CN114563329A - Optical detection device and cell analyzer - Google Patents
Optical detection device and cell analyzer Download PDFInfo
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- CN114563329A CN114563329A CN202011360237.2A CN202011360237A CN114563329A CN 114563329 A CN114563329 A CN 114563329A CN 202011360237 A CN202011360237 A CN 202011360237A CN 114563329 A CN114563329 A CN 114563329A
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- 238000001917 fluorescence detection Methods 0.000 claims description 28
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
- G01N15/10—Investigating individual particles
- G01N15/14—Optical investigation techniques, e.g. flow cytometry
- G01N15/1434—Optical arrangements
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
- G01N15/10—Investigating individual particles
- G01N15/14—Optical investigation techniques, e.g. flow cytometry
- G01N15/1434—Optical arrangements
- G01N15/1436—Optical arrangements the optical arrangement forming an integrated apparatus with the sample container, e.g. a flow cell
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/01—Arrangements or apparatus for facilitating the optical investigation
- G01N21/03—Cuvette constructions
- G01N21/05—Flow-through cuvettes
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/47—Scattering, i.e. diffuse reflection
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
- G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
- G01N21/64—Fluorescence; Phosphorescence
- G01N21/645—Specially adapted constructive features of fluorimeters
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
- G01N15/10—Investigating individual particles
- G01N15/14—Optical investigation techniques, e.g. flow cytometry
- G01N15/1434—Optical arrangements
- G01N2015/144—Imaging characterised by its optical setup
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/47—Scattering, i.e. diffuse reflection
- G01N2021/4704—Angular selective
- G01N2021/4707—Forward scatter; Low angle scatter
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
- G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
- G01N21/64—Fluorescence; Phosphorescence
- G01N21/645—Specially adapted constructive features of fluorimeters
- G01N2021/6482—Sample cells, cuvettes
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- General Health & Medical Sciences (AREA)
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Abstract
The invention is suitable for the field of cell analysis equipment, and discloses an optical detection device and a cell analyzer, wherein 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 forward scattering signals generated by the light source irradiating a cell to be detected, the forward scattering detection assembly comprises a first focusing lens, a diaphragm assembly and a first detector, and the diaphragm assembly is arranged between the first focusing lens and the first detector; the first focusing lens is arranged between the flow chamber and the diaphragm assembly and used for enabling forward scattered light rays generated by the light source irradiating the cell to be detected to converge and then to enter the first detector through the diaphragm assembly, the first focusing lens is a spherical lens, and the number of the first focusing lenses is one. The single spherical lens is adopted to collect the forward scattering signals and converge the forward scattering signals on the first detector, so that the size and the cost of the optical detection device are effectively reduced, and the miniaturization design of the cell analyzer is facilitated.
Description
Technical Field
The present 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
At present, most five-classification blood cell analyzers adopt a laser scattering principle to measure cells, and a system with high optical signal quality requirements generally adopts a plurality of spherical lenses or complex-surface aspheric lenses to collect forward scattering signals, and then utilizes an aperture diaphragm structure to shield stray light and effectively receive signals. In the prior art, the optical detection device of the five-classification blood cell analyzer has the following defects in specific application:
1) in the prior art, a forward scattering signal is generally collected by using a complex lens (aspheric lens) or a plurality of spherical lenses with planar incident surfaces, which results in a high cost and a large volume of an optical detection device.
2) Among the prior art, the light trap type of aperture diaphragm generally adopts circular aperture, utilizes round hole aperture diaphragm to carry out the shielding of the inside miscellaneous light of optical detection device promptly, like this, has higher position degree requirement to the circular port in optical detection device design and debugging process to lead to debugging structure complicacy, problem with high costs to appear.
3) In the prior art, a detector for receiving the fluorescent light is provided at the focal point of the focusing assembly. In order to ensure the optical signal-to-noise ratio, an optical filter is usually used to shield the interference of scattered light, and a circular aperture diaphragm with a smaller aperture is used to shield the space of stray light inside the optical detection device. Because the fluorescence signal is very weak, compared with the forward scattering signal, the requirement on the positioning of a mechanical structure or the debugging of a detector is higher, and further the whole optical detection device has higher cost and larger volume.
Disclosure of Invention
The first objective of the present invention is to provide an optical detection apparatus, which aims to solve the technical problems of high cost and large size of the optical detection apparatus caused by the fact that a complex lens or a plurality of spherical lenses with planar incident surfaces are used for signal collection of forward scattering signals in the prior art.
In order to achieve the purpose, the invention provides the following scheme: an optical detection device applied to a cell analyzer, the optical detection device comprising:
the flow chamber is used for allowing cells to be detected of the detection sample liquid to queue and pass under the wrapping of the diluent;
a light source for emitting light toward the cell to be measured flowing through the flow chamber;
the forward scattering detection assembly is used for collecting forward scattering signals generated when the light source irradiates the cell to be detected, the forward scattering detection assembly comprises a first focusing lens, a diaphragm assembly and a first detector, and the diaphragm assembly is arranged between the first focusing lens and the first detector; first focusing lens locate flow chamber with between the diaphragm subassembly, in order to be used for the messenger the light source shines pass after the forward scattering light who produces on the cell that awaits measuring assembles the diaphragm subassembly gets into first detector, first focusing lens is spherical lens, just first focusing lens's quantity is one.
The optical detection device provided by the first object of the invention adopts a single spherical lens (namely, the first focusing lens) to collect the forward scattering signal and converge the forward scattering signal on the first detector, so that the volume and the cost of the optical detection device are effectively reduced, and the miniaturization design of a cell analyzer is facilitated.
A second objective of the present invention is to provide an optical detection apparatus, which aims to solve the technical problems of high cost and large size of the optical detection apparatus caused by the fact that the detector for receiving the fluorescent light is arranged at the focal position of the focusing assembly in the prior art.
