CN202177574U - Photoelectric sensor for blood cell analysis - Google Patents
Photoelectric sensor for blood cell analysis Download PDFInfo
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- CN202177574U CN202177574U CN2011202412493U CN201120241249U CN202177574U CN 202177574 U CN202177574 U CN 202177574U CN 2011202412493 U CN2011202412493 U CN 2011202412493U CN 201120241249 U CN201120241249 U CN 201120241249U CN 202177574 U CN202177574 U CN 202177574U
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- blood cell
- flow chamber
- photoelectric sensor
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- cell analysis
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Abstract
The utility model relates to a photoelectric sensor for blood cell analysis, which comprises a flow chamber. The flow chamber allows sheath fluid and sample fluid to circulate inside. When the sample fluid, sheathed by the sheath fluid, flows in the flow chamber, blood cells in the sample fluid can pass through a detecting area which is arranged at one end of the flow chamber one another. An optical irradiation unit and a photoelectric detection unit are disposed at the other end of the flow chamber, corresponding to the end of the flow chamber provided with the detecting area. When a focus spot formed by the optical irradiation unit irradiates the blood cells in the detecting areas, the photoelectric detection unit can receive scattered light and fluorescent light generated when the focus spot passes through the blood cells. The photoelectric detection unit can convert the received scattered light and the fluorescent light into analysis signals of blood cells to be output. According to the photoelectric sensor for blood cell analysis, forward scatter is not involved in cell classifying, the forward scatter is not received or detected, the structure of a detecting system is simplified, and production and maintenance costs are reduced. Simultaneously, the stability of the system is improved, the photoelectric sensor for blood cell analysis is compact in structure and convenient to install and use, improves detection accuracy, and is safe and reliable.
Description
Technical field
The utility model relates to a kind of photoelectric sensor, and especially a kind of photoelectric sensor that is used for the blood cell analysis belongs to the technical field that blood cell is analyzed.
Background technology
Blood cell in the human peripheral blood has three types to be respectively red blood cell, leucocyte and blood platelet, and wherein leucocyte is divided into five types, is respectively eosinophil, neutrophil leucocyte, basophilic granulocyte, lymphocyte, monocyte.In early days blood cell being analyzed all is to rely on manual work to carry out artificial cognition at microscopically through morphology; Coulter had invented a kind of instrument that can analyze automatically blood cell afterwards; Its principle is: particle flux can cause the conductivity at these two ends, hole to change when crossing a full of liquid aperture; The rate of change of conductivity and the volume of particle are proportional; The otherness that so just can utilize the blood cell volume is divided into three types with the blood cell of peripheral blood: leucocyte, red blood cell and blood platelet, because leucocyte volume ratio red blood cell is big from volume, erythrocyte volume is bigger than blood platelet.
Yet the Coulter principle but can't be with leukocytic five sub-category separately, and overlapping because leukocytic five sub-category have on volume, difference is on inner structure.After flow cytometer has been invented by Becton Dikinson company, utilize the principle of optical scattering can the inside result of cell be distinguished, the nineties in last century, a lot of companies were incorporated into low cytometric analysis in the blood cell analyzer one after another; Formation and the modern times five classification blood cell analyzer that leucocyte is carried out five classification, there are Beckman Coulter, ABBOTT in famous company; Sysmex; Siemens, ABX, Mindray.
Patent US6228652 has disclosed a kind of blood cell analyzer device based on flow cytometer, and it utilizes forward direction low angle scattering (LMALS) and forward direction high angle scattered light (UMALS) that leucocyte is carried out the part classification.
Patent US2009310122 has disclosed other a kind of blood cell analyzer, utilizes forward scattering light, side scattered light and fluorescence that leucocyte is carried out five classification.
Patent US5631165 has disclosed other a kind of five classification blood cell analyzers, has utilized multi-angle polarization and depolarization scattered light to carry out leucocyte five classification.
More than the instrument blood cell analyzed based on the method for flow cytometry, all adopted the volume of forward scattering light pair cell to differentiate.Yet the volume of cell is very responsive to the angular range of forward scattering light, so just requires the forward scattering angle precision of instrument very strict, brings higher cost for the production debugging and the maintenance of instrument like this.
Summary of the invention
The purpose of the utility model is to overcome the deficiency that exists in the prior art, and a kind of photoelectric sensor that blood cell is analyzed that is used for is provided, its compact conformation, and convenient mounting and regulation reduces use cost, and stability is high, and is safe and reliable.
