Optical detection device and cytometer

Abstract

The application is suitable for the field of cell analysis equipment, and discloses an optical detection device and a cell analyzer. The optical detection device comprises a flow chamber, a light source and a forward scattering detection assembly. The forward scattering detection assembly is used for collecting a forward scattering signal generated by the light source irradiating on a cell to be measured. The forward scattering detection assembly comprises a first focusing lens, an aperture assembly and a first detector. The aperture assembly is arranged between the first focusing lens and the first detector. The first focusing lens is arranged between the flow chamber and the aperture assembly, so as to make forward scattering light generated by the light source irradiating on the cell to be measured converge and then pass through the aperture assembly to enter the first detector. The first focusing lens is a spherical lens, and the number of the first focusing lens is one. The single spherical lens is used for collecting the forward scattering signal and converging the forward scattering signal on the first detector, so that the volume and cost of the optical detection device are effectively reduced, and the miniaturization design of the cell analyzer is facilitated.

Description

Technical Field

[0001] This invention relates to the field of cell analysis equipment, and more particularly to an optical detection device for a cell analyzer and a cell analyzer. Background Technology

[0002] Currently, most five-part differential hematology analyzers use laser scattering to measure cells. For systems requiring high optical signal quality, multiple spherical lenses or complex-shaped aspherical lenses are typically used to collect the forward-scattered signal, followed by aperture diaphragm structures for stray light shielding and effective signal reception. However, the optical detection devices in existing five-part differential hematology analyzers have the following drawbacks in practical applications:

[0003] 1) In the prior art, forward scattering signals are generally collected using complex lenses (aspherical lenses) or multiple spherical lenses with flat incident surfaces. This results in higher cost and larger size of the optical detection device.

[0004] 2) In the prior art, the type of light-transmitting hole of the aperture stop is generally a small circular hole, that is, the circular aperture stop is used to shield stray light inside the optical detection device. In this way, the circular hole has high positional accuracy requirements in the design and debugging process of the optical detection device, which leads to the problems of complex debugging structure and high cost.

[0005] 3) In existing technologies, the detector used to receive fluorescence light is located at the focal point of the focusing component. To ensure the optical signal-to-noise ratio, filters are typically used to shield against interference from scattered light, and small-aperture circular apertures are used to spatially shield stray light inside the optical detection device. Because fluorescence signals are very weak, compared to forward-scattered signals, they require more precise positioning of the mechanical structure or adjustment of the detector, resulting in higher cost and larger size for the entire optical detection device. Summary of the Invention

[0006] The first objective of this invention is to provide an optical detection device that addresses the technical problem of high cost and large size of optical detection devices in the prior art, which uses complex lenses or multiple spherical lenses with flat incident surfaces to collect forward-scattered signals.

[0007] To achieve the above objectives, the present invention provides an optical detection device applied to a cell analyzer, the optical detection device comprising:

[0008] A flow chamber, wherein the flow chamber is used for the test cells of the test sample solution to pass through in a queue under the influence of the diluent;

[0009] A light source, the light source being used to emit light toward the test cells flowing through the flow chamber;

[0010] a forward scattering detection component for collecting forward scattering signals generated by the light source irradiating on the cells to be measured, the forward scattering detection component comprising a first focusing lens, a diaphragm component and a first detector, the diaphragm component being arranged between the first focusing lens and the first detector; the first focusing lens being arranged between the flow chamber and the diaphragm component for converging the forward scattering light generated by the light source irradiating on the cells to be measured to pass through the diaphragm component into the first detector, the first focusing lens being a spherical lens, and the number of the first focusing lens being one.

[0011] The optical detection device provided by the first object of the present application effectively reduces the volume and cost of the optical detection device by using a single spherical lens (i.e. the first focusing lens) to collect and converge the forward scattering signals on the first detector, which is conducive to the miniaturization design of the cell analyzer.

[0012] The second object of the present application is to provide an optical detection device, which aims to solve the technical problem of high cost and large volume of the optical detection device caused by arranging the detector for receiving fluorescent light at the focal point of the focusing component in the prior art.

[0013] To achieve the above object, the present application provides a solution: an optical detection device applied to a cell analyzer, the optical detection device comprising:

[0014] a flow chamber for queuing the cells to be measured of a detection sample liquid to pass through under the entrainment of a diluent;

[0015] a light source for emitting light towards the cells to be measured flowing through the flow chamber;

[0016] a fluorescence detection component for collecting fluorescent signals generated by the light source irradiating on the cells to be measured, the fluorescence detection component comprising a focusing component, a filter and a second detector, the filter being arranged between the focusing component and the second detector, the focusing component being arranged between the flow chamber and the filter for converging the fluorescent light generated by the light source irradiating on the cells to be measured to pass through the filter into the second detector, the second detector being located between the filter and the focal point of the focusing component.

[0017] The optical detection device provided by the second object of the present application can cancel or expand the aperture of the fluorescent directional aperture diaphragm by designing the second detector for collecting fluorescent light before the focal point of the focusing component, so that not only the volume and cost of the optical detection device can be effectively reduced to ensure the signal-to-noise ratio of the fluorescent light, but also the positioning accuracy requirement of the target surface of the second detector can be greatly reduced.

[0018] A third object of the present application is to provide an optical detection device which aims to solve the technical problem of complex debugging structure and high cost caused by the use of a circular aperture stop in the prior art for internal stray light shielding of the optical detection device.

