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    • 专利摘要:
    In addition to laser spot arrays, an apparatus and method are provided for performing CCD-based confocal spectroscopy. The sample is scanned by a plurality of excitation laser scanning spots. Scanning spots are generated by converting a laser excitation beam into a beam array, for example using only multibeam generating optics such as a Damann grating. Each scanning spot scans and excites separate areas of the sample. The fluorescence emitted by the sample is imaged by focusing on the surface of the CCD detector, which is electronically divided into bins of pixel, each bin corresponding to one scanning spot. Each bin serves as a confocal opening, and the confocal depth of focus can be controlled by changing the size of the bin. A plurality of CCD detectors are used for multichannel imaging of individual wavelengths. These devices and methods are useful for any spectroscopy application, including microscopy and microvolume laser scanning cytometry (MLSC).
    公开号:KR20010090718A
    申请号:KR1020017002397
    申请日:1999-08-20
    公开日:2001-10-19
    发明作者:루이스제이. 디이츠；이얀 왈톤；스코트 노튼
    申请人:써로메드, 인크.；
    IPC主号:
    专利说明:

    Novel optical structures for microvolume laser-scanning cytometers {NOVEL OPTICAL ARCHITECTURES FOR MICROVOLUME LASER-SCANNING CYTOMETERS}
    [1] Microvolume Laser Scanning Cytometry (MLSC) is a method of analyzing the representation of biological markers in biological fluids. See U.S. Patent Nos. 60 / 122,798, filed July 21, 1999, Cytometry 23: 177-186 (1996) to U.S. Patents 5,547,849 and 5,556,764, Dietz et al. (Each of which is referred to as part of the specification). Samples such as blood are cultured in capillaries with one or more fluorescently-labeled probes that bind specifically to specific biological markers, such as membrane proteins displayed on the surface of blood cells. Thereafter, the sample is analyzed by the MLSC instrument, which scans the excitation light coming from the laser over the sample along one axis of the capillary tube while the capillary itself is moved to the perpendicular axis by the automated stage. The fluorescent probe in the sample emits stokes-shifted rays in response to the excitation rays, which are collected by a cytometer and used to form an image of the sample. In such images, cells or particles entrapped in the fluorescent probes can be identified and measured by image analysis algorithms. Final information about the expression of biological markers in the sample can be used for diagnostic and predictive medical purposes.
    [2] Current laser scanning cytometers are based on flying spot confocal laser scanners. These systems use a rotating or reciprocating mirror, such as a mirror mounted on a galvanometer, to scan the laser excitation light in one direction along the sample. The sample is interpreted at right angles to the scan direction. The parallel excitation laser beam follows the epi-illumination path along the microscope objective and focuses on the sample and the mirror scan center is imaged at the entrance pupil of the microscope objective. Thereafter, the light rays emitted from the sample retrace the excitation ray path back to the scanning mirror where the excitation light rays are collected by the microscope objective lens and scanned. The emitted light rays are focused on the optical detector through the aperture after separating the excitation light reflected through the dichroic filter and the long pass filter. The opening serves as a spatial filter and reduces the amount of out-of-focus light entering the detector. The wider the aperture, the greater the focus depth of the system. The detector produces a signal proportional to the intensity of the incident light. Thus, when the laser scans the sample, the image is assembled pixel by pixel. Such optical structures are typically called confocal fluorescence detection.
    [3] To detect a plurality of fluorescent probes, the laser scanning cytometry system also includes a dichroic filter that separates the emitted light beam into its component wavelengths. Each distinct wavelength is imaged on an individual detector through an individual aperture. In this way, the image of the sample is assembled pixel by pixel for each emission wavelength. The individual images are called channels, and the final multicolor image is obtained by combining the individual channels.
    [4] The use of confocal four-channel fluorescence detection for MLSC is schematically illustrated in FIG. 1 and described in a US provisional application entitled “Microvolume Laser Scanning Cytometry” filed July 21, 1999. This application is incorporated herein by reference in its entirety and is hereby incorporated by reference. In this embodiment, the light rays from the laser are scanned onto a capillary array where each capillary contains a sample containing fluorescently labeled species. Specifically, parallel excitation light rays are provided by the He-Ne laser. Parallel excitation light rays are detected by an excitation dichroic filter. Upon reflection, light rays are transmitted on the galvanometer-driven scan mirror. The scan mirror can be vibrated quickly over a range of angles (eg +/- 2.5 degrees) fixed by a galvanometer. The scanning mirror reflects the projection beam into two relay lenses that image the scan mirror into the entrance pupil of the microscope objective lens. This optical configuration translates a particular scan angle in the mirror to a particular field position at the focal point of the microscope objective. The angular sweep is generally chosen to be within 1 mm scan width at the focal point of the objective lens. The relationship between the scan angle and the field position is essentially linearly proportional to this configuration and the angle in this range. Furthermore, the microscope objective lens focuses the incoming parallel beams and collects them in the focal plane of the objective lens. The spot diameter is what determines the optical resolution, which is determined by the focal length of the objective lens and the diameter of the parallel beam. Fluorescent samples placed in the capillary array in the path of the passed excitation beam emit stroke-shift rays. This light beam is collected and parallelized by the objective lens. This parallelized ray still strikes the scan mirror which emerges from the two paralleled relay lenses and reflects and scans them. The stroke-shift beam then passes through an excitation dichroic filter (most excitation rays reflected within the optics to this point are reflected by this dichroic) and then serve to filter the reflected excitation rays. Passes through the long pass filter (1). The fluorescent dichroic filter 10 then divides the two most blue fluorescent colors from the two optimal colors. The two deep blues are focused into the opening 1 to significantly reduce the out of focus fluorescence signal. After passing through the opening, the fluorescent dichroic 2 also separates the individual blues from each other. The individual blues are then parsed into two separate photomultipliers 1, 2. The two optimal colors are separated from the two blue colors by the fluorescent dichroic 10 and then focused into the opening 2. After passing through the opening 2, the optimum colors are separated from each other by the fluorescent dichroic 3. The individual reds are then parsed into photomultipliers 3, 4. In this way, four individual fluorescent signals can be sent simultaneously from the sample stored in the capillary to the individual photomultiplier light detectors PMT1-4. Each photomultiplier generates a current in response to the incoming fluorescent photon flux. Each of these currents is converted into individual voltages by a single preamplifier of the detection electronics. The voltages are sampled at regular intervals by the analog-to-digital converter to determine the pixel intensity value of the scanned image.