In order to achieve the purpose, the invention provides the following scheme: an optical detection device applied to a cell analyzer, the optical detection device comprising:
the flow chamber is used for allowing cells to be detected of the detection sample liquid to queue and pass under the wrapping of the diluent;
a light source for emitting light toward the cell to be measured flowing through the flow chamber;
fluorescence detection subassembly, fluorescence detection subassembly is used for collecting the light source shines the fluorescence signal that produces on the cell that awaits measuring, fluorescence detection subassembly includes focus subassembly, light filtering piece and second detector, light filtering piece locates focus subassembly with between the second detector, focus subassembly is located flow the room with between the light filtering piece, so that the light source shines the fluorescence light that produces on the cell that awaits measuring assembles the back and passes light filtering piece gets into the second detector, the second detector is located light filtering piece with between the focus of focus subassembly.
The optical detection device provided by the second object of the invention can cancel or enlarge the aperture of the aperture diaphragm in the fluorescence direction by designing the second detector for collecting the fluorescence light before the focus of the focusing assembly, thereby not only effectively reducing the volume and the cost of the optical detection device and ensuring the fluorescence signal-to-noise ratio, but also greatly reducing the requirement on the positioning precision of the target surface of the second detector.
The third objective of the present invention is to provide an optical detection apparatus, which aims to solve the technical problems of complicated debugging structure and high cost caused by the adoption of an aperture stop with a circular light-transmitting hole to shield stray light inside the optical detection apparatus in the prior art.
In order to achieve the purpose, the invention provides the following scheme: an optical detection device for use in a cell analyzer, the optical detection device comprising:
the flow chamber is used for allowing cells to be detected of the detection sample liquid to queue and pass under the wrapping of the diluent;
a light source for emitting light toward the cell to be measured flowing through the flow chamber;
a forward scattering detection component for collecting forward scattering signals generated by the light source irradiating the cell to be detected, the forward scattering detection assembly comprises a first focusing lens, a diaphragm assembly and a first detector, the diaphragm assembly is arranged between the first focusing lens and the first detector, the first focusing lens is arranged between the flow chamber and the diaphragm assembly, so that the forward scattered light generated by the light source irradiating the cell to be detected is converged and then enters the first detector through the diaphragm assembly, the stop assembly includes a straight stop and a first aperture stop, the straight stop being located between the first focusing lens and the first aperture stop, the first aperture diaphragm is positioned between the straight baffle and the first detector, and a first light-transmitting hole for transmitting light rays and irradiating the light rays on the first detector is arranged in the first aperture diaphragm in a penetrating manner;
the side scattering detection assembly is used for collecting side scattering signals generated by the light source irradiating the cells to be detected; the side scattering detection assembly comprises a fourth aperture diaphragm and a third detector, the fourth aperture diaphragm is arranged between the flow chamber and the third detector, and a fifth light-transmitting hole for light to penetrate and irradiate the third detector is formed in the fourth aperture diaphragm in a penetrating mode;
at least one of the first light-transmitting hole and the fifth light-transmitting hole is a non-circular hole, the size of the non-circular hole in the first direction is larger than that in the second direction, the first direction is perpendicular to the second direction, and the first direction is parallel to the flowing direction of the cell to be detected.
The optical detection device provided by the third object of the present invention sets the light hole on the aperture stop located 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 cell to be detected, so that the requirement for the mechanical structure precision can be greatly reduced compared with the traditional circular aperture stop while the diffuse reflection stray light inside the optical detection device is reduced, thereby facilitating the simplification of the debugging structure of the optical detection device and the reduction of the cost of the optical detection device.
A fourth object of the present invention is to provide a cell analyzer comprising a reaction cell, a reagent supply device, a sampling unit, a diluent supply device, a transport device, an analyzing unit, an output unit, and any one of the above optical detection devices;
the reaction tank is used for providing a reaction field for a sample to be detected and a reagent so as to prepare a detection sample liquid;
the sampling unit is used for collecting a sample to be detected and discharging the sample to be detected into the reaction tank;
the reagent supply device is used for conveying a reagent into the reaction tank;
the conveying device is used for driving the detection sample liquid to be conveyed from the reaction pool to the flowing chamber and driving the diluent liquid to be conveyed from the diluent supplying device to the flowing chamber, so that the cells to be detected of the detection sample liquid are queued to pass through the flowing chamber under the entrainment of the diluent liquid;
the optical detection device is used for detecting the detection sample liquid which is wrapped by the diluent and passes through the flow chamber;
the analysis unit is used for analyzing the optical signal fed back by the detector to obtain the detection result of the detection sample liquid;
the output unit is used for outputting the detection result of the analysis unit.
The cell analyzer according to the fourth object of the present invention is advantageous in miniaturization and low-cost design of the cell analyzer because of the use of the optical detection device.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the structures shown in the drawings without creative efforts.
Fig. 1 is a schematic structural diagram of an optical detection apparatus according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of light propagating on a forward scatter detection assembly according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of the propagation of light on the first focusing lens according to an embodiment of the present invention;
fig. 4 is a schematic structural diagram of a first light-transmitting hole according to an embodiment of the present invention;
FIG. 5 is a schematic view of the light propagating on the fluorescence detection assembly and the side scatter detection assembly according to an embodiment of the present invention;
fig. 6 is a schematic structural diagram of a fifth light hole according to an embodiment of the invention;
FIG. 7 is a schematic view of a cell analyzer according to an embodiment of the present invention;
FIG. 8 is a schematic view of the light propagating on the fluorescence detection assembly according to the second embodiment of the present invention.
The reference numbers illustrate:
100. an optical detection device; 110. a flow chamber; 120. a light source; 121. a laser; 122. a front dimming component; 130. a forward scatter detection assembly; 131. a first focusing lens; 1311. a first incident surface; 1312. a first exit surface; 132. a diaphragm assembly; 1321. a straight stop diaphragm; 1301. a resisting part; 1302. a second light-transmitting hole; 1322. a first aperture stop; 1303. a first light-transmitting hole; 1304. a first aperture wall; 1305. a second aperture wall; 133. a first detector; 140. a fluorescence detection component; 141. a focusing assembly; 1411. a second focusing lens; 1401. a second incident surface; 1402. a second exit surface; 1412. a third focusing lens; 1403. a third incident surface; 1404. a third exit surface; 142. a light filtering member; 143. a second detector; 144. a second aperture stop; 1441. a third light-transmitting hole; 145. a third aperture stop; 1451. a fourth light-transmitting hole; 150. a side scatter detection assembly; 151. a fourth aperture stop; 1511. a fifth light hole; 1501. a third aperture wall; 1502. a fourth aperture wall; 152. a third detector; 160. a dichroic mirror; 200. a reaction tank; 300. a reagent supply device; 400. a sampling unit; 500. a diluent supply device; 600. a conveying device; 700. an analysis unit; 800. and an output unit.
