• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    An instrument for biological analysis includes a base, an excitation source, an optical sensor, an optical excitation system and an optical emission system. The base is configured to receive a sample holder comprising a plurality of biological samples. The optical sensor is configured to receive emissions from biological samples in response to the excitation source. The instrument may additionally include a sensor lens surrounded by a lens housing and a focusing mechanism including a gear that engages the lens housing, the focusing mechanism being accessible from outside the housing to adjust a focus. The instrument may further include a sensor opening arranged along an optical emission path and a blocking structure arranged to cooperate with the sensor opening, in such a way that none of the radiation reflected from an illuminated surface near the sample holder is received by the optical sensor which also does not reflect another surface of the instrument.
    公开号:BR112017016937B1
    申请号:R112017016937-1
    申请日:2016-02-05
    公开日:2021-02-17
    发明作者:Mingsong CHEN；Kuan Moon Boo；Tiong Han Toh；Mauro Aguanno；Soo Yong Lau；Huei Steven Yeo；Wei Fuh Teo
    申请人:Life Technologies Corporation；
    IPC主号:
    专利说明:

    [0001] [001] The present invention relates, in general, to systems, devices and methods for observing, testing and / or analyzing one or more biological samples, and more specifically to systems, devices and methods comprising an optical system for observing, testing and / or analyze one or more biological samples. Description of the related technique Brief Description of the Drawings
    [0002] [002] The modalities of the present invention can be better understood from the following detailed description when read in conjunction with the accompanying drawings. Such modalities, which are for illustrative purposes only, describe new and not obvious aspects of the invention. The drawings include the following figures:
    [0003] [003] FIG 1 is a schematic representation of a system according to an embodiment of the present invention.
    [0004] [004] FIG 2 is a schematic representation of an excitation source according to an embodiment of the present invention.
    [0005] [005] FIG 3 is a normalized spectrum graph of various light sources, including a light source according to an embodiment of the present invention.
    [0006] [006] FIG 4 is a graph of spectral integration in various wavelength bands for the light source spectra shown in FIG. 3.
    [0007] [007] FIGS. 5 and 6 are perspective views of an instrument housing in accordance with an embodiment of the present invention.
    [0008] [008] FIG 7 is a solid model representation of an optical and sample processing system according to an embodiment of the present invention.
    [0009] [009] FIG 8 is an enlarged representation of the solid model and the optical system shown in FIG. 7.
    [0010] [010] FIG 9 is an exploded view of a portion of the sample processing system shown in FIG. 7.
    [0011] [011] FIG 10 is a sectional view of a portion of the optical system shown in FIG. 7.
    [0012] [012] FIG 11 is a top perspective view of an imaging unit according to an embodiment of the present invention.
    [0013] [013] FIG 12 is a sectional view of the imaging unit shown in FIG. 11.
    [0014] [014] FIGS. 13 and 14 are perspective views from the bottom of the imaging unit shown in FIG. 11.
    [0015] [015] FIGS. 15-17 are enlarged views of the portions of the imaging unit shown in FIG. 11.
    [0016] [016] FIG 18 is a sectional view of the system shown in FIGS. 6 and 8.
    [0017] [017] FIGS. 19 and 20 are schematic representations of a system according to an embodiment of the present invention. Detailed description of the drawings
    [0018] [018] As used here, the terms "radiation" or "electromagnetic radiation" mean radiant energy released by certain electromagnetic processes that may include one or more electromagnetic radiation of visible light (for example, radiant energy characterized by one or more wavelengths between 400 nanometers and 700 nanometers or between 380 nanometers and 800 nanometers) or invisible (for example, infrared, near infrared, ultraviolet (UV), X-ray or gamma-ray radiation).
    [0019] [019] As used here, an excitation source means a source of electromagnetic radiation that can be directed to at least one sample containing one or more chemical compounds in such a way that electromagnetic radiation interacts with at least one sample to produce electromagnetic radiation of emission indicative of a condition of at least one sample. The excitation source may include a light source. As used here, the term "light source" refers to an electromagnetic radiation source that comprises an electromagnetic spectrum having a peak or maximum output (for example, energy, power or intensity) that is within the visible wavelength range. of the electromagnetic spectrum (for example, electromagnetic radiation within a wavelength in the range of 400 nanometers to 700 nanometers or in the range of 380 nanometers and 800 nanometers). Additionally or alternatively, the excitation source may comprise electromagnetic radiation within at least a portion of the infrared (near infrared, medium infrared and / or far infrared) or ultraviolet (near ultraviolet and / or extreme ultraviolet) portions of the electromagnetic spectrum.Additionally or alternatively, the excitation source may comprise electromagnetic radiation in other length bands waveform of the electromagnetic spectrum, for example, in the X-ray and / or wave portions radio s of the electromagnetic spectrum. The excitation source may comprise a single light source, for example, an incandescent lamp, a gas discharge lamp (for example, halogen lamp, xenon lamp, argon lamp, Krypton lamp, etc.), a light-emitting diode (LED), an organic LED (OLED), a laser or similar. The excitation source can comprise a plurality of individual light sources (for example, a plurality of LEDs or lasers). The excitation source can also include one or more excitation filters, such as a high-pass filter, a low-pass filter or a band-pass filter. For example, the excitation filter can include a color filter and / or a dichroic filter. The excitation source comprises a single beam or a plurality of spatially and / or temporarily separated beams.
    [0020] [020] As used here, an "emission" means electromagnetic radiation produced as a result of an interaction of radiation from an excitation source with one or more samples containing or believed to contain one or more chemical and / or biological molecules or compounds of interest. The emission may be due to reflection, refraction, polarization, absorption and / or other optical effect by the sample in the radiation from the excitation source. For example, the emission may comprise a luminescence or fluorescence induced by the absorption of excitation electromagnetic radiation by one or more samples. As used here, "emission light" refers to an emission comprising an electromagnetic spectrum with a peak or maximum output (for example, power, energy or intensity) that is within the visible band of the electromagnetic spectrum (for example, electromagnetic radiation within wavelength ranging from 420 nanometers to 700 nanometers).
