Cell analyzer and optical detection system thereof

Abstract

The utility model relates to a cell analyzer and an optical detection system thereof, the optical detection system comprises a light source module, a flow cell and an optical detection unit, the light source module comprises a laser source, a first aspheric lens and a second aspheric lens, a primary optical axis of the first aspheric lens penetrates through the laser source and the second aspheric lens, and a secondary optical axis of the second aspheric lens penetrates through the flow cell. The first aspheric lens is used for collimating light emitted by the laser source; the primary optical axis penetrates through the flow cell, and the second aspheric lens enables the collimated light beam to generate a focusing light spot in the flow cell so as to excite a measured biological sample passing through the flow cell to generate a to-be-measured optical signal; and the optical detection unit is arranged corresponding to the flow cell and is used for detecting the to-be-detected optical signal. Through the arrangement of the first aspheric lens and the second aspheric lens, the complex design of multiple times of convergence of a spherical lens or a cylindrical lens is simplified, the inherent astigmatism characteristic of the laser source is improved, the quality of converged light spots output by the laser source is improved, and then the detection performance of the cell analyzer is improved.

Description

Technical Field

[0001] The utility model relates to the technical field of cell analyzers, in particular to a cell analyzer and an optical detection system thereof. Background Art

[0002] As a conventional analytical instrument, cell analyzers are widely used in the fields of life sciences and medicine. They are usually based on the principle of flow cytometry and can measure and analyze target particles or cells in the sample being tested. Cell analyzers generally include a light source, a flow cell, and an optical signal detection part, wherein the flow cell is used to form a place where the incident light source interacts with the particles or cells being tested. When the incident light source irradiates the particles or cells being tested in the flow cell, light scattering signals and fluorescence signals are generally generated, wherein the light scattering signal is consistent with the wavelength of the incident light source, and mainly characterizes the physical characteristics of the particles or cells being tested, such as size, internal complexity, etc.; the fluorescence signal is different from the wavelength of the incident light source, and is mainly generated by dye probes. The dye probes can specifically bind to certain parts of the particles or cells being tested, and the target of interest can be analyzed by detecting the fluorescence signal generated by the dye probe. The optical signal detection part is used to collect the optical signals generated by the particles or cells being tested, and form electrical signals that can be processed by the analyzer through photoelectric conversion.

[0003] The light source has a significant impact on the analytical performance of the cell analyzer. Considering that the measured particles or cells are generally at the micron level, such as white blood cells in human blood at 8-20um, red blood cells at 6-8um, and platelets at 2-4um, the signals generated by these target particles under the excitation of the light source are also small, which is prone to the problem of insufficient system resolution. Therefore, the light source outputs a beam size at the micron level to increase the optical power per unit area, which is of great significance to the detection performance of the analyzer.

[0004] At present, the light source of the cell analyzer generally includes semiconductor lasers, and for the common red and blue light bands, it is usually a laser diode. Laser diodes have different divergence angles in the emitting PN junction plane, and for TM mode laser diodes, the light beam is generally converged into a micron-level spot in the direction of the large divergence angle to illuminate the particles or cells to be measured.

[0005] However, due to the influence of the large divergence angle of the laser diode, the light beam emitted by the laser diode cannot generally be directly converged into a focused spot by a lens. The industry usually uses a collimating lens to collimate the elliptical light beam emitted by the laser diode into parallel light, and then uses one or more spherical mirrors or cylindrical mirrors to converge the collimated light beam into a micron-level beam. However, when using a spherical lens or a cylindrical mirror to focus the light, the system aberration is large. In order to reduce the aberration, multiple spherical lenses or cylindrical mirrors are generally used to converge multiple times. However, this method increases the volume and cost of the entire light source part on the one hand, and increases the difficulty in production and assembly on the other hand. Especially for the gradually converging system, once there are installation errors such as assembly eccentricity between the lenses, it has a significant impact on the quality of the light beam output by the light source part. Utility Model Content

[0006] The embodiment of the utility model provides a cell analyzer and an optical detection system thereof to solve the above technical problems.