Detailed Description
The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. 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 invention.
It should be noted that all the directional indicators (such as up, down, left, right, front, and rear … …) in the embodiment of the present invention are only used to explain the relative position relationship between the components, the motion situation, and the like in a specific posture, and if the specific posture is changed, the directional indicator is changed accordingly.
It will also be understood that when an element is referred to as being "secured to" or "disposed on" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or be indirectly connected to the other element through intervening elements.
In addition, the descriptions relating to "first", "second", etc. in the present invention are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In addition, technical solutions between various embodiments may be combined with each other, but must be realized by a person skilled in the art, and when the technical solutions are contradictory or cannot be realized, such a combination should not be considered to exist, and is not within the protection scope of the present invention.
The first embodiment is as follows:
as shown in fig. 1 to 7, an optical detection apparatus 100 according to a first embodiment of the present invention is applied to a cell analyzer. The optical detection device 100 includes a flow cell 110, a light source 120, a forward scatter detection assembly 130, a fluorescence detection assembly 140, and a side scatter detection assembly 150, wherein the flow cell 110 is used for arranging the cells to be detected of the detection sample liquid to pass through under the wrapping of the dilution liquid; the light source 120 is used for emitting light toward the cell to be measured flowing through the flow cell 110; the forward scattering detection component 130 is used for collecting forward scattering signals generated by the light source 120 irradiating on the cell to be detected; the fluorescence detection component 140 is used for collecting a fluorescence signal generated by the light source 120 irradiating the cell to be detected, and the side scattering detection component 150 is used for collecting a side scattering signal generated by the light source 120 irradiating the cell to be detected.
In this embodiment, the optical detection apparatus 100 includes three detection modules, namely, a forward scattering detection module 130, a fluorescence detection module 140 and a side scattering detection module 150, which can be used to simultaneously collect the forward scattering signal, the side scattering signal and the fluorescence signal generated by the light source 120 irradiating the cell to be detected. Of course, in certain applications, the optical detection device 100 may not include the forward scatter detection assembly 130, the fluorescence detection assembly 140, and the side scatter detection assembly 150 at the same time, depending on the requirements of different detection items, for example, the optical detection device 100 may include only one or two of the forward scatter detection assembly 130, the fluorescence detection assembly 140, and the side scatter detection assembly 150 as an alternative embodiment.
Specifically, the forward scattering detection assembly 130 is disposed on the optical axis of the light emitted from the light source 120, and the collected forward scattering signal (also called low-angle scattering signal) can represent the size of the cell volume to be detected. The fluorescence detection component 140 and the side scattering detection component 150 are both disposed at the side of the optical axis of the light emitted from the light source 120, and the side scattering signal (also called high angle scattering signal) collected by the side scattering detection component 150 can represent the complexity of the particles inside the cell to be detected. The intensity of the fluorescence signal collected by the fluorescence detection component 140 can be used to characterize the degree of staining of the cells to be detected.
Preferably, referring to fig. 1, the light source 120 includes a laser 121 and a front dimming assembly 122 disposed between the laser 121 and the flow cell 110. The front dimming component 122 is mainly used for focusing the light emitted from the laser 121.
Preferably, the light emitted from the light source 120 forms an elliptical light spot at the center of the flow cell 110, the minor axis of the elliptical light spot is parallel to the flow direction of the cell to be detected, and the major axis of the elliptical light spot is perpendicular to the flow direction of the cell to be detected. When the cell to be detected passes through the light beam irradiation region of the light source 120 (the oval light spot at the center of the flow cell 110), low-angle scattered light (forward scattered light), high-angle scattered light (side scattered light) and fluorescent light are simultaneously generated, and the forward scattering detection assembly 130, the fluorescent detection assembly 140 and the side scattering detection assembly 150 are respectively used for collecting the low-angle scattered light, the high-angle scattered light and the fluorescent light.
As a preferred embodiment of this embodiment, the light source 120 forms an elliptical light spot in the flow cell 110 with a size: the minor axis is 10um-25um, and the major axis is 200um-350 um.
Preferably, referring to fig. 1 and 2, the forward scatter detection assembly 130 includes a first focusing lens 131, an aperture assembly 132, and a first detector 133, the aperture assembly 132 being disposed between the first focusing lens 131 and the first detector 133 for limiting the angular range of the light beam transmitted therethrough; the first focusing lens 131 is disposed between the flow chamber 110 and the diaphragm assembly 132, and is used for converging forward scattered light rays generated by the light source 120 irradiating the cell to be detected, and then the converged forward scattered light rays pass through the diaphragm assembly 132 and enter the first detector 133, wherein the first focusing lens 131 is a spherical lens, and the number of the first focusing lenses 131 is one. The forward scattered light generated by the light source 120 irradiating the cell to be detected irradiates the first focusing lens 131, is converged by the first focusing lens 131, is limited by the diaphragm assembly 132, and finally reaches the first detector 133, thereby completing the collection of the forward scattered signal. In this embodiment, only one spherical lens (i.e., the first focusing lens 131) is used to collect the forward scattering signal and converge the forward scattering signal on the first detector 133, so that the size and cost of the optical detection apparatus 100 can be effectively reduced, which is beneficial to the miniaturization design of the cell analyzer.
