CN218496689U - Sample optical detection system and blood cell analyzer - Google Patents
Sample optical detection system and blood cell analyzer Download PDFInfo
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- CN218496689U CN218496689U CN202221716748.8U CN202221716748U CN218496689U CN 218496689 U CN218496689 U CN 218496689U CN 202221716748 U CN202221716748 U CN 202221716748U CN 218496689 U CN218496689 U CN 218496689U
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Abstract
The application discloses a sample optical detection system and a blood cell analyzer, wherein the sample optical detection system comprises a flow chamber, a light source device, a light processing device and a light receiving device; the flow chamber is used for allowing first particles in a sample to be tested to pass along a first direction; a light source device for illuminating first particles passing through the flow cell; the light processing device comprises a collecting assembly and a diaphragm assembly, wherein the collecting assembly is used for collecting scattered light generated by the first particles irradiated by the light source device and passing through the flow chamber, and the scattered light is converged at the corresponding diaphragm assembly; the diaphragm assembly is used for filtering scattered light of the first particles in the first position range and enabling the scattered light of the first particles in the second position range to pass; the light receiving device is at least used for receiving the scattered light of the first particles in the second position range and outputting corresponding electric signals. The embodiment of the application aims to effectively eliminate the interference of the sidelobe signal of the large particle and accurately obtain the blood cell detection result.
Description
Technical Field
The application relates to the field of optical detection, in particular to a sample optical detection system and a blood cell analyzer.
Background
Currently, an optical detection system in a blood cell analyzer generally uses a laser as a light source, for example, a five-classification blood cell analyzer mostly uses a laser scattering principle to measure blood cells in a blood sample, and can count and classify the blood cells by using at least two measurement channels, especially three measurement channels.
In five-class applications, the RET channel requires simultaneous detection of particles such as platelets and red blood cells. In particular, for large particles (such as red blood cells), the amplitude of the main lobe signal is large, so the amplitude of the side lobe signal is also large, and may be close to the amplitude of the main lobe signal of small particles (such as platelets). Therefore, when large particles and small particles in blood cells are simultaneously detected due to interference of side lobe signals of the large particles, blood cell detection results cannot be accurately obtained.
SUMMERY OF THE UTILITY MODEL
The embodiment of the application provides a sample optical detection system, which aims to effectively eliminate interference of a sidelobe signal of a large particle and accurately obtain a blood cell detection result.
In order to achieve the above object, in a first aspect, the embodiments of the present application adopt the following technical solutions:
a sample optical detection system comprises a flow chamber, a light source device, a light processing device and a light receiving device;
the flow chamber is used for allowing first particles in a sample to be tested to pass along a first direction; a light source device for illuminating the first particles passing through the flow cell; the light processing device comprises a collection assembly and a diaphragm assembly, wherein the collection assembly is used for collecting scattered light and/or side fluorescent light generated by the first particles irradiated by the light source device through the flow chamber and converging the scattered light and/or the side fluorescent light at the corresponding diaphragm assembly; the diaphragm assembly is used for filtering the scattered light and/or the side fluorescent light of the first particles in a first position range and enabling the scattered light and/or the side fluorescent light of the first particles in a second position range to pass through, and the first position range and the second position range are adjacently arranged in the first direction; the light receiving device is at least used for receiving the scattered light and/or the lateral fluorescence of the first particles in the second position range and outputting corresponding electric signals.
Optionally, the scattered light comprises forward scattered light, and the flow cell is further configured to pass second particles in the sample to be tested in the first direction;
the diaphragm assembly comprises a first light-transmitting part, a first light blocking part, a second light blocking part and two second light-transmitting parts; the first light transmitting portion is configured to pass the forward scattered light of the first particles in a second position range; the first light blocking part and the second light blocking part are arranged at intervals in the first direction and are positioned on two sides of the first light transmission part, and the first light blocking part and the second light blocking part are used for filtering the forward scattering light of the first particles in a first position range; the two second light transmission parts are arranged at intervals in the first direction, one of the two second light transmission parts is positioned on one side of the first light blocking part far away from the first light transmission part, the other one of the two second light transmission parts is positioned on one side of the second light blocking part far away from the first light transmission part, and the two second light transmission parts are used for enabling the forward scattering light of the second particles to pass through; the light receiving device is at least used for receiving the forward scattered light of the first particles in a second position range and the forward scattered light of the second particles and outputting corresponding electric signals.
Optionally, the scattered light comprises forward scattered light, and the flow cell is further configured to pass second particles in the sample to be tested in the first direction;
the diaphragm assembly comprises a third light blocking part, a fourth light blocking part and a third light transmitting part; the third light blocking part and the fourth light blocking part are arranged at intervals in the first direction and are used for filtering the forward scattered light of the first particles in a first position range; the third light transmission part is arranged around the third light blocking part and the fourth light blocking part, and the third light transmission part is used for enabling the forward scattered light of the first particles in a second position range to pass through and the forward scattered light of the second particles to pass through; the light receiving device is at least used for receiving the forward scattered light of the first particles in a second position range and the forward scattered light of the second particles and outputting corresponding electric signals.
Optionally, the third light-transmitting portion is fabricated on a substrate material by a photolithography process or an etching process.