[0007] An optical detection system for a cell analyzer, the optical detection system comprising:

[0008] A light source module, comprising a laser source, a first aspheric lens and a second aspheric lens arranged in sequence, wherein the first aspheric lens has a main optical axis, the main optical axis passes through the laser source and the second aspheric lens, and the first aspheric lens is used to collimate the light emitted by the laser source;

[0009] a circulation cell, which is arranged corresponding to the light source module and through which the main optical axis passes; the second aspheric lens enables the collimated light beam to generate a focused light spot in the circulation cell to excite the biological sample to be tested passing through the circulation cell to generate a light signal to be tested; and

[0010] The optical detection unit is arranged corresponding to the circulation pool and is used to detect the optical signal to be detected.

[0011] In one embodiment, the light source module includes a plano-concave cylindrical mirror, and the plano-concave cylindrical mirror is arranged between the first aspheric lens and the second aspheric lens, or the plano-concave cylindrical mirror is arranged between the second aspheric lens and the circulation pool.

[0012] In one of the embodiments, the cylindrical generatrix of the plano-concave cylindrical mirror is parallel to the flow direction of the biological sample to be tested in the circulation pool.

[0013] In one embodiment, the optical detection unit includes a first scattering detection module, which includes a third aspheric lens, a long-wave pass dichroic mirror and a first detector arranged in sequence. The side scattered light in the light signal to be measured that is perpendicular to the propagation direction of the incident light is emitted from the circulation pool, passes through the third aspheric lens and the long-wave pass dichroic mirror, and is reflected by the long-wave pass dichroic mirror to the first detector.

[0014] In one embodiment, the third aspheric lens is attached to the outer surface of the outer wall of the circulation cell, and the refractive index of the third aspheric lens is greater than the refractive index of the outer wall of the circulation cell.

[0015] In one embodiment, the focal length of the third aspheric lens is f, the center thickness of the third aspheric lens is d, the diameter is D, the thickness of the outer wall of the circulation pool is h, f≤d+h / 2, and D≤h.

[0016] In one embodiment, the first scattering detection module includes a doublet lens and a plano-convex lens which are sequentially arranged between the third aspheric lens and the long-wave pass dichroic mirror.

[0017] In one embodiment, the combined focal length of the third aspheric lens, the doublet lens and the plano-convex lens is no more than 10 mm.

[0018] In one embodiment, the optical detection unit includes a fluorescence detection module and a second detection module, the fluorescence detection module includes a filter and a second detector, and the light transmitted from the long-wave pass dichroic mirror is converged to the second detector through the filter; the second detection module includes an angle aperture, a focusing lens and a third detector arranged in sequence along the main optical axis, the angle aperture is arranged corresponding to the circulation pool, and the light emitted from the angle aperture is focused to the third detector through the focusing lens to detect the scattered light signal in the light signal to be measured that is in the same wavelength band as the light incident to the circulation pool.

[0019] A cell analyzer comprises a sampling unit, a reaction unit, a signal processing unit, an output unit and the optical detection system described in any one of the above items, wherein the sampling unit is used for aspirating and transporting an initial biological sample, the reaction unit is used for reacting the initial biological sample with a corresponding reagent to generate a biological sample to be detected suitable for detection by the optical detection system, and the signal processing unit is used for processing the output signal of the optical detection unit and presenting the detection result through the output unit.