Preferably, as shown with reference to fig. 1 to 3, the first focusing lens 131 has a first incident surface 1311 disposed toward the flow chamber 110 and a first exit surface 1312 disposed toward the diaphragm assembly 132, the first incident surface 1311 being a spherical surface convexly disposed toward the flow chamber 110. Here, the first incident surface 1311 is designed to be a convex spherical structure, that is, the first incident surface 1311 is a spherical surface protruding toward the flow chamber 110, so that the reflected light of the first incident surface 1311 deviates from the original incident light beam direction, and the design of spatial shielding is easy, thereby effectively reducing the occurrence of the phenomenon that the light is reflected back to the light source 120 by the first incident surface 1311, which causes unstable output of the light source 120, and further causes the forward scattering optical signal-to-noise ratio not meeting the cell detection requirement.
Preferably, referring to fig. 1-3, in the present embodiment, the first exit surface 1312 is a spherical surface convexly disposed toward the diaphragm assembly 132; of course, in certain applications, the first exit surface 1312 may be a planar surface or other surface as an alternative embodiment.
Preferably, as shown in fig. 1 and 2, the diaphragm assembly 132 includes a straight diaphragm 1321 and a first aperture diaphragm 1322, the straight 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 diaphragm 1321 and the first detector 133, the first aperture diaphragm 1322 penetrates through a first light transmitting hole 1303 through which light passes and irradiates on the first detector 133, the straight diaphragm 1321 has a blocking portion 1301 and two second light transmitting holes 1302, the blocking portion 1301 is used for blocking direct light passing through a cell to be measured, and the two second light transmitting holes 1302 are respectively located on two sides of the straight blocking portion and are used for allowing light converged by the first focusing lens 131 to pass and irradiate on the first aperture diaphragm 1322. The low-angle scattered light caused by the scattering of the cell to be detected is collected by the first focusing lens 131 when passing through the flow cell 110, then passes through the second light transmitting hole 1302 of the straight blocking diaphragm 1321, converges at the position of the first aperture diaphragm 1322, and is finally received by the first detector 133, and the volume information of the cell to be detected can be represented according to the size, pulse width and area of the low-angle scattered signal received by the first detector 133. Meanwhile, the part of the direct light that penetrates through the cell to be detected is shielded by the shielding part 1301 of the shielding diaphragm 1321, so that the saturation of the low-angle scattering signal can be prevented, and the effective identification of the low-angle scattering signal can be ensured.
Preferably, as shown in fig. 1, 2 and 4, the first light-transmitting hole 1303 is a non-circular hole, the inner wall of the first light-transmitting hole 1303 includes two first hole walls 1304 and two second hole walls 1305, the two first hole walls 1304 are oppositely disposed in the first direction X, and the two second hole walls 1305 are oppositely disposed in the second direction YThe two first hole walls 1304 are respectively connected, that is, the first hole walls 1304 and the second hole walls 1305 are alternately connected and enclosed to form a closed annular wall. The first direction X and the second direction Y are perpendicular to each other, the first direction X is parallel to the flow direction of the cells to be detected, and the distance L between the two first hole walls 1304 is1Greater than the distance L between the two second aperture walls 13052I.e. the dimension L of the first light-transmitting hole 1303 in the first direction X1Is larger than the dimension L in the second direction Y2. Here, by setting the first light-transmitting hole 1303 of the first aperture stop 1322 to be a non-circular hole and making the size L of the first light-transmitting hole 1303 in the first direction X1Is larger than the dimension L in the second direction Y2And the direction with larger size is parallel to the flowing direction of the cell to be detected, so that the requirement on the precision of a mechanical structure can be greatly reduced while the diffuse reflection stray light in the optical detection device 100 is reduced, thereby being beneficial to simplifying the complex debugging structure of the optical detection device 100 and reducing the cost of the optical detection device 100.
Referring to fig. 1-3, as a preferred embodiment of this embodiment, the first light-transmitting hole 1303 is a kidney-shaped hole, the two first hole walls 1304 are both semi-circular arc surfaces, and the two second hole walls 1305 are parallel planes. First light trap 1303 adopts waist type hole, both can satisfy the design requirement that first light trap 1303 is different in size in two vertical directions, and the design of accessible semicircle face reduces the stress concentration phenomenon of first light trap 1303 pore wall again to do benefit to the structural reliability who improves first aperture diaphragm 1322. Of course, in a specific application, the first light-transmitting holes 1303 are not limited to be kidney-shaped holes, for example, as an alternative embodiment, the first light-transmitting holes 1303 may be designed as elliptical holes or rectangular holes.
Preferably, referring to fig. 1 and 5, the fluorescence detecting assembly 140 includes a focusing assembly 141, a filter 142 and a second detector 143, the filter 142 being disposed between the focusing assembly 141 and the second detector 143; the focusing assembly 141 is disposed between the flow chamber 110 and the filter 142, so that the fluorescent light generated by the light source 120 irradiating the cell to be measured is converged and then passes through the filter 142 to enter the second detector 143, and the second detector 143 is located between the filter 142 and the focal point a of the focusing assembly 141. The fluorescence light generated by the light source 120 irradiating the cell to be measured is collected by the focusing assembly 141 through the flow cell 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 set before the focusing focus a of the fluorescence direction focusing assembly 141, so that the spot size of the fluorescence signal can be ensured to match the target surface optical effective area of the second detector 143, and the internal nucleic acid content information of different cells to be detected can be reflected according to the size, pulse width and area of the fluorescence signal.
Preferably, the cut-off range of the filter 142 for light in the spectral range of the light source 120 is above OD 6. OD is an abbreviation for optical density. OD6 indicates a 0.0001% transmittance of light from the light source 120 through the filter 142. In this embodiment, the third detector 152 is designed before the focus a of the focusing assembly 141 in combination with the target surface size of the second detector 143, the design of the aperture stop in front of the second detector 143 is cancelled, and the cut-off of the optical filter 142 for the light in the spectrum band of the laser 121 is designed to be more than OD6, so that the size of the optical detection apparatus 100 can be effectively reduced, the signal-to-noise ratio of fluorescence is ensured, and the requirement for the target surface positioning accuracy of the third detector 152 can be greatly reduced.
Preferably, the filter 142 is a filter, that is, the filter 142 is a sheet-shaped member, which has a simple structure and a small thickness, and is beneficial to reducing the volume of the optical detection apparatus 100.
