] When operating the equipment as described in this description, particles that are erroneously counted as another type of particles in a particle counter channel can be measured separately and accurately. Exemplary methods can also be used to determine particle counts or concentrations of particles that cannot be accurately detected in the particle counter. These particles include, but are not limited to, particles outside the normal volume ranges and / or particles present in concentrations close to or outside the high or low end of detectable concentrations in the particle counter. Similarly, when operating an equipment of the described system, especially comprising a particle counter and an image analyzer in combination with the exemplary particle contrast agent and PIOAL compositions, as described in the present description, some particles that can be counted erroneously like another type of particles in a particle counter channel can be measured separately and accurately. The methods of the present invention can also be used in some cases to determine the particle count or the concentrations of particles that cannot be accurately detected in the particle counter. These particles include, but are not limited to, particles outside a detection range and / or particles present in concentrations close to or beyond the high or low end of detectable concentrations in the particle counter. This is done by applying the information obtained from the image analyzer.
[00018] In general, when operating equipment as described herein, for example, using exemplary particle contrast agent compositions and PIOAL coating fluids, analysis of a sample containing particles, such as blood cells or other fragments, can be performed in detection ranges that are outside the nominal detection range for a particle counter. Similarly, using the described systems and compositions, the analysis of a blood fluid sample can be performed in extended detection ranges based on a parameter, such as the concentration or volume of the particle. The extended detection ranges may be outside the detection range for a particle counter.
[00019] In some embodiments, a system or equipment may include a particle counter. In other embodiments, this particle counter has at least one detection range. In certain respects, the analyzer and processor can be configured to provide additional information to correct test errors associated with the particle counter and, in addition, determine the precise particle count or the concentration of different categories and / or subcategories of particles in the particle. sample. As long as information is available from the particle counter and the analyzer on the counts, one or more reasons and / or distribution in relation to at least two of the particle categories and / or subcategories, then errors in the counts, categorization and / or subcategorization of the particle counter can be corrected, and the counts, categories and / or subcategories can be derived from those that were not initially reported by the particle counter.
[00020] The modalities of the present invention encompass systems and methods for the quantification of cells or particles present in a blood fluid sample, using exemplary range of detection or dynamic range techniques.
[00021] For example, the exemplifying modalities comprise techniques for correcting the inaccurate number of particles associated with at least one detection range, based on a parameter such as the volume of the particles. When operating the equipment as described in the present invention, particles outside the detection range for concentration and / or volume can be detected and measured accurately.
[00022] For use in the present invention, the term "detection limit" or "outside the detection range" associated with a particle counter produced in this description will be understood to encompass a range, within which the particle count is more accurate. and / or outside which the particle count is less accurate or even inoperable. A detection range can include an upper and / or lower detection limit, typically expressed as a maximum or minimum concentration, but also possibly expressed as a maximum or minimum frequency at which particles are counted within a given tolerance. precision. Consequently, the modalities of the present invention encompass systems and methods for parallel analysis of flow cells and impedance of fluid blood samples for quantification of abundant and / or sparse species counts.
[00023] A detection range can be based on the concentration, which can include a local concentration, and / or other specified criteria or criteria. For example, it can be difficult to accurately detect and count in a particle counter a particle such as a fragment or blood cell smaller than a normal PLT (that is, having a diameter of less than 2 μm). It can be difficult to detect and count accurately on a particle counter an abnormal cell larger than a regular white cell (that is, having a diameter greater than 15 μm). In addition, at high concentrations, RBCs and PLTs can be difficult to count accurately. Even after dilution, RBCs and PLTs can aggregate to form agglomerations, resulting in false readings of the particle counts obtained using a particle counter. Furthermore, it is difficult to provide an accurate count of some immature or abnormal blood cells present in the sample at low concentrations.
[00024] As an example, when using the equipment described here, the measurement detection range, the upper detection limit for WBCs, can be extended up to 300,000, 400,000, 500,000, 600,000, 700,000, 800,000, 900,000, or 1,000. 000 per (volume unit) in some modalities. The lower detection limit for PLTs can be extended to minus 20,000, 19,000, 18,000, 17,000, 16,000, 15,000, 14,000, 13,000, 12,000, 11,000, 10,000, 9,500, 9,000, 8,500, 8,000, 7,500, 7,000, 6,500, 6,000, 5,500, 5,000, 4,500, 4,000, 3,500, 3,000, 2,500, 2,000, 1,500 or 1,000, or 500 per μl in some modalities.
[00025] Similarly, the exemplifying modalities include techniques for correcting inaccurate results obtained in a particle counter by differentiating different classes (including members of each class) of particles detected in a channel. As described here, some particles have similar morphology or volume and can be detected in one channel. For example, "giant" PLTs, aggregates or clusters of PLT and nucleated RBCs can be counted as "WBCs" in a channel designed to detect WBCs. In addition, other species, such as non-lysed cells, cryoglobulin, heinz bodies, and malaria parasite, can be counted as "WBCs" to produce a greater WBC count than actually exists in the sample. Similarly, the high concentration of giant WNCs and PLTs can be counted as "RBCs" and result in a RBC count greater than the actual value. The presence of microcytic red cells, inclusions of red cells, fragments of white cells, dust particles, hemolysis / schistocytes and even electronic / electrical noise can result in a higher than real PLT count. On the other hand, nuclear shadow cells and coagulation within the same class or confusion of a class of cells with another class can result in inaccurate and inferior counting of the corresponding class of cells in the particle counter.
[00026] In some aspects of the methods of the present description, a first category and / or subcategory of particles is present in the sample in a concentration above a detection range applicable to the first category and / or subcategory of particles; and a second category and / or subcategory of particles is present in the sample within a detection range applicable to the second category and / or subcategory of particles. In other aspects of the methods of the present invention, the first category and / or subcategory of particles is present in the sample at a concentration below a detectable range applicable to the first category and / or subcategory of particles, and the second category and / or subcategory of particles. particles is present in the sample within a detection range applicable to the second category and / or subcategory of particles. In other respects, the first category and / or subcategory of particles comprises at least one type of abnormal blood cells, immature blood cells, aggregated blood cells, blood cells having a diameter greater than 15 microns, and blood cells having a diameter less than 2 microns; and the second category and / or subcategory of particles comprises white blood cells.
[00027] When operating the equipment as described in the present description, particles that are erroneously counted as another type of particles in a particle counter channel can be measured separately and accurately. Exemplary methods can also be used to determine particle counts or concentrations of particles that cannot be accurately detected in the particle counter. These particles include, but are not limited to, particles outside the normal volume ranges and / or particles present in concentrations close to or outside the high or low end of detectable concentrations in the particle counter. Similarly, when operating an equipment of the described system, especially comprising a particle counter and an image analyzer in combination with the exemplary particle contrast agent and PIOAL compositions, as described in the present description, some particles that can be counted erroneously like another type of particles in a particle counter channel can be measured separately and accurately. The methods of the present invention can also be used in some cases to determine the particle count or the concentrations of particles that cannot be accurately detected in the particle counter. These particles include, but are not limited to, particles outside a detection range and / or particles present in concentrations close to or beyond the high or low end of detectable concentrations in the particle counter. This is done by applying the information obtained from the image analyzer.
[00028] In general, when operating equipment as described herein, for example, using exemplary particle contrast agent compositions and PIOAL coating fluids, analysis of a sample containing particles, such as blood cells or other fragments, can be performed in detection ranges that are outside the nominal detection range for a particle counter. Similarly, using the described systems and compositions, the analysis of a blood fluid sample can be performed in extended detection ranges based on a parameter, such as the concentration or volume of the particle. The extended detection ranges may be outside the detection range for a particle counter.
[00029] In some embodiments, a system or equipment may include a particle counter. In other embodiments, this particle counter has at least one detection range. In certain respects, the analyzer and processor can be configured to provide additional information to correct test errors associated with the particle counter and, in addition, determine the precise particle count or the concentration of different categories and / or subcategories of particles in the particle. sample. As long as information is available from the particle counter and the analyzer on the counts, one or more reasons and / or distribution in relation to at least two of the particle categories and / or subcategories, then errors in the counts, categorization and / or subcategorization of the particle counter can be corrected, and the counts, categories and / or subcategories can be derived from those that were not initially reported by the particle counter.
[00030] In one aspect, the modalities of the present invention encompass methods for measuring an amount of a first type of cells in a blood fluid sample. The sample can include a second type of cells. Exemplary methods include determining a population of the second cell type in a first sample volume by passing the first volume through a hematology cell counter, capturing images of a first number of the first cell types and a second number of the second types cells by injecting a second volume of the sample into a coating fluid that flows inside a flow cell to provide a sample stream having a thickness and width greater than the thickness, the captured images being captured along of an image path that crosses the thickness of the sample stream, determine a ratio between the first number of the first cell type and the second number of the second cell types using the captured images, and calculate a measure of the number of cells in the first cell type in the sample using the ratio and population of the second cell type. In some cases, the cell quantity measurement includes a cell concentration for the first type of cells in the blood fluid sample. In some cases, the cell quantity measurement includes a cell count for the first cell type in the blood fluid sample. In some cases, the cell counter has a first precision associated with counting the first cell type and a second precision associated with counting the second cell type, the second precision being greater than the first precision. In some cases, the hematology cell counter has a desired precision range, the desired precision range extending between a minimum population of cells in the first volume and a maximum population of cells in the first volume, with the determined population of the second type of cells in the volume is within the desired precision range, and the measurement of the amount of cells calculated from the first type of cells in the sample is outside the desired precision range. In some cases, methods include determining a population of the first cell type in the first volume of the sample as a result of the flow of the first volume through the hematology cell counter, with the population determined for the first cell type in the first volume being above or below a desired precision range for the first cell type, and is different from the measurement of the number of cells calculated from the first cell type. In some cases, the determined population of the first cell type is zero. In some cases, the determined population of the first cell type is greater than zero. In some cases, the hematology cell counter includes a sensor mechanism that detects a change in electrical impedance in response to a second type of cell that flows through the cell counter. In some cases, the hematology cell counter includes a sensor mechanism that detects an obstruction of a light path in response to a second type of cells flowing through the cell counter. In some cases, the hematology cell counter has a lower limit of detectable concentration and a maximum limit of detectable concentration for the first type of cells, and a lower limit of detectable concentration and an upper limit of detectable concentration for the second type of cell. cells, the determined population of the second type of cells is based on a concentration parameter detected for the second type of cells that is above the minimum limit and below the maximum limit for the second type of cells, and the first type of cells is present at a concentration that is below the minimum limit or above the maximum limit for the first cell type. In some cases, the hematology cell counter has a minimum detectable volume limit and a maximum detectable volume limit for the first type of cells, and a minimum detectable volume limit and a maximum detectable volume limit for the second cell type. cell type, the determined population of the second cell type is based on a volume parameter detected for the second cell type that is above the minimum limit and below the maximum limit for the second cell type, and the first cell type it is present in a volume parameter that is below the minimum limit or above the maximum limit for the first type of cells. In some cases, the hematology cell counter has a minimum detectable size limit and a maximum detectable size limit for the first type of cells, and a minimum detectable size limit and a maximum detectable volume size for the second type of cells. cells, the determined population of the second type of cells is based on a size parameter detected for the second type of cells that is above the minimum limit and below the maximum limit for the second type of cells, and the first type of cells is present in a size parameter that is below the minimum limit or above the maximum limit for the first cell type. In some cases, determining the population of the second cell type in the first sample volume involves grouping together the cells of the first cell type and the cells of the second cell type. In some cases, methods include calculating a measure of the number of cells of the second cell type in the sample using the ratio and population of the second cell type. In some cases, determining the population of the second cell type in the first sample volume comprises grouping together the cells of the first cell type and cells of the second cell type, the methods additionally including determining a population of the first cell type in the first volume of the sample as a result of the flow of the first volume through the hematology cell counter, and the calculation of the measure of the quantity of cells of the first type of cells in the sample uses the ratio, the population of the second type of cells, and the population of the first cell type. In another aspect, the embodiments of the present invention encompass systems for measuring an amount of a first type of cells in a blood fluid sample. The sample can include a second type of cells. Exemplary systems include a hematology cell counter having a channel and an output, the output operatively coupled to the channel in order to generate signals indicative of a population of the second type of cells in a first sample volume flowing through the channel, a flow cell configured to facilitate the flow of a sample stream, the sample stream having a second sample volume and a coating fluid, and having a thickness and width greater than the thickness, a configured imaging equipment to capture images of a first number of the first cell type and a second number of the second cell type, the captured images being captured along an image path that crosses the thickness of the sample stream, a processor, an analysis module of images having a machine-readable code that incorporates tangible medium executed in the processor to determine a ratio between the first number of the first ti cell number and the second number of the second cell types using the captured images, and a cell quantity module that comprises a machine-readable code that incorporates a tangible medium executed in the processor to calculate a measure of the quantity of cells of the first type of cells in the sample using the ratio and signals indicative of a population of the second type of cells. In some cases, the processor is coupled to the hematology cell counter to receive signals indicative of the population of the second cell type. In some cases, the processor is attached to the imaging equipment to receive the captured images. In some cases, the flow cell and imaging equipment are components of a hematology analyzer that performs geometric hydrofocusing and viscosity combined for imaging the cells in the blood fluid sample. In some cases, a difference in viscosity between the coating fluid and the blood fluid sample, in combination with a decrease in the size of the flow path of the flow cell, is effective for hydrofocusing the sample stream in one location. capture image of the flow cell.
[00031] The above and many other features and concomitant advantages of the modalities of the present invention will be evident and further understood by reference to the following detailed description when considered in conjunction with the accompanying drawings. BRIEF DESCRIPTION OF THE DRAWINGS
[00032] Figure 1 is a schematic illustration, in partial section and not to scale, showing operational aspects of an exemplary flow cell, autofocus system and high optical resolution imaging device for analyzing sample images using image processing. digital images.
[00033] Figures 3A and 3B provide additional cross-sectional views of flow cells according to the modalities of the present invention.
[00034] Figure 2 is a perspective illustration of a flow cell according to an exemplary embodiment.
[00035] Figure 3 is a medium longitudinal sectional view along lines 3-3 of the flow cell shown in Figure 2.
[00036] Figures 3A and 3B provide additional cross-sectional views of flow cells according to the modalities of the present invention.
[00037] Figure 4 illustrates aspects of an imaging system according to the modalities of the present invention.
[00038] Figures 4A and 4B represent aspects of flow cells according to the modalities of the present invention.
[00039] Figures 4A-1 and 4A-2 represent cross-sectional views of the coating fluid envelope (eg, PIO-AL) and dimensions of the sample fluid stream within a flow cell of an outlet port of the cannula and an image capture site, respectively, according to the modalities of the present invention.
[00040] Figures 4K and 4L show a sample stream flowing through a flow cell image capture site in accordance with the modalities of the present invention.
[00041] Figure 4O shows a comparison between images obtained using PIOAL and images obtained using a non-PIOAL coating fluid according to the modalities of the present invention.
[00042] Figures 4P and 4Q show a comparison between images obtained using a standard coating fluid and an exemplary PIOAL fluid according to the modalities of the present invention.
[00043] Figure 5 is a block diagram showing additional aspects of systems and methods for obtaining the dynamic range or detection range for the analysis of particles in blood samples, according to the modalities of the present invention.
[00044] Figure 6 shows an example equipment for the analysis of a sample according to the modalities of the present invention.
[00045] Figure 6A represents aspects of an exemplary counter or counting module according to the modalities of the present invention.
[00046] Figure 6B represents aspects of a module system according to the modalities of the present invention.
[00047] Figure 7 represents aspects of systems and methods for measuring an amount of a first type of cells in a blood fluid sample according to the modalities of the present invention.
[00048] Figure 8 shows a method for analyzing a sample containing particles according to the modalities of the present invention.
[00049] Figure 9 illustrates a method of exemplifying the concentration of two subcategories of particles according to the modalities of the present invention.
[00050] Figures 10A, 10B, 10C, and 10D show the detection of categories of particles according to the modalities of the present invention. DETAILED DESCRIPTION OF THE INVENTION
[00051] The present description refers to equipment, systems, compositions and methods for analyzing a sample containing particles. In one embodiment, the invention relates to an automated particle imaging system that comprises an analyzer that can be, for example, a visual analyzer. In some embodiments, the visual analyzer may additionally comprise an automated processor to facilitate the analysis of the images.
[00052] According to this description, a system comprising a visual analyzer is provided for obtaining images of a sample comprising particles suspended in a liquid. The system can be useful, for example, in the characterization of particles in biological fluids, such as in the detection and quantification of erythrocytes, reticulocytes, nucleated erythrocytes, platelets and leukocytes, including differential counting, categorization and subcategorization and analysis of leukocytes. Other similar uses, such as characterizing blood cells from other liquids, are also contemplated.
[00053] The discrimination of blood cells in a blood sample is an exemplary application for which the subject matter of the invention is particularly well suited. The sample is prepared by automated techniques and presented to a high resolution optical imaging device as a thin stream of sample in a tape format to be imaged periodically while the stream of sample in a tape format passes through a field of view. . Particle images (such as blood cells) can be distinguished from each other, categorized, subcategorized and counted, using processing techniques programmed with pixel image data, either exclusively automatically or with limited human help, to identify and count cells or particles. In addition to the cell images, which can be stored and made available in the case of unusual or critical particle resources, the output data includes a count of the occurrences of each particular category and / or subcategory of the cell or particle distinguished from the recorded sample images.
[00054] The different particle counts found in each image can be further processed, for example, used to accumulate precise and statistically significant cell ratios for each of the categories and / or subcategories distinguished in the sample as a whole. The sample used for visual discrimination can be diluted, but the cell proportions in each category and / or subcategory are represented in the diluted sample, particularly after numerous images have been processed.
[00055] The equipment and methods disclosed herein are useful for discriminating and quantifying in cells in samples based on visual distinctions. The sample may be a biological sample, for example, a sample of body fluid comprising white blood cells, including, without limitation, blood, serum, bone marrow, lavage fluid, effusions, exudates, cerebrospinal fluid, pleural fluid, fluid peritoneal, amniotic fluid. In some embodiments, the sample may be a solid tissue sample, for example, a biopsy sample that has been treated to produce a cell suspension. The sample can also be a suspension obtained from treating a faecal sample. A sample can also be a production line or laboratory sample comprising particles, such as a cell culture sample. The term sample can be used to refer to a sample obtained from a patient or laboratory or from any fraction, portion or aliquot of the same. The sample can be diluted, divided into portions, or stained in some processes.
[00056] In one aspect, the systems, compositions and methods of the present description surprisingly provide high quality images of cells in a stream. In one aspect, the visual analyzer can be used in methods of the present description to provide an automated image based on the differential WBC count. In certain embodiments, the methods of the present description refer to the automated identification of visual distinctions, including morphological features and / or abnormalities to determine, diagnose, predict, predict and / or support a diagnosis of whether an individual is healthy or has a disease, condition, abnormality and / or infection and / or is responsive or unresponsive to treatment. The system may further comprise a particle counter in some embodiments. Applications include categorization and / or subcategorization, and counting cells in a fluid sample, such as a blood sample. Other similar uses for counting additional types of particles and / or particles in other fluid samples are also contemplated. The system, compositions and methods of the present invention can be used for visualization of images and categorization and subcategorization in real time using any suitable automated particle recognition algorithm. The images captured for each sample can be stored for viewing at a later date.
[00057] In another aspect, the equipment, compositions and methods of the present invention surprisingly provide an image based on the categorization and sub-categorization and signaling of more accurate cells, which reduces the rate of manual analysis compared to the rate of manual analysis when using current automated analyzers. The systems, compositions and methods reduce the rate of manual analysis and allow manual analysis to be performed on the instrument. In addition, the systems, compositions and methods of the present description also reduce the percentage of signaled samples during automated analysis as requiring manual analysis.
[00058] The present description also refers to systems, methods and compositions for combining a complete blood count (CBC) counter with an analyzer, such as a visual analyzer, in order to obtain a CBC and an image based on in the differential leukocyte count expanded and an expanded platelet count based on the image, thus extending the effective detection range for the platelet count.
[00059] Consequently, in some embodiments, the present description provides equipment and a method for analyzing a sample containing particles, for example, blood cells. According to this description, a visual analyzer is provided to obtain images of a sample comprising particles suspended in a liquid. In some embodiments, the visual analyzer comprises a flow cell and an autofocus component, in which a liquid sample containing particles of interest is required to flow through a flow cell having a window through which a camera coupled to a lens lens captures digital images of the particles. The flow cell is coupled to a sample fluid source, such as a diluted and / or treated blood sample or other body fluid sample, as described herein, and to a source of a clear coating fluid, or alignment liquid. of intracellular organelles and / or particles (PIOAL).
[00060] In one embodiment, the equipment also comprises a particle counter having at least one detection range, as well as an analyzer, and a processor. The analyzer and processor are configured to provide additional information to correct count, categorization, and subcategorization errors associated with the particle counter, and, in addition, determine the precise particle count or concentration of different particle categories and / or subcategories in the sample.
[00061] The present description provides methods and compositions useful for aligning the intracellular organelle and / or particle in carrying out image analysis of the sample. In some embodiments, the present description refers to methods and compositions for an imaging and counting system combined with the ability to perform a complete blood count (CBC) and an expanded WBC differential (WBC) based on the image capable of identifying and counting cell types, such as WBCs, RBCs and / or platelets, including, for example, neutrophils, lymphocytes, monocytes, eosinophils, basophils, reticulocytes, nucleated RBCs, blasts, promyelocytes, myelocytes, or metamielocytes, and provide image-based information for WBC counts and morphologies, erythrocyte counts and morphologies (RBC) and platelet counts and morphologies (PLT).
[00062] In other embodiments, the present description refers to a PIOAL that can be used in the analysis of particles based on the image, as described here. The cell category and / or subcategory counting in blood samples is used in the present description as non-limiting examples of sample classifications that can be analyzed. In some embodiments, the cells present in the samples may also include bacterial or fungal cells, as well as white blood cells (leukocytes), red blood cells (erythrocytes) and / or platelets. In some modalities, particle suspensions obtained from tissues or aspirates can be analyzed.
[00063] The discrimination of blood cells in a blood sample is an exemplary application for which the subject matter of the invention is particularly well suited. The sample is prepared by automated techniques and presented to a high resolution optical imaging device as a sample stream in a tape format to be imaged periodically while the sample stream passes through a field of view. Particle images (such as blood cells) can be distinguished from each other, categorized, subcategorized and / or counted, using processing techniques programmed with pixel image data, either exclusively automatically or with limited human help, to identify and count cells or particles. In addition to the cell images, which can be stored and made available in the case of unusual or critical particle resources, the output data includes a count of the occurrences of each particular category and / or subcategory of the cell or particle distinguished from the recorded sample images. The counts of different particles found in each image can be further processed, for example, used to accumulate precise and statistically significant proportion ratios, or functions of the same cells of each of the categories and / or subcategories distinguished in the sample as a whole. The sample used for visual discrimination can also be highly diluted, but the proportions of cells in each category and / or subcategory are represented in the distribution for the diluted sample, particularly after numerous images have been processed.
[00064] In some respects, samples are presented, imaged and analyzed in an automated way. In the case of blood samples, the sample can be substantially diluted with water or saline, which reduces the extent to which the visualization of some cells can be hidden by other cells in an undiluted or less diluted sample. Cells can be treated with agents that enhance the contrast of some aspects of cells, for example, using permeabilizing agents to make cell membranes permeable, and histological stains to adhere and to reveal elements such as granules and the nucleus. In some embodiments, it may be desirable to stain an aliquot of the sample for counting and characterizing particles that include reticulocytes, nucleated erythrocytes, platelets, and for differentiating, characterizing and analyzing leukocytes. In other embodiments, samples containing erythrocytes can be diluted prior to their introduction into the flow and imaging cell.