[0019] To achieve the above object, the present application provides a solution: an optical detection device applied to a cell analyzer, the optical detection device comprising:

[0020] a flow chamber for queuing the cells to be detected in the detection sample liquid to pass through under the entrainment of the diluent;

[0021] a light source for emitting light towards the cells to be detected flowing through the flow chamber;

[0022] a forward scattering detection assembly for collecting forward scattering signals generated by the light emitted by the light source onto the cells to be detected, the forward scattering detection assembly comprising a first focusing lens, a diaphragm assembly and a first detector, the diaphragm assembly being arranged between the first focusing lens and the first detector, the first focusing lens being arranged between the flow chamber and the diaphragm assembly for converging the forward scattering light generated by the light emitted by the light source onto the cells to be detected to pass through the diaphragm assembly into the first detector, the diaphragm assembly comprising a straight light blocking diaphragm and a first aperture stop, the straight light blocking diaphragm being located between the first focusing lens and the first aperture stop, the first aperture stop being located between the straight light blocking diaphragm and the first detector, the first aperture stop being provided with a first light transmission hole for light to pass through and be emitted onto the first detector;

[0023] a side scattering detection assembly for collecting side scattering signals generated by the light emitted by the light source onto the cells to be detected; the side scattering detection assembly comprising a fourth aperture stop and a third detector, the fourth aperture stop being arranged between the flow chamber and the third detector, and the fourth aperture stop being provided with a fifth light transmission hole for light to pass through and be emitted onto the third detector;

[0024] At least one of the first light transmission hole and the fifth light transmission hole is a non-circular hole, the non-circular hole having a size in a first direction greater than a size in a second direction, the first direction and the second direction being perpendicular to each other, and the first direction being parallel to the flow direction of the cells to be detected.

[0025] The optical detection device provided in the third aspect of the present application sets the light-transmitting hole on the aperture diaphragm in front of the detector in at least one of the forward scattering detection assembly and the side scattering detection assembly as a non-circular hole, and sets the length direction of the non-circular hole to be parallel to the flow direction of the cells to be detected, so that the internal diffuse reflection stray light of the optical detection device can be reduced, and the requirement for the mechanical structure precision can also be greatly reduced relative to the traditional circular aperture diaphragm, thereby facilitating the simplification of the debugging structure complexity of the optical detection device and the reduction of the cost of the optical detection device.

[0026] The fourth aspect of the present application is to provide a cell analyzer, which comprises a reaction pool, a reagent supply device, a sampling unit, a diluent providing device, a conveying device, an analysis unit, an output unit and any one of the optical detection devices described above;

[0027] The reaction pool is used to provide a reaction site for the sample to be detected and the reagent to prepare a detection sample liquid;

[0028] The sampling unit is used to collect the sample to be detected and discharge the sample to be detected into the reaction pool;

[0029] The reagent supply device is used to convey the reagent into the reaction pool;

[0030] The conveying device is used to drive the detection sample liquid from the reaction pool to the flow chamber and to drive the diluent from the diluent providing device to the flow chamber, so that the cells to be detected in the detection sample liquid are queued through the flow chamber under the entrainment of the diluent;

[0031] The optical detection device is used to detect the detection sample liquid entrained by the diluent through the flow chamber;

[0032] The analysis unit is used to analyze the detection result of the detection sample liquid according to the optical signal fed back by the detector;

[0033] The output unit is used to output the detection result of the analysis unit.

[0034] The cell analyzer provided in the fourth aspect of the present application is beneficial to the miniaturization and low-cost design of the cell analyzer due to the adoption of the optical detection device described above. BRIEF DESCRIPTION OF DRAWINGS

[0035] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the drawings needed to be used in the embodiments or the prior art description will be briefly introduced below. Obviously, the drawings in the following description are only some embodiments of the present application, and other drawings can also be obtained according to the structures shown in the drawings without creative labor.

[0036] Figure 1 is a structural schematic diagram of the optical detection device provided by embodiment one of the present application;

[0037] Figure 2 is a propagation schematic diagram of the light on the forward scattering detection component provided by embodiment one of the present application;

[0038] Figure 3 is a propagation schematic diagram of the light on the first focusing lens provided by embodiment one of the present application;

[0039] Figure 4 is a structural schematic diagram of the first light-transmitting hole provided by embodiment one of the present application;

[0040] Figure 5 is a propagation schematic diagram of the light on the fluorescence detection component and the side scattering detection component provided by embodiment one of the present application;

[0041] Figure 6 is a structural schematic diagram of the fifth light-transmitting hole provided by embodiment one of the present application;

[0042] Figure 7 is a structural schematic diagram of the cell analyzer provided by embodiment one of the present application;

[0043] Figure 8 is a propagation schematic diagram of the light on the fluorescence detection component provided by embodiment two of the present application.

[0044] BRIEF DESCRIPTION OF THE DRAWINGS

[0045] 100, optical detection device; 110, flow cell; 120, light source; 121, laser; 122, pre- light module; 130, forward scatter detection module; 131, first focusing lens; 1311, first entrance surface; 1312, first exit surface; 132, aperture module; 1321, straight- stop aperture; 1301, stop; 1302, second through hole; 1322, first aperture stop; 1303, first through hole; 1304, first hole wall; 1305, second hole wall; 133, first detector; 140, fluorescence detection module; 141, focusing module; 1411, second focusing lens; 1401, second entrance surface; 1402, second exit surface; 1412, third focusing lens; 1403, third entrance surface; 1404, third exit surface; 142, filter; 143, second detector; 144, second aperture stop; 1441, third through hole; 145, third aperture stop; 1451, fourth through hole; 150, side scatter detection module; 151, fourth aperture stop; 1511, fifth through hole; 1501, third hole wall; 1502, fourth hole wall; 152, third detector; 160, dichroic mirror; 200, reaction cell; 300, reagent supply device; 400, sampling unit; 500, diluent supply device; 600, conveying device; 700, analysis unit; 800, output unit. DETAILED DESCRIPTION

[0046] The technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, rather than all the embodiments of the present application. Based on the embodiments in the present application, all other embodiments obtained by a person of ordinary skill in the art without creative effort belong to the scope of protection of the present application.