    [0021] [021] As used here, a lens means an optical element configured to direct or focus the incident electromagnetic radiation in order to converge or diverge that radiation, for example, to provide a real or virtual image, either at a finite distance or at a optical infinity. The lens may comprise a single optical element with an optical power provided by refraction, reflection and / or diffraction of the incident electromagnetic radiation. Alternatively, the lens may comprise a composite system including a plurality of optical elements, for example, including, but not limited to, an achromatic lens, a doublet lens, triplet lens or camera lens. The lens can be at least partially housed or at least partially enclosed by a lens case or lens mount.
    [0022] [022] As used here, the term "optical power" means the ability of a lens or optical element to converge or diverge light to provide a focus (real or virtual) when disposed in the air. As used here, the term "focal length" means the reciprocal of the optical power. As used herein, the term "diffractive power" or "diffractive optical power" means the power of a lens or optical element, or portion thereof, attributable to the diffraction of light incident on one or more diffraction orders. Unless otherwise stated, the optical power of a lens, optic or optical element is from a reference plane associated with the lens or optical element (for example, a main plane of an optical element).
    [0023] [023] As used herein, the term "biological sample" means a sample or solution containing any type of chemical or biological component and / or any target molecule of interest to a user, manufacturer or distributor of the various embodiments of the present invention described or implied here, as well as any sample or solution that contains related chemical products or compounds used to perform a test, experiment or biological test. These biological chemicals, components or target molecules may include, but are not limited to, DNA sequences (including cell-free DNA), RNA sequences, genes, oligonucleotides, molecules, proteins, biomarkers, cells (for example, tumor cells circulating), or any other suitable target biomolecule. A biological sample can comprise one or more of at least one target nucleic acid sequence, at least one primer, at least one buffer, at least one nucleotide, at least one enzyme, at least one detergent, at least one blocking agent or at least one dye, marker and / or probe suitable for detecting a target or reference nucleic acid sequence. In various modalities, such biological components can be used in conjunction with one or more methods and PCR systems in applications such as fetal diagnostics, multiplex dPCR, viral detection and quantification standards, genotyping, sequencing assays, experiments or protocols, validation sequencing, mutation detection, detection of genetically modified organisms, detection of rare alleles and / or variation in copy number.
    [0024] [024] According to the modalities of the present invention, one or more samples or solutions containing at least one biological target of interest can be contained, distributed, or divided among a plurality of small sample volumes or reaction regions (for example, volumes or regions such as less than or equal to 10 nanoliters, less than or equal to 1 nanoliter, or less than or equal to 100 picoliters). The reaction regions described here are generally illustrated as being contained in wells located in a substrate material; however, other forms of reaction regions according to the modalities of the present invention can include reaction regions located within indentations or through holes formed in a substrate, solution stains distributed on the surface of a substrate, samples or solutions located at sites samples or volumes of a capillary or microfluidic system, or within or in a plurality of microgranules or microspheres
    [0025] [025] Although devices, instruments, systems and methods according to the modalities of the present invention are generally directed to dPCR and qPCR, the modalities of the present invention can be applicable to any PCR processes, experiments, assays or protocols in which a large number of reaction regions is processed, observed and / or measured. In a dPCR assay or experiment, according to the modalities of the present invention, a diluted solution containing at least one target polynucleotide or nucleotide sequence is subdivided into a plurality of reaction regions, so that at least some of these reaction regions contain a molecule of the target nucleotide sequence or no target nucleotide sequence. When the reaction regions are subsequently thermally cycled in a PCR protocol, procedure, assay, process or experiment, the reaction regions that contain one or more molecules of the target nucleotide sequence are extensively amplified and produce a positive and detectable detection signal , while those containing no target nucleotide sequences are not amplified and do not produce a detection signal, or produce a signal that is below a predetermined threshold or noise level. Using Poisson statistics, the number of target nucleotide sequences in an original solution distributed between the reaction regions can be correlated with the number of reaction regions that produce a positive detection signal. In some embodiments, the detected signal can be used to determine a number, or range of numbers, of target molecules contained in the original solution. For example, a detection system can be configured to distinguish between reaction regions containing one target molecule and reaction regions containing two or at least two target molecules. Additionally or alternatively, the detection system can be configured to distinguish between reaction regions containing a number of target molecules that are at or below a predetermined amount and reaction regions containing more than the predetermined amount. In certain embodiments, qPCR and dPCR processes, trials or protocols are conducted using a single device, instruments or systems and methods.
    [0026] [026] With reference to FIG. 1, a system, apparatus or instrument 100 for biological analysis comprises one or more of an electronic processor, computer or controller 200, a base, assembly or set of sample blocks 300 configured to receive and / or process a biological or biochemical sample and / or an optical system, apparatus or instrument 400. Without limiting the scope of the present invention, system 100 may comprise a sequencing instrument, a polymerase chain reaction (PCR) instrument (for example, a time PCR instrument) real (qPCR) and / or digital PCR (dPCR)), capillary electrophoresis instrument, an instrument to provide genotyping information, or the like.
    [0027] [027] Electronic processor 200 is configured to control, monitor and / or receive data from optical system 400 and / or base 300. Electronic processor 200 can be physically integrated into optical system 400 and / or base 300. Additionally or alternatively, the electronic processor 200 can be separated from the optical system 400 and the base 300, for example, an external desktop computer, a laptop computer, a notepad computer, a tablet computer or the like. The communication between the electronic processor 200 and the optical system 400 and / or base 300 can be carried out directly through a physical connection, such as a USB cable or similar, and / or indirectly through a wireless or network connection (for example , via Wi-Fi connection, a local area network, internet connection, cloud connection, etc.). The electronic processor 200 may include electronic memory storage containing instruction parameters, routines, algorithms, test and / or configuration, test and / or experimental data or the like. The electronic processor 200 can be configured, for example, to operate various components of the optical system 400 or to obtain and / or process data provided by the base 300. For example, the electronic processor 200 can be used to obtain and / or process optical data provided by one or more photodetectors of the optical system 400.
    [0028] [028] In certain embodiments, the electronic processor 200 can be integrated into the optical system 400 and / or base 300. The electronic processor 200 can communicate with an external computer and / or transmit data to an external computer for further processing, for example, using a hardwire connection, a local area network, an internet connection, a cloud computing system or similar. The external computer can be a physical computer, such as a desktop computer, a laptop computer, a notepad computer, a tablet computer, or another, which is located within or near system 100. Additionally or alternatively, one or both of the external computer and the electronic processor 200 may include a device or virtual system, such as a cloud computing or storage system. Data can be transferred between the two through a wireless connection, a cloud storage or computing system or similar. Additionally or alternatively, the data from the electronic processor 200 (for example, from the optical system 400 and / or base 300) can be transferred to an external memory storage device, for example, an external hard drive, a USB memory module, a cloud storage system, or similar.