[00065] Particulars regarding sample preparation equipment and methods for dilution, permeabilization and histological staining of the sample, are generally performed using precision valves and pumps operated by one or more programmable controllers, and are not central to this description. Examples can be found in patents issued to International Remote Imaging Systems, Inc, such as US 7,319,907, on programmable controls. Similarly, techniques for distinguishing between certain categories and / or subcategories of cells by their attributes, such as relative size and color can be found in US 5,436,978, in connection with white blood cells (leukocytes). The disclosures of these patents are hereby incorporated by reference.
[00066] To facilitate the capacity, speed and efficiency by which particles, such as cells, are categorized and / or subcategorized, it is advantageous to provide transparent, high-quality images of blood cells for automated analysis by the data processing system. According to the present description, a stream of prepared sample is arranged on a thin strip having a stable position between the opposite walls of a flow cell. The positioning of the sample stream and its leveling in thin ribbon format can be achieved by the flow between the layers of a PIOAL introduced into the flow cell which differs in the viscosity of the sample fluid and is flowed through a symmetrical flow channel.
[00067] The PIOAL has an adequate viscosity and density, and the flow rates at the point of introduction into the sample flow cell are such that the sample fluid is leveled on a thin strip. The sample stream in tape format is transported together with the PIOAL, to pass in front of a viewing port, where an objective lens and a light source are arranged to allow viewing of the sample stream in tape format. The fluid sample is introduced, for example, injected at a point where the flow path of the PIOAL narrows symmetrically. As a result, the fluid stream of the sample is flattened and extended on a thin ribbon. A PIOAL of this description can be used as the coating fluid with any visual analyzer of the present description. In one embodiment, the PIOAL can be inserted at one end of the flow cell to carry the sample fluid with it towards discharge.
[00068] The size of the tape-shaped sample stream in the viewing area is affected by geometric thinning of the PIOAL flow path and differential linear velocity of the sample fluid and the PIOAL resulting in the thinning and stretching of the shaped sample stream of tape. The initial differential linear velocity of the sample for PIOAL can vary from 0.5: 1 to 5: 1. The cross section of the PIOAL flow path can be thinned by reducing the depth by a factor of about 10: 1, 15: 1, 20: 1, 25: 1, 30: 1, 35: 1, 40 : 1, 45: 1, 50: 1, 55: 1, 60: 1, 65: 1, 70: 1, 75: 1, 80: 1, 85: 1, 90: 1, 95: 1, 100: 1 , 105: 1, 110: 1, 115: 1, 125: 1, 130: 1, 140: 1, 150: 1, 160: 1, 170: 1, 180: 1, 190: 1, or 200: 1. In one embodiment, the geometric thinning is 40: 1. In one embodiment, the geometric thinning is 30: 1. The factors taken into account are the transit time through the flow cell, the desired rate of sample throughput, obtaining a sample stream thickness in tape format comparable to the particle size, obtaining particle alignment and organelles, obtaining the content of focus particles, balancing pressure, flow and viscosity within operating limits, optimizing the thickness of the sample stream in ribbon format, achieving a desired linear speed, fabricability considerations and sample volumes and PIOAL required.
[00069] The length and volume of the cannula and the flattening of the cross section can be selected to reduce the period of sample flow instability, thereby increasing productivity. In some embodiments, the period of flow instability may be less than about 3, 2.75, 2.5, 2.25, 2, 1.75, 1.5 1.25, or less than about 1 second . A smaller cannula volume can also reduce the time and volume of diluent needed to clean the cannula between runs of samples. In some embodiments, the transit time through the flow cell is 1, 2, 3, or 4 seconds, or any range between any two of these times. In some modalities, the transit time may be less than 4, 3 or 2 seconds.
[00070] The viscosities and flow rates of the sample fluid and the PI-OAL and the flow cell contour are arranged in such a way that the flow of PIOAL flattens and extends the flow of the sample to a flat ribbon consistently across the viewing area in a safe place. The fluid stream of the sample can be compacted to approximately 2 to 3 μm of fluid flow thickness. Various types of blood cells have diameters larger than the flow thickness. Shear forces in the direction parallel to the flow direction cause an increase in the projection of the particle image under imaging conditions in the focal plane of the high resolution optical imaging device and / or causing intraparticle structures, for example , intracellular structures, organelles or lobes, are positioned, repositioned, and / or better positioned to be substantially parallel to the direction of flow. The depth of the high resolution field imaging device is up to 7 μm, for example, 1 to 4 μm.
[00071] The flow cross section of PIOAL, with the ribbon-shaped sample stream carried with it, is constant through a viewing zone in front of a viewing port through which the objective lens is directed. The objective lens can be the objective component of a high resolution optical imaging device or digital image capture device. The sample stream in ribbon format follows a path through the viewing zone, in a known and repeatable position within the flow cell, for example, at a known and repeatable distance from two walls of the flow cell, being discharged downstream.
[00072] The optical information from the sample particles is detected by a detection section in the analyzer, when the strip-shaped sample stream is transported through the viewing zone in front of the viewing port, thus generating data of the particles / cells contained in the sample. The use of this analyzer allows the capture, processing, categorization and subcategorization and counting of cells and / or particles contained in samples. The PIOAL liquid can be prepared by adding viscosity modifying agent, buffering agent, pH adjusting agent, antimicrobial agent, ionic strength modifier, surfactant, and / or a chelating agent. The exemplary features and / or functional components of the analyzer in the present description may include, for example, the ability to capture and / or process image analysis data, sample color processing, image processing, and / or image identification. particle images, counting, and / or categorization and subcategorization.
[00073] In one embodiment, the present description is based on the surprising and unexpected discovery that adding an adequate amount of a viscosity agent to the PIOAL significantly improves the alignment of cells / particles in a flow cell, leading to greater percentage of cells in focus, or cellular components, and higher quality images of cells and / or particles in the stream. The addition of the viscosity agent increases the shear forces on cells, such as RBCs, which improves the alignment of cells in a plane substantially parallel to the direction of flow, which results in image optimization. This also results in the positioning, repositioning, and / or better positioning of intraparticle structures, such as intracellular structures, organelles or lobes substantially parallel to the direction of flow, which results in image optimization. The viscosity agent also reduces cell misalignment, generally, but not limited to, cells that are smaller in diameter than the flow stream.
[00074] The alignment of cells that are smaller in diameter than the flow current, for example, erythrocytes, can be obtained, for example, by increasing the viscosity of PIOAL, or by increasing the flow rate ratio . This results in the alignment of RBCs parallel to the flow direction. In some embodiments, a reduction in RBC misalignment and / or an increase in RBC alignment is achieved by increasing the PIOAL viscosity.
[00075] The thickness of the sample stream in tape format can be affected by the relative viscosities and flow rates of the sample fluid and PIOAL. The sample source and / or the PIOAL source, for example, comprising precision displacement pumps, can be configured to deliver the sample and / or the PIOAL at controllable flow rates to optimize the dimensions of the tape-shaped sample stream, this is like a thin ribbon at least as wide as the field of view of the high resolution optical imaging device or the digital image capture device.
[00076] The flow cross section of PIOAL, with the ribbon-shaped sample stream carried with it, is constant through a viewing zone in front of a viewing port through which the high resolution optical imaging device is targeted. The ribbon-shaped sample stream follows a path through the viewing zone, at a known and repeatable distance from any of the walls at the front and rear of the flow cell being discharged downstream.
[00077] The term high resolution optical imaging device can include devices that are capable of obtaining images of particles with sufficient visual distinctions to differentiate features and / or morphological changes. Exemplary high resolution image optical devices may include devices with an optical resolution of 1 µm or less, including, for example, 0.4 to 0.5 µm, such as, for example, 0.46 µm.
[00078] In some embodiments, the images obtained in any of the compositions and / or methods of the present invention can be digitized images. In some embodiments, the images are obtained under microscopy images. In certain embodiments, images can be obtained manually. In other modalities, at least part of the image acquisition process is automated. In some embodiments, images can be obtained using a visual analyzer that comprises a flow cell, a high resolution optical imaging device or the digital image capture device, optionally with an autofocus feature.
[00079] In one embodiment, the images provide information about the cytosolic, cell nucleus and / or nuclear components of the cell. In one embodiment, the images provide information related to the granular component and / or other morphological features of the cells. In one embodiment, the images provide information regarding the cytosolic, nuclear and / or granular components of the cells. Granular and / or nuclear images and / or resources are crucial for cell categorization and sub-categorization either independently or in combination with each other.
[00080] In one aspect of the methods of the present invention, the cells placed in contact with the particle and / or imaged contrast agent composition are the nucleated erythrocytes. In yet another aspect, the methods of the present invention refer to a method for performing erythrocyte categorization and subcategorization based on the image comprising: a) imaging a portion of the erythrocytes; and b) determine the morphology of the imaged erythrocytes. For use in the present invention, erythrocytes (RBC) can include, for example, normal or abnormal erythrocytes, reticulocytes, nucleated erythrocytes, and / or in cells infected with malaria. In some embodiments, image formation is carried out using the equipment of the present description, such as equipment comprising a particle counter, a visual analyzer and a processor.
[00081] For use in the present invention, an exemplary complete blood count (CBC) may include a test panel typically requested by a doctor or other medical professional that provides information about the particles and / or cells in a blood sample from a patient. patient. Examples of cells circulating in the bloodstream can generally be divided into three types: including, but not limited to, for example, white blood cells (eg, leukocytes), red blood cells (eg, erythrocytes) , and platelets (thrombocytes).
[00082] For use in the present invention, abnormally high or low counts may indicate the presence of the disease, disorder and / or condition. Thus, BCC is one of the blood tests commonly performed in medicine, since it can provide an overview of a patient's general health status. Consequently, BCC is routinely performed during annual physical exams.
[00083] For use in the present invention, typically, a phlebotomist collects the subject's blood sample, the blood is usually collected in a test tube typically containing an anticoagulant (eg EDTA, sometimes citrate) to prevent its coagulation. The sample is then transported to a laboratory. Sometimes, the sample is taken by a finger prick using a Pasteur pipette for immediate processing by an automated counter. In one embodiment, the image of the particle is captured while the particle is surrounded by a coating fluid or PIOAL. In certain embodiments, the blood sample can be seen on a slide prepared with a sample of the patient's blood under a microscope (a blood film, or peripheral smear). In certain embodiments, the complete blood count is performed by an automated analyzer.
[00084] For use in the present invention, in general, blood analyzers can aspirate a very small amount of specimen through a narrow tube. The sensors can detect the count and / or the number of cells that pass through the tube, and can identify the type of cell. Exemplary sensors can include light detectors (for example, visible, UV or IR) and / or electrical impedance. Exemplary detection parameters can include cell size, volume and / or resources. In certain embodiments, sensors can detect visible and non-visible light over a spectrum of wavelengths ranging from about 200 nm to about 10,000 nm. In certain embodiments, the sensors can detect a wavelength between about 380 nm and 760 nm.
[00085] For use in the present invention, the data / parameters of a blood count can include, for example, whole red blood cells; hemoglobin - the amount of hemoglobin in the blood; hematocrit or packaged cell volume (PCV); average corpuscular volume (MCV) - the average volume of red cells (anemia is classified as microcytic or macrocytic based on whether this value is above or below the expected normal range. Other conditions that can affect MCV include thalassemia, reticulocytosis and alcoholism); mean corpuscular hemoglobin (MCH) - the average amount of hemoglobin per erythrocyte, in picograms; mean corpuscular hemoglobin concentration (MCHC) - the mean hemoglobin concentration in cells; width of distribution of red blood cells (RDW) - the variation in cell volume of the RBC population; white blood cells; neutrophilic granulocytes (may indicate bacterial infection, typically increased in acute viral infections). Due to the segmented appearance of the nucleus, neutrophils are often called "segs". The nucleus of less mature neutrophils is not segmented, but has an elongated band or shape. Less mature neutrophils - those that have recently been released from the bone marrow into the bloodstream - are known as "bands". Other data / parameters for a blood count may also include, for example, lymphocytes (for example, increased with some viral infections, such as glandular fever, and in chronic lymphocytic leukemia (LLC), or decreased by HIV infection); monocytes (may be increased in bacterial infection, tuberculosis, malaria, Rocky Mountain spotted fever, monocytic leukemia, chronic ulcerative colitis and regional enteritis; eosinophilic granulocytes (for example, increased in parasitic infections, asthma, or allergic reaction basophilic granulocytes (for example, increased in bone marrow related conditions, such as leukemia or lymphoma.
[00086] For use in the present invention, the data / parameters of a blood count can also include, for example, the data associated with platelets, including platelet numbers, information about their size and the size range in the blood; mean platelet volume (MPV) - a measurement of the mean platelet size.
[00087] In another aspect of the methods of the present invention, cells brought into contact with the particle and / or imaged contrast agent composition are abnormal cells, such as cells infected with malaria, atypical lymphocytes. In some aspects of the present invention, cells are abnormal cells that can be used to identify, predict, diagnose, predict, or support a diagnosis of a condition, disease, infection and / or syndrome.
[00088] In another aspect of the methods of the present invention, the cells are platelets.
[00089] Unless expressly stated otherwise, references to "particle" or "particles" made in the present description will be understood to encompass any formed or discrete object dispersed in a fluid. For use in the present invention, "particle" can include all detectable and measurable components (for example, by image and / or other measurable parameters) in biological fluids. The particles are of any material, any shape and any size. In certain embodiments, the particles can comprise cells. Examples of particles include, but are not limited to, cells, including blood cells, fetal cells, epithelial cells, stem cells, tumor cells or bacteria, parasites, or fragments of any of the foregoing or other fragments in a biological fluid. Blood cells can be any blood cell, including any normal or abnormal, mature or immature cells that potentially exist in a biological fluid, for example, red blood cells (RBCs), white blood cells (WBCs), platelets (PLTs) and other cells. The limbs also include immature or abnormal cells. Immature WBCs can include metamielocytes, myelocytes, pro-myelocytes and blasts. In addition, for mature RBCs, members of RBCs may include nucleated RBCs (NRBCs) and reticulocytes. PLTs can include "giant" PLTs and PLT nodes. Blood cells and elements formed are described further in another section in the present description.
[00090] Exemplary particles can include elements formed in samples of biological fluids, including, for example, spherical and non-spherical particles. In certain embodiments, in certain embodiments, the particles may comprise non-spherical components. The image projection of non-spherical components can be maximized in the focal plane of the high resolution optical imaging device. In certain embodiments, the non-spherical particles are aligned in the focal plane of the device of the high resolution optical imaging device (aligned in a plane substantially parallel to the direction of flow). In some embodiments, platelets, reticulocytes, nucleated RBCs, and WBCs, including neutrophils, lymphocytes, monocytes, eosinophils, basophils, and immature WBCs including blades, promyelocytes, myelocytes, or metamielocytes are counted and analyzed as particles.
[00091] For use in the present invention, the detectable and measurable particle parameters may include, for example, non-image based and / or visual indices of size, shape, symmetry, contour and / or other characteristics.
[00092] The sample can be an isolated and / or prepared biological sample, including, for example, a sample of body fluid, a sample of blood, serum, cerebrospinal fluid, pleural fluid, peritoneal fluid, saliva, seminal fluid, tears, sweat, milk, amniotic fluid, washing fluid, bone marrow aspirate, effusions, exudates, or other sample obtained from an individual (for example, biopsy sample that was treated to produce a cell suspension, or a sample of production line or laboratory comprising particles). In some embodiments, the sample may be a solid tissue sample, for example, a biopsy sample that has been treated to produce a cell suspension. The sample can also be a suspension obtained from treating a faecal sample. A sample can also be a laboratory, chemical, industrial or production line sample comprising particles, such as a cell culture sample. The term sample can be used to refer to a sample obtained from a patient or laboratory or from any fraction, portion or aliquot of the same. The sample can be diluted, divided into portions, or treated with a contrast agent, in some processes.
[00093] The methods disclosed herein are applicable to samples from a wide range of organisms, including mammals, for example, humans, non-human primates (eg, monkeys), horses, cows or other livestock, dogs, cats or other mammals kept as pets, rats, mice or other laboratory animals; birds, for example, chickens; reptiles, for example, alligator; fish, for example, salmon and other farmed species; and amphibians.
[00094] Samples can be obtained by any conventional method, for example, excretion, extraction, collection, aspiration, or a biopsy. The sample may be from an individual considered healthy, for example, a sample collected as part of a routine physical examination. The sample may also be from an individual who has, is at risk for, or who is suspected of having a disorder. The disorder can be the result of an illness, a genetic abnormality, an infection, an injury, or unknown causes. Alternatively or in addition, the methods may be useful for monitoring an individual during the course of treatment for a disorder. When there are signs of an inability to respond to treatment and / or therapy, a doctor may choose an alternative or adjuvant agent. Depending on the condition of the individual and the particular disorder, if applicable, samples may be collected once (or twice, three times, etc.), daily, weekly, monthly, or annually.
[00095] The particles may vary depending on the sample. The particles can be biological cells, for example, blood cells, fetal cells, stem cells, tumor cells or fragments thereof. In some embodiments, the particles can be an infectious agent, for example, a virus or bacteria.
[00096] Reference to "blood cells" made in this description will be understood to encompass all normal or abnormal cells, mature or immature, that potentially exist in a biological fluid, for example, red blood blood cells (RBC), cel - white blood cells (WBCs), platelets (PLTs) and other cells. In general, normal RBCs, PLTs, and WBCs have a particle diameter in the range of 6-8 μm, 2-3 μm, and 8-15 μm, respectively. Normal RBCs, WBCs and PLTs are present in whole blood samples from normal patients in an approximate concentration range of 3.9 to 5.7 x 1012 cells / L, 1.4 to 4.5 x 1012 cells / L, 3.5 to 11 x 1012 cells / L, respectively. See, Barbara J. Bain, Blood Cells, A Practical Guide, 4th ed, Blackwell Publishing, 2007, 3436.
[00097] The reference to a "formed element" will be understood as covering non-fluid elements present in biological fluid samples. Formed elements include, for example, blood cell classes based on scientific classification or physiological function including erythrocytes (RBCs), leukocytes (WBCs) and platelets (PLTs), WBC nodules, leukocyte subclasses, which include lymphocytes mature and immature leukocytes such as monocytes, neutrophils, eosinophils, basophils. The "elements formed" for use in the present invention also include particles, such as microorganisms, bacteria, fungi, parasites, or fragments thereof or other cellular fragments. The main members of WBCs include, but are not limited to, neutrophils, lymphocytes, monocytes, eosinophils and basophils. The limbs also include immature or abnormal cells. For example, immature WBCs can include metamielocytes, myelocytes, pro-myelocytes. In addition, for mature RBCs, members of RBCs may include nucleated RBCs (NRBCs) and reticulocytes. PLTs can include regular PLTs, and "giant" PLTS whose size is close to that of normal WBCs. The reference to a "member" or "members" of a category and / or subcategory of particles made in the present description will be understood as covering individual particles within a category or subcategory of particles.
[00098] Unless expressly stated otherwise, reference to a "category" of particles made in the present description will be understood to encompass a group of particles detected using at least one measurement, detected or derived detection criterion, such as size , shape, texture, or color. In some embodiments, the members of at least one category and / or subcategory of particles counted by the equipment of the present description will be the same type of element formed.
[00099] Such particles can be detected in a "channel". The reference to "channel" made in the present description should be understood as covering a portion of the particle counter that comprises a detector coupled to a signal source, providing an output that varies with the greater or lesser detection of particles that meets at least a channel detection criterion. For example, a channel detection criterion can be based on the size or volume of the particles. In some embodiments, the number of channels in a particle counter is one. In some other embodiments, the number of channels in a particle counter is two or more.
[000100] A category and / or subcategory of particles detected in a particle counter channel can comprise different classes and subclasses of particles, and the members of particles grouped into two or more subclasses. The reference to a "category" of particles made in the present description will be understood as covering a grouping of particles that corresponds to the measured, detected or derived criteria, such as size, shape, texture, or color. In some embodiments, the members of at least one category and / or subcategory of particles counted by the equipment of the present description will be the same type of element formed.
[000101] For use in the present invention, the term high resolution optical imaging device can include devices that are capable of obtaining images of particles with sufficient visual distinctions to differentiate features and / or morphological changes. Exemplary high resolution image optical devices may include devices with an optical resolution of 1 µm or less, including, for example, 0.4 to 0.5 µm, such as, for example, 0.46 µm.
[000102] For use in the present invention, particle contrast agent compositions can be adapted for use in combination with a liquid intracellular organelle and / or particle alignment (PIOAL) in a visual analyzer to analyze particles in a sample of a individual. The exemplary PIOAL is useful, as an example, in methods for the automated recognition of different types of particles in a sample from an individual.
[000103] In another aspect, cells can be involved in PIOAL when images are obtained. Suitable exemplifying intracellular organelle alignment liquids are described herein.
[000104] For use in the present invention, "alignment" can be characterized in part by the alignment of spherical and / or non-spherical particles. For example, particles, like non-spherical particles, can be aligned in a plane substantially parallel to the direction of flow. In certain embodiments, the alignment of the non-spherical particles is characterized by the orientation of the increase of the particles in an image projection of the non-spherical particles under imaging conditions in the focal plane of the high resolution optical imaging device. Particles such as spherical particles can have an increase in the amount of intraparticle content in focus of the particles and cells, which is effective in generating visual distinctions for the categorization and subcategorization of the particles. The intraparticulate structures of the particles, such as spherical particles, can be positioned, repositioned and / or better positioned to be substantially parallel to the direction of flow. For example, intracellular structures, organelles or lobes can also be positioned, repositioned, and / or better positioned to be substantially parallel to the direction of flow.
[000105] The reference to a "class" of particles made in the present description will be understood as covering a group of particles based on the scientific classification. For example, For example, three main classes of blood cells exist in a whole blood sample, including RBCs, WBCs and PLTs.
[000106] The reference to a "member" or "members" of particles made in this description will be understood to encompass particles in a category or subcategory of particles. For example, each category of blood cells can be further divided into subcategories or members. The main members of WBCs include, but are not limited to, neutrophils, lymphocytes, monocytes, eosinophils and basophils. The limbs also include immature or abnormal cells. For example, immature WBCs can include metamielocytes, myelocytes and pro-myelocytes. In addition, for mature RBCs, members of RBCs may include nucleated RBCs (NRBCs) and reticulocytes. PLTs can include regular PLTs, and "giant" PLTs whose size is close to that of normal WBCs.
[000107] Reference to "immature cells" will be understood to encompass cells at a certain stage of development, for example, within the bone marrow or shortly after release from the bone marrow, but before full development in a mature cell .
[000108] Reference to "abnormal cells" will be understood to encompass cells with irregular morphological characteristics or cells associated with a particular disease or condition, or associated irregularities that may, in some cases, be associated with certain diseases or conditions. Examples of certain diseases include, but are not limited to, erythrocytosis, polycythemia, anemia, erythroblastopenia, leukocytosis, leukopenia, lymphocytosis, lymphocytopenia, granulocytosis, granulocytopenia or agranulocytosis, neutrophilia, neutropenia, baseline, and thrombocytosis, thrombocytopenia and pancytopenia. A class of cells can increase or decrease in the bloodstream. In some conditions, abnormal cells much larger than regular white cells have a small concentration in a blood sample. Variations in size, shape, color and / or intracellular structures can be associated with certain diseases or conditions.
[000109] Reference to the "counting" of particles or "particle counting" made in the present description will be understood as covering the numbers of particles obtained from a channel of a particle counter. Reference to the "concentration" of a class or a particle member made in the present description will be understood to mean the numbers of particles per unit volume (for example, per liter) or by a sample of known volume. For example, a particle counter can provide counts or concentrations or another function based on the count for the particle categories, while a visual analyzer can provide counts, concentrations, ratios or other parameters based on the concentration for each particle category or subcategory.
[000110] Reference to "reason" made in the present description will be understood as covering any quantitative and / or proportioned ratio of two categories / subcategories, classes or members of particles. Examples of such a ratio include, but are not limited to, a ratio by concentration, weight, and / or by number of particles. Typically, the ratio concerns the numerical fraction of the count of a category, class or member in relation to the count of another such category, class or member. In some embodiments, determinations using weighted or heavy counts and / or proportional ratios can also be made. Hematology - Particle analysis system
[000111] Now returning to the drawings, Figure 1 schematically shows an exemplary flow cell 22 for transporting a fluid sample through a viewing zone 23 of a high resolution optical imaging device 24 in a configuration to form particle images microscopic images in a stream of sample stream 32 using digital image processing. The flow cell 22 is coupled to a source 25 of the sample fluid that may have undergone processing, as brought into contact with a particle contrast and heating agent composition. Flow cell 22 is also coupled to one or more sources 27 of a liquid intracellular organelle and / or particle alignment (PIOAL), such as a clear glycerol solution with a viscosity that is greater than the viscosity of the sample fluid.
[000112] The sample fluid is injected through a flattened opening at a distal end 28 of a sample feed tube 29, and into the flow cell 22, at a point where the flow of PIOAL has been substantially established resulting in in a symmetrical and stable laminar flow of the PIOAL above and below (or on opposite sides of) the ribbon-shaped sample stream. Sample and PIOAL streams can be supplied by means of precision metering pumps that move the PIOAL with the injected fluid sample along a substantially narrowing flow path. PIOAL wraps and compacts the fluid sample in zone 21, where the flow path narrows. Consequently, the decrease in the thickness of the flow path of zone 21 can contribute to a geometric focus of the sample stream 32. The sample fluid strip 32 is wrapped and transported together with the PIOAL downstream of the narrowing zone 21, passing through in front of, or otherwise, through the viewing zone 23 of the high resolution optical imaging device 24 where images are collected, for example, using a CCD 48. Processor 18 can receive pixel data as input from CCD 48. The sample fluid strip flows together with the PIOAL to a discharge 33.