    [5] There is another known method for obtaining multichannel information in a microscopy environment. For example, it is known to use fluorophores that emit light as overlapping emission spectra, but they have different emission time constants. Time-resolved microscopy systems typically use very fast laser pulses and fast detection circuitry to solve nanosecond-range time signs of fluorophores in time-domains. Optionally, the measurement may be made in the frequency domain using an amplitude-modulated laser source and detection circuit that measure phase shift and modulation amplitude. Both techniques add enormous complexity to the fluorescence measurement system.
    [6] A typical MLSE instrument is to use a photomultiplier tube (PMT) as the light detector. Because PMT is cost effective and has a high data read rate, samples can be scanned quickly. However, the biggest disadvantage of PMT is low quantum efficiency. For example, in red near the infrared region of the electromagnetic spectrum, the PMT has a quantum efficiency of less than 10%, that is, less than one photon out of ten hitting the PMT is actually detected.
    [7] In order to have a high sensitivity and a high measurement speed, it is desirable to use a high performance laser source. For each fluorophore, there is a proportional relationship between the intensity of the excitation illuminance and the intensity of the emitted light. This proportionality is applied only until the fluorophore is saturated. At this point, the ground state of the fluorophore is basically depleted and all of the fluorophores are present in the excited electronic configuration. Increasing the laser power beyond the saturation point does not increase the intensity of the emitted light. This effect is particularly evident with fluorophores with long fluorescent life cycles, such as inorganic fluorophores and quantum dot nanocrystals. These molecules are saturated at relatively low power densities because of the long time constants of their fluorescent emission. Other undesirable processes, including photodestruction and intersystem crossing, can occur at high laser power. In many applications, it is desirable to operate the power density slightly below saturation.
    [8] In order to increase the speed so that confocal images can be obtained, the microscope system has been developed in such a way that a continuous laser excitation beam scans across the sample, rather than a single spot. In response, a series of emission light rays produced by the sample cause phases to form on a slit shaped aperture. Because light is scattered over a series of pixels, speed constraints by fluorophore photo-physics are avoided. However, the change in the lateral resolution with the depth of field and also the depth of focus of the line scanner is inversely proportional to the numerical aperture of the objective lens. MLSC applications require large field depths to accurately image cells of thick blood suspension. High sensitivity and speed require high numerical aperture lenses, but this will result in incredibly small field depths. This tradeoff ultimately results in limited speed and sensitivity.
    [9] Due to the constraints of using PMT as a photo detector, much research is currently underway towards developing more efficient detectors that allow fast image acquisition at low saturation power densities. One such photodetector is a charge coupled device (CCD). See, eg, G. Holst's CCD Array, Camera and Display Second Edition, JCD Publishing, and SPIE Optical Engineering Publisher 1998. The CCD consists of an array of sensitive photodetectors connected to each other, each of which has a quantum efficiency of over 80%. Despite their high efficiency, CCDs are not ideal for use in MLSC environments. One reason is that a CCD is usually used as an imaging device in which the entire field of view is excited and the CCD captures all emitted light rays within the field of view. When used in this way, field depth and sensitivity are combined like a line scanner. Moreover, full field illuminance and collection means that a significant amount of light out of focus is excited and received by the CCD detector. Although the CCD is used in a non-imaging mode in combination with the scan laser spot and the pinhole opening, in the same way that PMT is used, additional problems are encountered. First, if PMT is replaced with a CCD for multi-channel image acquisition at the same time, a separate CCD is required for each channel. The cost of providing a separate high efficiency CCD for each channel adds significantly to the cost of the instrument. Moreover, since the CCD takes significantly longer to read than the PMT, this places a large limit on the rate at which data is obtained.
    [10] The present invention relates to an optical structure for a spectroscope capable of acquiring data at a much faster rate than conventional systems. The instrument according to the invention can also be used for time-analytical measurement of fluorophore emission. The method and instrument according to the invention is useful in any application where spectroscopic data from a sample is required. According to a preferred embodiment, the methods and apparatus of the present invention are used for MLSC.
    [11] The present invention utilizes a CCD in which binning is used to divide a single CCD into groups of pixels that simultaneously collect data from multiple different sample regions. Preferred embodiments of the present invention utilize multiple laser excitation spots in combination with CCD photodetectors. In some embodiments, individual bins are subdivided to provide spectral information for each sample region. The pixel intensity values for each bin are collected by the computer to provide a seamless image of the sample in each channel.