Optionally, the lengths of the third light blocking portion and the fourth light blocking portion are both greater than a first preset light blocking portion length value, and the first preset light blocking portion length value is determined according to the sample flow width of the first particles in the flow chamber and the magnification of the forward scattered light.
Optionally, the length of the first light transmission part is smaller than a preset light transmission part length value, and the preset light transmission part length value is determined according to the inner wall distance of the flow chamber and the amplification factor of the forward scattered light.
Optionally, a width of the first light-transmitting portion is smaller than a preset light-transmitting portion width value, where the preset light-transmitting portion width value is determined according to a width of a corresponding main lobe signal in the forward scattered light of the first particle and an amplification factor of the forward scattered light.
Optionally, widths of the first light blocking portion and the second light blocking portion are both greater than a second preset light blocking portion width value, and the second preset light blocking portion width value is determined according to a width of a side lobe signal corresponding to the forward scattered light of the first particle and an amplification factor of the forward scattered light.
Optionally, the optical detection system further comprises a collimating mechanism and a shaping mechanism;
the collimation mechanism is used for receiving the detection light emitted by the light source device and collimating the detection light;
the shaping mechanism is used for receiving the collimated detection light and shaping the detection light to irradiate particles passing through the flow chamber, and comprises a first lens and a first doublet lens which are sequentially arranged, the first lens is used for diverging the detection light collimated by the collimating mechanism along a first direction, the first doublet lens is used for converging the detection light diverged by the first lens along the first direction and a second direction, and the first direction is perpendicular to the second direction.
In order to achieve the above object, in a second aspect, the embodiments of the present application adopt the following technical solutions:
a blood cell analyzer comprises a sampling part, a reaction part, an optical detection system and a controller;
the sampling part is used for collecting a blood sample; the reaction part is used for providing a reagent and allowing the blood sample and the reagent to react to form the sample to be detected; the optical detection system as described above; the controller is used for receiving the electric signals output by the scattered light and/or the lateral fluorescence from the optical detection system and obtaining a blood cell detection result according to the electric signals.
The sample optical detection system provided by the embodiment of the application comprises a flow chamber, a light source device, a light processing device and a light receiving device; the scattered light and/or the side fluorescent light generated by the first particles passing through the flow chamber are irradiated by the collecting light source device, and are converged at the corresponding diaphragm assembly, so that the diaphragm assembly filters the scattered light and/or the side fluorescent light of the first particles in the first position range, the scattered light and/or the side fluorescent light of the first particles in the second position range passes through the diaphragm assembly, and finally, the scattered light and/or the side fluorescent light of the first particles in the second position range are received by the light receiving device, and corresponding electric signals are output, so that the interference of side lobe signals of large particles can be effectively eliminated, and meanwhile, when the large particles and the small particles in blood cells are detected, the interference of the side lobe signals of the large particles can be avoided, and the blood cell detection result can be accurately obtained.
It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the disclosure of the embodiments of the present application.
Drawings
In order to more clearly illustrate the technical solutions in the embodiments of the present application, the drawings needed to be used in the description of the embodiments are briefly introduced below, and it is obvious that the drawings in the following description are only some embodiments of the present application, and it is obvious for those skilled in the art to obtain other drawings based on these drawings without creative efforts.
FIG. 1 is a graph showing the amplitude of platelet and red blood cell signals in a forward scattered light obtained by the prior art;
FIG. 2 is a block diagram of a sample optical detection system according to an embodiment of the present disclosure;
FIG. 3 is a schematic top view structure diagram of a sample optical inspection system according to an embodiment of the present disclosure;
fig. 4 is a schematic view of an application scenario of forming a main lobe signal and a side lobe signal of a first particle according to an embodiment of the present application;
FIG. 5 is a schematic block diagram of a diaphragm assembly provided in an embodiment of the present application;
FIG. 6 (a) is a schematic view of an application scenario of scattered light generated by particles passing through a flow cell illuminated by light according to an embodiment of the present disclosure;
fig. 6 (b) is a schematic view of an application scenario in which scattered light is irradiated on a diaphragm assembly according to an embodiment of the present application;
FIG. 7 is a schematic block diagram of another diaphragm assembly provided in an embodiment of the present application;
FIG. 8 is a schematic block diagram of another diaphragm assembly provided in an embodiment of the present application;
fig. 9 is a schematic block diagram of a blood cell analyzer according to an embodiment of the present disclosure;
reference numerals:
1000. a blood cell analyzer;
100. a sample optical detection system; 10. a light source device; 20. a flow chamber; 30. a light processing device; 31. a collection assembly; 310. a second lens; 311. a first meniscus lens; 312. a first biconvex lens; 313. a third lens; 314. a second biconvex lens; 315. a second meniscus lens; 32. a diaphragm assembly; 320. a first light-transmitting portion; 321. a first light blocking part; 322. a second light blocking part; 323. a second light-transmitting portion; 324. a third light blocking portion; 325. a fourth light blocking portion; 326. a third light-transmitting portion; 327. a light shielding portion; 40. a light receiving device; 50. a collimating mechanism; 60. a shaping mechanism; 61. a first lens; 62. a first cemented doublet lens; a-a first range of positions; b-a second range of positions;
200. a sampling section;
300. a reaction section;
400. and a controller.