[000113] As shown here, the narrowing zone 21 may have a proximal flow path portion 21a having a proximal thickness PT and a distal flow path portion 21b having a distal thickness DT, such that the distal thickness DT is less than the proximal thickness PT. The sample fluid can therefore be injected through the distal end 28 of the sample tube 29 at a location that is distal from the proximal portion 21a and proximal to the distal portion 21b. Thus, the fluid sample can introduce the PIOAL envelope as the PIOAL stream is compacted by zone 21, with the sample fluid injection tube having a distal outlet port through which the sample fluid is injected into the flowing coating fluid, the distal outlet port being delimited by decreasing the size of the flow path of the flow cell.
[000114] The high resolution digital optical imaging device 24 with objective lens 46 is directed along an optical axis that intercepts the sample stream in ribbon format 32. The relative distance between objective 46 and flow cell 33 it is variable by operating a motor unit 54, to resolve and collect a scanned image focused on a photodetector array. Flow cell
[000115] A practical embodiment of the flow cell 22 is further represented in Figures 2 and 3. As shown here, the flow cell 22 can be coupled with a sample source 25 and also a source 27 of PIOAL material. The fluid sample is injected into flow cell 22 through cannula 29, for example, through a distal outlet port 31 from cannula 29. Typically, the PIOAL coating fluid is not in a laminar flow state as it moves through a curved channel section 41 in the flow cell from the source 27 towards the viewing zone 23. However, the flow cell 22 can be configured so that the PIOAL coating fluid is or becomes whether to laminate, or has a flat speed profile, as it passes through the distal outlet port 31, where the sample fluid is introduced into the flowing coating fluid. The fluid sample and the PIOAL can flow along the flow cell 22, in a direction usually indicated by the arrow A and then out of the flow cell 22 via the discharge 33. The flow cell 22 defines a path internal flow 20 that symmetrically narrows (for example, the transition zone 21) in the direction of flow A. The symmetry of the flow path contributes to a robust and centralized flow of the sample stream. The flow cell 22 is configured to direct a flow 32 of the sample involved with the PIOAL through a display zone 23 in the flow cell, that is, behind the display port 57. Associated with the display port 57 is a pattern autofocus 44. Flow cell 22 also has a rounded or recessed seat 58, which is configured to accept or receive a microscope objective (not shown).
[000116] According to some modalities, the autofocus pattern 44 can have a position that is fixed in relation to the flow cell 22, and that is located at a distance of displacement from the plane of the sample stream in tape format 32 In the modality illustrated here, the standard autofocus (target 44) is applied directly to the flow cell 22, at a location that is visible in an image collected through the viewing port 57 by a high resolution optical imaging device. (not shown). The flow cell 22 can be constructed of a first layer or upper section 22a and a second layer or lower section 22b. A transparent or glass window panel 60 is fixed or integral with the first section 22a. Panel 60 can define at least a portion of the sample flow path within the flow cell. The light from the light source 42 can travel through an aperture or passage of the autofocus pattern 44 in order to illuminate the particles of the sample flowing within the flow stream 32.
[000117] In some cases, the thickness of the panel 60 can have a value within a range from about 150 μm to about 170 μm. As noted above, panel 60 can define or form part of the flow path or coating channel (for example, PIAOL). Using a thin panel 60, it is possible to place the microscope objective very close to the sample fluid strip and, consequently, obtain highly enlarged images of particles that flow along the flow path.
[000118] Figure 3A represents the aspects of a flow cell modality, where the distance between the image axis 355 and the portion of the distal transition zone 316 is about 8.24 mm. The distance between the distal portion of the transition zone 316 and the outlet opening of the cannula 331 is about 12.54 mm. The distance between the cannula outlet port 331 and the liner fluid inlet 301 is about 12.7 mm. The distance between the cannula outlet port 331 and a portion of the proximal transition zone 318 is about 0.73 mm. Figure 3B represents the aspects of a flow cell modality, where the exit port of the cannula has been transferred to a more distal location in relation to the transition zone, in comparison with the mode of Figure 3A. As shown here, the distal end of the cannula is advanced to the narrowing transition zone of the flow cell, and a distance between the imaging axis 355 and the portion of the distal transition zone 316 is within a range from about from 16 mm to about 26 mm. In some cases, the distance between the image axis 355 and the portion of the distal transition zone 316 is about 21 mm.
[000119] With reference again to Figure 1, the internal contour of the flow cell (for example, in the transition zone 21) and the flow rates of PIOAL and of the sample can be adjusted in such a way that the sample is formed in a current in tape format 32. The stream may be approximately as thin as or even thinner than the particles that are involved in the tape-shaped sample stream. White blood cells can have a diameter of about 10 μm, for example. By providing a ribbon-shaped sample stream, less than 10 μm thick, cells can be oriented when the ribbon-shaped sample stream is extended by the coating fluid, or PIOAL. Surprisingly, stretching the ribbon-shaped sample stream along a narrowing flow path within the PIOAL layers of different viscosity from the ribbon-shaped sample stream, such as a higher viscosity, advantageously tends to align the non-spherical particles in a plane substantially parallel to the direction of flow and apply forces on the cells, improving the focused contents of the intracellular structures of the cells. The optical axis of the high resolution optical imaging device 24 is substantially normal (perpendicular) to the plane of the ribbon-shaped sample stream. The linear velocity of the tape-shaped sample stream at the image point can be, for example, 20-200 mm / second. In some embodiments, the linear speed of the ribbon-shaped sample stream can be, for example, 50-150 mm / second.
[000120] The thickness of the sample stream in tape format can be affected by the relative viscosities and flow rates of the sample fluid and PIOAL. The sample source 25 and / or the PIOAL source 27, for example, comprising precision displacement pumps, can be configured to supply the sample and / or the PIOAL at controllable flow rates to optimize the dimensions of the sample stream in tape 32, that is, as a thin tape, at least as wide as the field of view of the high resolution optical imaging device 24.
[000121] In one embodiment, the PIOAL source 27 is configured to deliver the PIOAL to a predetermined viscosity. The viscosity can be different from the viscosity of the sample, and can be greater than the viscosity of the sample. The viscosity and density of the PIOAL, the viscosity of the sample material, the flow rate of the PIOAL and the flow rate of the sample material are coordinated to maintain the tape-shaped sample stream at an offset distance from the autofocus pattern , and with predetermined dimensional characteristics, such as an advantageous tape-shaped sample stream thickness.
[000122] In a practical modality, the PIOAL has a linear velocity greater than the sample and a viscosity greater than that of the sample, thus extending the sample on the flat ribbon. The viscosity of PIOAL can be up to 10 centipoises.
[000123] With reference also to Figures 2 and 3, the internal flow path of the flow cell narrows downstream from the injection point of the ribbon-shaped sample stream to the PIOAL, to produce a thick sample flow in ribbon format, for example, up to 7 μm, and / or the internal flow path produces a sample stream width of 500 - 3,000 μm. In exemplary modalities, as shown in Figure 1, the internal flow path of the flow cell begins a narrowing transition zone upstream from the injection point of the sample flow to the PIOAL.
[000124] In another embodiment, the internal flow path narrows to produce a tape-shaped sample stream thickness of 2 - 4 μm thick, and / or the internal flow path results in the sample-shaped stream stream 2000 mm wide tape. These dimensions are particularly useful for hematology. The thickness of the chain, in this case, is less than the diameter of some particles, such as red blood cells in their relaxed state. Consequently, these particles can become reoriented to return their widest dimension to the image axis, which is useful in revealing distinctive features.
[000125] The linear speed of the sample stream in tape format can be limited enough to prevent the motion blur of the scanned image in the image exposure time of the photodetector matrix. The light source can optionally be a strobe light that is flashed to apply high incident amplitude for a short time. As the autofocus pattern 44 and the image are in the same field of view, the light source is configured to illuminate the ribbon-shaped sample stream and the autofocus pattern simultaneously. However, in other modalities, the field of view for imaging and auto focus may be different, for example, illuminated and / or imaged separately.
[000126] The developments in question have aspects of method as well as equipment. A method of focusing a visual analyzer comprises focusing a high resolution optical imaging device 24, which can be a high resolution digital optical imaging device or the digital image capture device, in a focus pattern. fixed 44 relative to a flow cell 22, the autofocus pattern 44 being located at a displacement distance 52 from a ribbon-shaped sample stream 32. The high resolution digital optical imaging device 24 has a lens with an optical axis, which intersects the ribbon-shaped sample stream 32. A relative distance between the objective and the flow cell 22 is varied by the operation of a motor unit 54, while the distance along of the optical axis between the high resolution optical imaging device and the optimal focus point is known. The high resolution digital optical imaging device is configured to resolve and collect a scanned image in a photodetector array. The motor unit is operated to focus the autofocus pattern in an autofocus process. The motor unit is then operated across the travel distance, thus focusing the high resolution optical imaging device on the ribbon-shaped sample stream.
[000127] The method can further include the formation of the sample stream in tape format to a tape format. The ribbon format is presented so that the optical axis of the high resolution optical imaging device is substantially perpendicular to the ribbon-shaped sample stream, this is normal to the plane of the ribbon-shaped stream.
[000128] Figure 4 represents aspects of a 400 system for imaging particles in a blood fluid sample. As shown here, system 400 includes a fluid sample injection system 410, a flow cell 420, and an image capture device 430 and a processor 440. The flow cell 420 provides a flow path 422 that transmits a flow of the coating fluid, optionally in combination with the sample fluid. According to some embodiments, the sample fluid injection system 410 may include or be coupled with a cannula or tube 412. The sample fluid injection system 410 may be in fluid communication with the flow path 422, and may operate to inject fluid sample 424 through a distal outlet port 413 of the cannula 412 and to a flow coating fluid 426 within the flow cell 420 to provide a stream of sample fluid 428. For example, the processor 440 may include or be in operational association with a storage medium having a computer application that, when run by the processor, is configured to cause the sample fluid injection system 410 to inject sample fluid 424 into the flowing coating 426. As shown here, coating fluid 426 can be introduced into flow cell 420 by a coating fluid injection system 450. For example, the process 440 may include or be in operational association with a storage medium having a computer application that, when run by the processor, is configured to cause the sample fluid injection system 450 to inject coating fluid 426 into the cell flow 420.
[000129] The sample fluid stream 428 has a first thickness T1 adjacent to the injection tube 412. The flow path 422 of the flow cell has a decrease in the size of the flow path such that the thickness of the fluid stream sample 428 decreases from the first thickness T1 to a second thickness T2 adjacent to an image capture location 432. The image capture device 430 is aligned with the image capture location 432 to form the image of a first plurality of particles from the first fluid sample at image capture site 432 of flow cell 420.
[000130] Processor 440 is coupled with the fluid sample injector system 410, the image capture device 430 and optionally the coating fluid injection system 450. Processor 440 is configured to stop injection of the first sample fluid into the flowing coating fluid 426 and start injection of the second sample fluid into the flowing coating fluid 426 in such a way that the sample fluid transients are initiated. For example, processor 440 may include or be in operational association with a storage medium having a computer application that, when run by the processor, is configured to cause the sample fluid injection system 410 to inject the second sample fluid. sample to the coating fluid flowing 426 so that the sample fluid transients are initiated.
[000131] Additionally, processor 440 is configured to start capturing an image of a second plurality of particles from the second sample fluid at image capture location 432 of flow cell 420 after the sample fluid transients and within 4 seconds of imaging the first plurality of the particles. For example, processor 440 may include or be in operational association with a storage medium having a computer application that, when run by the processor, is configured to cause the image capture device 430 to start capturing an image from a second plurality of particles from the second sample fluid at the image capture site 432 of the flow cell 420 after the sample fluid transients and within four seconds of imaging the first plurality of particles.
[000132] As shown in the flow cell embodiment shown in Figure 4A, a decrease in the size of the flow path (for example, in the transition zone 419a) can be defined by the opposite walls 421a, 423a of the flow path 422a. Opposite walls 421a, 423a can tilt radially inward along the flow path 422a, generally symmetrical over a transverse plane 451a which bisects the fluid stream of sample 428a. The plane 451a can bisect the sample stream 428a, where the sample stream has a first thickness T1, at a location where the sample stream 428a exits a distal portion 427 of the sample cannula or injection tube 412a. Similarly, the plane 451a can bisect the sample stream at 428a where the sample stream has a second thickness T2, at a location where the sample stream 428a passes the image capture location 432a. According to some modalities, the first thickness T1 has a value of about 150 μm and the second thickness T2 has a value of about 2 μm. In such cases, the compression ratio of the sample tape current is 75: 1. According to some modalities, the first thickness T1 has a value within a range from about 50 μm to about 250 μm and the second thickness T2 has a value within a range from about 2 μm to about 10 μm. As the fluid in the sample stream flows through the flow cell, the tape tapers as it accelerates and is extended. Two flow cell features can contribute to the thinning of the sample fluid strip. First, a speed difference between the coating fluid envelope and the sample fluid tape can work to reduce the thickness of the tape. Second, the tapered geometry of the transition zone can work to reduce the thickness of the tape.
[000133] Typically, the first thickness T1 is much larger than the size of the sample particles and therefore the particles are contained entirely within the sample strip stream. However, the second thickness T2 may be smaller than the size of certain particles in the sample, and therefore these particles may extend out of the sample fluid and into the surrounding coating fluid. As shown in Figure 4A, the current from the sample strip can generally flow along the same plane as it exits the cannula and travels towards the image capture location.
[000134] The flow cell can also provide a separation distance 430a between the distal cannula portion 427 and the imaging site 432a. According to some embodiments, the distal portion 427a of the sample fluid injection tube 412a can be positioned at an axial separation distance 430a from the image capture location 432a, where the axial separation distance 432a has a value of about 21 mm. In some cases, the axial separation distance 430a has a value within a range from about 16 mm to about 26 mm.
[000135] The axial separation distance 430a between the image capture location and the cannula outlet port can impact the transition time for the fluid sample as the fluid travels from the outlet port to the capture site of image. For example, a relatively shorter axial separation distance 430a can contribute to a shorter transition time, and a relatively longer axial separation distance 430a can contribute to a longer transition time.
[000136] The position of the outlet port in the distal portion of the cannula 427a in relation to the transition zone of the flow path 419a, or in relation to the proximal portion 415a of the flow zone transition zone 419a, can also be inference in time transition to the sample fluid as the fluid travels from the outlet port to the image capture location. For example, the coating fluid may have a relatively slower speed in the proximal portion 415a, and a relatively fast speed in a location between the proximal portion 415a and the distal portion 416a. Consequently, if the cannula outlet port at the distal portion 427a is positioned at the proximal portion 415a, it will take a long period of time for the sample fluid to reach the imaging location, not just because the travel distance is longer , but also because the initial velocity of the sample fluid after it leaves the distal cannula port is slower (due to the slower rate of the coating fluid). In other words, the longer the sample fluid is present in the thicker portion (for example, near the proximal portion 415a) of the flow cell, the longer it takes the sample to reach the image capture location. On the other hand, if the cannula exit port in the distal portion 427a is positioned distal to the proximal portion 415a (for example, in a central location between the proximal portion 415a and distal portion 416a, as shown in Figure 4A), it will it takes a shorter period of time for the sample fluid to reach the image capture location, not only because the travel distance is shorter, but also because the initial velocity of the sample fluid after it leaves the distal cannula port is faster (due to faster coating fluid speed). As discussed here in another section, the coating fluid is accelerated as it flows through transition zone 419a, due to the narrowing of the cross-sectional area of zone 419a.
[000137] According to some modalities, with a shorter transition time, more time is available for image collection at the image capture location. For example, as the duration of the transition time from the distal tip of the cannula to the image area decreases, it is possible to process more samples in a given period of time and, relatively, it is possible to obtain more images in a given period of time. time (for example, images per minute).
[000138] While there are advantages associated with positioning the distal portion of the cannula exit port 427 closer to the image capture site 432a, it is also desirable to maintain a certain distance between the port and the capture site. For example, as shown in Figure 3, an optical lens or front lens of an imaging device can be positioned on the seat 58 of the flow cell 22. If the outlet port 31 of the cannula is very close to the seat 58, then the Sample fluid may not be stabilized enough after being injected into the coating fluid to provide desired imaging properties at the image capture site. Similarly, it may be desirable to keep the tapered transition region 21 at a distance from the viewing area 23, so that the tapered region does not interfere with the positioning of the seat 58, which receives the lens from the viewing device. image capture.
[000139] With continued reference to Figure 4A, the downstream end 427a of the sample fluid injection tube 412a can be positioned distal to a proximal portion 415a of the flow path transition zone 419a. Similarly, the downstream end 427a of the sample fluid injection tube 412a can be positioned proximal to a distal portion 416a of the flow path transition zone 419a. Consequently, according to some embodiments, the sample fluid can be injected from the injection cannula 412a and into the flow cell at a location within the transition zone 419a.
[000140] According to some modalities, the symmetry in decreasing the size of the flow path (for example, in the transition zone of the flow path 419a) operates in order to limit the misalignment of particles in the fluid sample of blood. For example, such symmetry can be effective in limiting the misalignment of the orientation of the imaging of red blood cells in the blood fluid sample to less than about 20%.
[000141] According to some modalities, the methods disclosed here are operable for the signaling rate during the analysis of the blood count to below 30%, 29%, 28%, 27%, 26%, 25%, 24% , 23%, 22%, 21%, 20%, 19%, 18%, 17%, 16%, 15%, 14%, 13%, 12%, 11%, 10%, 9%, 8%, 7 %, 6% or 5% of the samples.
[000142] According to some modalities, the 432a image capture site has a 433a field of view between about 150 μm x 150 μm and 400 μm x 400 μm. In some cases, the image capture site 432a has a field of view 433a of about 275 μm x 275 μm. In some cases, the field of view can be defined in terms of length times width. If expressed as a surface area, a field of view of 275 μm x 275 μm has an area of 75,625 μm2. According to some modalities, the field of view can be determined by the lens of the imaging device and its magnification. In some cases, the field of view may correspond to the extent of the field (area) that is imaged by the optical collection elements (for example, objective, tube lens, and camera). In some cases, the field of view is much smaller than the viewport of the transparent area at the image capture location.
[000143] Figures 4A-1 and 4A-2 illustrate the effects of hydrofocalization on the sample stream as it travels from the cannula exit port to the image capture location. As shown in Figure 4A-1, the sample stream can have a height H (S) of about 150 μm and a width W (S) of about 1350 μm. In addition, the PIOAL coating flow can have an H (P) height of about 6000 μm and a W (P) width of about 4000 μm. After hydrofocusing, as shown in Figure 4A-2, the sample stream can have a height H (S) of about 2 μm and a width W (S) of about 1350 μm. In addition, the PIOAL coating stream can have a height H (P) of about 150 μm and a width W (P) of about 4000 μm. In one embodiment, the cross-sectional area of the PIOAL coating current at the cannula outlet is 40 times larger than the cross-sectional area near the image capture site.
[000144] According to some modalities, it may be useful to determine the cross section of the flow cell channel at the image capture location. This can correspond to the height of the H (P) coating current of about 150 μm and a width W (P) of about 4000 μm as shown in Figure 4A-2. It may also be useful to determine the volumetric flow rate of the combined coating and sample fluid flowing through the flow cell at the image capture site. When the cross-sectional area and flow are known, it is possible to determine the speed of the sample fluid and the combined coating at the image capture location.
[000145] According to some modalities, the sample flow and the coating fluids through the flow cell can be approximated by a parallel plate profile model. Similarly, the flow in the center of the sample fluid stream (for example, as shown in Figure 4A-2), can be about 1.5 times the average flow of the combined fluid and sample stream.
[000146] According to some modalities, the cross-sectional area of the sample flow at the cannula outlet (for example, W (S) x H (S) in Figure 4A-1) is 40 times larger than the area of the transverse section - sample flow salt at the image location (for example, W (S) x H (S) in Figure 4A-2). The volumetric flow of the coating fluid in the imaging area can be about 45 μL / second. The volumetric flow rate of the sample fluid in the imaging area can be about 0.232 μL / second. In some cases, the cross-sectional area of the combined sample and coating streams at the imaging site is 600,000 μm2. In some cases, the average speed of the flow current at the imaging site is 75 mm / second.
[000147] The flow or speed can be determined as the rate that results in transparent and concentrated cellular images. The exemplary flow rates and velocities were discovered based on flows of the two samples that were observed to reach certain shapes or characteristics of the sample flow stream ribbon at the imaging site. For example, at a flow rate of about 75 mm / s (or within a range of 20-200 mm / s), the cells do not flow very slowly so that there are overlays of cells in consecutive images, and the cells do not flow very fast so that ghosting effects are created (blurry image). Similarly, by avoiding excessively high flow rates, it is possible to conserve more reagent and sample. According to some modalities, an optimal or desired linear speed can be achieved both by changing the volumetric flow (pump rate) and by the cannula shape.
[000148] The flow rate of the sample stream through the image capture zone may also be related to the performance of the image capture device in relation to the function of the flow cell. For example, if the sample stream flows very quickly, it may be difficult to obtain transparent images of particles contained in the sample (for example, the shutter speed of the image capture device may be very low, thus producing blurry image). Similarly, if the sample stream flows very slowly, the image capture device can take consecutive images of the same particle (for example, the same particle remains in the capture structure for two image captures). In some embodiments, the speed of the sample tape can be modulated (for example, by adjusting any of a variety of flow cell operating parameters) in relation to the image capture rate, so that there is minimal flow between the catches of the structure and, consequently, a high percentage of the sample is imagined.
[000149] According to some modalities, the particle analysis system and associated components can be configured so that as the coating fluid and fluid sample flow through the flow cell, the coating fluid can flow at a coating fluid volumetric rate of 45 μL / s and the fluid sample can flow at a fluid sample volumetric flow rate of 0.232 μL / s (or within a range of 0.2 to 0.35 μL / s). In some cases, the ratio between the flow of the coating fluid and the flow of the sample fluid is about 200. In some cases, the ratio between the flow of the coating fluid and the flow of the sample fluid has a value within of a range from about 70 to 200. In some cases, the ratio between the flow of the coating fluid and the flow of the sample fluid is about 193. In some cases, the ratio between the flow of the coating fluid coating and flow rate of the sample fluid is about 70. In some cases, a ratio between the volume of the coating fluid and the volume of the fluid sample flowing within the flow cell may be within a range of 25: 1 to 250: 1.
[000150] According to some modalities, the system and associated components can be configured so that the coating fluid and the fluid sample flow through the flow cell 420, the coating fluid can flow at a fluid speed of 75 mm / s coating before the imaging area and the fluid sample can flow at a fluid sample rate between 130 mm / s before the imaging area. In some cases, a ratio between the volume of coating fluid and the volume of the fluid sample flowing within the flow cell may be within the range of 100: 1 to 200: 1.
[000151] In some cases, a flow cell may have a minimum compression ratio of about 50: 1 and a maximum compression ratio of about 125: 1. In some cases, the minimum compression ratio can be around 30: 1 or 20: 1. This compression ratio refers to the ratio of the thicknesses of the flow current H (S): H (S) when comparing Figure 4A-1 with Figure 4A-2. This compression ratio can be influenced by a combination of geometric compression (for example, the ratio of coating fluid thicknesses H (P): H (P) when comparing Figure 4A-1 with Figure 4A-2, which also it can generally correspond to the dimensions of the tapering transition zone of narrowing of the flow cell 419a shown in Figure 4A) and a hydrodynamic compression (for example, also corresponding to a difference in speed). According to some modalities, the geometric compression ratio is about 40: 1.
[000152] The decrease in the size of the flow path, corresponding to the transition zone, can be defined by a proximal portion of the flow path having a proximal thickness or height, and a distal portion of the flow path having a distal thickness or height. which is less than the proximal thickness or height. For example, as shown in the partial view of Figure 4B, the transition zone 419b of the flow path may have a length L between a proximal portion 415b and a distal portion 416b, where the proximal portion 415b has a proximal height 417b and the distal portion 416b has a distal height 418b. As noted in another section of the present invention, the shape or contour of the transition zone can be curved or smooth, and, for example, can be provided in the shape of an S curve or a tangent curve. According to some modalities, the proximal height 417b has a value of about 6000 μm. In some cases, the proximal height 417b has a value within a range from about 3000 μm to about 8000 μm. According to some modalities, the distal height 418b has a value of about 150 μm. In some cases, the distal height 418b has a value within a range from about 50 μm to about 400 μm.
[000153] The geometry of the transition zone 419a can provide a first angle α1 between the first flow path contour 403b and the transverse bisection plane 451b, and a second angle α2 between the second flow path contour 404b and the plane bisection cross section 451b. In some cases, angle α1 is about 45 degrees and angle α2 is about 45 degrees. In some cases, the angle α1 has a value within a range from about 10 degrees to about 60 degrees. In some cases, the angle α2 has a value within a range from about 10 degrees to about 60 degrees. According to some modalities, the angles α1 and α2 have the same value. Angles α1 and α2 can be selected in order to maintain a laminar flow or minimize the turbulence of the sample fluid, as it travels from the proximal portion 415b to the distal portion 416b, which in turn can improve alignment of the particles in the sample along the transverse plane 451b. As noted above with reference to Figure 4A, the proximal and distal contours or portions of the transition zone can be curved or smooth, rather than angled.
[000154] As shown in Figure 4K, a strip of sample stream R flowing through a 432k image capture location of a 420k flow cell can have a T thickness of about 2 μm. In some cases, the T thickness of the sample stream tape can be up to about 3 μm. Typically, cells or particles that are less than the thickness of the sample stream will be contained within the tape. An exemplary red blood cell (RBC) can be present as a biconcave disk and can have a diameter D of between about 6.2 μm and about 8.2 μm. In addition, an exemplary red blood cell can have a maximum T1 thickness between about 2 μm and about 2.5 μm and a minimum T2 thickness between about 0.8 μm and about 1 μm. In some cases, red blood cells can be up to about 3 μm thick. Exemplary human platelets can vary in size, and can also have a thickness or diameter of about 2 μm. Although not shown here in scale, the flow cell can define a thickness of the flow path H having a value of about 150 μm, at the image capture location. In some cases, the flow path thickness F has a value between 50 μm and 400 μm. This thickness of flow path F can also correspond to the distal height 418b of the distal portion 461b shown in Figure 4B.