[0020] The above optical detection system is used in a cell analyzer. The optical detection system includes a light source module, a circulation cell and an optical detection unit. The light source module includes a laser source, a first aspheric lens and a second aspheric lens arranged in sequence. The first aspheric lens has a main optical axis, which passes through the laser source and the second aspheric lens. The first aspheric lens is used to collimate the light emitted by the laser source. The circulation cell is arranged correspondingly to the light source module. The second aspheric lens enables the collimated light beam to generate a focused light spot in the circulation cell to stimulate the biological sample to be tested passing through the circulation cell to generate a light signal to be measured. The optical detection unit is arranged correspondingly to the circulation cell to detect the light signal to be measured. The arrangement of the first aspheric lens and the second aspheric lens simplifies the cumbersome design of multiple spherical lenses or cylindrical mirrors converging, and the aspheric surface shape can greatly improve the inherent astigmatism characteristics of the laser source, improve the quality of the converging light spot output by the laser source, and thus improve the detection performance of the cell analyzer. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] In order to more clearly illustrate the embodiments of the utility model or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the utility model. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0022] Figure 1 is a module block diagram of a cell analyzer according to an embodiment;

[0023] Figure 2 is a schematic diagram of an optical detection system of a cell analyzer according to an embodiment of the present invention from one perspective;

[0024] Figure 3 for Figure 2 A schematic diagram of another perspective of the optical detection system of the cell analyzer shown;

[0025] Figure 4 A schematic diagram of the working principle of a flow cell of an optical detection system according to an embodiment;

[0026] Figure 5a is a light intensity distribution diagram of a focused light spot in the central area of ​​a flow cell after using a first aspheric lens and a second aspheric lens in one embodiment;

[0027] Figure 5b for Figure 5a The intensity distribution diagram of the focused light spot on the short axis is shown;

[0028] Figure 6a It is a light intensity distribution diagram of the focused light spot in the central area of ​​the flow cell when a conventional spherical mirror with the same curvature radius is used for convergence in the related art;

[0029] Figure 6b for Figure 6a The intensity distribution diagram of the focused light spot on the short axis is shown;

[0030] Figure 7 is a schematic diagram of an optical detection system of a cell analyzer according to another embodiment;

[0031] Figure 8 A schematic diagram of the relative positions of a flow cell and a collection lens in the related art;

[0032] Fig. 9 Schematic diagram of the relative positions of the flow cell, the third aspheric lens and the collecting lens in one embodiment;

[0033] Fig.10 is a schematic diagram of simulation results of the collection angle of the third aspheric lens in one embodiment;

[0034] Fig.11 It is a dot pattern of the converging light spot formed by the fluorescence with the center of the flow cell as the light-emitting point, an emission half-angle of 40 degrees and a wavelength peak of 670nm after passing through the third aspherical lens.

[0035] Reference numerals:

[0036] Sampling unit 100, reaction unit 200, optical detection system 300, light source module 310, laser source 311, first aspheric lens 313, second aspheric lens 315, plano-concave cylindrical mirror 317, circulation pool 320, optical detection unit 330, first scattering detection module 331, third aspheric lens 3311, long-wave pass dichroic mirror 3313, first detector 3315, double cemented lens 3317, plano-convex lens 3319, fluorescence detection module 340, filter 341, second detector 343, second detection module 350, angle stop 351, focusing lens 353, third detector 355, signal processing unit 400, output unit 500, main optical axis Z DETAILED DESCRIPTION

[0037] In order to facilitate the understanding of the present invention, the present invention will be described more comprehensively with reference to the accompanying drawings. The accompanying drawings provide preferred embodiments of the present invention. However, the present invention can be implemented in many different forms and is not limited to the embodiments described herein. On the contrary, the purpose of providing these embodiments is to make the understanding of the disclosure of the present invention more thorough and comprehensive.

[0038] It should be noted that when an element is referred to as being "fixed to" another element, it may be directly on the other element or there may be a central element. When an element is considered to be "connected to" another element, it may be directly connected to the other element or there may be a central element at the same time. The terms "vertical", "horizontal", "left", "right" and similar expressions used herein are for illustrative purposes only.

[0039] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as those commonly understood by those skilled in the art in the technical field of the present invention. The terms used herein in the specification of the present invention are only for the purpose of describing specific embodiments and are not intended to limit the present invention. The term "and / or" used herein includes any and all combinations of one or more related listed items.