The technical scheme that provides according to the utility model; The said photoelectric sensor that is used for the blood cell analysis; Comprise and allow sheath fluid and the logical flow chamber of sample flow; Said sample liquid is when flowing in flow chamber under the parcel of sheath fluid, and sample liquid inner blood cell can pass through the detection zone of flow chamber end one by one; Flow chamber is provided with light irradiation unit and photodetection unit corresponding to the end that detection zone is set; During blood cell in the focal beam spot irradiating and detecting district that said light irradiation unit forms; The photodetection unit can receive scattered light and the fluorescence that produces through blood cell, and said photodetection unit converts scattered light that receives and fluorescence the output of into blood cell analytic signal.
Said flow chamber comprises the chamber body of being processed by optically transparent material, and said chamber body is provided with commutating zone corresponding to the other end that detection zone is set, and the center of said commutating zone is provided with sample liquid input field; Said commutating zone is connected with detection zone through accelerating region.
Hole formation detection zone is detected through being provided with in the center of an end in the body of said chamber, and the axis in said detection hole and the axis of chamber body are located along the same line; Said detection hole is rectangular or square, and the aperture of detecting the hole is 200 μ m ~ 400 μ m.
The Reynolds number of sheath fluid fluid layer stream is less than 2300 in the said flow chamber.
Said light irradiation unit comprises at least one semiconductor laser light resource; Be provided with the laser alignment lens and first condenser lens on the light ray propagation direction of said semiconductor laser light resource successively, the light that semiconductor laser light resource penetrates focuses on the center that back focus is positioned at detection zone through the laser alignment lens and first condenser lens.
Said photodetection unit comprises second condenser lens, and said second condenser lens is positioned on the light ray propagation direction perpendicular to light irradiation unit; Second condenser lens is assembled light path and is provided with dichroic beamsplitter, and the reflected light path of said dichroic beamsplitter is provided with second photodetector, and the transmitted light path of dichroic beamsplitter is provided with first photodetector.
Be provided with the long logical color filter and first diaphragm between said first photodetector and dichroic beamsplitter, the contiguous dichroic beamsplitter of the logical color filter of said length.
Be provided with second diaphragm between said second photodetector and dichroic beamsplitter.
Said light irradiation unit is radiated at the hot spot ovalize of detection zone center, and the corresponding oval short-axis direction of said hot spot is the flow direction of blood cell in the sample liquid, and said oval minor axis length is less than two leukocytic diameters; The corresponding oval major axis of hot spot is less than the detection zone width.
Said flow chamber is provided with inhales appearance and road control module at night, and the output terminal of said photo detecting unit links to each other with data analysis unit with signal Processing.
The advantage of the utility model: inject sheath fluid and sample liquid in the flow chamber simultaneously, sample liquid gets into detection zone under sheath fluid parcel and compression, and blood cell passes through detection zone one by one; The oval hot spot that light irradiation unit focuses on back formation is radiated on the blood cell; And generation side scattered light and fluorescence; Said fluorescence receives through first photodetector and converts electric signal into, and side scattered light receives through second photodetector and converts electric signal into; Signal Processing and data analysis unit are handled back output leucocyte check and analysis result according to the electric signal of first photodetector and second photodetector; During sampling analysis, forward scattering light is not participated in cytological classification, forward scattering light is not received and surveys, and has simplified the detection system structure; Reduce production and maintenance cost, made system stability improve compact conformation simultaneously; Easy to install, improved accuracy of detection, safe and reliable.
Description of drawings
Fig. 1 is the user mode figure of the utility model.
Fig. 2 is the structured flowchart of the utility model.
Fig. 3 is the structural representation of the utility model flow chamber.
Fig. 4 is that the A-A of Fig. 3 is to cut-open view.
Fig. 5 is the detection synoptic diagram of the utility model flow chamber detection zone.
Fig. 6 is the dichroic beamsplitter functional schematic.
Fig. 7 is the spectral curve of long logical color filter.
Fig. 8 is the integrally-built synoptic diagram of the utility model.
Fig. 9 is the structural representation of the utility model light irradiation unit.
Description of reference numerals: 1-semiconductor laser light resource; 2-laser alignment lens; 3-first condenser lens; 4-second condenser lens; The 5-dichroic beamsplitter; The long logical color filter of 6-; 7-first diaphragm; 8-first photodetector; 9-second diaphragm; 10-second photodetector; The 11-light irradiation unit; The 12-flow chamber; The 13-photo detecting unit; The 14-hot spot; The 20-substrate; The 30-light source assembly; 40-flow chamber seat; The 50-lens mount; 60-first probe assembly; 70-dichroscope assembly; 80-second detector assembly; The 100-photoelectric sensor; The 121-commutating zone; The 122-accelerating region; The 123-detection zone; 124-detects the hole; 125-chamber body; 126-sample liquid input field; 200-signal Processing and data analysis unit and 300-inhale appearance and liquid road control module.