[000155] As shown in Figure 4K, the ratio between the thickness T of the sample fluid stream and the particle thickness (red blood cells) is about 1: 1. According to some modalities, a ratio between the thickness T of the sample fluid stream at the image capture site and a size of one of the particles is within a range of 0.25 to 25. In some cases, the thickness T can have a value within a range of 0.5 μm to 5 μm. A viscosity differential between the coating fluid and the sample fluid can be selected in order to achieve a desired positioning of the sample stream from the strip within the flow cell.
[000156] As discussed in another section of the present invention, as well as copending US Patent Application No., the viscosity differences between the sample tape fluid R and the coating fluid can operate to align or orient the particles in the stream. sample, for example, red blood cells, along the flow direction. When so aligned, as shown in Figure 4K, the imaging device or camera can take images of the red blood cells in such a way that they appear round, because the main surface of the blood cell faces the camera. In this way, the red blood cells assume an alignment that presents a low resistance in relation to the flow. Consequently, the relative viscosity characteristics of the coating fluid and the fluid sample can contribute to a high percentage or number of red blood cells facing the chamber, thus improving the evaluation capacity of the particle analysis system.
[000157] According to some modalities, the viscosity characteristics of the coating fluid operate to limit the misalignment of particles in the blood fluid sample. For example, viscosity differentials can be effective in limiting the misalignment of the imaging orientation of red blood cells (erythrocytes) in the blood fluid sample to less than about 10%. That is, 90 or more erythrocytes out of 100 erythrocytes in a sample can be aligned so that their main surfaces face the imaging device. A symmetrical narrowing transition zone can provide a value of 20%. According to some modalities, the coating fluid has a refractive index similar to that of water (ie n = 1.3330). In some cases, the coating fluid has a water content of about 89%. In addition to the alignment effects observed as a result of the viscosity differential, the alignment effects are also observed as a result of a bilateral tapered transition zone. In some cases, it is observed that a bilateral tapered transition zone (ie symmetrical) is twice as effective for aligning the particles, compared to an asymmetric tapered transition zone model.
[000158] The efficient alignment of erythrocytes can contribute to a better diagnosis. In some cases, the shape of the imaged erythrocytes can be used to determine whether a patient from whom the sample is obtained has a particular disease or physiological condition. For example, patients with sickle cell disease have blood cells that are abnormally shaped (that is, sickle-shaped). Consequently, by obtaining high-quality images of the aligned red blood cells, it is possible to ensure an accurate diagnosis. Other variations in the shape of red blood cells, for example, red blood cells having a thin peripheral area and a large central flat area, through which the red blood cell appears to have the profile of a bicycle tire, can be imagined effectively using the present alignment techniques. Similarly, red blood cells with a small central portion and a thick peripheral area, through which the red blood cell appears to have the profile of a truck tire, can be imaged for diagnostic purposes. The improved imaging techniques disclosed herein are also useful for the evaluation of other characteristics of red blood cells, such as hemoglobin content, iron content, and the like.
[000159] Without sticking to any particular theory, it is believed that a viscosity differential between the viscosity of the coating fluid and the viscosity of the sample fluid produces a modified parabolic profile, the profile being generally parabolic and having a central impact, corresponding to a central area of the flow, where the acceleration is increased, and the central impact contributes to the alignment of sample particles or organelles between the particles. According to some modalities, the difference in speed between the sample tape and the coating and the difference in viscosity generate shear forces to increase the alignment of organelles or intracellular particles. Exemplary aspects of the parabolic profile of the coating fluid are discussed in the corresponding US patent application no. , the content of which is incorporated herein by reference.
[000160] White blood cells are typically larger than red blood cells and platelets. For example, exemplary neutrophils and eosinophils can have a diameter of between about 10 μm and about 12 μm. Exemplary basophils can have a diameter of between about 12 μm and about 15 μm. Exemplary lymphocytes (small) can have a diameter of between about 7 μm and about 8 μm, and exemplary lymphocytes (large) can have a diameter of between about 12 μm and about 15 μm. Exemplary monocytes can have a diameter of between about 12 μm and about 20 μm. The configuration of the particle analysis system, including the interaction between the coating fluid and the sample fluid strip as they pass through the flow cell, can operate to compact white blood cells as they travel through the site image capture 432l, as shown in Figure 4L. Consequently, for example, a central portion of the white blood cell (WBC) can be positioned inside the sample fluid strip R, and the peripheral portions of the white blood cell can be positioned inside the coating fluid. Consequently, as the white blood cell is transported through the flow cell by the tape, the sides of the white blood cell can extend into the coating fluid.
[000161] According to some modalities, differences in viscosity between the coating fluid and the sample fluid can operate to align the organelles or other intracellular resources that are present inside the cells, such as white blood cells. Without sticking to any particular theory, it is believed that the shear forces associated with the differential viscosity between the coating fluid and the sample fluid can act on white blood cells in order to align intracellular resources . In some cases, the shear forces associated with the speed differentials between the coating fluid and sample fluid can contribute to such an alignment. These alignment effects can be impacted by a size differential between the particles and the sample fluid strip as well. For example, when the particle portions extend out of the sample fluid strip and into the surrounding coating fluid, the shear forces associated with the difference in viscosity can have a pronounced effect on the alignment of intracellular features.
[000162] As shown in Figure 4L, portions of a cell, such as a white blood cell, may extend into the lining fluid. The embodiments of the present invention encompass coating fluid compositions that do not fragment or lyse the cell, or otherwise, compromise the integrity of the outer cell membrane when the cell is exposed to the coating fluid. A viscosity agent in the coating fluid can operate to maintain the viability of cells in the sample fluid stream, so as to leave the structure (eg, shape) and content (eg, nucleus) of the cells intact when the membrane or cell wall crosses an interface between the sample fluid strip and the coating fluid envelope or otherwise extends from the sample fluid stream to the flowing coating fluid.
[000163] Often, there are compressive forces that act on the cells or particles as they flow within the sample fluid strip along the flow cell. Consequently, the cells may come into contact with the coating fluid while the cells are in a compressed state or are otherwise subjected to compressive forces as a result of a narrowing transition zone. The coating fluid viscosity agent can operate to protect the compressed cells from being fragmented or destroyed when they emerge from the thin sample fluid strip and become exposed to the viscous coating fluid, at least until the cells reach the image capture location. Consequently, the viscosity agent composition of the coating fluid can operate as a cell protector, at the same time, also improving the alignment of the particles or intraparticle content.
[000164] With reference to Figures 4K and 4L, in some cases, the cell or particle portions may extend out of the thin sample fluid strip R and into the surrounding coating fluid. As discussed in copending US Patent Application No., the coating fluid may contain cell protectors that inhibit or prevent the coating fluid from breaking or lysing the cells or particles. For example, the coating fluid may contain cell protectors that preserve the structural integrity of the cell walls as the cells are exposed to the chemical environment of the coating fluid. Similarly, cell protectors can also operate to preserve the structural integrity of cell walls as the cells experience any shear forces induced by the flow cell geometry, and a difference in speed and / or viscosity between the fluid sample and coating fluid. Similarly, protectors can protect cells or particles from forces resulting from the difference in speed between the sample fluid and the coating fluid. In this way, the cells maintain their viability as they reach the site of image capture.
[000165] Shear forces can be significant at the interface between the sample fluid strip and the coating fluid envelope. According to some modalities, the flow within the flow path of the flow cell can be characterized by a parabolic flow profile. According to some modalities, particles that are large enough will be subjected to a certain amount of shear force, even when those particles are completely contained within a single fluid phase (that is, either inside the envelope of coating fluid, or alternatively, inside the sample fluid strip).
[000166] In some cases, the speed of the coating fluid may be different from the speed of the sample fluid. For example, the coating fluid may be traveling at 80 mm / second and the sample fluid may be traveling at 60 mm / second. Consequently, in some cases, the fluid sample exits the distal cannula port at a speed of the sample fluid, which is slower than the speed of the coating fluid in the surrounding envelope. Consequently, the coating fluid can operate to drag the sample fluid along the flow path of the cannula, thereby accelerating the sample fluid and reducing the thickness of the sample fluid strip. The sample fluid tape maintains total mass and volume, so that as it travels faster it becomes thinner. According to some modalities, both the coating fluid and the sample fluid have a speed between about 20 and 200 mm / second at the image capture site.
[000167] Typically, the sample fluid velocity increases as the sample fluid travels from the cannula outlet port to the image capture location. In some cases, the speed of the sample fluid at the imaging site is 40 times the speed of the sample fluid as it exits the cannula port in the distal cannula portion. According to some modalities, the decrease in the cross-sectional area of the sample tape is linear with the increase in speed. According to some modalities, if the coating speed at the cannula outlet is greater than the speed of the sample tape this will also increase the final speed of the sample tape in the imaging area.
[000168] The coating fluid can operate to apply significant shear forces to the sample fluid strip and to particles within the sample fluid strip. Some forces are parallel to the direction of flow, and particles can also encounter forces that are perpendicular to the direction of flow. Often, as the coating fluid and sample fluid approach the image capture location or zone, the sample and coating fluids travel at, or close to, the same speed. Consequently, the contour or interface between the sample and coating fluids as they pass through the image capture site, may exhibit lower shear forces, compared to the contour or interface at the distal cannula outlet port or in the imaging zone. tapered transition. For example, in the tapered transition zone, the contour or interface between the coating fluid envelope and the sample fluid strip may be in transition, such that the sample strip that is initially slower and thicker becomes it becomes faster and thinner, and the particles in the sample fluid become more aligned. In other words, shear forces can be prominent in the tapered transition zone, and can dissipate to the image capture location. The shear forces at the image capture site can be represented by a parabolic profile, and can be much less than the shear forces in the tapered transition zone. Consequently, cells or particles may experience higher shear forces as they pass through the transition zone, and lower shear forces as they pass through the image capture site. According to some modalities, the difference in viscosity between the sample and coating fluids can put the red blood cells in alignment and thus in focus. According to some modalities, the difference in viscosity between the sample and coating fluids can put the white blood cell organelles in alignment and thus in focus. Similarly, improved imaging results can be obtained for cell components and organelles that are aligned and brought into focus, resulting from the geometric narrowing of the current and the difference in speed between the sample and coating fluids.
[000169] As noted in another section of the present invention, and with reference to Figures 4K and 4L, as the coating fluid and sample fluid R flow through a reduction in the size of the flow path or transition zone of a flow cell, and toward a 432k or 432l imaging site, a viscosity hydrofocusing effect induced by an interaction between the coating fluid and the sample fluid R associated with a viscosity difference between viscosity of the coating fluid and the viscosity of the sample fluid, in combination with a geometric hydrofocalization effect induced by an interaction between the coating fluid and the sample fluid R associated with reducing the size of the flow path or transition zone, provides a target imaging state on at least some of the plurality of particles at the 432k or 432l imaging site.
[000170] In some cases, the embodiments of the present invention include compositions for use with a hematology system, as described here, as a coating or particle fluid and intracellular organelle alignment fluid (PIOAL). Such coating fluids or PIOALs are suitable for use in a visual analyzer of combined geometric hydrofocusing and viscosity. The PIOAL can operate to direct or facilitate the flow of a blood sample fluid of a given viscosity through a flow cell narrowing transition zone of the visual analyzer. The PIOAL can include a fluid that has a higher viscosity than the sample viscosity. A viscosity hydrofocalization effect induced by an interaction between the PIOAL fluid and the sample fluid associated with the viscosity difference, in combination with a geometric hydrofocalization effect induced by an interaction between the PIOAL fluid and the PIOAL fluid sample associated with the transition zone of the narrowing flow cell, can be effective in providing a target imaging state in at least some of the plurality of particles in a visual analyzer imaging site, maintaining the viability of the cells in the sample fluid of blood.
[000171] Figure 4M represents an exemplary 400 m neutrophil (a type of white blood cell) having internal organelles, such as lobes 410 m. As a result of the viscosity differential between the sample fluid and the coating fluid, the internal organelles can line up inside the cell, as indicated by Figure 4N. Consequently, intracellular organelles can be effectively imaged with a 430m image capture device, without the organelles overlapping each other. That is, instead of the lobes being stacked on top of each other as shown in Figure 4M, when viewed from the imaging or optical axis of the image capture device, the lobes are aligned and seated side by side as shown in Figure 4N . Consequently, the lobes can be viewed in the captured image more effectively. The internal alignment of the organelle is a surprising and unexpected result of the viscosity differential between the sample and coating fluids. Consequently, the improved imaging results corresponding to cell alignment and focus are achieved through the features of viscosity differential, hydrodynamic flow, and geometric compression.
[000172] As noted in another section of the present invention, and with reference to Figures 4M and 4N, as the coating fluid and sample fluid R flow through a reduction in the size of the path or transition zone of a flow cell, and towards an imaging location of a 430 m or 430n image capture device, a viscosity hydrofocalization effect induced by an interaction between the coating fluid and the sample fluid R associated with a difference of viscosity between the viscosity of the coating fluid and the viscosity of the sample fluid, in combination with a geometric hydrofocalization effect induced by an interaction between the coating fluid and the sample fluid R associated with reducing the size of the flow path or transition zone, provides a target imaging state on at least some of the plurality of particles at the imaging site. According to some modalities, the target image state may correspond to a distribution of image states.
[000173] In some cases, the target imaging state may involve an orientation of the target intraparticle structure (for example, alignment and / or position) in relation to a focal plane at the location of the imaging. For example, as shown in Figure 4N, the internal structures 410 m (for example, intracellular structure, organelle, lobe, or the like) can be oriented in relation to the F focal plane. In some cases, the target alignment involves an alignment of target intraparticle structure in relation to the focal plane F at the imaging site, similar to the particle alignment relationship shown in Figure 4K-3. In some cases, the target position involves a position of the target intraparticle structure in relation to a focal plane at the image location, similar to the particle position relationship shown in Figure 4K-1. In some cases, the target orientation of the intraparticle structure may include both a target alignment in relation to the focal plane and also a target position in relation to the focal plane. In some cases, the target imaging state may involve target deformation at the imaging site. For example, as shown in Figure 4N, the 400 m particle has a compacted shape, compared to the particle shape shown in Figure 4M. Consequently, it can be seen that the flow cell operation can produce a lateral compression effect on the particle shapes. Similarly, intraparticle resources can be positionally or directionally oriented (for example, aligned with respect to the focal plane F and / or plane of the ribbon flow) as the particle itself is compacted in shape. According to some embodiments, a difference in speed between the coating and sample fluids can produce friction within the flow stream, and a difference in viscosity between the coating and sample fluids can amplify the hydrodynamic friction.
[000174] Any of a variety of hematology or blood particle analysis techniques can be performed using images of the sample fluid flowing through the flow cell. Often, image analysis may involve determining certain parameters of cells or particles, or measuring, detecting, or evaluating certain resources of the cells or particles. For example, image analysis may involve the evaluation of cells or particle size, cell nucleus resources, cell cytoplasm resources, intracellular organelle resources and the like. Similarly, analysis techniques may cover certain methods of counting or grading or diagnostic tests, including white blood cell differentials (WBC). In some cases, images obtained using the flow cell can withstand a 5-part differential WBC test. In some cases, images obtained using the flow cell can withstand a 9-part WBC differential test. Similarly, with reference to Figure 4, processor 440 may include or be in operational association with a storage medium having a computer application that, when run by the processor, is configured to make the system 400 differentiate different types of cells based on the images obtained from the image capture device. Similarly, with reference to Figure 6B, processor 604b may include or be in operational association with a storage medium having a computer application that, when run by the processor, is configured to make the 600b system or the 642b system differentiate different types of cells based on the images obtained from the image capture device. For example, testing or diagnostic techniques can be used to differentiate various cells (for example, neutrophils, lymphocytes, monocytes, eosinophils, basophils, metamielocytes, myelocytes, promyelocytes and blasts).
[000175] Figure 4O shows a comparison between images obtained using PIOAL and images obtained using a non-PIOAL coating fluid. The use of PIOAL resulted in more cellular content in focus, such as the lobes, cytoplasm, and / or granules. In this example, a PIOAL comprising a viscosity agent (about 30% glycerol) was used to process the sample. The pH was adjusted to a pH of about 6.8 to 7.2 and the sample mixture was made isotonic (by 0.9% sodium chloride). The results presented here demonstrate the effectiveness of an exemplary PIOAL used in an image analyzer to align cells and intracellular organisms.
[000176] Figures 4P and 4Q show a comparison between images obtained using a standard coating fluid (Figure P upper and lower panels) and images obtained using an exemplary PIOAL fluid (Figure 4Q upper and lower panels). As shown here, the use of PIOAL has resulted in an improved RBC alignment. The sample was analyzed using an instrument focusing protocol (on an example target 44 as represented in Figure 1) and the target was brought into focus by a visual analyzer. The focusing system was then displaced by the displacement distance 52, resulting in particles in the ribbon-shaped sample stream that are in focus. The blood sample was previously diluted using a sample diluent. The sample flowed through a cannula and along a flow path of a flow cell, thus generating a ribbon-shaped sample stream (for example, 2 microns thick) that was between two layers of PIOAL or coating standard (on the controls). The visual analyzer then generates focused images of the particles in the ribbon-shaped sample stream (for example, at about 60 frames per second) to be used for the analysis. The blood sample is obtained from an individual and processed for analysis by the blood analyzer. Images of RBCs in a flow cell are captured while the sample is processed using a standard coating fluid or a PIOAL. The relative percentages demonstrate a significant improvement in the number of RBCs aligned based on image data (for example, 4P and 4Q). The result showed that PIOAL was effective in increasing the percentage of RBC alignment while flowing in the ribbon-shaped sample stream with the targeting protocols / instrument, as described here.
[000177] It was also observed that the implementation of PIOAL results in the best alignment was based on the use of increasing levels of glycerol (gly) in symmetrical and asymmetric flow cells.
[000178] These results provide evidence for the surprising and unexpected discovery that certain PIOAL compositions have unexpected properties of cell alignment and repositioning of intracellular structures when used to perform particle / cell analysis based on the image. Dynamic range extension
[000179] Figure 5 is a block diagram showing additional aspects of systems and methods for obtaining the dynamic range or detection range for the analysis of particles in blood samples, according to the modalities of the present invention. As shown here, at least one digital processor 18 is coupled to operate the motor unit 54 and to analyze the scanned image from the photodetector matrix as collected at different focusing positions in relation to the target autofocus pattern 44. The processor 18 is configured to determine a focusing position of the autofocus pattern 44, that is, for autofocusing on the target autofocus pattern 44 and thereby establish an optimal distance between the high resolution optical imaging device 24 and the autofocus pattern 44. This can be accomplished by image processing steps, such as applying an algorithm to assess the level of contrast in the image at a first distance, which can apply to the entire image or at least in an edge of the autofocus pattern 44. The processor moves engine 54 to another position and evaluates the contrast at that position or edge, and after two or more determinate iterations am an optimal distance that maximizes the focus accuracy in the auto focus pattern 44 (or can optimize the focus accuracy if moved to that position). The processor is based on the fixed spacing between the target autofocus pattern of the autofocus 44 and the ribbon stream sample stream, processor 18 then controls the motor 54 to move the high resolution optical imaging device 24 to the correct distance to focus on the 32-stranded sample stream. More specifically, the processor operates the engine to shift the distance between the high-resolution optical imaging device and the 32-stranded sample stream by the offset distance 52 (see Figure 1) by which the ribbon-shaped sample stream is shifted from the target 44 autofocus pattern. In this way, the high-resolution optical imaging device is focused on the ribbon-shaped sample stream .
[000180] According to some modalities, the visual analyzer 17 is an example analyzer 17 of Figure 1. The visual analyzer 17 can comprise at least one flow cell 22 and at least one imaging device 24 as an imaging device high resolution optical having an imaging sensor like a digital camera. The visual analyzer 17 can also comprise a sample injector 29. Sample injector 29 is configured to deliver sample 12 to at least one flow cell 22. Flow cell 22 defines an internal PIOAL flow path that narrows, for example, symmetrically in the direction of the flow. The flow cell 22 is configured to direct a flow 32 of the sample through a display zone in the flow cell 22.
[000181] Figure 5 illustrates autofocus and other aspects of digital imaging as described. Such techniques can be used in conjunction with blood cell equipment that is not based on imaging or perhaps less related to image than the described modalities, such as Coulter blood cell counters, also known as flow cytometers. Such counters are known for detecting and counting blood cells and particles in fluids, but generally not by imaging. In such a counter, a flow cell is arranged to carry a flow of enveloped particles in a fluid. The flow cell narrows to force the particles along the flow path in a single row. A pair of electrodes or other detectors that span the flow path produce a count by detecting a pulsed change in electrical impedance, or obstructing a light path between the light source and a photodetector when cells pass.
[000182] Flow cytometers are advantageous because a large number of cells or other particles can be counted, much greater than the number of cells that can be imaged practically in a visual counter. But flow cytometers are not as effective at distinguishing between cells by type, or they allow distinctions between normal and abnormal cells, or they distinguish clustered cells, such as platelet nodules, from discrete blood cells. When operating an analyzer, for example, the visual analyzer, as described, through a statistically significant number of image frames of a sample stream in a tape format, a proportional ratio or distribution of blood cell types can be measured. Proportional ratios determined from a visual analyzer, or a function thereof, are applied to blood cell counts, and higher numbers of blood cells are counted by the cytometer, although with less discrimination or no discrimination as to the type of cells, to provide an accurate total blood count, which exploits the peculiar advantages of both types of analyzers.
[000183] According to some modalities, particle counts can be inferred by applying an algorithm, for example, an algorithm based on a proportional particle count ratio. Figure 5 illustrates an exemplary equipment adapted for blood analysis. In some embodiments, the particle counter 15 and visual analyzer 17 can be connected in series instead of in parallel. The particle counter 15 can be, for example, a Coulter blood cell counter, which detects and counts blood cells and particles in fluids. In such a counter, a flow path (not shown) is arranged to carry a flow of enveloped particles in a fluid. The flow path narrows to force particles on the flow path in a single row. A pair of electrodes or other detectors that span the flow path produce a count by detecting a pulsed change in electrical impedance, or obstructing a light path between the light source and a photodetector when cells pass. The particle counter 15 is configured to count a large number of cells or other particles. But the particle counter 15 may not be able to distinguish between members in subcategories of cells and / or distinguish between normal and abnormal cells, or to distinguish clustered cells, such as platelet nodules, from discrete blood cells.
[000184] The visual analyzer 17 may also comprise at least one contact chamber 25 configured to supply at least one chemical substance comprising at least one of a diluent, a permeabilizing agent, and a contrast agent effective to generate visual distinctions for the categorization and / or sub-categorization of particles. For example, as shown with reference to Figures 1 and 5, the contacted sample is introduced into the flow cell through the sample injector 29, and an intracellular organelle alignment reagent or coating is introduced from the injector 27. A diluent can be used to dilute the sample to an appropriate concentration. A contrast agent and / or permeabilization agent is used to generate visual distinctions to categorize and / or sub-categorize particles. PIOAL is used to align certain types of cells or cellular structures in one direction for better imaging. In some embodiments, at least one chemical can be applied to contact a first sample, and then the treated sample is delivered over the visual analyzer 17. Treatment of the sample with at least the addition of at least one chemical can be carried out at room temperature. In some embodiments, such a treatment can be carried out at a temperature, such as 10, 15, 20, 25, 30, 35, 36, 37, 38, 38, 39, 40, 45, 46, 47, 48, 49 or 50 ° C. The treatment at a selected temperature can be carried out in an incubator that is separate from the visual analyzer 17, or in a visual analyzer 17, which is temperature controlled.
[000185] In some embodiments, the visual analyzer may have a contrast agent injector to place the sample in contact with a contrast agent and / or permeabilizing agent or surfactant. In other modalities, the sample can be placed in contact with the contrast agent, permeabilizing agent before injection into the visual analyzer. In other embodiments, the visual analyzer contains a heating element to heat the sample while in contact with the contrast agent and / or permeabilization agent, at a controlled temperature for a controlled time. The visual analyzer can also have a cooling element to cool the sample mixture after the heating step. Exemplary contrast agent methods and compositions that can be used for processing blood fluid samples are disclosed in Copending US Patent Application Number, the content of which is incorporated herein by reference.
[000186] When operating the visual analyzer 17 as described, through a statistically significant number of image frames of a sample stream in ribbon format, a proportional ratio of cells in categories and / or subcategories of cells can be determined by the processor 18. The proportional ratios determined from the visual analyzer 17 are applied to blood cell counts, and the largest numbers of blood cells are counted by the particle counter 15, although with less discrimination or no discrimination as to the members within a cell category and / or subcategory, to provide an accurate whole blood count that exploits the peculiar advantages of both the particle counter 15 and the visual analyzer 17.
[000187] In addition to providing accurate results, the equipment comprising a particle counter 15 and a visual analyzer 17 offers significant advantages for improving the speed of the analysis. In Figure 5, the precise results of counting different blood cells can be produced via screen 63. During an analysis process, the operator can interact with processor 18 via terminal 65. Previously, up to about 25% at 30% of the results were analyzed manually by producing slides with the contrast agent that were examined under the microscope by an operator. In comparison, an exemplary method using the equipment of the present invention comprises a CBC in a particle counter, and the categorization and / or subcategorization of blood cells according to some modalities. When operating the equipment described in this description, the images can be reviewed on the visual analyzer and the samples will require less frequent manual analysis.