    [0029] [029] In certain embodiments, the base 300 is configured to receive a sample holder or sample carrier 305. Sample holder 305 may comprise a plurality or matrix of spatially separate reaction regions, sites or locations 308 to contain a plurality or corresponding matrix of biological or biochemical samples 310. Reaction regions 308 may comprise any plurality of volumes or isolation sites or configured to isolate the plurality of biological or biochemical samples 310. For example, reaction regions 308 may comprise a plurality through holes or through wells in the substrate or assembly (for example, sample wells in a standard microtiter plate), a plurality of sample granules, microgranules or microspheres in a channel, capillary or chamber, a plurality of distinct locations in one flow cell, a plurality of sample stains on a substrate surface, or a plurality of wells s or openings configured to receive a sample holder (for example, the wells in a sample block set configured to receive a microtiter plate).
    [0030] [030] The base 300 may comprise a sample block set configured to control the temperature of the sample holder 305 and / or biological samples 310. The sample block set 300 may comprise one or more of a sample block, a Peltier device or other device for controlling or cycling the temperature, and / or a heat sink (for example, to help stabilize the temperature). The base 300 may comprise a thermal controller or a thermocycler, for example, to provide or perform a PCR assay.
    [0031] [031] Reaction apparatus 300 may include sample holder 305. At least some of the reaction regions 308 may include one or more biological samples 310. Biological or biochemical samples 310 may include one or more of at least one sequence of target nucleic acid, at least one primer, at least one buffer, at least one nucleotide, at least one enzyme, at least one detergent, at least one blocking agent, or at least one dye, marker and / or probe suitable for detecting a target or reference nucleic acid sequence. The sample holder 305 can be configured to perform at least one of a PCR assay, a sequencing assay or a capillary electrophoresis assay, a blot assay. In certain embodiments, the sample holder 305 may comprise one or more of a microtiter plate, a substrate comprising a plurality of wells or through-holes, a substrate comprising one or more channels or capillaries, or a chamber comprising a plurality of granules or spheres containing one or more biological samples. Reaction regions 308 can comprise one or more of a plurality of wells, a plurality of through holes in the substrate, a plurality of distinct locations on a substrate or within a channel or capillary, a plurality of microgranules or microspheres within a reaction volume, or similar. Sample holder 305 can comprise a microtiter plate, for example, where reaction regions 308 can comprise at least 96 wells, at least 384 or at least 1536 wells.
    [0032] [032] In certain embodiments, the sample holder 305 may comprise a substrate including a first surface, a second opposite surface and a plurality of through holes disposed between the surfaces, the plurality of through holes configured to contain one or more samples biological, for example, as discussed in US Patent Application Publication numbers 2014-0242596 and WO 2013/138706, whose patent applications are hereby incorporated by reference as if they were fully disclosed herein. In such embodiments, the substrate may comprise at least 3096 through holes or at least 20,000 through holes. In certain embodiments, sample holder 305 may comprise a series of capillaries configured to pass one or more target molecules or sequence of molecules.
    [0033] [033] In certain embodiments, the system 100 can optionally include a heated or temperature-controlled cover 102 that can be arranged above the sample holder 305 and / or base 300. The heated cover 102 can be used, for example, to avoid condensation above samples contained in sample holder 305, which can help maintain optical access to biological samples 310.
    [0034] [034] In certain embodiments, the optical system 400 comprises an excitation source, light source, radiation source or light source 402 that produces at least one first excitation beam 405a characterized by a first wavelength and a second beam excitation wave 405b characterized by a second wavelength that is different from the first wavelength. Optical system 400 also comprises an optical sensor or optical detector 408 configured to receive emissions or radiation from one or more biological samples in response to excitation source 410 and / or one or more excitation beams 405a, 405b. Optical system 400 further comprises an optical excitation system 410 arranged along an optical excitation path 412 between excitation source 402 and one or more biological samples to be illuminated. The optical system 400 further comprises an optical emission system 415 arranged along an optical emission path 417 between the illuminated sample (s) and the optical sensor 408. In certain embodiments, the optical system 400 can comprise a beam splitter 420. The optical system 400 may optionally include a beam shield or radiation deflector 422 configured to reduce or prevent the reflection of radiation in the optical emission path 417 from the excitation source 402 that invades the beam splitter. bundles 420.
    [0035] [035] In the embodiment illustrated in FIG. 1, as well as in other embodiments of the invention described herein, the excitation source 402 comprises a radiation source 425. The radiation source 425 may comprise one or more of at least one incandescent lamp, at least one gas discharge lamp, at least one light-emitting diode (LED), at least one organic light-emitting diode and / or at least one laser. For example, the radiation source 425 may comprise at least one halogen lamp, xenon lamp, argon lamp, krypton lamp, diode laser, argon laser, xenon laser, excimer laser, solid state laser, helium-neon laser, dye laser or combinations thereof. The radiation source 425 may comprise a light source characterized by a maximum or central wavelength in the visible band of the electromagnetic spectrum. Additionally or alternatively, the radiation source 425 may comprise an ultraviolet, infrared or near infrared source with a corresponding maximum or central wavelength within one of these wavelength bands of the electromagnetic spectrum. The radiation source 425 can be a broadband source, for example, with a spectral bandwidth of at least 100 nanometers, at least 200 nanometers, or at least 300 nanometers, where the bandwidth is defined as a band over which output intensity, power or energy is greater than a predetermined amount (for example, where the predetermined amount is either about 1%, 5% or 10% of a maximum or central wavelength of the radiation source ). The excitation source 402 may additionally comprise a source lens 428 configured to condition the emissions from the radiation source 425, for example, to increase the amount of excitation radiation received in the sample holder 305 and / or in the biological samples 310. A source lens 428 may comprise a single lens or may be a composite lens comprising two or more elements.