[0047] It should be noted that all directional indications, such as upper, lower, left, right, front, back, etc., in the embodiments of the present application are only used to explain the relative positional relationship, movement condition, etc. between components in a certain posture, and if the certain posture changes, the directional indications also change accordingly.

[0048] It should also be noted that when an element is referred to as being "fixed" or "set" on another element, it can be directly on the other element or can have a middle element. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or can be indirectly connected to the other element through a middle element.

[0049] Furthermore, the use of terms such as "first" and "second" in this invention is for descriptive purposes only and should not be construed as indicating or implying their relative importance or implicitly specifying the number of technical features indicated. Therefore, a feature defined with "first" or "second" may explicitly or implicitly include at least one of that feature. Additionally, the technical solutions of the various embodiments can be combined with each other, but only on the basis of being achievable by those skilled in the art. When the combination of technical solutions is contradictory or impossible to implement, such a combination of technical solutions should be considered non-existent and not within the scope of protection claimed by this invention.

[0050] Example 1:

[0051] like Figures 1-7 As shown, the optical detection device 100 provided in Embodiment 1 of the present invention is applied to a cell analyzer. The optical detection device 100 includes a flow chamber 110, a light source 120, a forward scattering detection component 130, a fluorescence detection component 140, and a side scattering detection component 150. The flow chamber 110 is used for the test cells of the test sample solution to pass through in a queue under the influence of the diluent; the light source 120 is used to emit light toward the test cells flowing through the flow chamber 110; the forward scattering detection component 130 is used to collect the forward scattering signal generated by the light source 120 illuminating the test cells; the fluorescence detection component 140 is used to collect the fluorescence signal generated by the light source 120 illuminating the test cells; and the side scattering detection component 150 is used to collect the side scattering signal generated by the light source 120 illuminating the test cells.

[0052] In this embodiment, the optical detection device 100 includes three sets of detection components: a forward scattering detection component 130, a fluorescence detection component 140, and a side scattering detection component 150. These components can be used to simultaneously collect the forward scattering signal, side scattering signal, and fluorescence signal generated when the light source 120 illuminates the cell to be tested. Of course, in specific applications, depending on the requirements of different detection items, the optical detection device 100 may not simultaneously include the forward scattering detection component 130, the fluorescence detection component 140, and the side scattering detection component 150. For example, as an alternative implementation, the optical detection device 100 may also include only one or any two of the three components: the forward scattering detection component 130, the fluorescence detection component 140, and the side scattering detection component 150.

[0053] Specifically, the forward scattering detection component 130 is arranged on the optical axis of the light emitted by the light source 120, and the forward scattering signal (also referred to as low-angle scattering signal) collected thereby can represent the size of the volume of the cell to be measured. The fluorescence detection component 140 and the side scattering detection component 150 are both arranged on the side of the optical axis of the light emitted by the light source 120, and the side scattering signal (also referred to as high-angle scattering signal) collected by the side scattering detection component 150 can represent the complexity of the internal particles of the cell to be measured. The fluorescence signal intensity collected by the fluorescence detection component 140 can represent the degree of staining of the cell to be measured.

[0054] Preferably, with reference to Figure 1 As shown in the figure, the light source 120 includes a laser 121 and a pre-light modulation component 122 arranged between the laser 121 and the flow chamber 110. The pre-light modulation component 122 is mainly used for focusing the light emitted by the laser 121.

[0055] Preferably, the light emitted by the light source 120 forms an elliptical spot at the center of the flow chamber 110, the short axis direction of the elliptical spot is parallel to the flow direction of the cell to be measured, and the long axis direction of the elliptical spot is perpendicular to the flow direction of the cell to be measured. When the cell to be measured passes through the light beam irradiation area (the elliptical spot at the center of the flow chamber 110) of the light source 120, low-angle scattering light (forward scattering light), high-angle scattering light (side scattering light) and fluorescence light will be generated at the same time, and the forward scattering detection component 130, the fluorescence detection component 140 and the side scattering detection component 150 are respectively used for collecting the low-angle scattering light, the high-angle scattering light and the fluorescence light.

[0056] As a preferred embodiment of the present embodiment, the elliptical spot formed by the light source 120 at the flow chamber 110 has a size of 10um-25um in the short axis direction and 200um-350um in the long axis direction.

[0057] Preferably, with reference to Figure 1 and Figure 2As shown, the forward scattering detection component 130 comprises a first focusing lens 131, a diaphragm component 132 and a first detector 133, the diaphragm component 132 is arranged between the first focusing lens 131 and the first detector 133 for limiting the light beam angle range passing therethrough; the first focusing lens 131 is arranged between the flow chamber 110 and the diaphragm component 132 for converging the forward scattering light generated by the light source 120 irradiating on the cells to be detected to enter the first detector 133 through the diaphragm component 132, the first focusing lens 131 is a spherical lens, and the number of the first focusing lens 131 is one. The forward scattering light generated by the light source 120 irradiating on the cells to be detected will irradiate on the first focusing lens 131, and then converge through the first focusing lens 131, pass through the diaphragm component 132 for limiting, and finally shoot to the first detector 133, so as to complete the collection of the forward scattering signal. In this embodiment, only one spherical lens (i.e. the first focusing lens 131) is used to collect and converge the forward scattering signal on the first detector 133, which can effectively reduce the volume and cost of the optical detection device 100, and is beneficial to the miniaturization design of the cell analyzer.