[000188] The motor 54 may comprise a stepper motor oriented with slightly less precision than the distinctive features imaged by the digital image capture device, especially the aspects of blood cells. As long as the location of the high resolution optical imaging device 24 is set to locate the position of the optical lens within the width of the ribbon-shaped sample stream, the view of the cell / particle in the ribbon-shaped sample stream is focusing. The autofocus pattern can be located on an edge of a field of view of the high resolution optical imaging device or digital image capture device, and does not interfere with viewing for this reason.
[000189] Furthermore, when the high resolution optical imaging device is moved over the displacement distance and the autofocus pattern goes out of focus, the features that appear in focus are the blood cells, as opposed to the auto focus. According to some modalities, the autofocus pattern can be defined by formats in the field of view. The shapes are relatively thin, discrete shapes of a limited size, and therefore, after moving through the displacement distance, the shapes become substantially invisible in the scanned image when focused on the ribbon-shaped sample stream. A typical travel distance can be, for example, 50 to 100 μm in a flow cell sized for hematology imaging applications (blood cells). In some embodiments, the autofocus feature keeps the high resolution optical imaging device within 1 μm of the optimal focusing distance.
[000190] The flow rates of the internal contour of the flow cell and the PIO-AL and the sample can be adjusted in such a way that the sample is formed in a ribbon-shaped stream. The stream may be approximately as thin as, or even thinner than, the particles that are involved in the tape-shaped sample stream. White blood cells can have a diameter of about 10 μm, for example. By providing a ribbon-shaped sample stream, less than 10 μm thick, cells can be oriented when the ribbon-shaped sample stream is extended by the coating fluid, or PIOAL. Surprisingly, the stretching of the ribbon-shaped sample stream along a narrowing flow path within the PIOAL layers of different viscosity from the ribbon-shaped sample stream, such as a higher viscosity, advantageously tends to align the non-spherical particles in a plane substantially parallel to the direction of flow, and apply forces on the cells, improving the contents in focusing on intracellular cell structures. The optical axis of the high resolution optical imaging device 24 is substantially normal (perpendicular) to the plane of the sample stream in tape format. The linear velocity of the tape-shaped sample stream at the image point can be, for example, 20-200 mm / second. In some embodiments, the linear velocity of the ribbon-shaped sample stream can be, for example, 50-150 mm / second.
[000191] The thickness of the sample stream in tape format can be affected by the relative viscosities and flow rates of the sample fluid and PIOAL. The sample source 25 and / or the PIOAL source 27, for example, comprising precision displacement pumps, can be configured to supply the sample and / or the PIOAL at controllable flow rates to optimize the dimensions of the sample stream in tape 32, that is, as a thin tape, at least as wide as the field of view of the high resolution optical imaging device 24.
[000192] In one embodiment, the PIOAL source 27 is configured to deliver the PIOAL to a predetermined viscosity. The viscosity can be different from the viscosity of the sample, and can be greater than the viscosity of the sample. The viscosity and density of the PIOAL, the viscosity of the sample material, the flow rate of the PIOAL and the flow rate of the sample material are coordinated to maintain the tape-shaped sample stream at an offset distance from the autofocus pattern , and with predetermined dimensional characteristics, such as an advantageous tape-shaped sample stream thickness.
[000193] In a practical modality, the PIOAL has a linear velocity greater than the sample and a viscosity greater than that of the sample, thus extending the sample on the flat ribbon. The viscosity of PIOAL can be up to 10 centipoises.
[000194] In the modality shown in Figure 5, the same digital processor 18 that is used to analyze the digital pixel image obtained from the photodetector matrix is also used to control the autofocus engine 54. However, the image device - high resolution optical image 24 is not autofocused for each captured image. The autofocus process can be performed periodically or, for example, when the temperature or other changes in the process are detected by appropriate sensors, or when the image analysis detects a potential need for refocusing. It is also possible, in other modalities, to have the hematology image analysis performed by a processor and to have a separate processor, optionally, associated with its own photodetector matrix, arranged to handle the autofocusing steps for a fixed target. 44.
[000195] In Figure 5, at least one said digital processor 18 is configured to autofocus at programmed times or under programmed conditions or on user demand, and is also configured to perform categorization and subcategorization based on the image of the particles. Exemplary particles include cells, white blood cells, red blood cells and the like.
[000196] In one embodiment, said at least one digital processor 18 is configured to detect an auto focus reset signal. The autofocus reset signal can be triggered by a detected change in temperature, a decrease in the quality of the focus as discerned by the parameters of the pixel image data, time passing, or user input. Advantageously, it is not necessary to recalibrate in order to measure travel distance 52 to recalibrate. Optionally, autofocus can be programmed to recalibrate at certain frequencies / intervals between runs for quality control and / or to maintain focus.
[000197] The travel distance 52 varies slightly from one flow cell to another, but remains constant for a given flow cell. As a setup process when pairing an image analyzer with a flow cell, the displacement distance is first estimated and then during the calibration steps, in which the auto focus and imaging aspects are exercised, the distance of exact displacement for the flow cell is determined and introduced as a constant in the programming of the processor 18.
[000198] With reference to Figure 6, an exemplary equipment 10 for analyzing a sample 12 containing the particles includes a particle counter 15 having at least one detection range, an analyzer 17, and a processor 18 according to some modalities. The block diagram in Figure 6 is for the purpose of illustration. The particle counter 15, analyzer 17 and processor 18 may or may not be connected to each other. In some embodiments, the processor can be coupled to the particle analyzer and / or counter. In other embodiments, the processor may be a component of the analyzer and / or particle counter.
[000199] The particle counter 15 comprises at least one channel, and is configured to provide a particle count of at least one category and / or sub-category of particles. In some embodiments, a particle counter 15 comprises at least two channels for different categories and / or subcategories of particles. In some embodiments, particles are counted by detecting electrical impedance or scattering light from the sample. An example of a suitable particle counter 15 includes, but is not limited to, a flow cytometer. In some embodiments, detection can occur in each of a plurality of channels responsive to different physical properties, either simultaneously or sequentially.
[000200] Analyzer 17 is configured to differentiate between different categories and / or subcategories and corresponding members of each category and / or subcategory of particles. Examples of a suitable analyzer 17 include, but are not limited to, a visual analyzer, a digital camera, or any other pixel data analyzer that can capture pixel data, and is programmed to discriminate attributes represented in a pixel file. Processor 18 and analyzer 17 are configured to apply an algorithm, such as determining a proportional ratio of the counts of two categories or two subcategories of corresponding particles, and applying such a proportional ratio to the particle count of at least one category and / or subcategory of particles obtained in at least one channel of the particle counter 15. After analyzing the data, processor 18 provides, at output 20, an accurate measurement of the concentration of each category and each corresponding subcategory of particles in the sample 12.
[000201] In some embodiments, in sample 12, at least a first category and / or subcategory of particles may be present in a concentration outside of a detection range applicable to the first category and / or subcategory of particles while at least one second category and / or subcategory of particles is present in a concentration within a detection range applicable to the second category and / or subcategory of particles. The concentration of the second category and / or subcategory of particles is determined in the particle counter 15. A proportional ratio of the first category and / or subcategory to the second category and / or subcategory of particles is determined in the analyzer 17. The concentration of particles in the the first category and / or subcategory is calculated in processor 18 at least in part, by applying such a ratio proportional to the concentration of the second category and / or subcategory of particles.
[000202] In some embodiments, a category and / or subcategory of particles detected in at least one particle counter channel 15 may comprise at least two classes of particles. And each class of particles can comprise a plurality of subclasses. The particle counter 15 is configured to detect a plurality of particles that satisfy one or more selection criteria, for example, based on a predetermined size range, and to provide a particle count of the same. The selection criteria cover members of at least two classes of particles. Analyzer 17 and processor 18 are programmed to distinguish members from at least two categories and / or subcategories of particles. A distribution of each of the members over at least two categories and / or subcategories is determined in processor 18. Processor 18 uses such a distribution to correct the particle count for members of at least one of at least two categories and / or subcategories obtained in the particle counter 15.
[000203] More specifically, equipment 10 can be used to identify and quantify different blood cells, including RBCs, WBCs, PLTs, and other blood cells, fetal cells, or bacterial cells, viral particles, parasites, cysts, including cysts parasites, crystals, or fragments thereof or other cellular fragments in the sample.
[000204] Figure 6A represents aspects of an exemplary counter or count module 600a, according to the modalities of the present invention. Such counters can operate to control or perform various mechanical functions, as well as electronic and photometric measurement functions for WBC, RBC and PLT cell counts and hemoglobin measurements. Exemplary counters can be used to prepare samples for CBC analysis and to generate CBC parameter measurements through bath sets at the opening (eg, WBC 610a bath and RBC 620a bath). According to some embodiments, the counter 15 of Figure 6 can be represented by the counter 600a of Figure 6A. Similarly, according to some embodiments, counter 15 in Figure 5 can be represented by counter 600a in Figure 6A. According to some embodiments, the counter 722 of Figure 7 can be represented by the counter 600a of Figure 6A.
[000205] The cellular elements of the blood (for example, erythrocytes, leukocytes and platelets) can be counted using electrical impedance methods. For example, an aspirated whole blood sample can be divided into two aliquots and mixed with an isotonic diluent. The first dilution can be delivered to the bath at the RBC (erythrocyte) opening 620a, and the second can be delivered to the bath at the WBC (leukocyte) opening 610a. In the erythrocyte chamber, erythrocytes and platelets can be counted and broken down by electrical impedance, as cells pass through the sensory openings. For example, particles between 2 and 20 μl can be counted as platelets, and particles greater than 36 μl can be counted as erythrocytes. For the processing of the leukocyte chamber, an erythrocyte lysis reagent can be added to the leukocyte dilution aliquot to lyse the erythrocytes and release hemoglobin, and then the leukocytes can be counted by the impedance in the sensing openings of the leukocyte bath. In some cases, baths can include multiple openings. Thus, for example, a blood cell count used in a blood cell enumeration technique can be obtained by using a bath in triple erythrocyte openings.
[000206] An exemplary technique for preparing a complete blood count sample may include two processes, sample collection and sample placement. Sample collection can occur when 165 µL of the patient's sample is aspirated and directed to a Blood Sampling Valve (BSV). A BSV can operate to target specific volumes of the patient's sample with the processing reagents to distribute it to the two baths in tri-plas openings. The patient sample and processing reagents can be placed at the bottom of the opening baths at an angle that, with a round design, allows the sample and reagents to mix completely without mixing bubbles. The sample can then be prepared for measurement and analysis. According to some modalities, in the leukocyte bath, 6.0 mL (± 1.0%) of the diluent and 28 µL of the sample can be combined with 1.08 mL (± 1.0%) of cell lysate DxH for a final dilution of 1: 251. According to some modalities, in the erythrocyte bath, 10 mL (± 1.0%) of the diluent and 1.6 µL of the sample can be combined for a final dilution of 1: 6250. After the patient sample and reagents are mixed, vacuum and opening current can be applied to the openings for cell count and cell volume measurements. Erythrocyte and platelet counts may also include the application of drag flow to prevent recirculation of cells near the opening. In certain modalities, the data capture for erythrocytes and platelets can be a maximum of 20 seconds and for leukocytes a maximum of 10 seconds. In certain modalities, all the analog pulses generated by the opening sets can be amplified by a "pre-amp" card and then sent to a hemogram signal conditioning analyzer card for converting from analog to digital and extracting parameters. According to some modalities, a system can be used to measure multiple parameters for each cellular event, and a digital parameter extraction process can be used to provide digital measurements, such as time, volume (pulse attributes including pulse width and amplitude) ), count and count rate, and waiting time. Such measurements can be used for pulse editing, coincidence correction, count recording, generation of histograms for leukocytes, erythrocytes and platelets, histogram recording, pattern analysis and interference correction and the like.
[000207] Figure 6B is a simplified block diagram of an example module system that broadly illustrates how the individual elements of the system for a 600b module system can be implemented in a separate or integrated manner. The module system 600b may be part of, or be in connectivity with, a particle analysis system for imaging particles in a blood sample fluid, according to the modalities of the present invention. The 600b module system is well suited for producing data or instructions related to dynamic range extension techniques, receiving input related to dynamic range extension techniques, and / or processing information or data related to dynamic range techniques. dynamic range extension, as described in this document. In some cases, the 600b module system includes hardware elements that are electrically coupled via a 602b bus subsystem, including one or more 604b processors, one or more 606b input devices as user interface input devices, and / or one or more 608b output devices, such as user interface output devices. In some cases, the system 600b includes a network interface 610b, and / or an analyzer / counter system interface 640b that can receive signals from and / or transmit signals to an analyzer / counter system 642b. In some cases, an analyzer / counter system 642b may include an analyzer 17 and / or a particle counter 15, as shown in Figure 6. In some cases, the 600b system includes software elements, for example, shown here as being located presently within a working memory 612b of a memory 614b, an operating system 616b, and / or other code 618b, as a program configured to implement one or more aspects of the techniques presented in the present invention.
[000208] In some embodiments, the module system 600b may include a storage subsystem 620b that can store the basic programming and data constructs that provide the functionality of the various techniques presented in the present invention. For example, software modules implementing the functionality of method aspects, as described here, can be stored in the storage subsystem 620b. These software modules can be run by one or more 604b processors. In a distributed environment, software modules can be stored in a plurality of computer systems and run by processors from the plurality of computer systems. Storage subsystem 620b can include memory subsystem 622b and file storage subsystem 628b. The memory subsystem 622b can include numerous memories including a main random access memory (RAM) 626b for storing instructions and data during program execution and a read-only memory (ROM) 624b in which the fixed instructions are stored. . The 628b file storage subsystem can provide persistent (non-volatile) storage for program files and data and can include tangible storage media that can optionally include sample, patient, treatment, assessment, and other data. The 628b file storage subsystem may include a hard disk drive, a floppy disk drive (floppy disk) together with removable associated media, a Read-Only Memory (CD-ROM), an optical drive, DVD, CD-R, CD RW, removable solid state memory, other removable media cartridges or media and the like. One or more of the units may be located in remote locations on other computers connected to other sites coupled to the 600b module system. In some cases, systems may include a computer-readable storage medium or another tangible storage medium that stores one or more sequences of instructions that, when executed by one or more processors, can cause the one or more processors to execute any aspect of the techniques or methods presented in the present invention. One or more modules implementing the functionality of the techniques presented in the present invention can be stored by the file storage subsystem 628b. In some embodiments, the software or code will provide the protocol to allow the 600b module system to communicate with the 630b communication network. Optionally, these communications can include communications by dial-up connection or Internet connection.
[000209] It is understood that the system 600b can be configured to perform various aspects of the methods of the present invention. For example, the 604b processor module or component may be a microprocessor control module configured to receive signals or data from a 632b sensor input module or device, a 606b user interface input module or device, and / or an analyzer / counter system 642b, optionally via an analyzer / counter system interface 640b and / or a network interface 610b and a communication network 630b. In some cases, the sensor input device (s) may include or be part of a particle analysis system that is equipped to obtain images of blood fluid samples. In some cases, user interface device (s) 606b and / or network interface 610b can be configured to receive image parameter signals generated by a particle analysis system that is equipped to obtain parameters of image. In some cases, the analyzer / counter system 642b may include or be part of a particle analysis system that is equipped to obtain imaging parameters and / or counting parameters related to blood fluid samples.
[000210] The module or component of the 604b processor can also be configured to transmit signals from particle analysis parameters or signals from image parameters, optionally processed according to any of the techniques presented here, to the module or output device of sensor 636b, for the 608b user interface output module or device, for the 610b network interface module or device, for the 640b network interface module or device, or any combination thereof. Each of the devices or modules according to the modalities of the present invention can include one or more software modules in a computer-readable medium that is processed by a processor, or hardware modules, or any combination thereof. Any one of a variety of commonly used platforms, such as Windows, MacIntosh and Unix, together with any of a variety of commonly used programming languages, can be used to implement modalities of the present invention.
[000211] The input devices of the 606b user interface can include, for example, a touchpad, a keyboard, pointing devices such as a mouse, a trackball, a graphics tablet, a scanner, a joystick, a touch of screen embedded in a screen, audio input devices like speech recognition systems, microphones, and other types of input devices. User input devices 606b can also download a computer executable code from a tangible storage medium or from a communication network 630b, the code including any of the methods or aspects thereof presented in the present invention. It will be understood that the terminal software can be updated from time to time and downloaded to the terminal, as appropriate. In general, the use of the term "input device" is intended to include a variety of conventional and proprietary devices and ways to insert information into a 600b module system.
[000212] The 606b user interface output devices may include, for example, a display subsystem, a printer, a fax machine, or non-visual displays, such as audio output devices. The display subsystem can be a cathode ray tube (TRC), a flat panel device, such as a liquid crystal display (LCD), a projection device, or the like. The display subsystem can also provide a non-visual display, such as through audio output devices. In general, the use of the term "output device" is intended to include a variety of conventional and proprietary devices and ways to provide information from the 600b module system to a user.
[000213] The bus subsystem 602b provides a mechanism for letting the various components and subsystems of the module system 600b communicate with each other, as intended or desired. The various subsystems and components of the 600b module system do not need to be in the same physical location, but can be distributed across multiple locations within a distributed network. Although the bus subsystem 602b is shown schematically as a single bus, alternative modalities of the bus subsystem can use multiple buses.
[000214] The network interface 610b can provide an interface to an external network 630b or other devices. The external communication network 630b can be configured to communicate, as needed or desired, with third parties. In this way, it can receive an electronic package from the 600b module system and transmit any information, as needed or desired, back to the 600b module system. As shown here, communication network 630b and / or analyzer / counter system interface 642b can transmit information or receive information from an analyzer / counter system 642b that is equipped to obtain images or corresponding image parameters and / or count parameters for blood fluid samples.
[000215] In addition to providing this infrastructure to communications links internal to the system, the 630b communications network system can also provide a connection to other networks, such as the Internet, and can comprise a wired, wireless, modem and / or by another type of interface connection.
[000216] It will be apparent to the person skilled in the art that considerable variations can be used according to specific requirements. For example, custom hardware may also be used and / or specific elements may be implemented in the hardware, software (including portable software, such as applets), or both. In addition, the connection to other computing devices, such as network input / output devices, can be used. The terminal module system 600b itself can be of different types, including a computer terminal, a personal computer, a laptop computer, a workstation, a network computer, or any other data processing system. Due to the variable nature of computers and networks, the description of the module system 600b shown in Figure 6B serves only as a specific example for purposes of illustrating one or more embodiments of the present invention. Various other configurations of the 600b module system are possible having more or less components than the module system shown in Figure 6B. Any of the modules or components of the 600b module system, or any combination of these modules or components, may be coupled or integrated, or otherwise configured to be in connectivity with any of the imaging and / or imaging system modalities. analyzing particles shown in the present invention. Likewise, any of the hardware and software components discussed above can be integrated with or configured to interface with another medical assessment or treatment system used elsewhere.
[000217] In some embodiments, the module system 600b can be configured to receive one or more image parameters of a blood fluid sample from an input module. The image parameter data can be transmitted to an evaluation module where the diagnostic or other results can be predicted or determined based on the analysis of the image data. Image or diagnostic data can be provided to a system user via an output module. In some cases, the module system 600b can determine diagnostic results for a blood fluid sample, for example, using a diagnostic module. Diagnostic information can be provided to a system user via an output module. Optionally, certain aspects of diagnosis can be determined by an output device, and transmitted to a diagnostic system or a sub-device of a diagnostic system. Any of a variety of data related to blood or patient fluid samples from which samples are obtained can be entered into the module system, including age, weight, sex, treatment history, medical history, and the like . The parameters of treatment regimens or diagnostic assessments can be determined based on this data.
[000218] Similarly, in some cases, a system includes a processor configured to receive incoming image data. Optionally, a processor, storage medium, or both, can be incorporated into a hematology or particle analysis machine. In some cases, the hematology machine can generate image data or other information for entry into the processor. In some cases, a processor, a storage medium, or both, can be incorporated into a computer, and the computer can be in communication with a hematology machine. In some cases, a processor, a storage medium, or both, can be incorporated into a computer, and the computer can be in remote communication with a hematology device over a network.
[000219] Figure 7 represents aspects of systems and methods for measuring a quantity of a first type of cells in a blood fluid sample, where the sample also includes a second type of cells, according to the modalities of the present invention. . As shown here, method 700 may include obtaining a first sample volume 720 and a second sample volume 730 from blood fluid sample 710. As indicated in step 724, the method may include determining a population of the second type of cells in the first volume 720 of the sample flowing the first volume through a 722 hematology cell counter. Often, the cell counter 722 is suitable for counting cells accurately when there is a sufficient amount of one electrically distinguishable type of cells in the sample, not when the amount of the cell type exceeds a certain threshold or threshold. Cell counters can be used to count red blood cells or the total number of other components (for example, large components) in a blood sample in a short period of time. In some cases, cell counters may encounter challenges in discriminating between white blood cells and other components (for example, large components) in the blood, or because there may be several different species, but with a relatively small number of each. .
[000220] In addition, method 700 may include obtaining images of a first number of the first cell types and a second number of the second cell types, as indicated by step 732, by injecting the second volume 730 of the sample into a coating fluid flowing inside a flow cell to provide a sample stream having a thickness and width greater than the thickness, the captured images being captured along an image path that crosses the thickness of the stream Sample. In some cases, image capture 732 can be performed using an analyzer 17 as depicted in Figure 5 and / or Figure 6. In some cases, analyzers can efficiently discriminate between white blood cells, giant platelets, and other large components in the blood fluid sample. However, there can be challenges when using such analyzers to obtain a complete count of the particles in a sample. Additionally, in some cases it may not be desirable to use the analyzer to obtain certain counts (for example, a count of all red blood cells) because such counting procedures may also involve performing a characterization of the particles, in addition to get the count. According to some modalities, the analyzer is used to obtain images for only a percentage or portion of the sample that is processed through the analyzer.
[000221] As shown in Figure 7, method 700 may include determining a ratio between the first number of the first type of cells 734 to the second number of the second type of cells 736, using the captured images, as indicated in step 738 The methods also include calculating a measure of the number of cells of the first cell type in the sample using the ratio 738 and the population of the second cell type 724, as indicated in step 740.
[000222] According to some modalities, the measurement of the quantity of cells calculated in step 740 is a concentration of cells for the first type of cells in the blood fluid sample 710. In some cases, the measurement of the quantity of cells calculated in the step 740 is a cell count for the first type of cells in the blood fluid sample 710. In some cases, the cell counter 722 has a first precision associated with counting the first type of cells and a second precision associated with the second type of cells, where the second precision is greater than or greater than the first precision. In some cases, (see, for example, Figures 10A and 10B) the hematology cell counter 722 has a desired precision range, and the desired precision range extends between a minimum population of cells in the first volume 720 and a maximum cell population in the first volume 720, where the population of the second cell type in the volume determined in step 724 is within the desired precision range, and in which the measured cell quantity of the first cell type in the sample calculated in step 740 is outside the desired precision range.
[000223] As additionally shown in Figure 7, (and with continued reference to Figures 10A and 10B) the methods may optionally include determining a population of the first type of cells 726 in the first volume of the sample as a result of the flow of the first volume through the hematology cell counter 722. The population determined for the first cell type 726 in the first volume may be above or below a desired precision range for the first cell type, and may also be different from the measured quantity of the first type of cell. cells as calculated in step 740. In some cases, (for example, FIG 10A), the determined population of the first type of cells 726 is zero. In some cases, (for example, Figure 10B), the determined population of the first cell type 726 is greater than zero.
[000224] According to some embodiments of the present invention, the hematology cell counter 722 may include a sensor mechanism that detects a change in electrical impedance in response to a second type of cell flowing through the cell counter. According to some embodiments, the hematology cell counter 722 includes a sensor mechanism that detects an obstruction of a light path in response to a second type of cells flowing through the cell counter.
[000225] In some cases, the 722 hematology cell counter has a lower detectable concentration limit and a maximum detectable concentration limit for the first type of cells, and a lower detectable concentration limit and a maximum detectable concentration limit for the second type of cells. The determined population of the second cell type 724 can be based on a concentration parameter detected for the second cell type that is above the minimum limit and below the maximum limit for the second cell type. The first cell type can be present at a concentration that is either below the minimum limit or above the maximum limit for the first cell type.