Preferably, the focal length of the focusing assembly 141 is greater than 4.0 mm.
Preferably, as shown with reference to fig. 1 and 5, focusing assembly 141 includes a second focusing lens 1411 and a third focusing lens 1412, second focusing lens 1411 is disposed between flow cell 110 and third focusing lens 1412, and third focusing lens 1412 is disposed between second focusing lens 1411 and filter 142. The second focusing lens 1411 has a second incident surface 1401 disposed toward the flow cell 110 and a second exit surface 1402 disposed toward the third focusing lens 1412, and the third focusing lens 1412 has a third incident surface 1403 disposed toward the second focusing lens 1411 and a third exit surface 1404 disposed toward the filter 142.
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 a spherical surface. As a preferred implementation of this embodiment, the second incident surface 1401 is a plane, and the second emergent surface 1402 is a spherical surface convexly disposed toward the third focusing lens 1412. Of course, the shapes of the second incident surface 1401 and the second exit surface 1402 are not limited thereto in specific applications.
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 a spherical surface. As a preferred embodiment of this embodiment, the third incident surface 1403 is a plane, and the third exit surface 1404 is a spherical surface convexly disposed toward the filter 142. Of course, the shapes of the third incident surface 1403 and the third exit surface 1404 are not limited thereto in specific applications.
Preferably, as shown in fig. 1 and 5, the fluorescence detecting assembly 140 further includes a third aperture stop 145, the third aperture stop 145 is disposed between the second focusing lens 1411 and the third focusing lens 1412, and the third aperture stop 145 is penetrated by a fourth light-transmitting hole 1451 for transmitting light and irradiating the third focusing lens 1412. The third aperture stop 145 is used to limit the collection angle range of the light beam.
Preferably, referring to fig. 1 and 5, the optical detection device 100 further includes a dichroic mirror 160, the dichroic mirror 160 is located between the focusing assembly 141 and the filter 142, and between the focusing assembly 141 and the side scattering detection assembly 150, for transmitting the fluorescent light generated by the light source 120 irradiating the cell to be detected and irradiating the fluorescent light onto the filter 142, and for reflecting the side scattering light generated by the light source 120 irradiating the cell to be detected onto the side scattering detection assembly 150. The dichroic mirror 160 is also called a dichroic mirror, and is characterized in that light of a certain wavelength (fluorescence light in this embodiment) is almost completely transmitted, and light of another wavelength (side scattering light in this embodiment) is almost completely reflected. In this embodiment, the side scattering detection assembly 150 and the fluorescence detection assembly 140 share the focusing assembly 141, and the dichroic mirror 160 is adopted to guide the fluorescent light and the side scattering light converged by the focusing assembly 141 to the detector of the fluorescence detection assembly 140 and the detector of the side scattering detection assembly 150, respectively, so that the structural compactness of the optical detection device 100 is effectively improved, and the reduction of the volume and the cost of the optical detection device 100 is facilitated.
Preferably, referring to fig. 1 and 5, the side scatter detecting assembly 150 includes a fourth aperture stop 151 and a third detector 152, the fourth aperture stop 151 is disposed between the dichroic mirror 160 and the third detector 152, and the fourth aperture stop 151 is penetrated by a fifth light transmission hole 1511 for transmitting light and irradiating the third detector 152. The fourth aperture stop 151 is used to limit the collection angle range of the side scattered light.
Preferably, referring to fig. 1, 5 and 6, the fifth light-transmitting hole 1511 is a non-circular hole, the inner wall of the fifth light-transmitting 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 respectively connect the two third hole walls 1501, that is, the third hole walls 1501 and the fourth hole walls 1502 are alternately connected to form a closed annular wall. The first direction X and the second direction Y are perpendicular to each other, the first direction X is parallel to the flow direction of the cell to be detected, and the distance L between the two third hole walls 15013Greater than the distance L between the two fourth aperture walls 15024I.e. the dimension L of the fifth light transmission hole 1511 in the first direction X3Is larger than the dimension L in the second direction Y4. Here, the fifth light transmission hole 1511 of the fourth aperture stop 151 is formed as a non-circular hole, and the dimension L of the fifth light transmission hole 1511 in the first direction X is set to be a non-circular hole3Is larger than the dimension L in the second direction Y4And the direction with larger size is parallel to the flow direction of the cell to be detected, so that the requirement on the precision of a mechanical structure can be greatly reduced while the diffuse reflection stray light in the optical detection device 100 is reduced, thereby being beneficial to simplifying the complicated debugging structure of the optical detection device 100 and reducing the cost of the optical detection device 100.
As a preferred embodiment of this embodiment, the fifth light-transmitting hole 1511 is a kidney-shaped hole, the two third hole walls 1501 are both semi-circular arc surfaces, and the two fourth hole walls 1502 are parallel planes. The fifth light transmission hole 1511 is a waist-shaped hole, which can meet the design requirements of the fifth light transmission hole 1511 in two vertical directions for different sizes, and the design of the semicircular arc surface can reduce the stress concentration phenomenon of the hole wall of the fifth light transmission hole 1511, thereby being beneficial to improving the structural reliability of the fourth aperture diaphragm 151. Of course, in a specific application, the fifth light transmission hole 1511 is not limited to a kidney-shaped hole, and for example, as an alternative embodiment, the fifth light transmission hole 1511 may be designed as an elliptical hole or a rectangular hole.
In a preferred embodiment of this embodiment, to reduce the requirement for the precision of the positioning of the optical system structure, on the premise of ensuring the signal noise requirement, both the aperture stop for the forward scattering signal channel (i.e., the first aperture stop 1322) and the aperture stop for the side scattering signal channel (i.e., the fourth aperture stop 151) are designed as light-transmitting holes, which are waist-shaped holes, elliptical holes, or rectangular holes; of course, in a specific application, as an alternative embodiment, only one of the aperture stop for the forward scattering signal channel (i.e., the first aperture stop 1322) and the aperture stop for the side scattering signal channel (i.e., the fourth aperture stop 151) may be designed as the light transmission hole, and a kidney-shaped hole, an elliptical hole, or a rectangular hole may be used.