[0058] Preferably, referring to Figures 1-3 As shown, the first focusing lens 131 has a first incident surface 1311 arranged towards the flow chamber 110 and a first exit surface 1312 arranged towards the diaphragm component 132, and the first incident surface 1311 is a spherical surface arranged convexly towards the flow chamber 110. Here, the first incident surface 1311 is designed as a convex spherical structure, i.e. the first incident surface 1311 is a spherical surface arranged convexly towards the flow chamber 110, so that the reflected light of the first incident surface 1311 deviates from the original incident light beam direction, which is easy for spatial shielding design, thereby effectively reducing the phenomenon that the light is reflected back to the light source 120 from the first incident surface 1311, causing unstable output of the light source 120, and further leading to that the forward scattering optical signal-to-noise ratio does not meet the cell detection requirements.

[0059] Preferably, referring to Figures 1-3 As shown, in this embodiment, the first exit surface 1312 is a spherical surface arranged convexly towards the diaphragm component 132; of course, in specific applications, as an alternative embodiment, the first exit surface 1312 can also be a flat surface or a surface with other shapes.

[0060] Preferably, referring to Figure 1 and Figure 2As shown, the diaphragm assembly 132 includes a straight light blocking diaphragm 1321 and a first aperture diaphragm 1322, the straight light blocking diaphragm 1321 is located between the first focusing lens 131 and the first aperture diaphragm 1322, the first aperture diaphragm 1322 is located between the straight light blocking diaphragm 1321 and the first detector 133, the first aperture diaphragm 1322 is provided with a first light transmission hole 1303 for light transmission and irradiation onto the first detector 133, the straight light blocking diaphragm 1321 has a blocking part 1301 for blocking the direct light transmitted through the cell to be measured and two second light transmission holes 1302 respectively arranged on the two sides of the straight part for light transmission and irradiation onto the first aperture diaphragm 1322. The low-angle scattered light caused by the scattering of the cell to be measured is collected by the first focusing lens 131 when passing through the flow chamber 110, then passes through the second light transmission hole 1302 of the straight light blocking diaphragm 1321, converges at the position of the first aperture diaphragm 1322, and finally is received by the first detector 133. According to the size, pulse width and area of the low-angle scattering signal received by the first detector 133, the volume information of the cell to be measured can be represented. At the same time, the direct light transmitted through the cell to be measured is blocked by the blocking part 1301 of the straight light blocking diaphragm 1321, so as to prevent the saturation of the low-angle scattering signal and ensure the effective identification of the low-angle scattering signal.

[0061] Preferably, as shown in Figure 1 、 Figure 2 and Figure 4 , the first light transmission hole 1303 is a non-circular hole, the inner wall of the first light transmission hole 1303 includes two first hole walls 1304 and two second hole walls 1305, the two first hole walls 1304 are oppositely arranged in the first direction X, the two second hole walls 1305 are oppositely arranged in the second direction Y and are respectively connected to the two first hole walls 1304, that is, the first hole wall 1304 and the second hole wall 1305 are alternately connected to form a closed annular wall surface. The first direction X and the second direction Y are perpendicular to each other, and the first direction X is parallel to the flow direction of the cell to be measured, the distance L1 between the two first hole walls 1304 is greater than the distance L2 between the two second hole walls 1305, that is, the size L1 of the first light transmission hole 1303 in the first direction X is greater than the size L2 in the second direction Y. Here, by setting the first light transmission hole 1303 of the first aperture diaphragm 1322 as a non-circular hole and making the size L1 of the first light transmission hole 1303 in the first direction X greater than the size L2 in the second direction Y, and the direction with larger size is parallel to the flow direction of the cell to be measured, so that the internal diffuse stray light of the optical detection device 100 can be reduced, and the requirement for mechanical structure precision can also be greatly reduced, thereby facilitating the simplification of the debugging structure complexity of the optical detection device 100 and the reduction of the cost of the optical detection device 100.

[0062] Referring to Figures 1-3 As shown in FIG. 13, as a preferred embodiment of the present embodiment, the first light-transmitting hole 1303 is a waist-shaped hole, both of the first hole walls 1304 are semicircular arc surfaces, and both of the second hole walls 1305 are parallel planes. The first light-transmitting hole 1303 adopts a waist-shaped hole, which can not only meet the design requirement that the size of the first light-transmitting hole 1303 is different in two perpendicular directions, but also reduce the stress concentration phenomenon of the hole wall of the first light-transmitting hole 1303 through the design of the semicircular arc surface, thereby facilitating the improvement of the structural reliability of the first aperture stop 1322. Of course, in specific applications, the first light-transmitting hole 1303 is not limited to a waist-shaped hole. For example, as an alternative embodiment, the first light-transmitting hole 1303 can also be designed as an elliptical hole or a rectangular hole.

[0063] Preferably, referring to Figure 1 and Figure 5 As shown in FIG. 14, the fluorescence detection assembly 140 includes a focusing assembly 141, a filter 142, and a second detector 143, the filter 142 is arranged between the focusing assembly 141 and the second detector 143; the focusing assembly 141 is arranged between the flow chamber 110 and the filter 142, so as to make the fluorescence light generated by the light source 120 irradiating on the to-be-detected cell converge and then pass through the filter 142 to enter the second detector 143, and the second detector 143 is located between the filter 142 and the focus point A of the focusing assembly 141. The fluorescence light generated by the light source 120 irradiating on the to-be-detected cell is collected by the focusing assembly 141 through the flow chamber 110, passes through the filter 142, and is finally received by the second detector 143 of the fluorescence channel. Here, the position of the second detector 143 is arranged before the converging focus point A of the focusing assembly 141 in the fluorescence direction, so that the spot size of the fluorescence signal can match the target surface optical effective area of the second detector 143, and then the internal nucleic acid content information of different to-be-detected cells can be reflected according to the fluorescence signal size, pulse width and area.