[000226] In some cases, the hematology cell counter 722 has a minimum detectable volume limit and a maximum detectable volume limit for the first type of cells, and a minimum detectable volume limit and a maximum detectable volume limit for the second type of cells. The determined population of the second cell type 724 can be based on a volume parameter detected for the second cell type that is above the minimum limit and below the maximum limit for the second cell type. The first cell type can be present in a volume parameter that is either below the minimum limit or above the maximum limit for the first cell type.
[000227] In some cases, the hematology cell counter 722 has a minimum detectable size limit and a maximum detectable size limit for the first type of cells, and a minimum detectable size limit and a maximum detected volume size. for the second type of cells. The determined population of the second cell type 724 can be based on a size parameter detected for the second cell type that is above the minimum limit and below the maximum limit for the second cell type. The first cell type can be present in a size parameter that is either below the minimum limit or above the maximum limit for the first cell type. According to some embodiments of the present invention, (see figures 13b, c), determining the population of the second cell type 724 in the first sample volume includes grouping together the cells of the first cell type and cells of the second cell type . In some cases, the methods may also include calculating a measure of the number of cells of the second cell type in the sample using the ratio and population of the second cell type. In some cases (for example, as shown in Figure 10D), determining the population of the second cell type 724 in the first sample volume includes grouping together the cells of the first cell type and the cells of the second cell type, and determining a population of the first cell type 726 in the first volume of the sample as a result of the flow of the first volume through the hematology cell counter 722. Measuring the number of cells of the first cell type in the sample as calculated in step 740 can use the reason 738, the population of the second cell type 724, and the population of the first cell type 726.
[000228] In other respects, for example as shown in Figure 8 and / or Figures 10A and 10B, a method is provided to analyze a sample containing particles. In such a method, a sample is provided on a particle counter having limits of detection, as indicated in step 72 in method 70 of Figure 8. At least one first category and / or subcategory of particles may be present in the sample at an outside concentration of a detection range applicable to the first category and / or subcategory of particles, and at least a second category and / or subcategory of particles is present in the sample within a detection range applicable to the second category and / or subcategory of particles. The concentration of the second category and / or subcategory of particles in the sample is determined with the particle counter, as indicated in step 74. The sample is also supplied to an analyzer to determine a proportional ratio of the first category and / or subcategory of particles to the second category and / or subcategory of particles, as indicated in step 76. The concentration of particles in the first category and / or subcategory can then be calculated, at least in part, by applying the ratio proportional to the concentration of the second category and / or particle subcategory, as indicated in step 78. Figure 10A shows the detection of particles in a sample below the detection range, and Figure 10B shows the detection of particles present in a sample above the detection range.
[000229] Figure 8, therefore, illustrates an exemplifying method 70 for determining the concentration of the first particle category, which is present in a sample in a concentration outside a detection range of a particle counter, according to some modalities . In step 72, also referring to Figures 6 and 8, a sample 12 is provided over a particle counter 15, which has at least one detection range. Sample 12 includes particles, which can be dispersed in a fluid. In some embodiments, the first category of particles is present in the sample at a concentration above an upper limit of a detection range applicable to the first category of particles. The second category of particles is present in the sample within a detection range applicable to the second category of particles. For example, the first category and / or subcategory of particles may include WBCs. The second category of particles can include platelets.
[000230] In some embodiments, the first category of particles is present in the sample at a concentration below a lower limit of a detectable range applicable to the first category of particles. The second category of particles is present in the sample within a detection range applicable to the second category of particles. For example, the first category of particles comprises platelets. The second category of particles comprises white blood cells.
[000231] In step 74 of Figure 8, the concentration of the second category of particles in the sample 12 is determined in the particle counter 15. The particle counter can comprise at least one channel. The second category of particles is measured in one of the channels in some modalities. The particle counter can comprise at least two channels in some embodiments. The first category of particles, if the concentration is within a detection range applicable to the first category of particles, can be counted in another channel.
[000232] In step 76 of Figure 8, sample 12 is supplied to an analyzer, such as a visual analyzer 17 (for example, as shown in Figures 5 or 6), to determine a proportional ratio of the first particle category to the second particle category. In some embodiments, the visual analyzer 17 comprises a flow cell 22 connected to an imaging device as described above. The proportional ratio of the first category of particles to the second category of particles can be determined according to the method described here. For example, at least one chemical, including at least one of a diluent, a permeabilizing agent, and a contrast agent can be introduced into the sample. Examples of chemicals, compositions, contrast agents, and related compositions that can be used for processing blood fluid samples are discussed in copending US patent application no. , the content of which is incorporated herein by reference. The contrast agent can be effective in generating visual distinctions that differentiate the first categories and / or subcategories from the second category and / or subcategories of particles. The prepared sample 12B shown in Figure 5 can be applied to at least one flow cell 22 in some embodiments. Particle images of the prepared sample 12B are captured. An image analysis is performed by the analyzer which can be a visual analyzer 17 and / or processor 18. A proportional ratio of the first category of particles to the second category of particles is then determined by analyzing the plurality of images of the sample stream in ribbon format.
[000233] In step 78 of Figure 8, the concentration of particles in the first category can then be calculated by processor 18 (for example, as shown in Figure 6), at least in part, by applying the ratio proportional to the concentration of the second category of particles.
[000234] The present description also provides methods for analyzing a sample containing particles. Figure 9 illustrates an exemplary process 80 for determining the concentration of two subcategories of particles, whose particles cannot be distinguished by the particle counter, according to some modalities. In step 82, a sample (for example, sample 12 in Figure 6) is provided for a particle counter (for example, particle counter 15 in Figure 6), which has a detection criterion that is met by at least two categories or subcategories of particles to be distinguished. The results of the particle counter cover these categories or subcategories within a single count in step 84 of Figure 9.
[000235] In step 86, the sample is supplied to the analyzer (as a visual analyzer) to determine a proportional ratio of the first category or subcategory of particles to the second category or subcategory of particles. In some embodiments, for example, as shown in Figures 5 and / or 6, a visual analyzer 17 includes a flow cell 22 connected to an imaging device.
[000236] The proportional ratio of the first category or subcategory of particles to the second category or subcategory of particles can be determined according to methods described herein. At least one chemical product comprising at least one of a diluent, a permeabilizing agent and a contrast agent is introduced into the sample. The contrast agent is effective in generating visual distinctions for categorizing and sub-categorizing particles that differentiate the first category or sub-category from the second category or sub-category of particles. As shown in Figure 5, the prepared sample 12B can be applied to at least one flow cell 22 in some embodiments. Particle images of the prepared sample 12B are captured. An image analysis is performed by the visual analyzer and / or processor 18. A proportional ratio of at least the first subcategory of particles to the second subcategory of particles is then determined by analyzing the plurality of images.
[000237] In step 88 of Figure 9, the concentration of particles in the first category or subcategory can then be calculated by processor 18, as represented in Figures 5 or 6, at least in part, by applying the ratio proportional to the single count (for example, step 84 of Figure 9) obtained from the particle counter.
[000238] In some modalities, the first category and / or subcategory of particles is present in the sample in a concentration above the upper limit of a detection range applicable to the first category and / or subcategory of particles. The second category and / or subcategory of particles is present in the sample within the detection range applicable to the second category and / or subcategory of particles. For example, the first category of particles comprises white blood cells. The second category of particles comprises platelets. As shown in Figure 10B, the particle count from the analyzer of the present description can be used to correct inaccurate particle counts associated with at least one detection range used by the particle counter, such as concentration, volume and / or size of particles. When operating the equipment described in this description, particles present in quantities above the upper limit of the detection range can be detected and measured with precision.
[000239] In some modalities, the first category and / or subcategory of particles is present in the sample below a lower limit of a detectable range of some parameter, for example, concentration, applicable to the first category and / or subcategory of particles, as illustrated in Figure 10A. The second category and / or subcategory of particles is present in the sample within the detection range applicable to the second category and / or subcategory of particles. As illustrated in Figure 10A, the proportional ratio of the particle count in the two categories and / or subcategories of the analyzer of the present description can be used to correct inaccurate particle counter counts for at least one category and / or subcategory. When operating the equipment described in this description, the particles present below the limit of the detection range, which are not detected by the particle counter, can be accurately measured.
[000240] As shown in Figure 10A, the particle counter provides a particle count for category 2. The analyzer provides a proportional particle count ratio for categories 1 and 2. By multiplying the proportional ratio times the particle count for category 2, the process reaches the particle count for category 1. The first category and / or subcategory of particles can comprise, for example, platelets. The second category and / or subcategory of particles comprises white blood cells. According to some modalities, the dynamic range or detection extension systems and method described herein can be used to obtain the accurate platelet count when the number of platelets contained in the sample is low.
[000241] In some embodiments, the analyzer includes an imaging device and a flow cell connected to the imaging device to determine a proportional ratio of the first category and / or subcategory of particles to the second category and / or subcategory of particles. At least one of a diluent, a permeabilizing agent, a contrast agent is introduced into the sample. The at least one chemical is effective for generating visual distinctions that differentiate the first and second categories and / or subcategories of particles. In a determination step such as a proportional ratio, the sample is applied to at least one flow cell present in some embodiments. A plurality of particle images from the sample are captured to provide a statistically significant estimate of a counting or proportional ratio. A proportional ratio of the at least first category and / or subcategory of particles to the second category and / or subcategory of particles is then determined by counting the particles in each of the first and second categories and / or subcategories of particles.
[000242] In another aspect, as shown in Figure 9 and / or Figure 10D, a method 80 for analyzing a sample containing particles is provided to correct the particle count obtained in a particle counter. For example, the analyzer results, for example, the relative count, of the present description can be used to obtain accurate particle counts of the categories and / or subcategories of particles that cannot be differentiated by the detection criteria or criteria used by the counter of particles alone.
[000243] In another embodiment shown in Figure 10C, the meter can provide a substantially accurate count for a plurality of particles. The plurality of particles encompasses members of at least two subcategories, but the count does not distinguish between the subcategories. The distribution of each of the members of at least two subcategories can be determined with an analyzer. The distribution of the subcategories is the proportional ratio of the counts of the respective subcategories to the total. A processor is programmed to distinguish members from at least two subcategories. Using the analyzer distribution and the total particle count of the particle counter, for example, as shown in Figure 10C, the particle count for members of at least one of the at least two subcategories can then be determined by the processor using the distribution of each member.
[000244] According to some modalities, as represented in Figure 10D, the sample can have two categories of particles present. In this context, categories can be interpreted to include the possibility of multiple categories and / or multiple subcategories. When operating the equipment described in this description, correction can be made for particle counting where at least some members of at least one additional category of particles are incorrectly categorized or subcategorized, by the particle counter, as members of a first category of particles. particles. In such a method, the count for a plurality of particles can be determined using a predetermined range, for example, size and / or volume range, to provide particle counts of the same with a particle counter. The predetermined range groups together the members of a first category of particles and at least some members of at least a second category of particles in the particle count. These particles in one or more categories or subcategories, which are incorrectly counted as another category of particles in an equipment channel, can be measured separately and accurately using the analyzer configured to distinguish a particle distribution over the first category of particles and at least a second category of particles in the sample. The distribution of categories and / or subcategories is the proportional ratio of the counts of the respective categories and / or subcategories to the total. The processor then uses the distribution to calculate the particle count for members of the first category and at least a second category and / or subcategory of particles. In these modalities, as illustrated in Figure 10D, the equipment and methods of the present description and the particle count in each of the categories and / or subcategories can be corrected.
[000245] As shown in Figure 10D, the particle counter can provide a substantially accurate total count comprising two categories. This count can include presumed counts for categories 1 and 2. However, the presumed count is inaccurate because the particle counter erroneously classified at least one member of category 2 with category 1. The analyzer provides a distribution of counts of particles based on a sample smaller than that used in the particle counter, for categories 1 and 2, but the analyzer produces an accurate distribution. The processor uses this information to arrive at an accurate count for both categories. This same process can be used for samples containing more than two categories and / or subcategories of particles.
[000246] For example, members of different categories or sub-categories of particles with similar size or morphology cannot be accurately categorized or subcategorized by the particle counter. For example, "giant" PLTs, PLT aggregates, nodules, multiple platelets and nucleated RBCs can be mistakenly counted as WBCs, resulting in a higher WBC count than actually exists in the sample. As another example, microcytic red cells, cell fragments, artifacts, and even electronic noise can be mistakenly counted as platelets, resulting in an inaccurate high PLT count.
[000247] In some embodiments, the analyzer is a visual analyzer that comprises an imaging device and a flow cell. As an example, at least one chemical product comprising at least one of a diluent, a permeabilizing agent, a contrast agent is introduced into the sample. The at least one chemical product is effective in generating visual distinctions that differentiate the first category and / or subcategory and the second category and / or subcategory of particles. In a step of determining such a distribution, the sample is applied to at least one flow cell present in some modalities.
[000248] In the step of determining a distribution of each of the members of at least two categories and / or subcategories of particles, at least a part of the sample is applied to at least one flow cell. The at least one chemical is effective in generating visual distinctions that differentiate members from categories and / or subcategories of particles. A plurality of particle imaging of the sample is captured. A plurality of particle images from the sample is captured to provide a statistically significant estimate of a proportional ratio or count. A proportional ratio of the at least first category and / or subcategory of particles to the second category and / or subcategory of particles is then determined by counting the particles in each of the first and second categories and / or subcategories of particles.
[000249] A proportional ratio of the members of each of the two or more subcategories of particles within a category and / or subcategory of particles, and / or a proportional ratio of the members of a first category and / or subcategory of particles to the members of at least one other category and / or subcategory of particles can be determined, based on the plurality of particle images in the sample. A count or concentration value for each category and / or subcategory of particles can be calculated, estimated, inferred and / or derived. As an example, the concentration of particle subcategories can be determined based on the proportional ratio of each particle subcategory of the analyzer, and by counting the total number of particles in the particle counter category. In some embodiments, members of at least two subcategories comprise at least one type of particles selected from a group consisting of subcategories of white blood cells, platelets and red blood cells.
[000250] Consequently, in some embodiments, the method further comprises determining a proportional ratio of the particle count in a category and / or subcategory of particles present in a concentration outside of a detection range applicable for a particle category of the particle counter versus the particle count in a second category and / or subcategory of particles that is within a detection range applicable to the second category and / or subcategory of particles, based on the plurality of particle images from the analyzer sample and / or processor. The sample concentration of the particle category and / or subcategory outside the detection range of the particle counter can then be determined by applying the ratio proportional to the particle count obtained in the particle counter. For example, in some modalities, the first category and / or subcategory of particles is present in the sample at a concentration above an upper limit of the detection range applicable to the first category and / or subcategory of particles. The second category and / or subcategory of particles is present in the sample within the detection range of the particle counter (below an upper limit and above the lower limit of the detection range) applicable to the second category and / or subcategory of particles. As another example, when the detection criteria, or criteria, used by the particle counter erroneously categorize particles by grouping particles of a first category and / or subcategory with particles of at least a second category and / or subcategory, the count of particles for the first and second categories and / or subcategories can be corrected from the proportional proportions of the particles determined from the plurality of images of the sample particles from the analyzer and / or from the visual processor.
[000251] The measurement detection range can be limited in a particle counter 15 alone in Figure 6. For example, the upper detection limit for WBCs can be less than 100,000 to 200,000 per μL in a particle counter 15. The lower detection limit for PLTs can be greater than 10,000 per μL. By using the equipment described here, the effective detection range of measurement can be extended, for example, the upper detection limit for WBCs can be extended up to about 300,000, 350,000, 400,000, 410,000, 420,000, 430,000, 440,000, 450,000, 460,000, 470,000, 480,000, 490,000, 500,000, 510,000, 520,000, 530,000, 540,000, 550,000, 560,000, 570,000, 580,000, 590,000, 600,000, 610,000, 620,000, 630,000, 640,000, 650,000, 660,000, 670,000, 680,000, 690,000, 700,000, 6,000,000 710,000, 720,000, 730,000, 740,000, 750,000, 760,000, 770,000, 780,000, 790,000, 800,000, 810,000, 820,000, 830,000, 840,000, 850,000, 860,000, 870,000, 880,000, 890,000, 900,000, 910,000, 920,000, 930,000, 940,000, 950,000, 940,000, 930,000, 940,000, 950,000 960,000, 970,000, 980,000, 990,000, or 1,000,000, 1,000,000, 1,010,000, 1,020,000, 1,030,000, 1,040,000, 1,050,000, 1,060,000, 1,070,000, 1,080,000, 1,090 .000, 1,100,000, 1,110,000, 1,120,000, 1,130,000, 1,140,000, 1,150,000, 1,160,000, 1,170,000, 1,180,000, or around 1,190,000, cells per μL, or any range between any two of the values, in some modalities. The lower detection limit for PLTs can be extended below to 10,000, 9,500, 9,000, 8,500, 8,000, 7,500, 7,000, 6,500, 6,000, 5,500, 5,000, 4,500, 4,000, 3,500, 3,000, 2,500, 2,000, 1,500 or 1,000, or 500, 400, 300, 200, or 100 cells per μL in some modalities.
[000252] The analyzer preferably comprises a visual analyzer 17 operable to determine a proportional ratio of the first category and / or subcategory of particles to the second category and / or subcategory of particles. In this embodiment, the proportional ratio as described above can be determined by analyzing the plurality of particle images in the sample taken in the visual analyzer 17.
[000253] The visual analyzer 17 can be configured to introduce into the sample at least one chemical product comprising at least one of a diluent, a permeabilizing agent and / or a contrast agent to generate visual distinctions for the categorization and sub-categorization of particles. Such visual differences differentiate members from at least two categories. The particle images from the sample are captured. The visual analyzer 17 and processor 18 are configured to determine a proportional ratio of each category or sub-category of particles, by discriminating between the images of the sample particles. The concentration of each category or subcategory of particles is then calculated. For example, the precise results of WBCs, giant PLTs and NRBCs can be determined. In a particle counter, due to similar size or morphology, giant PLTs and NRBc are counted as WBCs. When operating the described equipment, the particle count or concentration of giant PLTs and nRBCs can be reported accurately.
[000254] In some embodiments, the sample may comprise particles whose size is outside a detection size range of the particle counter 15. The visual analyzer 17 and processor 18 are configured to detect the particles and determine a proportional particle ratio out of a detection size range for particles within the size detection range of the particle counter 15, based on the images of the sample particles. The concentration of the particle category and subcategory outside the size detection range of the particle counter 15 can then be calculated.
[000255] Generally, methods for analyzing a sample containing the particles are provided to correct the particle count obtained in a particle counter. An exemplary method can be used to differentiate different categories of particles including the corresponding subcategories, which are part of the same category and / or subcategory of particles in the particle counter 15, for example, as shown in Figures 5 and 6. The method can be used to correct the particle counts obtained in the particle counter 15. In some embodiments, for example, the first category and / or subcategory of particles comprises one or more types of abnormal blood cells, immature blood cells, aggregated cells blood, or abnormally sized blood cells. The second category and / or subcategory of particles comprises white blood cells. When operating the equipment as described here, particles in subcategories can be distinguished by the analyzer, and the counts of the categories and / or subcategories of particles obtained from the particle counter can be corrected.
[000256] A sample or portion thereof is provided to the particle counter 15 to detect the particles and provide particle counts based on one or more selection criteria that can cover subcategories of at least two particle categories. For example, the supposed WBC category of the particle counter may also contain a small amount of giant PLTs and NRBCs. This category of the particle counter can further comprise subcategories of white blood cells that cannot be distinguished by the particle counter. Another portion of the sample can also be analyzed on the visual analyzer, as described below, to resolve these erroneous categorizations and / or subcategorize indistinct WBC subcategories.
[000257] The distribution of each of the at least two subcategories or categories can be determined in analyzer 17, as shown in Figure 5. Such distribution can be presented in a numerical ratio, proportional ratio and / or another function of the relative counts. In some embodiments, such a distribution can be determined according to methods disclosed here on a visual analyzer 17, comprising a flow cell 22, and an imaging device 24. As described, sample 12A, which can be a portion of a sample, is applied to at least one flow cell 22. At least one chemical comprising at least one of a diluent, a permeabilizing agent, a contrast agent is introduced into sample 12A. At least one chemical substance comprising at least one of a diluent, a permeabilizing agent and / or a contrast agent is effective in generating visual distinctions that differentiate at least two categories of particles, and differentiate at least two subcategories of at least one category of particles. A plurality of particle images from sample 12B is captured. An image analysis is performed by the visual analyzer 17 and / or processor 18.
[000258] In some embodiments, processor 18 is programmed to distinguish members from at least two categories and / or subcategories. A proportional ratio of the particle count in each of the at least two subcategories or categories of particles can be determined, based on the plurality of particle images in the sample. The particle count for the subcategories of at least one of the at least two categories obtained from the particle counter 15 can then be corrected in the processor 18, using the distribution of each of the subcategories. The concentration of each particle subcategory can be calculated in processor 18, based on the proportional ratio of each particle subcategory and the particle count of the particle category obtained from the particle counter.
[000259] The methods disclosed in this document can also be used to differentiate one or more types of particles outside a detection range in the particle counter 15, according to some modalities. For example, these particles can be blood cells or other fragments, which are too large or too small to be detected in the particle counter 15. In the visual analyzer 17 a proportional ratio of the counts of a particle type outside of a detection range on the particle counter for another type of particle within the detection range of the particle counter can be determined based on the plurality of particle images in the sample. The concentration of the type of particles outside the detection range in the sample can then be determined by applying, at least in part, the proportional ratio to the particle count obtained in the particle counter 15.
[000260] Consequently, the modalities of the present invention encompass hybrid systems and methods, for example, which combine, for example, photographic cell imaging and electronic cell counting techniques, for example, to analyze cells that may be difficult to distinguish electrically, or to analyze the cells present in quantities that make it difficult to obtain an accurate electronic count of them.
[000261] Each of the calculations or operations described here can be done using a computer or another processor that has hardware, software and / or firmware. The various steps of the method can be performed by modules, and the modules can comprise any of a wide variety of digital and / or analog data processing hardware and / or software arranged to perform the method steps described here. The modules optionally comprise data processing hardware adapted to perform one or more of these steps having appropriate machine programming code associated with it, the modules of two or more steps (or portions of two or more steps) being integrated into a single board or separated on different processor boards on any of a wide variety of integrated and / or distributed processing architectures. These methods and systems will often use a tangible medium including machine-readable code with instructions for performing the steps in the method described above. Suitable tangible media may comprise a memory (including a volatile memory and / or a non-volatile memory), a storage medium (such as a magnetic recording on a floppy disk, a hard disk, a tape, or the like; on an optical memory, such as a CD, CD-R / W, CD-ROM, DVD or the like; or any other digital or analog storage medium), or the like.
[000262] All patents, patent publications, patent applications, newspaper articles, books, technical references and the like discussed in the present disclosure are hereby incorporated by reference in their entirety for all purposes.
[000263] Different dispositions of the components represented in the drawings or described above, as well as the components and steps not shown or described, are possible. Similarly, some resources and sub-combinations are useful and can be used without reference to other resources and sub-combinations. The modalities of the invention have been described for illustrative and non-restrictive purposes, and alternative modalities will be apparent to readers of this patent. In certain cases, the steps of the method or operations can be performed or performed in different orders, or the operations can be included, deleted or modified. It can be understood that, in certain aspects of the invention, a single component can be replaced by multiple components, and multiple components can be replaced by a single component, to provide an element or structure or to perform a certain function or functions. Except where this substitution is not operational to practice certain modalities of the invention, this substitution is considered within the scope of the invention. Consequently, the present invention is not limited to the modalities described above or shown in the drawings, and various modalities and modifications can be made without departing from the scope of the claims below.