    [12] Summary of the Invention
    [13] Two issues limit the speed and sensitivity performance of prior art systems. First, commonly used PMT detectors have low quantum efficiency, especially in red near the infrared region of the optical spectrum. Second, these systems typically scan focused laser spots to excite fluorescence emission in the sample. For high sensitivity and measurement speeds, it is desirable to use high power density excitation sources. However, outside of a constant saturation power density (power per unit area per laser spot), the excitation source saturates the fluorescent label and prevents further improvement in sensitivity and specific speed.
    [14] A preferred embodiment of the present invention uses a CCM detector (instead of PMT) as a non-imaging light detection device in a confocal scanning structure, where a laser spot array is scanned across the sample instead of a single spot. Two features of the present invention address the aforementioned limitations. First, high power laser excitation is separated into multiple spots thereby reducing the power density at each spot and minimizing the sensitivity and laser power constraints due to fluorophore saturation. Second, by defining a plurality of effective confocal openings as "binned" regions of pixels on the two-dimensional surface of the device, the CCD is used in a non-imaging mode. Each binning area is matched with an excitation laser spot that is focused into the sample. This structure maintains the controllable field depth of the PMT-based confocal spot scanner and also has the advantage of the very high quantum efficiency available with the CCD detector.
    [15] 1 illustrates a single-spot multi-channel MLSC system in which a mechanical confocal opening and a photomultiplier are used. The main ray of each ray bundle is traced.
    [16] FIG. 2 shows a two-channel spectrometer system in which three samples are scanned into a laser excitation spot and finally the emission light is collected onto a CCD photodetector divided into three confocal bins.
    [17] 3 shows a 512 * 64 pixel CCD detector divided into three right angle confocal bins.
    [18] 4 illustrates the relative movement of these spots when three laser excitation spots are scanned over a moving sample.
    [19] 5 illustrates one embodiment of performing multispot, multichannel confocal spectroscopy using a single CCD and confocal slit opening.
    [20] Figure 6 schematically shows a 625 * 488 pixel CCD photodetector configured for a six spot system with four spectral channels.
    [21] FIG. 7 shows a temporal confocal spectroscopy system in which a binned CCD collects emission light beams every selected time after laser spot excitation.
    [22] FIG. 8 shows a time-analyzed confocal spectroscopy system in which multiple optical fibers act as confocal openings formed over a sample every predetermined time after laser spot excitation.
    [23] 9 schematically depicts a non epi-illuminated spot scanner system.
    [24] The present invention is directed to spectroscopy methods and apparatus that provide a number of new optical configurations and / or time resolutions of individual fluorophore emissions that enable high speed multichannel imaging. In a preferred embodiment, the present invention uses a CCD as a light detector, wherein groups of pixels on the CCD form bins that are imaged on the sample by scanning optics. In a preferred embodiment, each bin serves as a confocal opening. Since the size of the bin determines the width of the cone of emitted light, the larger the size of the bin, the greater the depth of field. Light incident on the outside of the CCD of the bin is not detected. Therefore, each bin functions the same as the opening of the mechanical confocal. In a preferred embodiment, the present invention uses an array of laser spots to simultaneously scan a sample at multiple locations. Light emitted from each spot is imaged on a separate confocal CCD bin, which is made by focusing the separate images from each spot together. In another embodiment, a series of bins is imaged and excited on the sample at different times so that each bin on the CCD exhibits a different emission time, thereby allowing time-resolved fluorescence measurements. . The advantage of using a CCD bin as the opening of the confocal is that the reconstruction of the device is performed simply by changing the size and position of the bin on the CCD, rather than by any mechanical operation. The advantage of using multiple spots is that lower laser power is provided to each spot compared to a single spot system. Low laser power density minimizes fluorophore saturation, but the total system throughput is preserved by simultaneously detecting radiation from multiple excitation spots.
    [25] In all of the examples below, the methods and apparatus of the present invention are described in the data of MLSC. Those skilled in the art will appreciate that the methods and apparatus of the present invention can be used in any spectroscopic or cytometry application, including microscopy applications. Additionally, while fluorescence imaging applications are described, such scanning systems can be applied to many light scattering detection modes. Examples of such possible modes include luminescence, phosphorescence, Roman scattering, Ralyeigh scattering and Mie scattering.
    [26] Multiple laser spot excitation system to detect CCD light incident on the bin
    [27] In one embodiment of the invention, the laser excitation beam is converted into a beam array by a device such as a Damann grating. Alternatively, other spot generating devices such as microlens arrays or fiber bundles can be used. The system is not limited to using spots of a typical array, but may use spots of a two-dimensional array. This system allows larger area CCD detector areas to be used, thus improving readout performance. Other embodiments of the device may use a laser diode array without using a single laser beam excitation source, thus eliminating the need for a separate beam generator. The source of the beam is imaged in the center of a scanning mirror device such as a galvanometer using a relay lens. Another embodiment of the apparatus of the present invention involves using another beam deflection method. Such methods include, but are not limited to, piezoelectric scanners, polygon mirrors, acoustic-optical deflectors, and hologons. In an embodiment of the invention, the scan center of the galvanometer is in turn imaged into the entrance pupil of the microscope objective by a second set of relay lenses. The laser beam array is therefore focused by the objective lens into a spot array in the focal plane of the objective lens. Each spot in the array scans and excites a separate region of the sample, which is moved at a constant speed along an axis perpendicular to the laser spot scan axis. The fluorescence emitted by the sample is collected by the objective lens and imaged on the surface of the CCD detector passing through a dichroic filter and electrically separated into bins of pixels of desired size. The emitted light impinging outside the CCD of the bin is not detected, and therefore the bin functions as an opening of the confocal that can be simply controlled by changing the bin dimension of the focal depth of the focus. The larger the area of the bin, the greater the depth of focus.