As a preferred implementation of this embodiment, the optical detection apparatus 100 works according to the following principle: a light beam emitted by the laser 121 is focused by the front dimming component 122, and then an elliptical light spot is formed at the central position of the flow chamber 110, wherein the minor axis direction of the elliptical light spot is consistent with the flow direction of the cells to be detected, and the major axis direction of the elliptical light spot is perpendicular to the flow direction of the cells to be detected; when the cell to be measured passes through the beam irradiation region (the elliptical light spot at the center of the flow cell 110), low-angle scattered light, side scattered light, and fluorescent light are simultaneously generated. The low-angle scattered light generated by the cell to be detected is collected by the first focusing lens 131 when passing through the flow cell 110, then passes through the second light transmitting hole 1302 of the stop 1321, converges at the position of the first aperture diaphragm 1322, and is finally received by the first detector 133, and the volume information of the cell to be detected can be represented according to the size, pulse width and area of the signal received by the first detector 133. In addition, the side scattered light and the fluorescence light generated by the cell to be detected are collected by the short focus converging lens group (i.e. the focusing assembly 141) composed of the second focusing lens 1411 and the third focusing lens 1412 through the flow cell 110, the collection angle range of the side scattered light is limited by the third aperture stop 145, wherein the side scattered light is reflected by the dichroic mirror 160, then is focused at the position of the fourth aperture stop 151, enters the third detector 152, and can be used for distinguishing the complexity information of the cell according to the size, the intensity and the area of the signal generated by the third detector 152; the fluorescence light passes through the dichroic mirror 160, passes through the filter 142, and is finally received by the second detector 143, and the information of the nucleic acid content in different cells can be reflected according to the size, pulse width and area of the fluorescence signal.
Referring to fig. 7, the present embodiment further provides a cell analyzer including a reaction cell 200, a reagent supply device 300, a sampling unit 400, a diluent supply device 500, a transport device 600, an analysis unit 700, an output unit, and the optical detection device 100.
The reaction cell 200 is used to provide a reaction field for the sample and the reagent to be detected, so as to prepare a detection sample solution. In this embodiment, the sample to be tested is a blood sample; of course, in certain applications, the sample to be tested may be a body fluid sample as an alternative embodiment.
The sampling unit 400 is used for collecting a sample to be tested and discharging the sample to be tested into the reaction cell 200. The sampling unit 400 comprises a sampling member, a power element for driving the sampling member to move, and a syringe for driving the sampling member to aspirate and discharge a sample to be measured. The sampling component can be a sampling needle or a sampling pipette, etc. The sampling component can move to a sample storage container (such as a test tube) for sampling under the driving of the power element, and then move to the reaction pool 200 for sample separation under the driving of the power element.
The reagent supply device 300 is used to supply reagents into the reaction cell 200.
The transport device 600 is used for driving the test sample solution to be transported from the reaction cell 200 into the flow chamber 110 and for driving the diluent to be transported from the diluent supply device 500 into the flow chamber 110, so that the cells to be tested for the test sample solution are queued through the flow chamber 110 under the entrainment of the diluent.
The optical detection device 100 is used for detecting a detection sample liquid that is carried by a diluent through a flow cell 110. The optical detection device 100 may be used for reticulocyte detection, leukocyte classification detection, or other types of optical detection items.
The analyzing unit 700 is configured to analyze an optical signal fed back by the detector to obtain a detection result of the detection sample liquid.
The output unit is used for outputting the detection result of the analysis unit 700. The output unit is preferably a display screen, which enables the detection result to be visually displayed.
The cell analyzer according to the present embodiment employs the optical detection device 100, and thus has the effective effect of the optical detection device 100.
Besides the optical detection device 100, the cell analyzer may also include other types of detection devices, such as a hemoglobin detection device, an impedance counting detection device, and the like, and the specific application can be set according to actual requirements. The hemoglobin detection device is used for detecting the concentration of hemoglobin; the impedance counting detection device is used for performing impedance counting detection such as red blood cell number detection and/or platelet counting detection.
In a preferred embodiment of this embodiment, the optical detection device 100 of the cell analyzer adopts a low-cost, miniaturized, and low-feedback light path structure design scheme, which can reduce the size and cost of the optical detection device 100 on the basis of the fluorescence detection cell analyzer, improve the signal-to-noise ratio of the optical system, provide an effective solution for the low-cost and miniaturized fluorescence detection cell analyzer, and simultaneously meet the noise suppression requirements of fluorescence detection and small particle detection, thereby ensuring the accuracy and reliability of cell classification and counting.
Example two:
referring to fig. 1, 5 and 8, the optical detection device 100 and the cell analyzer of the present embodiment are different from the first embodiment mainly in whether an aperture stop is disposed between the filter 142 and the second detector 143 in the fluorescence detection assembly 140. Specifically, in the first embodiment, the arrangement of the aperture stop between the filter 142 and the second detector 143 is eliminated; in this embodiment, the aperture stop between the filter 142 and the second detector 143 is not eliminated, but the light-transmitting hole on the aperture stop between the filter 142 and the second detector 143 is expanded, that is, the aperture d of the light-transmitting hole on the aperture stop between the filter 142 and the second detector 143 in this embodiment is larger than the aperture of the light-transmitting hole on the aperture stop between the filter 142 and the second detector 143 in the conventional technology.
Specifically, in this embodiment, the fluorescence detection assembly 140 further includes a second aperture stop 144 disposed between the light filtering member 142 and the second detector 143, the second aperture stop 144 is provided with a third light transmission hole 1441 for allowing light to pass through and irradiate the second detector 143, the third light transmission hole 1441 is a circular hole, and an aperture d of the third light transmission hole 1441 is greater than 1.2 mm. The second aperture stop 144 is used to limit the angular range of the light beam passing through it to shield stray light in the fluorescence direction.