[0040] refer to Figure 1 The utility model discloses a cell analyzer, which includes a sampling unit 100, a reaction unit 200, an optical detection system 300, a signal processing unit 400 and an output unit 500. The sampling unit 100 is used for the absorption and transportation of the initial biological sample; the reaction unit 200 is used for the initial biological sample to react with the corresponding reagent to generate a biological sample to be detected by the optical detection system 300; the signal processing unit 400 is used for processing the output signal of the optical detection system 300 and presenting the detection result through the output unit 500.

[0041] Specifically, after the initial biological sample containing cells or biological particles is sampled several times through the sampling unit 100, it is transported to the reaction unit 200 to react with the corresponding reagent. For example, when performing blood analysis, the initial blood sample reacts with a hemolytic agent or a fluorescent dye in the reaction unit 200. For example, when performing immunoassay, the protein to be tested in the initial serum sample reacts with magnetic beads in the reaction unit 200.

[0042] refer to Figure 2 and Figure 3 , the optical detection system 300 includes a light source module 310, a circulation cell 320, and an optical detection unit 330. The light source module 310 may include a laser source 311, a first aspheric lens 313, and a second aspheric lens 315 arranged in sequence, the first aspheric lens 313 has a main optical axis Z, and the main optical axis Z passes through the laser source 311 and the second aspheric lens 315. The circulation cell 320 is arranged corresponding to the light source module 310 and the main optical axis Z passes through the circulation cell 320. In some embodiments, the laser source 311 is used to generate laser light, which includes a laser diode, for example, which can generate blue light or red light.

[0043] The first aspheric lens 313 is used to collimate the light emitted by the laser source 311, and the second aspheric lens 315 allows the collimated light beam to generate a focused light spot in the flow cell 320 to stimulate the biological sample to be tested passing through the flow cell 320 to generate a light signal to be tested. The optical detection unit 330 is arranged corresponding to the flow cell 320 and is used to detect the light signal to be tested.

[0044] In some embodiments, the biological sample to be tested includes biological particles such as magnetic bead reaction complexes in an immunoassay process, and the diameter of the magnetic beads used is generally 1um or 2.8um; in other embodiments, the biological sample to be tested includes cells such as white blood cells, red blood cells or platelets in a blood analysis process, for example, the diameter of platelets is generally 2-4um.

[0045] The schematic diagram of the circulation pool 320 can be referred to Figure 4 The sample solution formed by the biological particles or cells to be tested flows into the flow cell 320 from the inlet 321 on one side, and the sheath liquid flows in from the other inlet 322; wrapped by the large flow of sheath liquid, the sample solution shrinks into a fast-flowing sample flow. When the biological particles or cells of the biological sample to be tested pass through the flow cell 320, the laser light generated by the light source module 310 passes through the first aspheric lens 313 and the second aspheric lens 315, and the light beam L1 contacts the biological particles or cells in the sample flow. Under the excitation of the focused light spot, scattered light L11 with the same wavelength as the incident light is generated. When the biological particles or cells are marked with fluorescent probes, the dye probes bound to the biological particles or cells excite fluorescence L12 with a wavelength different from that of the incident light.

[0046] In some embodiments, the numerical aperture NA of the first aspheric lens 313 is not less than 0.3, and both the incident surface and the exit surface of the first aspheric lens 313 have even-order aspheric surface characteristics. The conic coefficient k of the aspheric curve of the second aspheric lens 315 is between -1 and 0. The short axis size of the focused light spot is between 5um and 20um, more preferably between 5um-10um. The long axis size of the focused light spot is between 100um and 300um, more preferably between 150-250um.

[0047] The outer surface curve of an aspheric lens is generally defined by the following relationship:

[0048]

[0049] Where R is the radius of curvature, K is the cone coefficient, Y is the distance from the section to the axis, and A is the even-order aspheric coefficient.