    [28] Multi-spot systems can be used for multichannel imaging by, for example, using dichroic filters to separate fluorescence emission into individual wavelengths and directing each component wavelength to a separate CCD detector. In this embodiment, different CCDs are used for each channel, but the bin configuration for each CCD is the same. The CCD is read periodically while maintaining the proper registration of the individual color images. Therefore, this embodiment provides a multichannel MLSC device in which the confocal depth of focus is computer controlled (by changing the empty dimension) rather than mechanically controlled (by changing the size of the opening of the confocal).
    [29] FIG. 2 shows one embodiment of the invention in which three laser excitation spots are generated and the excitation dichroic is reflected on the galvanometer scan mirror. (In this figure, three spots are chosen to illustrate the present invention for convenience. As will be described below, the present invention includes any system using one or more spots.) Scanning spots are passed through a relay lens to a microscope. The incident pupil of the objective lens is reached and focused on the sample. Emission light (three radiation lines) from the sample is collected by the microscope objective lens and returned back to the dichroic filter along the path of the excitation spot. The emitted light passes through an excitation dichroic and long-pass filter, which is split into two wavelength portions by the emission dichroic filter. These two parts are then imaged on a CCD separated by the focus lens, each CCD divided into three confocal bins. A schematic diagram of a 512 x 64 pixel CCD detector divided into three rectangular confocal bins is provided in FIG. 3.
    [30] In a preferred embodiment, the linear array of laser spots excites radiation from the sample. The scanning mirror device rotates the scanning of the laser spot in a direction parallel to the line formed by the spot array. The total scan deflection of each spot is selected such that each spot scans past a sample length having a length approximately equal to the distance between the spots. The sample is moved along an axis perpendicular to the laser spot scan axis. This operation is schematically shown in FIG. 4A, where the three spots are scanned on the vertical axis and the sample is moved horizontally. Therefore, the relative spot movement follows the saw blade pattern. When the spot array is scanned along the sample by the scanning mirror device, the CCD bin is read out periodically. The timing of this read operation determines the pixel size within the scan range. Alternatively (FIG. 4B), the three spots are aligned parallel to the sample movement direction. Spots are scanned past the complete sample. When one spot reaches the scan start position of the next spot, the sample is reciprocated so that the first spot starts scanning again at the previous stop position of the last spot.
    [31] When scanning is performed, each laser spot produces a 2-D image obtained by the corresponding bin of the CCD detector. Images from each spot do not overlap, or only slightly overlap. Once scanning is complete, the individual images can be combined together by a computer to provide a single seamless image.
    [32] Any number of spots can be used in the present invention. The advantage of using multiple spots is that a low laser power density is applied to each spot, minimizing flowophore saturation. For example, each spot in the ten spot arrays has a power density of that one tenth as compared to the power density of the laser spot in a single spot system when using the same power laser source. However, each spot stays 10 times longer in any area of the sample compared to in a single spot system, so the total photon flux per image pixel is equal. Since all ten spots are excited and detected in parallel, the total scan time of the sample is the same in each case. However, by using the CCD as the photo detector, the sensitivity is significantly increased. CCDs can have quantum efficiencies that are at least three times the quantum efficiency of PMTs, and furthermore use lower excitation power densities, resulting in significant sensitivity due to saturation prevention, photo-destruction and other nonlinear process excitation Can be increased. Therefore, a multispot system using CCD detection may have a sensitivity of 6 to 10 times that of a single spot PMT system operating at the same scan rate. This increase in sensitivity can be developed to shorten the scan time, and thus, a multispot system can produce an image equivalent to a single spot system in a remarkably short time. Alternatively, a multispot CCD system may operate at the same scan rate as a single spot system but detect a radiation intensity that a conventional PMT single spot system could not detect at that scan rate. Another advantage of using low laser power densities is the use of saturated fluorophores at relatively low power densities such as inorganic fluorophores or quantum dot nanocrystals with long emission time constants.
    [33] The number limit of the spots is determined by the amount of crosstalk between the allowable spots and the required axial response of the system. The greater the number of spots in the array, the narrower the spacing of the confocal bins on the CCD. The axial response is effectively reduced in proportion to the bin size. Also, the closer the bins are, the more unacceptable light from one bin collides with each other, eventually reducing system sensitivity. The present invention includes any system having one or more spots. 2 to 1000 spots are preferred, and 5 to 400 spots are more preferred.
    [34] Using a CCD bin such as a confocal opening has a substantial advantage since it is relatively simple to change the depth dimension of the confocal of the field. The mechanical confocal openings in the focused optical system are typically only a few micrometers in diameter and therefore require a complex and accurate mechanical system to control the opening size. In contrast, the CCD bin can be changed simply by reconstructing the CCD array using a computer.