Detailed Description
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, and it is obvious that the described embodiments are some, but not all, of the embodiments of the present application. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
In the description of the present application, unless expressly stated or limited otherwise, the terms "mounted," "connected," and "connected" are to be construed broadly and include, for example, fixed and removable connections or integral connections; can be mechanically or electrically connected; they may be connected directly or indirectly through intervening media, or they may be interconnected between two elements. The specific meaning of the above terms in the present application can be understood in a specific case by those of ordinary skill in the art.
The flow diagrams depicted in the figures are merely illustrative and do not necessarily include all of the elements and operations/steps, nor do they necessarily have to be performed in the order depicted. For example, some operations/steps may be decomposed, combined or partially combined, so that the actual execution sequence may be changed according to the actual situation.
In the following, some embodiments of the present application will be described in detail with reference to the accompanying drawings, and features in the following examples and examples may be combined with each other without conflict.
First, referring to fig. 1, fig. 1 is a schematic diagram of amplitudes of platelets and erythrocytes in forward scattered light obtained by using the prior art, where, as shown in fig. 1, amplitudes of main lobe signals of erythrocytes are generally larger, side lobe signals thereof are distributed on two sides of the main lobe signals, and amplitudes of the side lobe signals are generally smaller than the main lobe signals, but as can be seen from fig. 1, amplitudes of the side lobe signals of erythrocytes are closer to amplitudes of the main lobe signals of platelets, since a RET channel needs to detect particles such as platelets and erythrocytes at the same time, a blood cell detection result cannot be accurately obtained due to interference of the side lobe signals of large particles.
In the prior art, a side lobe signal can be blocked by using a small hole in a front light processing module (located between a light source device and a flow chamber), however, due to the limitation of the result, the light spot at the focus is necessarily small (for example, less than 10 um), and the diaphragm is also necessarily small, which greatly increases the difficulty of processing and assembling. Moreover, since the detection light emitted by the light source device is coherent light, the pinhole can significantly amplify the diffraction effect, and can form more side lobes. In the prior art, a diffusion sheet rotating at a high speed is added at a focus by utilizing laser equipment with higher power to convert coherent light into incoherent light, so that a side lobe can be eliminated, but the structure is complex and is not suitable for an instrument for classifying five blood cells.
Therefore, there is a need for a sample optical detection system, which can effectively eliminate the interference of the sidelobe signal of large particles in five-classification applications, so as to accurately obtain the blood cell detection result.
The application provides a sample optical detection system 100, which can effectively eliminate interference of a side lobe signal of a large particle, and can avoid interference of the side lobe signal of the large particle when detecting the large particle and the small particle in a blood cell, thereby accurately obtaining a blood cell detection result.
Fig. 3 is a schematic top view configuration diagram of the sample optical detection system, i.e., a top view of the sample optical detection system from a top view angle in the first direction. Referring to fig. 2 to 3, a sample optical detection system 100 according to an embodiment of the present disclosure includes a light source device 10, a flow cell 20, a light processing device 30, and a light receiving device 40; the flow chamber 20 is configured to allow first particles in a sample to be detected to pass through along a first direction, where the sample to be detected may be a blood sample, and the blood sample includes multiple particles such as red blood cells, platelets, and reticulocytes, where the first particles are large particles in the blood sample, such as red blood cells, and particles with a particle diameter larger than a preset particle diameter may be considered as the large particles, and the preset particle diameter may be any value, and may be set according to an actual situation, and is generally 7um. The light source device 10 is configured to emit detection light in the optical axis direction, and irradiate the first particles passing through the flow cell 20 with the detection light, thereby generating scattered light and/or lateral fluorescence. The scattered light may include forward scattered light and side scattered light, among others.