    [0036] [036] In certain embodiments, excitation source 402 further comprises two or more excitation filters 430 mobile inside and outside the optical excitation path 412, for example, used in combination with a broadband excitation source 402. In such cases modalities, different excitation filters 430 can be used to select different wavelength bands or excitation channels suitable to induce fluorescence of a respective dye or marker within biological samples 310. One or more excitation filters 430 can be a width of wavelength band that is at least ± 10 nanometers or at least ± 15 nanometers. Excitation filters 430 may comprise a plurality of filters that together provide a plurality of pass bands suitable for fluorescence of one or more of a SYBR® dye or probe, a FAM TM dye or probe, a VIC® dye or probe , a ROX TM dye or probe, or a TAMRATM dye or probe. Excitation filters 430 can be arranged on a rotating filter wheel (not shown) or other appropriate device or apparatus providing different excitation channels using excitation source 402. In certain embodiments, excitation filters 430 comprise at least 5 filters or at least 6 filters.
    [0037] [037] In certain embodiments, excitation source 402 may comprise a plurality of individual excitation sources that can be combined using one or more beam splitters or beam combiner, so that the radiation from each individual excitation source is transmitted along a common optical path, for example, along the excitation optical path 412 shown in FIG. 1. Alternatively, at least some of the individual excitation sources can be arranged to provide excitation beams that propagate along different, non-overlapping optical paths, for example, to illuminate different reaction regions of the plurality of reaction regions 308. Each of the individual excitation sources can be treated, activated or selected to illuminate the reaction regions 308, for example, individually or in groups or all simultaneously. In certain embodiments, the individual excitation sources can be organized in a one-dimensional or two-dimensional matrix, where one or more of the individual excitation sources is characterized by a maximum or central wavelength that is different from at least one of the other sources of excitation. individual excitation in the matrix.
    [0038] [038] In certain embodiments, the first excitation beam 405a comprises a first wavelength range over which an intensity, power or energy of the first excitation beam 405a is above a first predetermined value and the second excitation beam 405b it comprises a second wavelength range over which an intensity, power or energy of the second excitation beam 405b is above a second predetermined value. The characteristic wavelength of the excitation beams 405a, 405b can be a central wavelength of the corresponding wavelength range or a wavelength of maximum intensity, power or electromagnetic energy over the corresponding wavelength range. The central wavelengths of at least one of the 405 excitation beams can be an average wavelength over the corresponding wavelength range. For each excitation beam 405 (for example, excitation beams 405a, 405b), the predetermined value may be less than 20% of the corresponding maximum intensity, power or energy; less than 10% of the corresponding intensity, power or maximum energy; less than 5% of the corresponding intensity, power or maximum energy; or less than 1% of the corresponding intensity, power or maximum energy. The predetermined values can be the same for all excitation beams 405 (for example, for both excitation beams 405a, 405b) or the predetermined values can be different from each other. In certain embodiments, the wavelength bands of the first and second excitation beams 405a, 405b do not overlap, while in other embodiments, at least one of the wavelength bands overlaps, at least partially, the other. In certain embodiments, the first and second central wavelengths are separated by at least 20 nanometers. In certain embodiments, at least one of the first and second wavelength bands has a value of at least 20 nanometers or at least 30 nanometers.
    [0039] [039] The optical excitation system 410 is configured to direct excitation beams 405a, 405b to one or more biological samples. Where applicable, references here to excitation beams 405a, 405b can be applied in the embodiment comprising more than two excitation beams 405. For example, excitation source 402 can be configured to target at least five or six excitation beams 405 Excitation beams 405a, 405b can be produced or supplied simultaneously, can be temporarily separated and / or can be spatially separated (for example, where excitation beams 405a are directed to a reaction region 308 and excitation beams 405b are directed to a different reaction region 308). Excitation beams 405 can be produced sequentially, for example, by sequentially activating and deactivating the individual radiation source of different colors 425 which are characterized by different wavelengths or sequentially placing different color filters in front of a single radiation source 425. Alternatively, the excitation of beams 405a, 405b can be produced simultaneously, for example, using a multi-wavelength band filter, a beam splitter or a mirror, or by coupling the different individual radiation source 425, as two light-emitting diodes of different colors (LEDs). In some embodiments, the excitation source 402 produces more than two excitation beams 405, wherein the optical excitation system 410 directs each excitation beams to one or more biological samples 310.
    [0040] [040] With reference to FIG. 2, excitation source 402 may comprise at least 5 individual radiant sources 425a, 425b, 425c, 425d, 425e which are combined to transmit along a common excitation optical path 412. Excitation source 402 may also include corresponding sources lenses 428a, 428b, 428c, 428d, 428e. The radiation from radial sources 425a, 425b, 425c, 425d, 425e can be combined using a plurality of combining optical elements 429a, 429b, 429c. The combining optical elements 429a, 429b, 429c can comprise one or more of a neutral density filter, a 50/50 beam splitter, a dichroic mirror or filter, a hub beam divider or the like. Combining optical elements 429a, 429b, 429c are an example of how to combine several individual sources 425 and it will be appreciated that other combinations and geometric arrangements of individual radial sources 425 and combining optical elements 429 are within the scope of the modalities of the present invention. One or more of the individual radiant sources 425a, 425b, 425c, 425d, 425e can be characterized by a range of wavelength and / or central wavelength that is different from the other individual radiant sources 425a, 425b, 425c, 425d, 425e .
    [0041] [041] With reference to FIGS. 3-4, the spectral distribution of the radiation source 425 can be selected in an unobvious manner to allow at least five excitation beams 405 of different colors or excitation channels to be used with a common beam splitter 420, while simultaneously maintaining acceptable or predetermined data produced for all excitation channels, for example, during each cycle of the qPCR assay. As used here, the term "excitation channel" means each of the various distinct electromagnetic wavelength bands provided by an excitation source (for example, excitation source 402) that are configured to illuminate one or more biological samples (for example, example, biological samples 310) .As used here, the term "emission channel" means each of several distinct emission wavelength bands over which electromagnetic radiation can pass to a sensor or optical detector (for example, sensor optical 408).
    [0042] [042] FIG 3 shows the relative energy over the wavelength spectrum for three different radiation sources. The dashed line graph is the spectrum of a halogen lamp (here called "Source 1") characterized by relatively low energy levels in the blue wavelength range of the visible spectrum and increased energy to a peak of around 670 nanometers. The dotted spectrum graph is a commercially available LED light source (here called "Source 2"), which has a maximum energy of about 450 nanometers and a smaller peak of about 530 nanometers to about 580 nanometers, decreasing gradually the energy in the red wavelength range of the visible spectrum. The solid line graph is the spectrum of another LED light source (hereinafter "Source 3") according to an embodiment of the present invention (for example, an exemplary spectrum for excitation source 402). FIG 4 shows the energy integrated in several excitation channels for each of the three sources shown in FIG. 3, where the spectra for these channels are those of the typical excitation filter used in the qPCR field. The wavelength ranges and excitation filter designations are shown below in Table 1, where X1 is excitation channel 1, X2 is excitation channel 2 and so on.