[0050] In one embodiment, the emission wavelength of the laser source 311 is 638 nm, the typical divergence half angle (FWHM) is 8 degrees and 30 degrees respectively, and the parameters of the first aspheric lens 313 and the second aspheric lens 315 are as follows:

[0051] Table 1 Parameters of the first aspheric lens

[0052] The first aspheric lens incident surface curve The first aspheric lens exit surface curve R 14.45 -4.33 K -105.23 -0.85 A2 0 0 A4 0.00106 -0.00052 A6 -0.000077 0.0000069 A8 0 0

[0053] Table 2 Parameters of the second aspherical lens

[0054] The second aspheric lens incident surface curve The second aspheric lens exit surface curve R 18.15 -151.23 K -0.74 0 A2 0 0 A4 0 0 A6 0 0 A8 0 0

[0055] Combination Figure 5a and Figure 5b It can be seen that after being collimated by the first aspheric lens 313 and converged by the second aspheric lens 315, the astigmatic beam of the laser source 311 can obtain a good convergence effect, and the short-axis focusing size is 7um, which can well realize the detection of biological samples with smaller particle sizes. Figure 5a As shown, the box size is 400um*400um. Figure 5a is the light intensity distribution diagram of the focused light spot in the central area of ​​the flow cell 320, Figure 5b It is the intensity distribution diagram of the focused light spot on the short axis.

[0056] refer to Figure 6a and Figure 6b When a conventional spherical mirror with the same radius of curvature is used for convergence, the inherent astigmatism of the laser source 311 cannot be well suppressed, and the size of the converged light spot cannot achieve the expected effect. At this time, the short-axis focusing size is 15um. Figure 6a is the light intensity distribution diagram of the focused light spot in the central area of ​​the flow cell 320, Figure 6b It is the intensity distribution diagram of the focused light spot on the short axis. It can be seen that when a conventional spherical mirror with the same radius of curvature is used for convergence, the overall spot size is significantly larger than that of the aspherical design, which will greatly affect the performance of the analyzer.

[0057] The above optical detection system 300 is used for a cell analyzer. The optical detection system 300 includes a light source module 310, a circulation pool 320 and an optical detection unit 330. The light source module 310 includes a laser source 311, a first aspheric lens 313 and a second aspheric lens 315 which are arranged in sequence. The first aspheric lens 313 has a main optical axis Z, which passes through the laser source 311 and the second aspheric lens 315. The first aspheric lens 313 is used to collimate the light emitted by the laser source 311; the circulation pool 320 is arranged corresponding to the light source module 310, and the second aspheric lens 315 enables the collimated light beam to generate a focused light spot in the circulation pool 320 to excite the biological sample to be measured passing through the circulation pool 320 to generate a light signal to be measured; the optical detection unit 330 is arranged corresponding to the circulation pool 320, and is used to detect the light signal to be measured. The arrangement of the first aspheric lens 313 and the second aspheric lens 315 simplifies the cumbersome design of multiple spherical lenses or cylindrical lenses converging, and the aspheric surface shape can greatly improve the inherent astigmatism characteristics of the laser source 311, improve the quality of the converging light spot output by the laser source 311, and thus enhance the detection performance of the cell analyzer.

[0058] In some embodiments, the light source module 310 includes a plano-concave cylindrical mirror 317, which is disposed between the second aspheric lens 315 and the flow cell 320. Figure 3 In some other embodiments, the plano-concave cylindrical mirror 317 is disposed between the first aspheric lens 313 and the second aspheric lens 315, as shown in FIG. Figure 7 shown.

[0059] Further, refer to Figure 3 , the cylindrical generatrix of the plano-concave cylindrical mirror 317 is parallel to the flow direction of the biological sample to be tested in the flow cell 320. In other words, the cylindrical generatrix direction of the plano-concave cylindrical mirror 317 is perpendicular to the fast axis direction of the laser source 311.