The collecting mechanism is arranged between the flow chamber 20 and the light receiving device 40, and the collecting assembly 31 is used for collecting scattered light and/or side fluorescent light generated by the first particles irradiated by the light source device 10 through the flow chamber 20 and converging the scattered light and/or the side fluorescent light at the corresponding diaphragm assembly 32; wherein the first particles irradiated by the detection light through the flow cell 20 may generate forward scattered light and/or side fluorescent light, and specifically, the corresponding diaphragm assemblies 32 may be respectively disposed at the focal points corresponding to different light rays, thereby allowing the scattered light and/or the side fluorescent light to be converged at the corresponding diaphragm assemblies 32. Referring to fig. 5, the aperture assembly 32 is used for filtering the scattered light and/or the side fluorescent light of the first particle in the first position range a and allowing the scattered light and/or the side fluorescent light of the first particle in the second position range B to pass through. The first position range a and the second position range B are adjacently arranged in the first direction, which is the flowing direction of the first particles in the sample to be measured in the flow chamber 20. As shown in fig. 4, the arrow direction corresponding to the dotted line in fig. 4 is the first direction, that is, the flowing direction of the first particle in the sample to be tested, the light source device 10 emits light to irradiate the first particle passing through the flow chamber 20, specifically, the position where the light is directly incident on the flow chamber 20 is the flow chamber detection position, and in fact, since the first particle flows in the flow chamber along the first direction, the first particle is respectively located below the flow chamber detection position, above the flow chamber detection position and above the flow chamber detection position at-x seconds, 0 seconds and x seconds, so that the coherence of the light is generated during the test. When the light propagates, the scattered light and/or the fluorescent light corresponding to the first particle at-x second is located above the scattered light and/or the fluorescent light corresponding to the first particle at 0 second (the corresponding signal received by the light receiving device 40 is a side lobe signal), and the scattered light and/or the fluorescent light corresponding to the first particle at x second is located below the scattered light and/or the fluorescent light corresponding to the first particle at 0 second (the corresponding signal received by the light receiving device 40 is a side lobe signal), so that the signal of the first particle is a side lobe signal, a main peak signal, and a side lobe signal in sequence in the first direction. When the scattered light and/or the side fluorescent light of the first particle reaches the diaphragm assembly 32, the scattered light rays and/or the side fluorescent light rays of the first particle corresponding to-x seconds and x seconds are distributed on both sides of the scattered light rays and/or the side fluorescent light rays corresponding to x seconds in the first direction, respectively. In the embodiment of the present application, in order to mainly eliminate the influence of the first particles corresponding to the-x second and the x second on the signal generated at the 0 second detection bit (i.e., the main lobe signal of the first particle) at different positions, it is necessary to eliminate the signals generated at the-x second and the x second (i.e., the side lobe signal of the first particle). Therefore, the first position range a of the diaphragm assembly 32 corresponds to the position of the scattered light ray and/or the side fluorescent light ray on the diaphragm assembly 32 for x seconds, and the second position range B corresponds to the position of the scattered light ray and/or the side fluorescent light ray on the diaphragm assembly 32 generated at the detection position for 0 seconds, so that the first position range a and the second position range B are adjacently arranged in the first direction, for example, as shown in fig. 5, the first position range a and the second position range B are adjacently arranged at least in the first direction, and the first position range a may also be arranged around the second position range B. The first position range a is actually used for filtering the scattered light and/or the side fluorescence corresponding to the first particle side lobe signal, and the second position range B is actually used for passing the scattered light and/or the side fluorescence corresponding to the first particle main lobe signal. The first range of positions a is a non-light-transmissive portion of the diaphragm assembly 32 and the second range of positions B is a light-transmissive portion of the diaphragm assembly.
The light receiving device 40 is at least used for receiving the scattered light and/or the lateral fluorescence of the first particles in the second position range B and outputting corresponding electric signals. In particular, for forward scattered light, side scattered light or side fluorescent light, a light receiving device 40 may be arranged behind its corresponding light processing device 30, respectively, for receiving said scattered light and/or said side fluorescent light of the first particles in the second position range B and outputting corresponding electrical signals. The light receiving device 40 may be configured to detect the light intensity of the scattered light and output a corresponding electrical signal, for example, the forward scattering light channel may be configured to measure the volume of the blood cells, the lateral scattering light channel may be configured to measure the complexity of the surface of the blood cells, and the lateral fluorescence channel may be configured to measure the content of nucleic acid in the blood cells.
In the sample optical detection system 100 provided in the embodiment of the present application, the light source device 10 is used for collecting scattered light and/or lateral fluorescence generated by first particles passing through the flow chamber 20, and the scattered light and/or the lateral fluorescence are converged at the corresponding diaphragm assembly 32, so that the diaphragm assembly 32 filters the scattered light and/or the lateral fluorescence of the first particles in the first position range a, and the scattered light and/or the lateral fluorescence of the first particles in the second position range B pass through, and finally the light receiving device 40 is used for receiving the scattered light and/or the lateral fluorescence of the first particles in the second position range B and outputting a corresponding electrical signal, thereby effectively eliminating interference of a large-particle side lobe signal, and avoiding interference of a large-particle side lobe signal when detecting large particles and small particles in blood cells, so as to accurately obtain a blood cell detection result.
Since the light source device 10 irradiates the first particles passing through the flow cell 20 to generate forward scattered light and/or side fluorescent light, the diaphragm assembly 32 may be disposed on the optical path corresponding to the forward scattered light, the side scattered light and the side fluorescent light, and the following description will take the example of disposing the diaphragm assembly 32 on the optical path corresponding to the forward scattered light as an example.