    [0043] [043] In the qPCR field, an important performance parameter is the total time to obtain emission data for samples containing various target dyes. For example, in some cases, it is desirable to obtain emission data for various dyes or probes over one or more emission channels, designated M1-M6, for each excitation channel used to illuminate the sample (s) (for example, example, M1-M6 with X1, M2-M6 with X2, M3-M6 with X3, M4-M6 with X4, M5-M6 with X5, and / or M6 with X6). The inventors found that when Source 2 is used in a system that has a single broadband beam splitter for five or six channels of emission / excitation filter (for example, excitation channels X1-X6 with emission channels combination M1-M6), the amount of time to obtain data for excitation channel 5 and / or excitation channel 6 could be unacceptably long for certain applications. To remedy this situation, it is possible to use one or more narrow band, dichroic beam splitters for excitation channels 1 and / or 2 to increase the amount of excitation light that receives the sample (s), and the amount of light emission received by the sensor (so that the overall optical efficiency is increased through the use of dichroic beam splitter, in this case). However, this prevents the use of a single beam splitter arrangement, as shown in FIG. 1 and, as a consequence, the corresponding advantages of a single beam splitter configuration (for example, reduction in size, cost, complexity) are lost. A better solution has been found in which a light source, such as Source 3, is used in combination with a single beam splitter (for example, a broadband beam splitter, such as a 50/50 beam splitter ), such as beam splitter 420. It has been found that the relative energy in excitation channels X1, X5, and / or X6 can be used to identify an excitation source 402 suitable for use with a single mode of splitter. beams to provide the acceptable total integration time for collecting emission data over five or six excitation channels. Using LED Source 2 and LED Source 3 as examples, the following data shown in Table 2 below can be derived for the data shown in FIGS. 3 and 4.
    [0044] [044] Based on such data, the inventors found that, in certain modalities, better performance (for example, in terms of reducing the time of integration of Channel 1) can be obtained when X1 / X2 is greater than 2, 02 (for example, greater than or equal to 3). In addition or alternatively, in other modalities, an improved performance (for example, in terms of reducing the integration time of Channel 1) can be obtained when X5 / X2 is greater than 0.49 (for example, greater than or equal to 0.9) and / or when X6 / X2 is greater than 0.38 (for example, greater than or equal to 0.9). For the criteria defined here, "X1" means an excitation channel that has a spectral output characterized by maximum power, energy or intensity within the wavelength band including 455-485 nanometers; "X2" means an excitation channel that has a spectral output characterized by maximum power, energy or intensity within the wavelength band including 510-530 nanometers; "X5" means an excitation channel that has a spectral output characterized by maximum power, energy or intensity within the wavelength band including 630.5-649.5 nanometers; "X6" means an excitation channel that has a spectral output characterized by maximum power, energy or intensity within the wavelength band including 650-674 nanometers.
    [0045] [045] With reference again to FIG. 1, the excitation beams 405 are directed along the optical excitation path 412 during operation to the sample processing base 300, for example, to reaction regions 308 when the sample holder 305 is present. When present, the lens of the source 428 is configured for the condition of excitation beams 405, for example, to capture and direct a large portion of the radiation emitted from the excitation source 402. In certain embodiments, one or more mirrors 432 ( for example, folded mirrors) can be incorporated along the optical excitation path 412, for example, to make the optical system 400 more compact and / or to provide the predetermined package dimensions. FIG illustrates a mirror 432; however, additional mirrors can be used, for example, to meet packaging design restrictions. As discussed in more detail below in this document, additional lenses can be arranged near the sample holder 305, for example, in order to further condition the 405 excitation beams and / or the corresponding emissions from the biological samples contained in a sample. or more reaction regions.
    [0046] [046] The 415 optical emission system is configured to target emissions from one or more biological samples from the 408 optical sensor. At least some of the emissions may comprise a fluorescent emission from at least some of the biological samples, in response to at least one of the excitation beams 405. Additionally or alternatively, at least some of the emissions comprise radiation from at least one of the excitation beams 405 which is reflected, refracted, diffracted, dispersed, or polarized by at least some of the biological samples. In certain embodiments, the optical emission system 415 comprises one or more emission filters 435 configured, for example, to block excitation radiation reflected or scattered in the optical emission path 417. In certain embodiments, there is a corresponding emission filter 435 for each excitation filter 430. With reference to FIG. 8, in certain embodiments, excitation filter 430 is arranged on an excitation filter wheel 431 and / or emission filters 435 are arranged on an emission filter wheel 436.
    [0047] [047] In certain embodiments, the optical emission system 415 comprises a 438 sensor lens configured to direct emissions from at least some of the biological samples to the optical sensor 408. The optical sensor 408 can comprise a single sensor element, for example, a photodiode detector or a photomultiplier tube, or the like. Additionally or alternatively, optical sensor 408 may comprise a matrix sensor including an array of sensors or pixels. The matrix sensor 408 may comprise one or more of a complementary metal-oxide-semiconductor (CMOS) sensor, a load-coupled device (CCD) sensor, a plurality of photodiodes detectors, a plurality of photomultiplier tubes, or the like . The sensor lenses 438 can be configured from an image from the emissions of one or more of the plurality of biological samples 310. In certain embodiments, the optical sensor 408 comprises two or more matrix sensors 408, for example, in which two or more images are formed from the emissions of one or more of the plurality of biological samples 310. In such embodiments, the emissions of one or more of the plurality of biological samples 310 can be divided to provide two signals of one or more of the plurality of biological samples 310. In certain embodiments, the optical sensor comprises at least two matrix sensors.