    [35] The use of CCDs in MLSC has marked improvements over prior art MLSC devices that use PMT for light detection. Biological fluids analyzed by MLSC can auto-fluoresce and absorb or scatter excitation light. By using fluorophores that are excited by red light (such as the 633 nm line from the HeNe laser), this problem is reduced and MLSC analysis can be performed on whole blood. However, PMT has a quantum efficiency of less than 10% in the red portion of the electromagnetic spectrum, which degrades the sensitivity when such fluorophores are used. In contrast, many types of CCDs have quantum efficiencies of at least 80% in the same region of the spectrum.
    [36] As previously described, current CCD detectors have a lower data read rate than PMT. If a single spot is scanned on the sample and the emitted light is imaged on the CCD, the CCD must be read sequentially for every single pixel in that image. In contrast, the multispot system provided by the present invention can simultaneously acquire data for X pixels, where X is the number of spots. Therefore, a 10 spot system provides data for 10 pixels in the image at each read event, whereas a single spot system provides data for only one single pixel at each read event. Therefore, the multispot system of the present invention can allow the advantage of the increased sensitivity provided by the CCD to be achieved while at the same time minimizing the problems associated with the low data reading speed of the CCD. CCDs with higher read rates are likely to be put to practical use in the future. Using such an improved CCD will further increase the sensitivity and speed of the apparatus and method of the present invention.
    [37] It should be noted that all embodiments of the present invention may use conventional PMTs as light detectors rather than CCDs. In such embodiments, the conventional confocal opening is to provide the necessary light rejection outside the focus fluorescence. These openings are aligned in a pattern consistent with the laser spot array.
    [38] Multiple laser spot excitation system for performing spectral analysis on a single CCD
    [39] In some embodiments, a single CCD is used for multichannel imaging of the sample. In this embodiment, one line of laser spot is scanned on top of the sample and the emitted light is imaged on one line of confocal opening as described above. The layout of the array of apertures parallels the layout of the array of laser spots, so that the emitted light from each laser spot passes through the other aperture. After the light passes through the aperture, each beam of emitted light passes through scattering optics that spread out the component wavelengths. Suitable wavelength dispersion optics include, but are not limited to, echelle gratings, holographic concave gratings, transmission gratings, or prisms. In addition, certain wavelengths can be mechanically incident on the detector using a constant deflection dispersion prism, such as a Pelin-Broca prism, or using a resonant grating filter. Electro-optical methods of selecting wavelengths include the use of an acoustooptic adjustable filter or an electro-optic resonant grating filter. The scattering optics also image each aperture on individual rectangular regions of the CCD such that light passing through each aperture develops in a spectrum along the long axis of one rectangle. Each rectangular region on one CCD is subdivided into bins along its long axis so that each bin collects different wavelengths of developed light. For example, for four color fluorescence detection, each rectangle can be subdivided into four spectral bins along its long axis. Therefore, each rectangular area on the CCD can essentially perform spectral analysis of the emitted light in response to excitation by a particular spot.
    [40] In a preferred system for this embodiment, the sample is scanned into one line of laser spot, and all emitted light from the sample is imaged on one rectangular “slit” confocal opening parallel to the line of laser spot. do. The emitted light then passes to a scattering optic that spectrally spreads each emitted beam of light at its component wavelengths. The dispersion axis is orthogonal to the long axis of the confocal "slit". The dispersion optics also image the component wavelengths from each emission spot on a separate rectangular CCD region. Here, the long axis of each CCD rectangle is parallel to the axis where the scattering optics develop the emission spot. Thus, the long axis of each CCD rectangle is orthogonal to the long axis of the "slit" opening. Each rectangular region is subdivided into spectral bins along its long axis such that each spectral bin collects light of different wavelengths generated by the dispersion of a single emission spot. The rectangular area of the CCD serves as a second "slit" confocal opening oriented in a dimension opposite the mechanical "slit" opening. As a result, the final image has confocals in both dimensions. The focal depth of this system can be controlled by changing the width of the mechanical "slit" opening and the width of each CCD rectangle equally.
    [41] 5 schematically illustrates one embodiment using slit openings and concave gratings for wavelength dispersion. In this figure, the laser light is reflected on the spot generating optics (by the mirror). Three laser spots are generated by the spot generating optics, passing through the lenses 1 and 2 to reach the dichroic filter, which reflects the laser spot on the scanning galvanometer mirror. The spot then passes through the lenses 3, 4 to reach the mirror 2, which is concentrated again at the entrance pupil of the microscope objective lens. The objective lens focuses the spot on the sample and the light emitted from the three spots is collected by the objective lens. The radiation beam follows the path of the laser spot again and returns to the dichroic filter. The emitted light passes through a dichroic filter and enters the lens 5 which focuses the light in the slit opening. The focused light passes through the long pass filter and then passes through the confocal slit opening oriented along the long axis of the slit parallel to the vertical axis. The radiation beam passing through the slit opening then falls on the concave grating which reimages the spot and wavelength onto the detector. In this figure, each radiation beam is spread at multiple wavelengths along the horizontal axis. Therefore, the horizontal axis of the CCD provides spectral information for each emitted ray and the vertical axis provides spatial information.
    [42] 6 diagrammatically shows a 625 pixel x 488 pixel CCD light detector configured for a six spot system with four spectrochannels. The CCD is divided into six rectangular regions and each region is subdivided into four optical bins. As shown in Figure 5, when used in combination with a vertically oriented slit aperture of the confocal, the horizontal axis of the CCD provides spectral information and the vertical axis provides spatial information. In FIG. 6 the height of each rectangle can be adjusted to change the confocal point of the image on the horizontal axis. Suitable CCDs for the present application are Pluto ™ CCDs available from Pixelvision.