In some embodiments, flow cell 20 is also used to pass second particles in the sample to be tested in the first direction. Wherein the second particles have a smaller diameter than the first particles. It should be noted that, as shown in fig. 6 (a), after the light passes through the flow chamber 20, a main-lobe signal and a side-lobe signal corresponding to the forward scattering light of the first particle are generated, and the main-lobe signal and the side-lobe signal corresponding to the forward scattering light of the first particle are collected by the collecting assembly 31. When the second position range B is small, the signal corresponding to each particle detected by the light receiving device is attenuated, especially for the second particle. Similarly, the second particle passes through the detection site after a certain time interval, and the corresponding forward scattered light is shown in fig. 6 (a), the solid line in fig. 6 (a) and 6 (b) indicates the forward scattered light of the first particle, and the dotted line in fig. 6 (a) and 6 (b) indicates the forward scattered light of the second particle. Since the size of the second particles is small (smaller than the size of the first particles), the forward scattering signal in the first direction is a diffuse spot (i.e., the scattering angle is large, see fig. 6 (a)), and therefore, in order to make the forward scattered light of the second particles pass through the diaphragm assembly 32 as much as possible, the diaphragm assembly 32 includes a first light transmitting portion 320, a first light blocking portion 321, a second light blocking portion 322, and two second light transmitting portions 323. As shown in fig. 6 (B), since the second position range B mainly corresponds to the position of the forward scattered light of the first particle on the diaphragm assembly 32, and the forward scattered light corresponding to the second particle is a diffuse spot (i.e. only part of the forward scattered light of the second particle passes through the second position range B, so that the signal intensity received by the light receiving device 40 to the second particle is low), the diaphragm assembly 32 needs to be arranged to block only the forward scattered light corresponding to the side lobe signal of the large particle, and to allow the forward scattered light corresponding to the small particle to pass through as much as possible. As shown in fig. 7, the diaphragm assembly 32 includes a first light-transmitting portion 320, a first light-blocking portion 321, a second light-blocking portion 322, and two second light-transmitting portions 323. The first light transmission part 320 is used for allowing the forward scattered light of the first particles in the second position range to pass through, and a region corresponding to the second position range B is a light transmission region of the first light transmission part 320; the first light-transmitting portion 320 may be a slit or a light-transmitting member. The first light blocking part 321 and the second light blocking part 322 are arranged at an interval in the first direction and located at two sides of the first light transmitting part 320, and both the first light blocking part 321 and the second light blocking part 322 are used for filtering forward scattered light of the first particles in a first position range a, where the first position range a is a light blocking area of the first light blocking part 321 and the second light blocking part 322; and the two second light transmitting portions 323 allow forward scattered light of the second particles to pass therethrough as much as possible.
The first transparent portion 320, the first light blocking portion 321, the second light blocking portion 322, and the two second transparent portions 323 are further provided with light blocking portions 327 on both sides in the second direction, and the light blocking portions 327 are used to block forward scattered light irradiated on both side edges of the diaphragm assembly 32.
The two second light transmitting portions 323 are spaced in the first direction, one of the two second light transmitting portions 323 is located on a side of the first light blocking portion 321 away from the first light transmitting portion 320, and the other is located on a side of the second light blocking portion 322 away from the first light transmitting portion 320, and the two second light transmitting portions 323 are used for allowing forward scattered light of the second particles to pass through. The light receiving device 40 is at least used for receiving the forward scattered light of the first particles in the second position range and the forward scattered light of the second particles and outputting corresponding electric signals. Accordingly, the corresponding main lobe signal of the forward scattered light of the first particle and the forward scattered light of the second particle can be caused to pass through the aperture assembly 32, and the light receiving device 40 can simultaneously receive the corresponding main lobe signal of the forward scattered light of the first particle and the forward scattered light of the second particle, so that large particles and small particles can be accurately detected, interference of side lobe signals of the large particles is avoided, and a blood cell detection result can be accurately obtained.
In some embodiments, the length of first light transmission portion 320 is less than a predetermined light transmission portion length value, which is determined according to the distance between the inner walls of flow cell 20 and the magnification of the forward scattered light. Since the side lobe signal of the blood cell detection result is mainly generated by the first particle, and the forward scattered light of the first particle is mainly concentrated in the range of 5 °, the focus of the ± 5 ° field angle can be regarded as the reference in consideration of the spherical aberration of the back light focus. Therefore, the length of the first light transmission portion 320 may be set to be smaller than a preset light transmission portion length value in consideration of the influence of spherical aberration.
The preset length of the light transmission part can be obtained by multiplying the distance between the inner wall of the flow cell 20 and the amplification factor of the forward scattered light. In general, the length of the first light transmission portion 320 may be smaller than the preset light transmission portion length value, and for example, the length of the first light transmission portion 320 may be 0.8 times the preset light transmission portion length value.
For example, if the distance between the inner walls of the flow cell 20 is 200um and the magnification of the forward scattered light is 5 times, the calculated preset light transmission portion length value is 1mm, and the length of the first light transmission portion 320 may be 800um.
In some embodiments, the width of the first light-transmitting portion 320 is smaller than a preset light-transmitting portion width value, which is determined according to the width of the corresponding main lobe signal in the forward scattered light of the first particles and the magnification of the forward scattered light. The width of the first light transmission portion 320 may be set to be smaller than a preset light transmission portion width value in consideration of the influence of the spherical aberration.
The preset light transmission part width value can be obtained by multiplying the width of the corresponding main lobe signal in the forward scattered light of the first particles and the amplification factor of the forward scattered light. Generally, the width of the first light transmission portion 320 may be smaller than the preset light transmission width value, and for example, the width of the first light transmission portion 320 may be 0.8 times the preset light transmission width value.
For example, if the width of the side lobe signal corresponding to the forward scattered light of the first particle is 20um and the amplification factor of the forward scattered light is 5 times, the preset light transmission portion length value is calculated to be 100um, and the length of the first light transmission portion 320 may be 80um.