    [0048] [048] The beam splitter 420 is arranged along both the excitation and emission optical paths 412, 417 and is configured to receive both between the first and the second excitation beams 405a, 405b during operation. In the illustrated embodiment shown in FIG. 1, beam splitter 420 is configured to transmit excitation beams 405 and reflect emissions from biological samples 310. Alternatively, beam divider 420 can be configured to reflect excitation rays and transmit emissions to from biological samples 310. In certain embodiments, the beam splitter 420 comprises a broadband beam splitter that has the same, or approximately the same, reflectance for all or most of the excitation beams 405 provided by the source of excitation 402 and directed to reaction regions 308 (for example, excitation beams 405a, 405b in the illustrated embodiment). For example, beam splitter 420 may be a broadband beam splitter characterized by a reflectance, which is constant, or approximately constant, over a wavelength band of at least 100 nanometers, over a wavelength band. at least 200 nanometers, or over a visible wavelength band of the electromagnetic spectrum, over the visible IV wavelength bands and near the electromagnetic spectrum, or over a 450 nanometer to 680 nanometer wavelength band. In certain embodiments, the beam splitter 420 is a neutral density filter, for example, a filter that has a reflectance of, or about, 20%, 50%, or 80% over the visible wavelength band of the electromagnetic spectrum. In certain embodiments, beam splitter 420 is a dichroic beam splitter that is transmissive or reflective over one or more selected wavelengths, for example, a multi-wavelength band beam splitter that is transmissive and / or reflective over more than one band of the centers of wavelengths at or near a peak wavelength of the 405 excitation beams.
    [0049] [049] In certain embodiments, beam splitter 420 is a single beam splitter configured to receive some or all of the plurality of excitation beams 405 (for example, excitation beams 405a, 405b), either alone or in combination with a single beam shield 422. Each excitation beam can be called an excitation channel, which can be used alone or in combination to excite different dyes or fluorescent probe molecules in one or more of the 310 biological samples. various prior art systems and instruments, for example, in the qPCR field, provide a plurality of excitation beams, using a separate beam splitter and / or beam discharge for each excitation channel and / or each emission channel system or instrument. In such prior art systems and instruments, chromatically selective dichroic filters are typically used in at least some of the excitation channels to increase the amount of radiation received in the samples. Disadvantages of systems and instruments that use different beam separators and / or beam bulkheads for each channel include an increase in size, cost, complexity and response time (for example, rates for increasing the mass that must be moved or rotated while switch between excitation and / or emission channels). The inventors have found that it is possible to replace these plural beam splitters and / or beam bulkheads with the single beam splitter 420 and / or single beam bulkhead 422, while still providing a predetermined or acceptable system or instrument performance, for example, by properly selecting the spectral distribution of the excitation source 402 and / or by configuring systems or instruments to reduce the amount of unwanted scattered radiation received by the optical sensor 408 (as discussed hereinafter). Thus, the modalities of the present invention can be used to provide systems and instruments that have reduced size, cost, complexity and response time compared to prior art systems and instruments.
    [0050] [050] With reference to FIGS. 5 and 6, in certain embodiments, system 100 comprises an instrument housing 105 and sample holder drawer 110 comprising base 300 and is configured during use to receive, hold, or contain sample holder 305 and to position the sample holder 305 to provide the optical coupling of the same with the optical system 400. With the drawer 110 closed (FIG. 6), the housing 105 can be configured to contain or include the sample processing system 300 and the optical system 400. In certain embodiments, housing 105 may contain or include all or portions of electronic processor 200.
    [0051] [051] With reference to FIGS. 7-9, in certain embodiments, the optical system 400 may further comprise a lens 440 and / or a lens array 442, which may comprise a plurality of lenses corresponding to each of the reaction regions 308 of the sample holder 305. lens 440 may comprise a field lens, which can be configured to provide a telecentric optical system for at least one sample holder 305, reaction regions 308, lens array 442, or an optical sensor 408. As shown in the embodiment illustrated in FIGS. 7 and 9, lens 440 may comprise a Fresnel lens.
    [0052] [052] With reference again to FIGS. 7 and 9, in certain embodiments, the base 300 comprises a sample block set 300 comprising a sample block 302, a temperature controller 303, such as a Peltier device 303, and a heat sink 304. The set of sample block 300 can be configured to provide a thermal controller or thermal cycle (for example, provide a PCR assay or temperature profile), maintain the temperature of the sample holder 305 or biological sample (s) 310, and / or otherwise maintain, control, adjust, or cycle the heat or temperature flow of the sample holder 305 or biological sample (s) 310.
    [0053] [053] With additional reference to FIGS. 10-14, in certain embodiments, optical system 400 includes an imaging unit 445 comprising an optical sensor circuit board 448, sensor lens 438 (which may be a composite lens, as illustrated in FIG. 10) , inner lens mount 449, outer lens mount 450, 452 threaded housing, and 455 focusing gear. The 448 optical circuit board sensor, 452 threaded housing, and 438 sensor lens together can form a well 458 that surrounds or contains optical sensor 408 and can be configured to prevent any external light from hitting optical sensor 408 which does not enter through the lens of sensor 438. The outer lens assembly 450 comprises an outer surface that contains gear teeth 460 which can be movably or slidably engaged with the focus gear teeth 455 through a resilient element (not shown), such as a spring. In certain embodiments, the focusing gear455 moves or slides along a groove 462 of a plate 465, as shown in FIG. 14. The internal lens assembly 449 comprises a threaded portion 468 that fits or engages with a threaded portion of the threaded housing 452.
    [0054] [054] The inner lens mount 449 can be fixedly mounted to the outer lens mount 450, while the threaded housing 452 is fixedly mounted relative to the 448 optical sensor circuit board. The inner lens mount 449 it is movably or swiveled to a 452 threaded housing. Thus, the focusing gear 455 and external lens assembly 450 can be coupled in such a way that a rotation of the focusing gear 455 also rotates the external lens assembly 450. This, in turn, causes the inner lens assembly 449 and the lens of the sensor 438 to move along an optical axis of the lens of the sensor 438 through the threads in the inner lens assembly 449 and the 452 threaded housing. In this way, the focus of the sensor lens 438 can be adjusted without directly engaging the lens of the sensor 438 or its associated assemblies 449, 450, which are buried within a very compact optical system 400. The coupling with the focus gear 455 can be r manual or automated, for example, using a motor (not shown), such as a stepper motor or a DC motor.