[0060] The second aspheric lens 315 can converge the light beam collimated by the first aspheric lens 313 into a micron-sized spot. The plano-concave cylindrical mirror 317 is used to adjust the long-axis size of the micron-sized spot to adapt to the sample flow sizes of different diameters in the flow cell 320. In general, the long-axis direction of the micron-sized spot is 13.5% (1 / e 2 ) size is above 200um.

[0061] Continue to refer Figure 2The optical detection unit 330 includes a first scattering detection module 331, and the first scattering detection module 331 includes a third aspheric lens 3311, a long-wave pass dichroic mirror 3313 and a first detector 3315 arranged in sequence. The side scattered light in the light signal to be measured that is perpendicular to the propagation direction of the incident light is emitted from the circulation pool 320, passes through the third aspheric lens 3311 and the long-wave pass dichroic mirror 3313, and is reflected by the long-wave pass dichroic mirror 3313 to the first detector 3315.

[0062] The scattered light in the measured light signal that is perpendicular to the propagation direction of the incident light is also usually called side scattered light or 90-degree scattered light. The dye probe bound to the measured biological particles or cells will generate a fluorescent signal under the excitation of the focused light spot. In order to improve the signal-to-noise ratio of the fluorescent signal and reduce the interference of the excitation light beam, the fluorescent signal is generally also detected on the other side of the flow cell 320, that is, on the same side as the side scattered light.

[0063] Combination Figure 8 In the related art, in a cell analyzer, an aspherical lens is generally used to realize the collection function of side scattered light and fluorescence, that is, to realize the function of a collection lens, such as the solution disclosed in CN213301970U. In this solution, since the biological particles to be measured have passed through the sample liquid and the outer wall of the flow cell 320 made of quartz glass, the light beam will have a certain degree of divergence, and when the light beam enters the air, the angle will be further expanded, which greatly reduces the collection angle range of the collection lens.

[0064] As shown in the following formula, since air is a medium with a low refractive index, the deflection angle increases when light is emitted from the optically dense medium of the sample liquid to the optically sparse medium of air.

[0065] sina= n 空气 sinb

[0066] n 液体

[0067] Where n 空气 is the refractive index of air, n 液体 is the refractive index of the sample liquid. In this case, the actual collection angle of the collection lens will be reduced, that is, angle a is smaller than angle b.

[0068] In this embodiment, the third aspheric lens 3311 is attached to the outer surface of the outer wall of the flow cell 320, and the refractive index of the third aspheric lens 3311 is greater than the refractive index of the outer wall of the flow cell 320. Fig. 9 , the third aspheric lens 3311 is attached to the outer surface of the outer wall of the circulation pool 320, according to the following formula:

[0069] sina= n 非球 sinb

[0070] n 液体

[0071] Where n 非球 This embodiment can reduce the system spherical aberration caused by large-angle emission of light by adjusting the aspheric curve of the light beam exit surface, thereby further improving the collection angle range.

[0072] Further, in some embodiments, the focal length of the third aspheric lens 3311 is f, the center thickness of the third aspheric lens 3311 is d, the diameter is D, the thickness of the outer wall of the circulation pool 320 is h, f≤d+h / 2, and D≤h. In other words, the focal length of the third aspheric lens 3311 is not greater than the sum of the center thickness of the lens and half of the wall thickness of the circulation pool 320, and the diameter of the third aspheric lens 3311 is not greater than the wall thickness of the circulation pool 320.

[0073] Further, refer to Figure 2 The first scattering detection module 331 may include a doublet lens 3317 and a plano-convex lens 3319 which are sequentially arranged between the third aspheric lens 3311 and the long-wave-pass dichroic mirror 3313. After the side scattered light is emitted from the side of the flow cell 320, it passes through the third aspheric lens 3311, and then passes through the doublet lens 3317 and the plano-convex lens 3319 in sequence, and then is reflected by the long-wave-pass dichroic mirror 3313 to the first detector 3315, forming a side scattered light signal, which is generally related to the complexity or lobation degree of the nucleus of the biological particle or cell being detected.