In some embodiments, the widths of the first light blocking part 321 and the second light blocking part 322 are greater than a second preset light blocking part width value, and the second preset light blocking part width value is determined according to the width of the sidelobe signal corresponding to the forward scattered light of the first particle and the amplification factor of the forward scattered light. The widths of the first light blocking part 321 and the second light blocking part 322 may be set to be greater than a second preset light blocking part width value in consideration of the influence of the spherical aberration.
The second preset light blocking part width value can be obtained by multiplying the width of a side lobe signal corresponding to forward scattered light of the first particles and the amplification factor of the forward scattered light. Generally, the widths of the first light blocking portion 321 and the second light blocking portion 322 are only required to be greater than the second preset light blocking portion width value, and exemplarily, the widths of the first light blocking portion 321 and the second light blocking portion 322 may be 1.2 times the second preset light blocking portion width value.
For example, if the width of the side lobe signal corresponding to the forward scattered light of the first particle is 10um and the amplification factor of the forward scattered light is 5 times, the second preset light blocking portion width value is calculated to be 50um, and the widths of the first light blocking portion 321 and the second light blocking portion 322 may be 60um.
In some embodiments, flow cell 20 is also used to pass second particles in the sample to be tested in the first direction.
As shown in fig. 8, the diaphragm assembly 32 includes a third light blocking portion 324, a fourth light blocking portion 325, and a third light transmitting portion 326. The third light blocking part 324 and the fourth light blocking part 325 are arranged at intervals in the first direction, and the third light blocking part 324 and the fourth light blocking part 325 are used for filtering forward scattered light of the first particles in the first position range; the third light transmission part 326 is arranged around the third light blocking part 324 and the fourth light blocking part 325, and the third light transmission part 326 is used for enabling the forward scattered light of the first particles in the second position range to pass through and the forward scattered light of the second particles to pass through; the light receiving device 40 is at least used for receiving the forward scattered light of the first particles in the second position range and the forward scattered light of the second particles and outputting corresponding electric signals.
The third light transmission section 326 is further provided with light shielding sections 327 on both sides in the second direction, the light shielding sections 327 shielding forward scattered light irradiated on both side edges of the aperture block 32, and the second direction is perpendicular to the first direction and perpendicular to the optical axis direction.
In some embodiments, the third light-transmitting portion 326 may be formed on the substrate material by a photolithography process or an etching process.
The third light-transmitting portion 326 may be obtained by fabricating a mask on a substrate material, which may include a film, plastic, or glass. Specifically, the optical mask can be used to fabricate the third light-transmitting portion 326 by fabricating various functional patterns on a substrate material such as a film, plastic, or glass and precisely positioning the functional patterns for a structure for selective exposure of a photoresist coating.
In some embodiments, the length of each of third light stop 324 and fourth light stop 325 is greater than a first predetermined light stop length value, which is determined based on the sample flow width of the first particles in flow cell 20 and the magnification of the forward scattered light.
Wherein the first predetermined light-blocking section length value can be obtained by multiplying the sample flow width of the first particles in the flow cell 20 by the amplification factor of the forward scattered light. Generally, the lengths of the third light blocking part 324 and the fourth light blocking part 325 are only required to be greater than the first preset light blocking part length value, and for example, the lengths of the third light blocking part 324 and the fourth light blocking part 325 may be 1.2 times the first preset light blocking part length value.
For example, if the sample flow width of the first particle in the flow cell 20 is 35um and the magnification of the forward scattered light is 5 times, the first preset light blocking part length value is calculated to be 175um, and the lengths of the third light blocking part 324 and the fourth light blocking part 325 may be 210um.
The first light blocking portion 321, the second light blocking portion 322, the third light blocking portion 324, and the fourth light blocking portion 325 have the same width; the distance in the first direction between the third light blocking part 324 and the fourth light blocking part 325 is the same as the width of the first light transmitting part 320.
It should be noted that, since the diaphragm assemblies 32 are installed and adjusted in the micron order, the installation and adjustment difficulty is high, and the system stability is also greatly tested. Therefore, the difficulty of adjusting the diaphragm assembly 32 can be reduced by increasing the magnification of the forward scattered light, for example, changing the magnification of the forward scattered light from 5 to 20, thereby increasing the size of the light blocking portion and the light transmitting portion.
In some embodiments, as shown in fig. 3, the optical detection system further includes a collimating mechanism 50 and a shaping mechanism 60, the collimating mechanism 50 is configured to receive the detection light emitted from the light source device 10 and collimate the detection light; the shaping mechanism 60 is configured to receive the collimated sensing light and shape the sensing light to illuminate particles passing through the flow cell 20.
The shaping mechanism 60 includes a first lens 61 and a first cemented doublet 62, which are sequentially disposed, the first lens 61 is configured to diverge the detection light collimated by the collimating mechanism 50 along the second direction, the first cemented doublet 62 is configured to converge the detection light diverged by the first lens 61 along the first direction and the second direction, and the first direction is perpendicular to the second direction.
Specifically, the collimated detection light sequentially passes through the first lens 61 and the first cemented doublet 62, and is directly shaped in at least two directions by the arrangement of the first cemented doublet 62, so that the two lenses do not need to be precisely adjusted to realize the shaping in the two directions of the detection light, the assembly process of the shaping mechanism 60 can be simplified, the precision requirement and the cost of the shaping mechanism are reduced, and the accuracy of subsequent detection results is improved.