    [0055] [055] With reference to FIGS. 11 and 13-17, in certain embodiments, the imaging unit 445 further comprises a locking mechanism or device 470. The locking device 470 comprises an edge or tooth 472 that can be slidably engaged between two teeth of the focusing gear 455 (see FIGS. 15-17). As illustrated in FIGS. 15 and 16, the locking device 470 can have a first position (FIG. 15) in which the focusing gear 455 is free to rotate and adjust the focus of the sensor lens 438 and a second position (FIG. 14) in which the focus gear 455 is locked in position and prevented or prevented from turning. In this way, the lens focus of sensor 438 can be advantageously blocked by avoiding direct blocking contact or engaging with the threads 468 of the inner lens assembly 449, which could damage the threads and prevent subsequent refocusing of the sensor lens 438 afterwards to have been locked in position. The operation of the 470 locking device can be manual or automated. In certain embodiments, the locking mechanism 470 further comprises a resilient element such as a spring (not shown), in which the rotation of the focusing gear 455 can be performed by exceeding a threshold force produced by the resilient element.
    [0056] [056] With reference to FIG. 18, the optical system 400 may also include an optical housing 477. In certain embodiments, the optical system 400 includes a radiation shield 475 comprising a sensor aperture 478 arranged along the optical emission path 417 and at least one structure of lock 480 arranged to cooperate with the opening of sensor 478 such that the only radiation from the excitation beams 405, and reflected from an illuminated surface or area 482, to pass through the opening of sensor 478 is the radiation that also reflected at least another surface of, or within, the optical housing 477. In other words, the radiation shield 475 is configured in such a way that the radiation from the excitation beams 405 reflected from the illuminated area 482 is prevented from passing directly through the opening 478 and therefore, to pass to the sensor lens 438 and to the optical detector 408. In certain embodiments, the illuminated area 482 comprises the area defined by all the openings 483 of the plug the heated 102 corresponding to the plurality of reaction regions 308.
    [0057] [057] In the illustrated embodiment of FIG.18, the blocking structure 480 comprises a shelf 480. The rays or dashed lines 484a and 484b can be used to illustrate the effectiveness of the blocking structure 480 in preventing light directly reflected from from the illuminated area 482, pass through the sensor opening 478 and into the sensor lens 438 and / or optical sensor 408. The radius 484a originates from an edge of the illuminated area 482 and only passes through the shelf 480, but does not pass through from the sensor opening 478. The radius 484b is another ray originating from the same edge of the illuminated area 482 that is blocked by the shelf 480. As can be seen, this ray would have entered through the sensor opening 478 had it not been for the shelf presence 480 .
    [0058] [058] With continued reference to FIG. 18, in certain embodiments, the optical system 400 may further comprise an energy or power detection unit comprising energy or power sensors 490 optically coupled to one end of a light tube 492. An opposite end 493 of the light tube light 492 is configured to be illuminated by excitation beams 405. The end of the light tube 493 can be illuminated, either directly by radiation contained in excitation beams 405 or indirectly, for example, by radiation dispersed over a diffuse surface. In certain embodiments, sensor 490 is located outside the optical excitation path 412 from excitation source 402. Additionally or alternatively, sensor 490 is located outside optical housing 477 and / or is located in a remote location outside the housing of instrument 105. In the illustrated embodiment shown in FIG. 18, light tube 493 is arranged near or adjacent to mirror 432 and can be oriented so that the face of the light tube is perpendicular, or almost perpendicular, to the surface of mirror 432 which reflects excitation beams 405. The inventors found that the low amount of energy or power intercepted by the 492 light tube, when oriented in this way, is sufficient for the purpose of monitoring the energy or power of the 405 excitation beams. Advantageously, by locating the 490 sensor outside the optical path of the excitation beams, a more compact 400 optical system can be provided.
    [0059] [059] In certain embodiments, the light tube 492 comprises a single fiber or a bundle of fibers. Additionally or alternatively, light 492 may comprise a rod made of a transparent or transmissive material, such as glass, Plexiglas, polymer-based material, such as acrylic, or the like.
    [0060] [060] With reference to FIGS. 19 and 20, in certain embodiments the instrument 100 comprises a position source 500 configured to emit radiation 502 and a corresponding position sensor 505 configured to receive radiation 502 from the position source 500. The position source 500 and the position sensor position 505 can be configured to produce a position signal indicative of a position of an optical element 435 disposed along an optical path. In certain embodiments, the instrument 100 may further comprise a radiation shield 510 configured to block at least some radiation 502 from a source position 505.
    [0061] [061] The foregoing presents a description of the best contemplated way of carrying out the present invention, and the form and process for preparing and using it, in complete, clear, concise and accurate terms that allow anyone skilled in the art to which belongs to make and use this invention. This invention is, however, susceptible to modifications and alternative constructions to that discussed above, which are completely equivalent. As a result, it is not intended to limit this invention to the particular embodiments described. On the contrary, it is intended to cover the modifications and alternative constructions covered by the spirit and scope of the invention as is generally expressed by the following claims, which particularly point and claim distinctly the subject matter of the invention.