[0064] Preferably, the cut-off range of the filter 142 to the spectrum light of the light source 120 is OD6 or more. OD is the abbreviation of optical density (optical density). OD6 indicates that the transmittance of the spectrum light of the light source 120 on the filter 142 is 0.0001%. In the present embodiment, in combination with the target surface size of the second detector 143, the third detector 152 is designed before the focus point A of the focusing assembly 141, and the design of the aperture stop in front of the second detector 143 is cancelled, and the cut-off of the filter 142 to the spectrum light of the laser 121 is designed to be OD6 or more, so that not only the volume of the optical detection device 100 can be effectively reduced, but also the fluorescence signal-to-noise ratio can be guaranteed, and the requirement for the positioning accuracy of the target surface of the third detector 152 can be greatly reduced.

[0065] Preferably, the light filter 142 is a filter, i.e. the light filter 142 is a sheet-shaped component, which is simple in structure and small in thickness, and is conducive to reducing the volume of the optical detection device 100.

[0066] Preferably, the focal length of the focusing assembly 141 is greater than 4.0 mm.

[0067] Preferably, referring to Figure 1 and Figure 5 As shown in the figures, the focusing assembly 141 comprises a second focusing lens 1411 and a third focusing lens 1412, the second focusing lens 1411 is arranged between the flow chamber 110 and the third focusing lens 1412, and the third focusing lens 1412 is arranged between the second focusing lens 1411 and the light filter 142. The second focusing lens 1411 has a second incident surface 1401 arranged towards the flow chamber 110 and a second exit surface 1402 arranged towards the third focusing lens 1412, and the third focusing lens 1412 has a third incident surface 1403 arranged towards the second focusing lens 1411 and a third exit surface 1404 arranged towards the light filter 142.

[0068] Preferably, the second focusing lens 1411 is a spherical lens, i.e. at least one of the second incident surface 1401 and the second exit surface 1402 is spherical. As a preferred embodiment of the present embodiment, the second incident surface 1401 is a plane, and the second exit surface 1402 is a spherical surface arranged convexly towards the third focusing lens 1412. Of course, in specific applications, the shapes of the second incident surface 1401 and the second exit surface 1402 are not limited thereto.

[0069] Preferably, the third focusing lens 1412 is a spherical lens, i.e. at least one of the third incident surface 1403 and the third exit surface 1404 is spherical. As a preferred embodiment of the present embodiment, the third incident surface 1403 is a plane, and the third exit surface 1404 is a spherical surface arranged convexly towards the light filter 142. Of course, in specific applications, the shapes of the third incident surface 1403 and the third exit surface 1404 are not limited thereto.

[0070] Preferably, referring to Figure 1 and Figure 5 As shown in the figures, the fluorescence detection assembly 140 further comprises a third aperture stop 145, the third aperture stop 145 is arranged between the second focusing lens 1411 and the third focusing lens 1412, and the third aperture stop 145 is provided with a fourth light transmission hole 1451 for allowing light to pass through and irradiate onto the third focusing lens 1412. The third aperture stop 145 is used to limit the collection angle range of the light beam.

[0071] Preferably, referring to Figure 1 and Figure 5As shown, the optical detection device 100 further comprises a dichroic mirror 160, which is located between the focusing assembly 141 and the filter 142, and between the focusing assembly 141 and the side scatter detection assembly 150, for allowing the fluorescent light generated by the light source 120 irradiating on the cells to be detected to pass through and irradiate on the filter 142, and for reflecting the side scatter light generated by the light source 120 irradiating on the cells to be detected to the side scatter detection assembly 150. The dichroic mirror 160, also known as a dichroic mirror, has the characteristic that light of a certain wavelength (fluorescent light in the present embodiment) can almost completely pass through, while light of another wavelength (side scatter light in the present embodiment) is almost completely reflected. In the present embodiment, the side scatter detection assembly 150 and the fluorescence detection assembly 140 share the focusing assembly 141, and the dichroic mirror 160 is used to guide the fluorescent light and the side scatter light after being converged by the focusing assembly 141 to the detector of the fluorescence detection assembly 140 and the detector of the side scatter detection assembly 150, respectively, thereby effectively improving the compactness of the optical detection device 100, and facilitating the reduction of the volume and cost of the optical detection device 100.

[0072] Preferably, referring to Figure 1 and Figure 5 As shown, the side scatter detection assembly 150 comprises a fourth aperture stop 151 and a third detector 152, the fourth aperture stop 151 is arranged between the dichroic mirror 160 and the third detector 152, and the fourth aperture stop 151 is provided with a fifth light transmission hole 1511 for allowing light to pass through and irradiate on the third detector 152. The fourth aperture stop 151 is used to limit the collection angle range of the side scatter light.