In the present embodiment, the first lens 61 is configured to diverge the detection light collimated by the collimating mechanism 50 along the second direction, and the first cemented doublet 62 is configured to converge the detection light diverged by the first lens 61 along the first direction and the second direction to realize shaping of the detection light in two directions, so as to facilitate subsequent detection.
In this embodiment, the first lens 61 may be a plano-concave cylindrical lens, the concave surface of the first lens 61 faces the collimating mechanism 50, and the plane of the first lens 61 faces the first cemented doublet 62, so that the detection light enters from the concave surface of the first lens 61 and exits from the plane surface of the first lens 61, thereby achieving the effect of diverging the detection light in the second direction.
In other embodiments, the first lens 61 may also be a plano-convex cylindrical lens, the convex surface of the first lens 61 faces the collimating mechanism 50, and the plane of the first lens 61 faces the first cemented doublet 62, so that the detection light enters from the convex surface of the first lens 61 and exits from the plane of the first lens 61, so as to achieve the effect of converging the detection light in the second direction.
In this embodiment, the collimating mechanism 50 may include an aspheric lens, a plane of the aspheric lens faces the light source mechanism, and a curved surface of the aspheric lens faces the shaping mechanism 60, so that the detection light enters from the plane of the aspheric lens and exits from the curved surface of the aspheric lens, so as to achieve a collimating effect on the detection light, which is beneficial to subsequent shaping and detection of light.
In some embodiments, for example, the forward scattered light is collected by the collecting assembly 31, which can further improve the light collecting effect and help to improve the accuracy of the detection result.
In this embodiment, as shown in fig. 3, the collecting assembly 31 may include a second lens 310 and a third lens 313, and the forward scattered light is sequentially transmitted through the second lens 310 and the third lens 313 to achieve collection of the forward scattered light.
In this embodiment, the second lens 310 may be a second double cemented lens formed by a first meniscus lens 311 and a first biconvex lens 312 coaxially disposed in sequence, the forward scattered light sequentially passes through the first meniscus lens 311, the first biconvex lens 312 and the third lens 313, a convex surface of the first meniscus lens 311 faces the flow chamber 20, a concave surface of the first meniscus lens 311 is cemented with one convex surface of the first biconvex lens 312, and the other convex surface of the first biconvex lens 312 faces the light receiving device 40, so that the forward scattered light is incident from the convex surface of the first meniscus lens 311 and exits from the other convex surface of the first biconvex lens 312, so as to achieve a converging effect on the forward scattered light, which is favorable for subsequent detection of light.
In this embodiment, the third lens 313 may be a third double cemented lens, the third double cemented lens is formed by a second biconvex lens 314 and a second meniscus lens 315 coaxially disposed in sequence, the forward scattered light sequentially passes through the second lens 310, the second biconvex lens 314 and the second meniscus lens 315, one convex surface of the second biconvex lens 314 faces the flow chamber 20, the other convex surface of the second biconvex lens 314 is cemented with the concave surface of the second meniscus lens 315, and the convex surface of the second meniscus lens 315 faces the photoelectric detection mechanism, so that the forward scattered light enters from one convex surface of the second biconvex lens 314 and exits from the convex surface of the second meniscus lens 315, so as to realize a converging effect on the forward scattered light, and facilitate subsequent detection on light.
In this embodiment, the photodetection mechanism may further include a side scattered light detection unit disposed in a side direction of the flow cell 20, and the side scattered light detection unit may be configured to receive side scattered light generated by side scattering of the reshaped light by the blood sample in the flow cell 20, and may detect the internal complexity of the blood cells of the blood sample, the number of blood cells, the density of cytoplasm and cell membrane of the blood cells, the content of cellular nucleic acid, and the like. Since the light path setting manner corresponding to the side scattered light and the side fluorescent light is similar to that of the forward scattered light, detailed description thereof is omitted here.
The application provides a blood cell analyzer 1000, which can effectively eliminate interference of a side lobe signal of a large particle, and can avoid interference of the side lobe signal of the large particle when detecting the large particle and a small particle in a blood cell, thereby accurately obtaining a blood cell detection result.
Referring to fig. 9, a blood cell analyzer 1000 according to an embodiment of the present disclosure includes a sampling unit 200, a reaction unit 300, a sample optical detection system 100, and a controller 400.
Wherein, the sampling part 200 is used for collecting blood samples; the reaction part 300 is used for providing a reagent, and the blood sample and the reagent react to form the sample to be tested; the sample optical detection system 100 can be a sample optical detection system as described previously; the controller 400 is configured to receive the electrical signals output by the scattered light and/or the side fluorescent light from the sample optical detection system 100, and obtain a blood cell detection result according to the electrical signals.
The above is only a specific embodiment of the present application, but the scope of the present application is not limited thereto, and any person skilled in the art can easily think of various equivalent modifications or substitutions within the technical scope of the present application, and these modifications or substitutions should be covered by the scope of the present application. Therefore, the protection scope of the present application shall be subject to the protection scope of the claims.