[0074] The use of doublet lens 3317 can reduce the dispersion problem caused by the different wavelengths of side scattered light and fluorescence. For example, in this embodiment, the wavelength of side scattered light is generally 635nm, while the emission spectrum of fluorescence is relatively wide, generally with a peak at 650nm and a far end of 800nm. The plano-convex lens 3319 can converge the light emitted from the doublet lens 3317.

[0075] In some embodiments, the combined focal length of the third aspheric lens 3311, the doublet lens 3317, and the plano-convex lens 3319 is no greater than 10 mm.

[0076] The optical detection unit 330 may further include a fluorescence detection module 340 and a second detection module 350. The fluorescence detection module 340 includes a filter 341 and a second detector 343. The light transmitted from the long-wave pass dichroic mirror 3313 is converged to the second detector 343 through the filter 341. Further, the passing band range of the filter 341 is consistent with the emission spectrum of the fluorescent probe bound to the cell or the biological particle to be detected, and at least includes the maximum emission peak of the fluorescent probe.

[0077] The fluorescence signal is also narrowed by the third aspheric lens 3311, and then sequentially passes through the double cemented lens 3317 and the plano-convex lens 3319, and then converges onto the second detector 343 after passing through the long-wave dichroic mirror 3313 and the filter 341 to form a fluorescence signal. The second detector 343 generally uses components with multiple photoelectric conversion effects inside, such as a photomultiplier tube PMT, an avalanche diode APD or a silicon photomultiplier tube SiPMT, MPPC.

[0078] In one embodiment, the third aspheric lens 3311 is made of D-ZLaF52La glass, whose refractive index is as high as 1.806. One side of the third aspheric lens 3311 is a plane, and the other side has an even-order aspheric surface shape, and the numerical aperture is 0.55. Fig.10 Under the simulation software, the collection angle can reach 40 degrees, and the focused spot diameter is within 1mm, which can match various detector areas relatively well.

[0079] further, Fig.11 The center of the flow cell 320 is taken as the light emitting point, the emission half angle is 40 degrees, and the fluorescence with a wavelength peak of 670nm forms a dot matrix of a convergent light spot after passing through the above-mentioned collecting lens, and the diameter of the convergent light spot is 0.7mm.

[0080] In the related art, the lateral light collection angle is generally within 30 degrees. Compared with the related art, this solution can increase the collection angle range by nearly 10 degrees, thereby improving the signal-to-noise ratio of side scattered light and fluorescence. Taking the fluorescence signal as an example, its light intensity distribution is isotropic. Therefore, in this embodiment, the fluorescence signal intensity corresponding to 40 degrees is (tan40o / tan30o) twice that of 30 degrees, that is, 2.11 times.

[0081] In other words, the arrangement of the third aspheric lens 3311 attached to the outer wall of the circulation pool 320 can greatly improve the lateral collection angle range without increasing the complexity of the system, thereby further improving the signal-to-noise ratio of the system detection and improving the detection performance of the cell analyzer.

[0082] The second detection module 350 includes an angle aperture 351, a focusing lens 353 and a third detector 355 arranged in sequence along the main optical axis Z, and the angle aperture 351 is arranged corresponding to the flow cell 320. Under the excitation of the focused light spot, the biological particles or cells to be detected will generate scattered light signals in the same band as the light incident to the flow cell 320, wherein the scattered light signals with the same propagation direction as the incident light, after passing through the angle aperture 351, are converged by the focusing lens 353 to the third detector 355, forming small-angle scattered light signals, which are generally related to the diameter or volume of the particles or cells to be detected.