    [43] As described above, conventional attempts to use line illumination in MLSC have not achieved desirable improvements in speed and sensitivity due to the interaction of the number of condensing apertures and the depth of the system subject. The present invention provides a method of dispersing excitation light over an area larger than a single spot for a first time while maintaining the subject's depth and axial response of a flying spot confocal laser scanner.
    [44] This embodiment is also mechanically simpler than the embodiment described above where a line of pinhole openings is used. Changing the size and orientation of a single slit opening is simpler than changing the size of a series of relatively smaller pinhole segments. Thus, this embodiment maintains the true two-dimensional confocal of the pinhole opening structure and also has the mechanical simplicity of the confocal slit structure.
    [45] An additional advantage of performing real light analysis on a CCD in the manner outlined above is that the CCD binning can be electronically controlled in the spectral dimension. Each detection color can be optimized for the specific analysis to be performed. It also eliminates the need for many many color filters in detection systems, which differ from unit-to-unit in a unit and can vary with temperature and humidity.
    [46] Another advantage of using the CCD system outlined above is that alignment of the mechanical confocal opening with the CCD can be easily achieved electronically. Rather than physically moving the openings, the position of the bins on the CCD can be adjusted to ensure that each bin is perfectly registered with the corresponding opening. For example, this method can be automated using test slides containing all fluorescent labels to be used in the assay.
    [47] In another embodiment of the present invention, it is possible to use non-epi-illumination of a sample. In this embodiment shown in FIG. 9, excitation light is taken into the sample without passing through a collection objective. This method is called off-axis-illumination (see, eg, US Pat. No. 5,578,832). As in epi-illumination, a fan of the laser beam occurs. Possible examples of forming optics optics include, but are not limited to, Darmann and other gratings, fiber optic bundles, micro-mirror arrays, acoustic light, and electro-optical devices. It is not limited. The fan of light rays is condensed again by a first fan lens and converged on a scanning device such as a reciprocating mirror with a second pan lens. The rays then pass through the final lens so that each spot is focused on the sample. The final lens is configured such that the excitation beam is approximately 45 degrees to the sample. The divergent light is then focused and again formed on a CCD detector with a tube lens. Undesired excitation light is removed with a long path cut filter. If the spot is not de-scanned, the scanned spot will be moved onto the detector. However, the modified CCD bin may be selected to read out along the X spot. Alternatively, the focused rays can de-scan the spot through a second reciprocating device such as a mirror in synchronization with the excitation mirror. For example, in the case where the wavelength is selected by an optical filter such as a dichroic filter, a number of different array detectors can be used to focus discrete wavelengths.
    [48] Despite the additional complexity that arises in de-scanning spots, off-axis has some advantages over epi-illumination. No excitation dichroic filter is required and very many different excitation wavelengths can be used without changing the filter. Moreover, extreme excitation wavelengths, i.e. ultraviolet or infrared light, may be used that are incompatible with the focusing optics. Reported examples of using these wavelengths are two-photon up-converting phosphors that use 980 nm excitation and emanate in the visible region and nano-crystals that are optimally excited within UV, <400 nm but emanate in the visible region. to be. Science 281: 2013 (1998), by Bruchez et al. SPIE, Wrisht et al., International Procedure for Optical Sensitive Biochemical Diagnostics of SPIE, International Society II (Feb10-Feb12 97v 2985 1997, San Jose, Calif.).
    [49] All embodiments of the present invention described above include a system design in which an area of a sample illuminated by a spot array is imaged on the surface of a CCD detector by an optical system. An embodiment of an alternative system, in conjunction with an optical system that does not make an image, such as fiber optics or fiber bundles, uses mechanical apertures to provide the necessary confocal apertures to deliver light through the apertures to the surface of the detector. The system designer can thus select the optimal spatial mapping between the excitation spot array and the detector surface. This allows designers to choose from a wide range of detector devices, or more effectively utilize device surface areas. For example, if the excitation spot array constitutes a linear array of spots, the linear array of apertures can be used to condense the light emitted from the sample passing light into the optical fiber, with one fiber or fiber bundle per aperture. . The outputs of multiple fibers or fiber bundles can be aligned, for example, into a two-dimensional array of squares and images can be made on the detector surface either directly or through distributed optics. In this way, the designer provides a better match to the form factor of a given CCD device, or fills the surface of the CCD with more spots than using only image-making optics.
    [50] Time-Analytical Spectroscopy System
    [51] The method of the present invention can be used to perform a time analysis MLSC. As described above, in time-analyzed fluorescence microscopy, after excitation illumination, the phases of the samples are taken at fixed time intervals. This makes it possible to observe multiple phosphors with different divergence time constants. In the present invention, a time analysis image can be obtained by creating a series of confocal CCD empty apertures on a sample behind a laser excitation spot at a predetermined time. The confocal bin is scanned onto the sample by the same optical system that scans the laser spot. Physical separation between the CCD bins is mapped to the difference in time for the sample. The time interval is a function of the scan rate across the sample.