[0073] Preferably, referring to Figure 1 , Figure 5 and Figure 6As shown, the fifth light transmission hole 1511 is a non-circular hole, the inner wall of the fifth light transmission hole 1511 includes two third hole walls 1501 and two fourth hole walls 1502, the two third hole walls 1501 are oppositely arranged in the first direction X, and the two fourth hole walls 1502 are oppositely arranged in the second direction Y and are respectively connected to the two third hole walls 1501, that is, the third hole wall 1501 and the fourth hole wall 1502 are alternately connected to form a closed annular wall surface. The first direction X and the second direction Y are perpendicular to each other, and the first direction X is parallel to the flow direction of the cells to be detected, the distance L3 between the two third hole walls 1501 is greater than the distance L4 between the two fourth hole walls 1502, that is, the size L3 of the fifth light transmission hole 1511 in the first direction X is greater than the size L4 in the second direction Y. Here, by setting the fifth light transmission hole 1511 of the fourth aperture diaphragm 151 as a non-circular hole, and making the size L3 of the fifth light transmission hole 1511 in the first direction X greater than the size L4 in the second direction Y, and the direction with the larger size is parallel to the flow direction of the cells to be detected, so that the internal diffuse reflection stray light of the optical detection device 100 can be reduced, and the requirement for mechanical structure precision can also be greatly reduced, thereby facilitating the simplification of the debugging structure complexity of the optical detection device 100 and the reduction of the cost of the optical detection device 100.

[0074] As a preferred embodiment of the present embodiment, the fifth light transmission hole 1511 is a waist-shaped hole, the two third hole walls 1501 are both semicircular arc surfaces, and the two fourth hole walls 1502 are parallel planes. The fifth light transmission hole 1511 adopts a waist-shaped hole, which can not only meet the design requirement that the size of the fifth light transmission hole 1511 in the two perpendicular directions is different, but also reduce the stress concentration phenomenon of the hole wall of the fifth light transmission hole 1511 through the design of the semicircular arc surface, thereby facilitating the improvement of the structural reliability of the fourth aperture diaphragm 151. Of course, in specific applications, the fifth light transmission hole 1511 is not limited to adopting a waist-shaped hole, for example, as an alternative embodiment, the fifth light transmission hole 1511 can also be designed as an elliptical hole or a rectangular hole.

[0075] In a preferred embodiment of the present embodiment, in order to reduce the accuracy requirement of the positioning of the optical system structure, the aperture diaphragm for the forward scattering signal channel (i.e. the first aperture diaphragm 1322) and the aperture diaphragm for the side scattering signal channel (i.e. the fourth aperture diaphragm 151) are both designed as a light transmission hole adopting a waist-shaped hole or an elliptical hole or a rectangular hole under the premise of guaranteeing the signal noise requirement; of course, in specific applications, as an alternative embodiment, only one of the aperture diaphragm for the forward scattering signal channel (i.e. the first aperture diaphragm 1322) and the aperture diaphragm for the side scattering signal channel (i.e. the fourth aperture diaphragm 151) can be designed as a light transmission hole adopting a waist-shaped hole or an elliptical hole or a rectangular hole.

[0076] As a preferred embodiment of the present embodiment, the working principle of the optical detection device 100 is as follows: the light beam emitted by the laser 121 forms an elliptical spot at the center of the flow chamber 110 after being focused by the pre-adjusting light component 122, and the short axis direction of the elliptical spot is consistent with the flow direction of the cells to be measured, and the long axis direction is perpendicular to the flow direction of the cells to be measured; when the cells to be measured pass through the light beam irradiation area (the elliptical spot at the center of the flow chamber 110), low-angle scattered light, side scattered light and fluorescent light are simultaneously generated. Among them, the low-angle scattered light scattered by the cells to be measured is collected by the first focusing lens 131 when passing through the flow chamber 110, then passes through the second light transmission hole 1302 of the light barrier 1321, converges at the position of the first aperture diaphragm 1322, and finally is received by the first detector 133. According to the signal size, pulse width and area received by the first detector 133, the volume information of the cells to be measured can be represented. In addition, the side scattered light and the fluorescent light scattered by the cells to be measured are collected by the short-focus converging lens group (i.e. focusing component 141) composed of the second focusing lens 1411 and the third focusing lens 1412 when passing through the flow chamber 110. The collection angle range of the side scattered light is limited by the third aperture diaphragm 145, wherein the side scattered light is reflected by the dichroic mirror 160, then focused at the position of the fourth aperture diaphragm 151, enters the third detector 152, and according to the signal size, intensity and area size generated by the third detector 152, the complexity information of the cells can be distinguished; and the fluorescent light transmits through the dichroic mirror 160, passes through the light filter 142, and is finally received by the second detector 143. According to the fluorescent signal size, pulse width and area, the nucleic acid content information in different cells can be reflected.

[0077] Referring to Figure 7 As shown in the figure, the present embodiment also provides a cell analyzer, which comprises a reaction pool 200, a reagent supply device 300, a sampling unit 400, a diluent providing device 500, a conveying device 600, an analysis unit 700, an output unit and the above-mentioned optical detection device 100.

[0078] The reaction pool 200 is used to provide a reaction field for the sample to be measured and the reagent to prepare the detection sample liquid. In the present embodiment, the sample to be measured is a blood sample; of course, in specific applications, as an alternative embodiment, the sample to be measured can also be a body fluid sample.

[0079] The sampling unit 400 is used for collecting the sample to be tested and discharging the sample to be tested into the reaction pool 200. The sampling unit 400 comprises a sampling component, a power element for driving the sampling component to move, and a syringe for driving the sampling component to suck and discharge the sample to be tested. The sampling component can be a sampling needle or a sampling pipette, etc. The sampling component can be moved to a sample storage container (such as a test tube, etc.) to sample under the driving of the power element, and then moved to the reaction pool 200 to sample under the driving of the power element.

[0080] The reagent supply device 300 is used for delivering reagents into the reaction pool 200.