Claims (10)
1. A sample optical detection system, comprising:
a flow chamber for first particles in a sample to be tested to pass along a first direction;
a light source device for illuminating the first particles passing through the flow cell;
a light processing device including a collection assembly and a diaphragm assembly, wherein the collection assembly is used for collecting scattered light and/or side fluorescent light generated by the first particles irradiated by the light source device through the flow chamber and converging the scattered light and/or the side fluorescent light at the corresponding diaphragm assembly; the diaphragm assembly is used for filtering the scattered light and/or the side fluorescent light of the first particles in a first position range and enabling the scattered light and/or the side fluorescent light of the first particles in a second position range to pass through, and the first position range and the second position range are adjacently arranged in the first direction;
and the light receiving device is at least used for receiving the scattered light and/or the lateral fluorescence of the first particles in the second position range and outputting corresponding electric signals.
2. The optical detection system of claim 1, wherein the scattered light comprises forward scattered light, and the flow cell is further configured to pass second particles in the sample to be tested in the first direction;
the diaphragm assembly includes:
a first light transmitting portion for passing the forward scattered light of the first particles in a second position range;
the first light blocking part and the second light blocking part are arranged at intervals in the first direction and are positioned on two sides of the first light transmission part, and the first light blocking part and the second light blocking part are used for filtering the forward scattering light of the first particles in a first position range;
two second light transmission parts, wherein the two second light transmission parts are arranged at intervals in the first direction, one of the two second light transmission parts is positioned on one side of the first light blocking part far away from the first light transmission part, the other one of the two second light transmission parts is positioned on one side of the second light blocking part far away from the first light transmission part, and the two second light transmission parts are used for enabling the forward scattered light of the second particles to pass through;
the light receiving device is at least used for receiving the forward scattered light of the first particles in a second position range and the forward scattered light of the second particles and outputting corresponding electric signals.
3. The optical detection system of claim 1, wherein the scattered light comprises forward scattered light, and the flow cell is further configured to pass second particles in the sample to be tested in the first direction;
the diaphragm assembly includes:
the third light blocking part and the fourth light blocking part are arranged at intervals in the first direction and are used for filtering the forward scattered light of the first particles in a first position range;
a third light transmitting portion that surrounds the third light blocking portion and the fourth light blocking portion, and that allows the forward scattered light of the first particles and the forward scattered light of the second particles to pass through within a second position range;
the light receiving device is at least used for receiving the forward scattered light of the first particles in a second position range and the forward scattered light of the second particles and outputting corresponding electric signals.
4. The optical inspection system of claim 3, wherein the third light-transmitting portion is fabricated on a substrate material by a photolithography process or an etching process.
5. The optical detection system of claim 4, wherein the third light barrier and the fourth light barrier each have a length greater than a first preset light barrier length value, the first preset light barrier length value determined based on a sample flow width of the first particles in the flow cell and a magnification of the forward scattered light.
6. The optical detection system of claim 2, wherein the length of the first light transmission portion is less than a predetermined light transmission portion length value, the predetermined light transmission portion length value being determined based on the distance between the inner walls of the flow cell and the magnification of the forward scattered light.
7. The optical detection system of claim 2, wherein a width of the first light transmission portion is smaller than a preset light transmission portion width value, the preset light transmission portion width value being determined according to a width of a corresponding main lobe signal in the forward scattered light of the first particles and a magnification of the forward scattered light.
8. The optical detection system according to claim 2, wherein the widths of the first light blocking portion and the second light blocking portion are each larger than a second preset light blocking portion width value, and the second preset light blocking portion width value is determined according to a width of a side lobe signal corresponding to the forward scattered light of the first particle and a magnification of the forward scattered light.
9. The optical detection system of claim 1, further comprising:
the collimation mechanism is used for receiving the detection light emitted by the light source device and collimating the detection light;
the shaping mechanism is used for receiving the collimated detection light and shaping the detection light to irradiate the particles passing through the flow chamber, and comprises a first lens and a first doublet lens which are sequentially arranged, wherein the first lens is used for diverging the detection light collimated by the collimating mechanism along a second direction, the first doublet lens is used for converging the detection light diverged by the first lens along the first direction and the second direction, and the first direction is perpendicular to the second direction.
10. A blood cell analyzer, comprising:
a sampling section for collecting a blood sample;
the reaction part is used for providing a reagent and allowing the blood sample and the reagent to react to form the sample to be detected;
a sample optical detection system as claimed in any one of claims 1 to 9; and
and the controller is used for receiving the electric signals output by the scattered light and/or the lateral fluorescence from the optical detection system and obtaining a blood cell detection result according to the electric signals.
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| CN202221716748.8U CN218496689U (en) | 2022-07-05 | 2022-07-05 | Sample optical detection system and blood cell analyzer |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116106524A (en) * | 2023-04-11 | 2023-05-12 | 深圳市帝迈生物技术有限公司 | Blood analysis device |
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN116106524A (en) * | 2023-04-11 | 2023-05-12 | 深圳市帝迈生物技术有限公司 | Blood analysis device |
| CN116106524B (en) * | 2023-04-11 | 2023-08-25 | 深圳市帝迈生物技术有限公司 | blood analysis device |
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