In this embodiment, the target surface size of the second detector 143 is combined, the second detector 143 is designed before the focal point a of the focusing assembly 141, the aperture d of the third light transmission hole 1441 on the second aperture stop 144 in front of the second detector 143 is enlarged, and the cut-off of the optical filter 142 for the light in the spectrum band of the laser 121 is designed to be above OD6, so that the volume of the optical detection apparatus 100 can be effectively reduced, the fluorescent signal-to-noise ratio is ensured, and the requirement for the positioning accuracy of the target surface of the second detector 143 can be greatly reduced.
In addition to the above differences, other structures of the optical detection device 100 and the cell analyzer provided in the present embodiment can be optimized with reference to the first embodiment, and will not be described in detail herein.
The above description is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention, and all modifications and equivalents of the present invention, which are made by the contents of the present specification and the accompanying drawings, or directly/indirectly applied to other related technical fields, are included in the scope of the present invention.
Claims (22)
1. An optical detection device is applied to a cell analyzer, and is characterized in that: the optical detection device includes:
the flow chamber is used for allowing cells to be detected of the detection sample liquid to queue and pass under the wrapping of the diluent;
a light source for emitting light toward the cell to be measured flowing through the flow chamber;
the forward scattering detection assembly is used for collecting forward scattering signals generated when the light source irradiates the cell to be detected, the forward scattering detection assembly comprises a first focusing lens, a diaphragm assembly and a first detector, and the diaphragm assembly is arranged between the first focusing lens and the first detector; first focusing lens locate flow chamber with between the diaphragm subassembly, in order to be used for making the light source shine pass after the forward scattering light that produces on the cell that awaits measuring assembles the diaphragm subassembly gets into first detector, first focusing lens are spherical lens, just first focusing lens's quantity is one.
2. The optical inspection device of claim 1, wherein: the first focusing lens is provided with a first incidence surface facing the flow chamber and a first emergent surface facing the diaphragm assembly, and the first incidence surface is a spherical surface convexly arranged facing the flow chamber.
3. The optical inspection device of claim 2, wherein: the first emergent surface is a spherical surface which is convexly arranged towards the diaphragm assembly; or, the first emergent surface is a plane.
4. An optical inspection device according to any one of claims 1 to 3, wherein: the diaphragm subassembly is including keeping off straight diaphragm and first aperture diaphragm, it is located to keep off straight diaphragm first focusing lens with between the first aperture diaphragm, first aperture diaphragm is located keep off straight diaphragm with between the first detector, first aperture diaphragm runs through to be equipped with and is used for supplying light to see through and shine first light trap on the first detector, it has stop portion and two second light traps to keep off straight diaphragm, stop portion is used for sheltering from and sees through the direct light of the cell that awaits measuring, two the second light trap is located respectively the both sides that keep off straight portion are in order to supply the light that first focusing lens assembles sees through and shines on the first aperture diaphragm.
5. The optical inspection device of claim 4, wherein: first light trap is non-circular hole, the inner wall of first light trap includes two first pore walls and two second pore walls, two first pore wall sets up relatively in the first direction, two the second pore wall sets up relatively in the second direction and connects two respectively first pore wall, the first direction with second direction mutually perpendicular, just the first direction with the flow direction of the cell that awaits measuring is parallel, two distance between the first pore wall is greater than two distance between the second pore wall.
6. The optical inspection device of claim 5, wherein: the first light-transmitting hole is a waist-shaped hole or an elliptical hole or a rectangular hole.
7. The optical detection device according to any one of claims 1 to 6, wherein: the optical detection device also comprises a fluorescence detection assembly, the fluorescence detection assembly is used for collecting a fluorescence signal generated when the light source irradiates the cell to be detected, the fluorescence detection assembly comprises a focusing assembly, a filter and a second detector, and the filter is arranged between the focusing assembly and the second detector; the focusing assembly is arranged between the flow chamber and the light filtering piece so as to enable the light source to irradiate the fluorescent light generated on the cell to be detected to converge and then penetrate through the light filtering piece to enter the second detector, and the second detector is positioned between the light filtering piece and the focus of the focusing assembly.
8. The optical inspection device of claim 7, wherein: the cut-off range of the light filter to the light of the light source spectrum band is more than OD 6.
9. An optical inspection apparatus according to claim 7 or 8, wherein: the focal length of the focusing assembly is greater than 4.0 mm.
10. An optical inspection device according to any one of claims 7 to 9, wherein: fluorescence detection subassembly is still including locating filter with second aperture diaphragm between the second detector, second aperture diaphragm runs through to be equipped with and is used for supplying light to see through and shine third light trap on the second detector, the aperture of third light trap is greater than 1.2 mm.
11. The optical detection device according to any one of claims 7 to 10, 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 optical filter.
12. The optical inspection device of claim 11, wherein: fluorescence detection subassembly still includes third aperture diaphragm, third aperture diaphragm is located second focusing lens with between the third focusing lens, third aperture diaphragm runs through to be equipped with and is used for supplying light to permeate through and shine fourth light trap on the third focusing lens.
13. The optical detection device according to any one of claims 7 to 12, wherein: the optical detection device also comprises a side scattering detection assembly and a dichroic mirror, wherein the side scattering detection assembly is used for collecting side scattering signals generated by the light source irradiating the cells to be detected; the dichroic mirror is positioned between the focusing assembly and the light filtering piece and between the focusing assembly and the side scattering detection assembly, so that fluorescent light generated by the light source irradiating the cells to be detected can penetrate through the dichroic mirror and irradiate the fluorescent light onto the light filtering piece, and the side scattering light generated by the light source irradiating the cells to be detected can be reflected onto the side scattering detection assembly.
14. The optical inspection device of claim 13, wherein: the side scattering detection assembly comprises a fourth aperture diaphragm and a third detector, the fourth aperture diaphragm is arranged between the dichroic mirror and the third detector, and the fourth aperture diaphragm penetrates through a fifth light-transmitting hole which is used for allowing light to penetrate and irradiate the third detector.
15. The optical inspection device of claim 14, wherein: the fifth light trap is non-circular hole, the inner wall of fifth light trap includes two third pore walls and two fourth pore walls, two the third pore wall sets up relatively on the first direction, two the fourth pore wall sets up relatively on the second direction and connects two respectively the third pore wall, the first direction with second direction mutually perpendicular, just the first direction with the flow direction of the cell that awaits measuring is parallel, two distance between the third pore wall is greater than two distance between the fourth pore wall.