[0083] The technical features of the above-described embodiments may be arbitrarily combined. To make the description concise, not all possible combinations of the technical features in the above-described embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0084] The above-mentioned embodiments only express several implementation methods of the utility model, and the description is relatively specific and detailed, but it cannot be understood as limiting the scope of the utility model patent. It should be pointed out that for ordinary technicians in this field, several modifications and improvements can be made without departing from the concept of the utility model, which all belong to the protection scope of the utility model. Therefore, the protection scope of the utility model patent shall be based on the attached claims.

Claims

1. An optical detection system for a cell analyzer, characterized in that: The optical detection system comprises: A light source module, comprising a laser source, a first aspheric lens and a second aspheric lens arranged in sequence, wherein the first aspheric lens has a main optical axis, the main optical axis passes through the laser source and the second aspheric lens, and the first aspheric lens is used to collimate the light emitted by the laser source; a circulation cell, which is arranged corresponding to the light source module and through which the main optical axis passes; the second aspheric lens enables the collimated light beam to generate a focused light spot in the circulation cell to excite the biological sample to be tested passing through the circulation cell to generate a light signal to be tested; and The optical detection unit is arranged corresponding to the circulation pool and is used to detect the optical signal to be detected.

2. The optical detection system according to claim 1, characterized in that: The light source module includes a plano-concave cylindrical mirror, which is arranged between the first aspheric lens and the second aspheric surface, or between the second aspheric lens and the flow cell.

3. The optical detection system according to claim 2, characterized in that: The cylindrical generatrix of the plano-concave cylindrical mirror is parallel to the flow direction of the biological sample to be tested in the flow cell.

4. The optical detection system according to any one of claims 1 to 3, characterized in that: The optical detection unit includes a first scattering detection module, which includes a third aspheric lens, a long-wave pass dichroic mirror and a first detector arranged in sequence. The side scattered light in the light signal to be measured that is perpendicular to the propagation direction of the incident light is emitted from the circulation pool, passes through the third aspheric lens and the long-wave pass dichroic mirror, and is reflected by the long-wave pass dichroic mirror to the first detector.

5. The optical detection system according to claim 4, characterized in that: The third aspheric lens is attached to the outer surface of the outer wall of the circulation cell, and the refractive index of the third aspheric lens is greater than the refractive index of the outer wall of the circulation cell.

6. The optical detection system according to claim 5, characterized in that: The focal length of the third aspheric lens is f, the center thickness is d, the diameter is D, the thickness of the outer wall of the circulation pool is h, f≤d+h / 2, and D≤h.

7. The optical detection system according to claim 5, characterized in that: The first scattering detection module includes a doublet lens and a plano-convex lens which are sequentially arranged between the third aspheric lens and the long-wave pass dichroic mirror.

8. The optical detection system according to claim 7, characterized in that: The combined focal length of the third aspheric lens, the doublet lens and the plano-convex lens is no greater than 10 mm.

9. The optical detection system according to claim 7, characterized in that: The optical detection unit includes a fluorescence detection module and a second detection module. The fluorescence detection module includes a filter and a second detector. The light transmitted from the long-wave pass dichroic mirror is converged to the second detector through the filter; the second detection module includes an angle aperture, a focusing lens and a third detector arranged in sequence along the main optical axis. The angle aperture is arranged corresponding to the circulation pool. The light emitted from the angle aperture is focused to the third detector through the focusing lens to detect the scattered light signal in the light signal to be measured that is in the same wavelength band as the light incident to the circulation pool.

10. A cell analyzer, characterized in that: The optical detection system comprises a sampling unit, a reaction unit, a signal processing unit, an output unit and the optical detection system according to any one of claims 1 to 9, wherein the sampling unit is used for absorbing and transporting the initial biological sample, the reaction unit is used for the initial biological sample to react with the corresponding reagent to generate a biological sample to be detected suitable for detection by the optical detection system, and the signal processing unit is used for processing the output signal of the optical detection unit and presenting the detection result through the output unit.

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