权利要求:
Claims (14)
[0001]
1. Method for measuring a quantity of a first type of cells in a blood fluid sample, the sample (25) including a second type of cells, the method characterized by the fact that it comprises: determining a population of the second type of cells in a first volume of the sample (720) through the flow of the first volume (720) through a hematology cell counter (722), in which the hematology cell counter (722) does not comprise an imaging device and does not visualize the first volume of the sample (720), and the hematology cells (722) have a first precision associated with counting the first type of cells and a second precision associated with the second type of cells, the second precision being higher than the first precision; capture images of a first number of the first cell types and a second number of the second cell types by injecting a second sample volume (730) into a coating fluid (726) that flows inside a flow cell (22 , 420) in order to provide a sample stream (32, 428) having a thickness and width greater than the thickness, the captured images being captured along an image path that crosses the thickness of the sample stream (32, 428); determining a ratio between the first number of the first cell type and the second number of the second cell types using the captured images; and calculating a measure of the number of cells of the first cell type in the sample using the ratio and population of the second cell type.
[0002]
2. Method according to claim 1, characterized in that the measure of the quantity of cells comprises: a concentration of cells for the first type of cells in the blood fluid sample (25); or a cell count for the first type of cells in the blood fluid sample (25).
[0003]
3. Method according to claim 1, characterized by the fact that the hematology cell counter (722) has a desired precision range, the desired precision range extending between a minimum population of cells in the first volume and a maximum population of cells in the first volume, the determined population of the second type of cells in the volume being within the desired precision range, and the measure of the amount of cells calculated from the first type of cells in the sample being outside the range desired accuracy.
[0004]
4. Method according to claim 1, characterized in that it additionally comprises determining a population of the first type of cells in the first volume of the sample (720) as a result of the flow of the first volume through the hematology cell counter (722 ), and the determined population of the first cell type in the first volume (720) is above or below a desired precision range for the first cell type, and is different from the measurement of the number of cells calculated from the first cell type .
[0005]
5. Method, according to claim 4, characterized by the fact that the determined population of the first type of cells is zero or greater than zero.
[0006]
6. Method, according to claim 1, characterized by the fact that the hematology cell counter (722) comprises both: a sensor mechanism that detects a change in electrical impedance in response to a second type of cells that flows through the cell counter (722); or a sensor mechanism that detects an obstruction of a light path in response to a second type of cells flowing through the cell counter (722).
[0007]
7. Method according to claim 1, characterized by the fact that: the hematology cell counter (722) has a lower limit of detectable concentration and a maximum limit of detectable concentration for the first type of cells, and a limit of minimum detectable concentration and maximum detectable concentration limit for the second cell type, the determined population of the second cell type is based on a concentration parameter detected for the second cell type that is above the lower limit and below the maximum limit for the second type of cells, and the first type of cells can be present in a concentration that is below the minimum limit or above the maximum limit for the first type of cells; or the hematology cell counter (722) has a minimum detectable volume limit and a maximum detectable volume limit for the first type of cells, and a minimum detectable volume limit and a maximum detectable volume limit for the second type of cells, the determined population of the second type of cells is based on a volume parameter detected for the second type of cells that is above the minimum limit and below the maximum limit for the second type of cells, and the first type of cells is present in a volume parameter that is below the minimum limit or above the maximum limit for the first type of cells.
[0008]
8. Method according to claim 1, characterized by the fact that: the hematology cell counter (722) has a minimum detectable size limit and a maximum detectable size limit for the first cell type, and a minimum detectable size limit and a maximum detectable volume size for the second cell type, the determined population of the second cell type is based on a detected size parameter for the second cell type that is above the minimum limit and below of the maximum limit for the second type of cells, and the first type of cells is present in a size parameter that is below the minimum limit or above the maximum limit for the first type of cells.
[0009]
9. Method according to claim 4, characterized in that it additionally comprises calculating a measure of quantity of cells of the second type of cells in the sample using the ratio and population of the second type of cells.
[0010]
10. Method according to claim 1, characterized in that the determination of the population of the second type of cells in the first volume of the sample (720) comprises grouping together the cells of the first type of cells and cells of the second type of cells , and, more preferably, the method further comprising determining a population of the first type of cells in the first volume of the sample (720) as a result of the flow of the first volume through the hematology cell counter (722), and the calculating the measure of the quantity of cells of the first cell type in the sample uses the ratio, the population of the second cell type, and the population of the first cell type.
[0011]
11. System for measuring a quantity of a first type of cells in a blood fluid sample, the sample including a second type of cells, the system characterized by the fact that it comprises: a hematology cell counter (722) having a channel and an output, the output operationally coupled to the channel in order to generate signals indicative of a population of the second type of cells in a first sample volume (720) flowing through the channel, the hematology cell counter being (722) does not comprise an imaging apparatus; a flow cell (22, 420) configured to facilitate the flow of a sample stream (32, 428), the sample stream (325, 428) comprising a second sample volume (730) and a coating fluid (426 ), and having a thickness and width greater than the thickness; an imaging equipment (24) configured to capture images of a first number of the first cell type and a second number of the second cell type in the second volume (730), the captured images being captured along an image path that crosses the thickness of the sample stream (32, 428); a processor (440) that determines a ratio between the first number of the first cell type and the second number of the second cell type using the captured images that calculates a measured quantity of cells of the first cell type in the sample using the ratio and the signs indicative of a population of the second type of cells.
[0012]
12. System according to claim 11, characterized by the fact that the processor (440) is coupled: to the hematology cell counter (722) to receive signals indicative of the population of the second type of cells; or to the imaging equipment (24) to receive the captured images.
[0013]
13. System according to claim 11, characterized by the fact that the flow cell (22, 420) and the imaging equipment (24) are components of a hematology analyzer that performs geometric hydrofocusing and viscosity combined for imaging the cells in the blood fluid sample.
[0014]
14. System according to claim 11, characterized by the fact that a difference between the viscosity of the coating fluid and the blood fluid sample, in combination with a decrease in the size of the flow path of the flow cell, is effective to hydrofocus the sample stream (32, 428) at an image capture location (432) of the flow cell (22, 420).