    [52] Such a system may, in one embodiment, schematically illustrated in FIG. 7, function as follows. At t = 0, the laser spot is excited to the first region of the sample where the phosphors F1 and F2 are present. F! Has a divergence time constant where the fluorescence emitted from F1 actually matches the excitation. Therefore, the light from F1 returns the path of the laser beam, penetrates the dichroic filter, and forms an image on the CCD bin B1. At t = 1, the scanning mirror is deflected, and the second region of the sample is subjected to excitation illumination. At t = 1, the excited F2 is emitted at the first region of the sample at t = 0. Since the scan mirror is deflected between t = 1 and t = 1, the optical path accompanying by F2 divergence is not matched with the laser path. As a result, the fluorescence from F2 follows the path traveled by a predetermined amount proportional to the fluorescence from F1. Light from F2 can be focused on the CCD by a separate confocal bin B2. It will be appreciated that additional bins can be defined on the CCD to obtain additional time intervals. The distance between bins (at a constant scan rate) determines the time interval between events for measuring each fluorescence.
    [53] In another embodiment, a multispot excitation array as described above is used for time analysis measurements. In this embodiment, the CCD is divided into a matrix of bins. In one dimension, the bins provide location information for the emitted light. In another dimension, the bins provide a time analysis fluorescence measurement. For example, a system that performs three temporal analysis measurements for each ten excitation laser spots constitutes a 10 × 3 array of CCD bins. To optimize detection for specific phosphors, the dimensions of each bin can be varied independently.
    [54] In another embodiment, time analysis spectroscopy is performed using multiple pinhole confocal openings operably connected to the light detection device. The space between the confocal openings determines the time interval for the instant of fluorescence measurement. As in the embodiment involving the CCD bin, after the sample is excited to a particular area, individual pinhole confocal openings are scanned over that area at different times. As an alternative to the pinhole opening, this embodiment can be performed using an optical fiber. The core of each fiber acts as a pinhole and the light propagated through the fiber is carried to multiple PMTs. As before, the spacing between the irradiated ends of the optical fibers determines the time interval between each type and measurement. This embodiment is shown schematically in FIG. 8.
    [55] In another embodiment, temporal analysis fluorescence spectroscopy is performed in tandem with divergent wavelength spectroscopy of light emitted at each time interval. In some embodiments, this is done using a series of pinhole openings that are imaged onto the sample behind a single laser excitation spot at different times, as described above. The divergent light passing through each aperture then passes through a scattering optic that accelerates the divergent light into constituent wavelengths, such as concave diffraction grating or prism. From each time interval the constituent wavelengths are imaged on a separate rectangular region of the CCD by the dispersion optics, where the long axis of the rectangle is parallel along the axis where the emitted light is spread. Each pinhole opening maps to a separate rectangular area on the CCD. Individual rectangles are subdivided into spectral bins along the long axis of the rectangle, and spread light from each aperture is directed onto the bins in a wavelength dependent manner.
    [56] In another embodiment, the present invention provides a method for performing multi-spot time analysis fluorescence spectroscopy in cooperation with fluorescence emission wavelength spectroscopy. This system functions in the same way as a multi-spot system with a confocal slit structure as described above. However, in order to perform time-analytical measurements, the system has a series of slit openings that are imaged onto the sample behind the excitation spot at time intervals. An image is created on the spectroscopic bins arranged in the rectangles, which are oriented at right angles to the confocal slit. In some embodiments, separate CCDs are used to create an image of light coming through each confocal opening. Thus, a three-slit configuration requires three CCDs. In other embodiments, a single CCD is used to create an image of light from all apertures. In this embodiment the CCD is configured to provide a rectangular matrix, with each opening imaged over a particular column (or row) of the rectangle on the CCD. Thus, a single CCD provides the data at the location, time analysis and the spectrum of each fluorescence emission instant.
    权利要求:
    Claims (30)
    [1" claim-type="Currently amended] In a confocal scanning system,
    (a) means for generating a plurality of excitation light spots, the emission light being emitted by the sample in response to excitation by each of the spots, thereby scanning the sample;
    (b) at least one detection device disposed thereon so that the emitted light is imaged simultaneously
    Confocal scanning system comprising a.
    [2" claim-type="Currently amended] The confocal scanning system of claim 1, wherein 3-100 spots are generated.
    [3" claim-type="Currently amended] The confocal scanning system of claim 1, wherein 5-25 spots are generated.
    [4" claim-type="Currently amended] The confocal scanning system of claim 1, wherein the emitted light comprises multiple component wavelengths.
    [5" claim-type="Currently amended] The confocal scanning system of claim 4, wherein each component wavelength is imaged on a detection device separated by dichroic filters.
    [6" claim-type="Currently amended] The confocal scanning system of claim 1, wherein the sample comprises a blood sample contained within a capillary.
    [7" claim-type="Currently amended] 7. The confocal scanning system of claim 6, wherein the capillary tube is translated perpendicular to the scan of excitation light.
    [8" claim-type="Currently amended] The confocal scanning system of claim 6, wherein the spots of the excitation light are scanned in a direction parallel to the capillary axis.
    [9" claim-type="Currently amended] 7. The confocal scanning system of claim 6, wherein spots of excitation light are scanned in a direction perpendicular to the capillary axis.
    [10" claim-type="Currently amended] The confocal scanning system of claim 1, wherein the one or more detection devices are charge coupled devices (CCDs).
    [11" claim-type="Currently amended] 11. The confocal scanning system of claim 10, wherein each CCD is divided into a plurality of bins, each bin collecting a portion of the emitted light generated from excitation of the sample by one of the spots.
    [12" claim-type="Currently amended] 12. The confocal scanning system of claim 11, wherein the size of each bin is selected such that only the emission light from within a predetermined focal depth of the sample is collected.