[0081] The delivery device 600 is used for driving the detection sample liquid to be delivered from the reaction pool 200 into the flow chamber 110, and for driving the dilution liquid to be delivered from the dilution liquid supply device 500 into the flow chamber 110, so that the cells to be tested in the detection sample liquid are queued through the flow chamber 110 under the wrapping of the dilution liquid.

[0082] The optical detection device 100 is used for detecting the detection sample liquid wrapped through the flow chamber 110 by the dilution liquid. The optical detection device 100 can be used for reticulocyte detection, white blood cell classification detection, or other types of optical detection projects.

[0083] The analysis unit 700 is used for analyzing the detection result of the detection sample liquid according to the optical signal fed back by the detector.

[0084] The output unit is used for outputting the detection result of the analysis unit 700. The output unit is preferably a display screen, so that the detection result can be intuitively displayed.

[0085] The cell analyzer provided in the embodiment has the effective effects of the optical detection device 100.

[0086] In addition to the optical detection device 100, the cell analyzer can also comprise other types of detection devices, such as a hemoglobin detection device, an impedance counting detection device, etc. The specific application can be set according to the actual needs. The hemoglobin detection device is used for hemoglobin concentration detection; the impedance counting detection device is used for red blood cell number detection and / or platelet counting detection, etc.

[0087] In a preferred embodiment of this invention, the optical detection device 100 of the cell analyzer adopts a low-cost, miniaturized, and low-feedback optical path structure design. Based on the fluorescence detection cell analyzer, it can reduce the size and cost of the optical detection device 100, improve the signal-to-noise ratio of the optical system, and provide an effective solution for low-cost and miniaturized fluorescence detection cell analyzers. At the same time, it meets the noise suppression requirements of fluorescence detection and small particle detection, thereby ensuring the accuracy and reliability of cell classification and counting.

[0088] Example 2:

[0089] Reference Figure 1 , Figure 5 and Figure 8 As shown, the optical detection device 100 and cell analyzer provided in this embodiment differ from those in Embodiment 1 mainly in whether an aperture stop is provided between the filter element 142 and the second detector 143 in the fluorescence detection component 140. Specifically, in Embodiment 1, the aperture stop between the filter element 142 and the second detector 143 was omitted; however, in this embodiment, the aperture stop between the filter element 142 and the second detector 143 is not omitted, but the light-transmitting aperture on the aperture stop between the filter element 142 and the second detector 143 is enlarged. That is, in this embodiment, the aperture diameter d of the light-transmitting aperture on the aperture stop between the filter element 142 and the second detector 143 is larger than the aperture diameter of the light-transmitting aperture on the aperture stop between the filter element 142 and the second detector 143 in the conventional technology.

[0090] Specifically, in this embodiment, the fluorescence detection component 140 further includes a second aperture stop 144 disposed between the filter 142 and the second detector 143. The second aperture stop 144 has a third light-transmitting hole 1441 through it for allowing light to pass through and illuminate the second detector 143. The third light-transmitting hole 1441 is a circular hole with a diameter d greater than 1.2 mm. The second aperture stop 144 is used to limit the angle range of the light beam transmitted through it, so as to shield stray light in the fluorescence direction.

[0091] In this embodiment, based on the target surface size of the second detector 143, the second detector 143 is designed in front of the focal point A of the focusing component 141, and the aperture d of the third light-transmitting hole 1441 on the second aperture stop 144 in front of the second detector 143 is enlarged. The cutoff of the filter element 142 for the spectral band of the laser 121 is designed to be greater than OD6. In this way, the volume of the optical detection device 100 can be effectively reduced, the fluorescence signal-to-noise ratio can be guaranteed, and the requirements for the target surface positioning accuracy of the second detector 143 can be greatly reduced.

[0092] In addition to the above differences, other structures of the optical detection device 100 and the cell analyzer provided by the embodiment can be correspondingly optimized and designed according to the first embodiment, and will not be described in detail here.

[0093] The above only describes the preferred embodiments of the present application, and does not limit the patent scope of the present application. Any equivalent structural transformation, direct / indirect application in other related technical fields, or the like made by using the content of the present application specification and drawings under the inventive concept of the present application is included in the patent protection scope of the present application.

Claims

1. An optical detection device applied to a cell analyzer, characterized in that: The optical detection device comprises: a flow chamber for queuing cells to be detected in a sample liquid to pass through under the entrainment of a diluent; a light source for emitting light towards the cells to be detected flowing through the flow chamber; a forward scattering detection assembly for collecting forward scattering signals generated by the light source irradiating on the cells to be detected, the forward scattering detection assembly comprising a first focusing lens, a diaphragm assembly and a first detector, the diaphragm assembly being arranged between the first focusing lens and the first detector, the first focusing lens being arranged between the flow chamber and the diaphragm assembly for converging forward scattering light generated by the light source irradiating on the cells to be detected to pass through the diaphragm assembly and enter the first detector, the diaphragm assembly comprising a straight light blocking diaphragm and a first aperture diaphragm, the straight light blocking diaphragm being arranged between the first focusing lens and the first aperture diaphragm, the first aperture diaphragm being arranged between the straight light blocking diaphragm and the first detector, the first aperture diaphragm being provided with a first light transmission hole for light to pass through and irradiate on the first detector; a side scattering detection assembly for collecting side scattering signals generated by the light source irradiating on the cells to be detected, the side scattering detection assembly comprising a fourth aperture diaphragm and a third detector, the fourth aperture diaphragm being arranged between the flow chamber and the third detector, and the fourth aperture diaphragm being provided with a fifth light transmission hole for light to pass through and irradiate on the third detector; at least one of the first light transmission hole and the fifth light transmission hole is a non-circular hole, the non-circular hole having a dimension in a first direction greater than a dimension in a second direction, the first direction and the second direction being perpendicular to each other, and the first direction being parallel to a flow direction of the cells to be detected.