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US20210108994A1|2019-10-11|2021-04-15|Beckman Coulter, Inc.|Method and composition for staining and sample processing|

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US11125675B2|2019-10-18|2021-09-21|Roger Lawrence Deran|Fluid suspended particle classifier|

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WO2021118882A1|2019-12-10|2021-06-17|Siemens Healthcare Diagnostics Inc.|Device for visualization of components in a blood sample|

法律状态:
2018-11-13| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|

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2019-11-19| B15I| Others concerning applications: loss of priority|Free format text: PERDA DA PRIORIDADE US61/799,152, DE 15/03/2013, REIVINDICADA NO PCT/2014/146061, CONFORME AS DISPOSICOES PREVISTAS NA LEI 9.279 DE 14/05/1996 (LPI), ART. 16,7O, DECRETO NO. 635, DE 21/08/1992, E CONVENCAO DA UNIAO DE PARIS (REVISTA EM ESTOCOLMO 14/07/1967), ART. 4O, ALINEA C, ITEM 1. ESTA PERDA SE DEU PELO FATO DO BRASIL NAO ACEITAR RESTAURACAO DE PRIORIDADE CONCEDIDA PELA OMPI (RESERVA DO BRASIL DE ACORDO COM A REGRA 49TER.1 ALINEA (G) E/OU 49TER.2 ALINEA (H) DO REGULAMENTO DE EXECUCAO DO PCT), UMA VEZ QUE O PRAZO PARA O DEPOSITO INTERNACIONAL COM REIVINDICACAO DE PRIORIDADE ULTRAPASSOU OS 12 (DOZE) MESES LEGAIS. |

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2019-12-10| B150| Others concerning applications: publication cancelled [chapter 15.30 patent gazette]|Free format text: ANULADA A PUBLICACAO CODIGO 15.9 NA RPI NO 2550 DE 19/11/2019, DEVIDO AO CONTEUDO DO DOCUMENTO RO132 DISPONIVEL NO SITE DA OMPI. |

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2020-03-31| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|

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2020-11-24| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|

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2021-01-26| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 18/03/2014, OBSERVADAS AS CONDICOES LEGAIS. |

优先权:

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申请号 | 申请日 | 专利标题

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US201361799152P| true| 2013-03-15|2013-03-15|

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US61/799,152|2013-03-15|

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US14/217,034|US10429292B2|2013-03-15|2014-03-17|Dynamic range extension systems and methods for particle analysis in blood samples|

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US14/217,034|2014-03-17|

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PCT/US2014/030939|WO2014146061A1|2013-03-15|2014-03-18|Dynamic range extension systems and methods for particle analysis in blood samples|

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