    [13" claim-type="Currently amended] 5. The confocal scanning system of claim 4, further comprising means for scattering the emitted light into its component wavelengths.
    [14" claim-type="Currently amended] 14. The confocal scanning system of claim 13, wherein said means for scattering emitted light at its component wavelengths is a dichroic filter.
    [15" claim-type="Currently amended] 14. The confocal scanning system of claim 13, wherein said means for scattering emitted light at its component wavelengths is a prism.
    [16" claim-type="Currently amended] 14. The confocal scanning system of claim 13, wherein said means for scattering emitted light at its component wavelengths is a grating.
    [17" claim-type="Currently amended] 14. The confocal scanning system of claim 13, wherein one detection device is used.
    [18" claim-type="Currently amended] 18. The confocal scanning system of claim 17, wherein said detection device is a CCD.
    [19" claim-type="Currently amended] The confocal scanning system of claim 1, further comprising a microscope objective.
    [20" claim-type="Currently amended] 20. The confocal scanning system of claim 19, wherein the excitation light and the emission light pass through the microscope objective lens.
    [21" claim-type="Currently amended] The confocal scanning system of claim 1, further comprising one or more fiber optics for transmitting the emitted light to one or more detection devices.
    [22" claim-type="Currently amended] 14. The confocal scanning system of claim 13, further comprising an aperture corresponding to each spot of emitted light such that only light emitted from within the predetermined focal depth of the sample passes through the detection device.
    [23" claim-type="Currently amended] 12. The confocal scanning system of claim 11, further comprising a slit aperture corresponding to each spot of emitted light such that only emitted light from within a predetermined focal depth of the sample passes through the detection device.
    [24" claim-type="Currently amended] In a confocal scanning system,
    (a) means for scanning a sample along an axis by generating a plurality of excitation light spots, the excitation light being emitted by the sample in response to excitation by the spot;
    (b) a spatial filter comprising a rectangular opening and arranged to image the emitted light thereon;
    (c) means for scattering the emitted light passing through the spatial filter at its component wavelengths;
    (d) a CCD arranged so that the component wavelengths are imaged thereon
    Including,
    The CCD is divided into rectangular pixel regions perpendicular to the spatial filter such that each rectangular region receives a portion of the emission light generated from excitation of the sample by one of the spots,
    Each rectangular region is divided into at least two spectral bins along its major axis such that each spectral bin collects different wavelengths of the portion,
    And the size of each spectral bin is selected such that the portion comprises emitted light from a predetermined focal depth of the sample.
    [25" claim-type="Currently amended] In a time-resolved confocal scanning system,
    (a) means for generating one or more diffraction-limited spots of excitation light to scan the sample along the axis;
    (b) a plurality of confocal apertures, each of the confocal apertures in which the emitted light generated from excitation of the sample by one of the spots is defined after excitation by the spot. Positioned to be measured by the scanning means in time;
    (c) photodetection means interlocked with said confocal opening
    Confocal scanning system comprising a.
    [26" claim-type="Currently amended] 27. A confocal scanning system according to claim 25, wherein said light detecting means is a CCD and said confocal opening comprises pixel bins on said CCD.
    [27" claim-type="Currently amended] In a confocal scanning system,
    An excitation energy transfer system for redirecting energy towards the first region of the sample;
    A light detection system for measuring the fluorescence of said sample induced by said energy,
    A spatial filter optically disposed between the sample and the light detection system to confine the measured fluorescence to at least one second region of the sample;
    A mechanism for coupling the energy transfer system and the spatial filter to the sample such that the first and second regions sequentially scan the sample
    Confocal scanning system comprising a.
    [28" claim-type="Currently amended] 28. The confocal scanning system of claim 27, wherein said mechanism scans said first and second regions with a distance and a speed that allows said fluorescence to be measured for a predetermined time after said energy.
    [29" claim-type="Currently amended] 28. The confocal scanning system of claim 27, further comprising a plurality of spatial filters comprising pinhole apertures aligned such that the fluorescence is measured multiple times after the energy.
    [30" claim-type="Currently amended] 28. The confocal scanning system of claim 27, wherein said energy comprises laser energy.
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    同族专利:
    公开号 | 公开日
    WO2000011024A3|2000-06-29|
    US6603537B1|2003-08-05|
    AU5900199A|2000-03-14|
    US6979830B2|2005-12-27|
    CA2341359A1|2000-03-02|
    US20040079893A1|2004-04-29|
    NZ510096A|2003-02-28|
    US6800860B2|2004-10-05|
    JP2002523731A|2002-07-30|
    EP1121582A4|2002-10-23|
    ZA200101459B|2002-02-21|
    AU749690B2|2002-07-04|
    US20050057749A1|2005-03-17|
    EP1121582A2|2001-08-08|
    WO2000011024A2|2000-03-02|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    法律状态:
    1998-08-21|Priority to US9750698P
    1998-08-21|Priority to US60/097,506
    1999-08-20|Application filed by 써로메드, 인크.
    1999-08-20|Priority to PCT/US1999/019374
    2001-10-19|Publication of KR20010090718A
    优先权:
    申请号 | 申请日 | 专利标题
    US9750698P| true| 1998-08-21|1998-08-21|
    US60/097,506|1998-08-21|
    PCT/US1999/019374|WO2000011024A2|1998-08-21|1999-08-20|Novel optical architectures for microvolume laser-scanning cytometers|
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