2. The optical detection device of claim 1, wherein: The first focusing lens has a first incident surface arranged towards the flow chamber and a first exit surface arranged towards the diaphragm assembly, and the first incident surface is a spherical surface arranged convexly towards the flow chamber.

3. The optical detection device of claim 2, wherein: The first exit surface is a spherical surface arranged convexly towards the diaphragm assembly, or the first exit surface is a plane.

4. The optical detection device according to any one of claims 1 to 3, characterized in that: The straight light blocking diaphragm has a blocking portion for blocking direct light passing through the cells to be detected and two second light transmission holes arranged respectively on two sides of the blocking portion for light converging by the first focusing lens to pass through and irradiate on the first aperture diaphragm.

5. The optical detection device according to any one of claims 1 to 3, characterized in that: The first light transmission hole is a non-circular hole, and an inner wall of the first light transmission hole comprises two first hole walls arranged oppositely in a first direction and two second hole walls arranged oppositely in a second direction and connected to the two first hole walls respectively, the first direction and the second direction being perpendicular to each other, and the first direction being parallel to the flow direction of the cells to be detected, and a distance between the two first hole walls being greater than a distance between the two second hole walls.

6. The optical detection device according to any one of claims 1 to 3, wherein: The first light transmission hole is a waist-shaped hole, an elliptical hole or a rectangular hole.

7. The optical detection device according to any one of claims 1 to 3, wherein: The optical detection device further comprises a fluorescence detection assembly for collecting fluorescence signals generated by the light source irradiating on the cells to be detected, the fluorescence detection assembly comprising a focusing assembly, a filter and a second detector, the filter being arranged between the focusing assembly and the second detector; the focusing assembly is arranged between the flow chamber and the filter, for converging the fluorescence light generated by the light source irradiating on the cells to be detected and then passing through the filter into the second detector, the second detector being located between the filter and the focal point of the focusing assembly.

8. The optical detection device of claim 7, wherein: The filter has an OD6 or above cut-off range for the light source spectrum.

9. The optical detection device of claim 7, wherein: The focusing assembly has a focal length of greater than 4.0 mm.

10. The optical detection device of claim 7, wherein: The fluorescence detection assembly further comprises a second aperture stop arranged between the filter and the second detector, the second aperture stop is provided with a third light transmission hole for light transmission and irradiation on the second detector, the third light transmission hole has an aperture of greater than 1.2 mm.

11. The optical detection device of claim 7, wherein: The focusing assembly comprises a second focusing lens and a third focusing lens, the second focusing lens is arranged between the flow chamber and the third focusing lens, and the third focusing lens is arranged between the second focusing lens and the filter.

12. The optical detection device of claim 11, wherein: The fluorescence detection assembly further comprises a third aperture stop, the third aperture stop is arranged between the second focusing lens and the third focusing lens, and the third aperture stop is provided with a fourth light transmission hole for light transmission and irradiation on the third focusing lens.

13. The optical detection device of claim 7, wherein: The optical detection device further comprises a dichroic mirror, the dichroic mirror is located between the focusing assembly and the filter and between the focusing assembly and the side scatter detection assembly, for transmitting the fluorescence light generated by the light source irradiating on the cells to be detected to the filter and reflecting the side scatter light generated by the light source irradiating on the cells to be detected to the side scatter detection assembly.

14. The optical detection device of claim 13, wherein: The fourth aperture stop is arranged between the dichroic mirror and the third detector, and the fourth aperture stop is provided with a fifth light transmission hole for light transmission and irradiation on the third detector.

15. The optical detection device of claim 1, wherein: The fifth light transmission hole is a non-circular hole, the inner wall of the fifth light transmission hole comprises two third hole walls and two fourth hole walls, the two third hole walls are oppositely arranged in a first direction, and the two fourth hole walls are oppositely arranged in a second direction and connected to the two third hole walls respectively, the first direction and the second direction are perpendicular to each other, and the first direction is parallel to the flow direction of the cells to be detected, and the distance between the two third hole walls is greater than the distance between the two fourth hole walls.

16. The optical detection device of claim 15, wherein: The fifth light transmission hole is a waist-shaped hole, an elliptical hole or a rectangular hole.

17. The optical detection device of any one of claims 1 to 3, wherein: The light source comprises a laser and a pre-light modulation assembly arranged between the laser and the flow chamber; and / or, The light emitted by the light source forms an elliptical spot at the center position of the flow chamber, the short axis direction of the elliptical spot is parallel to the flow direction of the cells to be detected, and the long axis direction of the elliptical spot is perpendicular to the flow direction of the cells to be detected.

18. A cell analyzer characterized by: The reaction cell, the reagent supply device, the sampling unit, the diluent supply device, the conveying device, the analysis unit, the output unit and the optical detection device as claimed in any one of claims 1 to 17; The reaction cell is used to provide a reaction site for the sample to be tested and reagents to prepare a detection sample solution; The sampling unit is used to collect the sample to be tested and discharge the sample to be tested into the reaction cell; The reagent supply device is used to convey reagents into the reaction cell; The conveying device is used to drive the detection sample solution from the reaction cell into the flow chamber and to drive the diluent from the diluent supply device into the flow chamber so that the cells to be tested in the detection sample solution are carried by the diluent and pass through the flow chamber in a queue; The optical detection device is used to detect the detection sample solution carried by the diluent through the flow chamber; The analysis unit is used to analyze the detection result of the detection sample solution according to the optical signal fed back by the detector; The output unit is used to output the detection result of the analysis unit.

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