    [0062] •Pedido de patente de desenho industrial U.S. número 29/516.847, depositado em 6 de Fevereiro de 2015; e •Pedido de patente de desenho industrial U.S. número 29/516.883; depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/112.910, depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/113.006, depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/113.183, depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/113.077, depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/113.058, depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/112.964, depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/113.118, depositado em 6 de Fevereiro de 2015; e •Pedido de patente provisório U.S. número 62/113.212, depositado em 6 de Fevereiro de 2015; e •Pedido de patente U.S. número___ (Life Technologies Número do Documento do Procurador LT01023), depositado em 5 de Fevereiro de 2016; e •Pedido de patente U.S. número ___(Life Technologies Número do Documento do Procurador LT01024), depositado em 5 de Fevereiro de 2016; e •Pedido de patente U.S. número ___(Life Technologies Número do Documento do Procurador LT01025), depositado em 5 de Fevereiro de 2016; e •Pedido de patente U.S. número ___(Life Technologies Número do Documento do Procurador LT01028), depositado em 5 de Fevereiro de 2016; e •Pedido de patente U.S. número ___(Life Technologies Número do Documento do Procurador LT01029), depositado em 5 de Fevereiro de 2016; e •Pedido de patente U.S. número___ (Life Technologies Número do Documento do Procurador LT01032), depositado em 5 de Fevereiro de 2016; e •Pedido de patente U.S. número ___(Life Technologies Número do Documento do Procurador LT01033), depositado em 5 de Fevereiro de 2016, todos os quais são também aqui incorporados por referência na sua totalidade[062] Exemplary systems for methods related to the various modalities described in this document include those described in the following documents: • US industrial design patent application number 29 / 516,847, filed on February 6, 2015; and • US industrial design patent application number 29 / 516,883; filed on February 6, 2015; and • US provisional patent application number 62 / 112,910, filed on February 6, 2015; and • US provisional patent application number 62 / 113,006, filed on February 6, 2015; and • US provisional patent application number 62 / 113,183, filed on February 6, 2015; and • US provisional patent application number 62 / 113,077, filed on February 6, 2015; and • US provisional patent application number 62 / 113,058, filed on February 6, 2015; and • US provisional patent application number 62 / 112,964, filed on February 6, 2015; and • US provisional patent application number 62 / 113,118, filed on February 6, 2015; and • US provisional patent application number 62 / 113,212, filed on February 6, 2015; and • US patent application number ___ (Life Technologies Attorney Document Number LT01023), filed on February 5, 2016; and • US patent application number ___ (Life Technologies Attorney Document Number LT01024), filed on February 5, 2016; and • US patent application number ___ (Life Technologies Attorney Document Number LT01025), filed on February 5, 2016; and • US patent application number ___ (Life Technologies Attorney Document Number LT01028), filed on February 5, 2016; and • US patent application number ___ (Life Technologies Attorney Document Number LT01029), filed on February 5, 2016; and • US patent application number ___ (Life Technologies Attorney Document Number LT01032), filed on February 5, 2016; and • US patent application number ___ (Life Technologies Attorney Document Number LT01033), filed on February 5, 2016, all of which are also incorporated herein by reference in their entirety
    权利要求:
    Claims (14)
    [0001]
    Instrument for biological analysis CHARACTERIZED by the fact that it comprises: an excitation source (402); an optical sensor (408) configured to receive emissions from biological samples (310) in response to the excitation source; an optical sensor circuit board (448); an optical excitation system (410) arranged along an optical excitation path (412); an optical emission system (415) arranged along an optical emission path (417); an imaging unit comprising: a first surface, a second opposite surface and a threaded housing (452) together, forming a cavity containing the optical sensor; a sensor lens (438); a lens housing (449, 450) at least partially surrounding the sensor lens and having a threaded portion that engages with a threaded portion of the threaded housing; and a focusing mechanism comprising a focusing gear (455) arranged to engage gear teeth provided with an outer surface of the lens housing, rotation of the focusing gear by rotating the lens housing to cause the sensor lens to move along an optical axis of the sensor lens via the threads in the lens housing and the threaded housing; wherein the first surface comprises a sensor lens surface; wherein the second surface comprises an optical sensor circuit board (448); and wherein the focusing mechanism is configured to be accessible from outside an optical housing that terminates the optical paths to adjust a focus of the sensor lens.
    [0002]
    Instrument, according to claim 1, CHARACTERIZED by the fact that it also comprises a beam divider (420) arranged along the optical excitation path and along the optical emission path.
    [0003]
    Instrument according to claim 1 or 2, CHARACTERIZED by the fact that the excitation source is configured to provide a plurality of excitation beams (405a, 405b) to illuminate biological samples, and in which at least some of the emissions comprise a fluorescent emission from at least some of the biological samples in response to at least one of the plurality of the excitation beams.
    [0004]
    Instrument according to any one of claims 1 to 3, CHARACTERIZED by the fact that the base comprises a thermal controller, and, optionally, in which a thermal controller configured to control a temperature of at least one of the base, the support of sample, or separate biological samples, or optionally, where the thermal controller comprises a thermocycler configured to perform a PCR assay.
    [0005]
    Instrument according to any one of claims 1 to 4, CHARACTERIZED by the fact that the optical excitation system comprises a sample lens configured to direct the excitation beams towards the base, wherein the sample lens comprises a field lens configured to extend over the plurality of spatially separated regions, and in which the sample lens is configured to provide a telecentric optical system for at least one of the sample holder, the spatially separated reaction regions, or the optical sensor.
    [0006]
    Instrument, according to claim 2, CHARACTERIZED by the fact that the beam separator comprises a constant reflectance over a wavelength band from 450 nanometers to 680 nanometers.
    [0007]
    Instrument, according to claim 2, CHARACTERIZED by the fact that the first excitation beam and the second excitation beam are temporally and / or spatially separated.
    [0008]
    Instrument according to claim 3, CHARACTERIZED by the fact that the plurality of excitation beam comprises a first excitation beam comprising a first wavelength band over which an intensity, power, or energy of the first excitation beam is above a first predetermined value, and a second excitation beam comprising a second wavelength range over which an intensity, power, or energy of the second excitation beam is above a second predetermined value, the first wavelength. A wave is at least one of (1) a central wavelength of the first wavelength range or (2) a wavelength of maximum electromagnetic intensity, power or energy over the first wavelength range, and the second wavelength wavelength is at least one of (1) a central wavelength of the second wavelength range or (2) a maximum intense wavelength electromagnetic age, power, or energy over the second wavelength range.
    [0009]
    Instrument according to claim 1, CHARACTERIZED by the fact that the excitation source comprises a plurality of individual excitation sources.
    [0010]
    Instrument, according to claim 9, CHARACTERIZED by the fact that the plurality of individual excitation sources forms a two-dimensional matrix of individual excitation sources.
    [0011]
    Instrument, according to claim 1, CHARACTERIZED by the fact that the optical sensor comprises a matrix sensor.
    [0012]
    Instrument according to claim 11, CHARACTERIZED by the fact that the matrix sensor comprises at least one of a complementary metal-oxide-semiconductor sensor or a load-coupled device sensor.
    [0013]
    Instrument, according to claim 1, CHARACTERIZED by the fact that the optical sensor comprises at least two matrix sensors.
    [0014]
    Instrument, according to claim 1, CHARACTERIZED by the fact that it also comprises a heated cover arranged adjacent to the base and including a plurality of openings configured to correspond to the plurality of reaction regions.
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    US20210214771A1|2021-07-15|
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    法律状态:
    2020-07-07| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2021-02-02| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2021-02-17| 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 05/02/2016, OBSERVADAS AS CONDICOES LEGAIS. |
    优先权:
    申请号 | 申请日 | 专利标题
    US201562112910P| true| 2015-02-06|2015-02-06|
    US62/112.910|2015-02-06|
    PCT/US2016/016886|WO2016127128A1|2015-02-06|2016-02-05|Systems and methods for assessing biological samples|
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