16. The optical inspection device of claim 15, wherein: and the fifth light-transmitting hole is a waist-shaped hole or an elliptical hole or a rectangular hole.
17. The optical detection device according to any one of claims 1 to 16, wherein: the light source comprises a laser and a preposed dimming component arranged between the laser and the flow chamber; and/or the presence of a gas in the atmosphere,
the light emitted by the light source forms an elliptical light spot at the center of the flow chamber, the minor axis direction of the elliptical light spot is parallel to the flow direction of the cells to be detected, and the major axis direction of the elliptical light spot is perpendicular to the flow direction of the cells to be detected.
18. An optical detection device is applied to a cell analyzer, and is characterized in that: the optical detection device includes:
the flow chamber is used for allowing cells to be detected of the detection sample liquid to queue and pass under the wrapping of the diluent;
a light source for emitting light toward the cell to be measured flowing through the flow chamber;
fluorescence detection subassembly, fluorescence detection subassembly is used for collecting the light source shines the fluorescence signal that produces on the cell that awaits measuring, fluorescence detection subassembly includes focus subassembly, light filtering piece and second detector, light filtering piece locates focus subassembly with between the second detector, focus subassembly is located flow the room with between the light filtering piece, so that the light source shines the fluorescence light that produces on the cell that awaits measuring assembles the back and passes light filtering piece gets into the second detector, the second detector is located light filtering piece with between the focus of focus subassembly.
19. The optical inspection device of claim 18, wherein: the cut-off range of the light filter to the light of the light source spectrum band is more than OD 6; and/or the presence of a gas and/or,
the focal length of the focusing assembly is greater than 4.0 mm.
20. An optical detection device is applied to a cell analyzer, and is characterized in that: the optical detection device includes:
the flow chamber is used for allowing cells to be detected of the detection sample liquid to queue and pass under the wrapping of the diluent;
a light source for emitting light toward the cell to be measured flowing through the flow chamber;
a forward scattering detection component for collecting forward scattering signals generated by the light source irradiating the cell to be detected, the forward scatter detection assembly comprises a first focusing lens, a diaphragm assembly and a first detector, the diaphragm assembly is arranged between the first focusing lens and the first detector, the first focusing lens is arranged between the flow chamber and the diaphragm assembly, so that the forward scattered light generated by the light source irradiating the cell to be detected is converged and then enters the first detector through the diaphragm assembly, the stop assembly includes a direct stop and a first aperture stop, the direct stop being located between the first focusing lens and the first aperture stop, the first aperture diaphragm is positioned between the straight baffle and the first detector, and a first light-transmitting hole for transmitting light rays and irradiating the light rays on the first detector is arranged in the first aperture diaphragm in a penetrating manner;
the side scattering detection assembly is used for collecting side scattering signals generated by the light source irradiating the cells to be detected; the side scattering detection assembly comprises a fourth aperture diaphragm and a third detector, the fourth aperture diaphragm is arranged between the flow chamber and the third detector, and a fifth light-transmitting hole for light to penetrate and irradiate the third detector is formed in the fourth aperture diaphragm in a penetrating mode;
at least one of the first light-transmitting hole and the fifth light-transmitting hole is a non-circular hole, the size of the non-circular hole in the first direction is larger than that in the second direction, the first direction is perpendicular to the second direction, and the first direction is parallel to the flowing direction of the cell to be detected.
21. The optical inspection device of claim 20, wherein: at least one of the first light transmission hole and the fifth light transmission hole is a kidney-shaped hole or an elliptical hole or a rectangular hole.
22. A cellular analyzer, comprising: comprises a reaction cell, a reagent supply device, a sampling unit, a diluent supply device, a conveying device, an analysis unit, an output unit and the optical detection device as claimed in any one of claims 1 to 21;
the reaction tank is used for providing a reaction field for a sample to be detected and a reagent so as to prepare a detection sample liquid;
the sampling unit is used for collecting a sample to be detected and discharging the sample to be detected into the reaction tank;
the reagent supply device is used for conveying a reagent into the reaction tank;
the conveying device is used for driving the detection sample liquid to be conveyed from the reaction pool to the flowing chamber and driving the diluent liquid to be conveyed from the diluent supplying device to the flowing chamber, so that the cells to be detected of the detection sample liquid are queued to pass through the flowing chamber under the entrainment of the diluent liquid;
the optical detection device is used for detecting the detection sample liquid which is wrapped by the diluent and passes through the flow chamber;
the analysis unit is used for analyzing the optical signal fed back by the detector to obtain the detection result of the detection sample liquid;
the output unit is used for outputting the detection result of the analysis unit.
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| CN202011360237.2A CN114563329A (en) | 2020-11-27 | 2020-11-27 | Optical detection device and cell analyzer |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN116106524A (en) * | 2023-04-11 | 2023-05-12 | 深圳市帝迈生物技术有限公司 | Blood analysis device |
| CN116399832A (en) * | 2023-04-24 | 2023-07-07 | 中元汇吉生物技术股份有限公司 | Optical detection system for analyzing blood cells and blood cell analyzer |
| CN118310944A (en) * | 2024-06-05 | 2024-07-09 | 深圳市帝迈生物技术有限公司 | Sample detection device and flow chamber preparation method |
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2020
- 2020-11-27 CN CN202011360237.2A patent/CN114563329A/en active Pending
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
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| 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 |
| CN116399832A (en) * | 2023-04-24 | 2023-07-07 | 中元汇吉生物技术股份有限公司 | Optical detection system for analyzing blood cells and blood cell analyzer |
| CN118310944A (en) * | 2024-06-05 | 2024-07-09 | 深圳市帝迈生物技术有限公司 | Sample detection device and flow chamber preparation method |
| CN118310944B (en) * | 2024-06-05 | 2024-10-15 | 深圳市帝迈生物技术有限公司 | Sample detection device and flow chamber preparation method |
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