Embodiment
Below in conjunction with concrete accompanying drawing and embodiment the utility model is described further.
As shown in Figure 1: in order to detect five types of cells in the leucocyte, said photoelectric sensor 100 comprises light irradiation unit 11, flow chamber 12 and photo detecting unit 13; Allow the circulation of sheath fluid and sample liquid in the said flow chamber 12, when in flow chamber 12, flowing under the parcel of sample liquid at sheath fluid, the cell in the sample liquid can pass through the detection zone 123 of flow chamber 12 ends one by one.Said light irradiation unit 11 and photo detecting unit 13 all are positioned at flow chamber 12 corresponding to the end that detection zone 123 is set, and photo detecting unit 13 is positioned on the optical propagation direction perpendicular to light irradiation unit 11.Focus on light irradiation unit 11 optical propagation directions on the blood cell in the hot spot 14 irradiating and detecting districts 123 that form; Hot spot 14 produces scattered light and fluorescence through blood cell; Photo detecting unit 13 can receive the scattered light and the fluorescence of generation; And convert the scattered light of said reception and fluorescence into the blood cell analytic signal and output to signal Processing and data analysis unit 200, said signal Processing and data analysis unit 200 can be accomplished the detection to five types of cells in the leucocyte according to the blood cell analytic signal.Flow chamber 12 is provided with inhales appearance and liquid road control module 300, can control the sheath fluid and the sample liquid of circulation in flow chamber 12 through inhaling appearance and liquid road control module 300, enables to satisfy test requirements.
Like Fig. 3 and shown in Figure 4: said flow chamber 12 comprises chamber body 125, rectangular parallelepiped or the cube structure of said chamber body 125 for being processed by optically transparent material.Be respectively equipped with commutating zone 121, accelerating region 122 and detection zone 123 in the chamber body 125, said commutating zone 121 lays respectively at the two ends in the chamber body 125 with detection zone 123, and commutating zone 121 is connected with detection zone 123 through accelerating region 122.The axis of commutating zone 121, accelerating region 122 and detection zone 123 and the axis of chamber body 125 are located along the same line.Detect hole 124 formation detection zones 123 through being provided with in the chamber body 125, the axis in said detection hole 124 and the axis of chamber body 125 are located along the same line, and it is rectangular or square detecting hole 124, and the aperture of detecting hole 124 is 200 μ m ~ 400 μ m.The center of commutating zone 121 is provided with sample liquid input field 126; In chamber body 125, import sample liquid through sample liquid input field 126; Commutating zone 121 is the sheath fluid input field corresponding to the outside of sample liquid input field 126, thereby can wrap up sample liquid through commutating zone 121 back sheath fluids.The outlet of sample liquid input field 126 is the circular hole of diameter 0.3mm; The outlet of commutating zone 121 is an accelerating region 122; Said accelerating region 122 is funnel-form, accelerating region 122 corresponding to the aperture, end in proximity detection district 123 less than the aperture of accelerating region 122 corresponding to contiguous commutating zone 121.The sheath flow that flows in the chamber body 125 will satisfy laminar flow condition, and promptly Reynolds number is less than 2300, and the laminar flow condition of sheath flow can be controlled realization through inhaling appearance and liquid road control module 300.Sheath flow and sample liquid are through behind the commutating zone 121; Sheath flow parcel sample liquid is assembled; When getting in the detection zone 123 through accelerating region 122 backs; The sheath flow is compressed to the width less than 2 blood cells with sample liquid, so that the blood cell in the sample liquid can get into one by one and pass through detection zone 123, thereby can realize the detection of single blood cell at every turn.
Like Fig. 2, Fig. 5, Fig. 6 and shown in Figure 7: said light irradiation unit 11 comprises at least one semiconductor laser light resource 1, and the bright dipping end of said semiconductor laser light resource 1 or optical propagation direction end are provided with the laser alignment lens 2 and first condenser lens 3.The laser beam of sending in the semiconductor laser light resource 1 is through behind laser alignment lens 2 collimations; Focus on respectively on mutually perpendicular both direction through first condenser lens 3, semiconductor laser light resource 1 focuses on the center that back focus is positioned at the detection zone 123 of flow chamber 12 again.Simultaneously, the hot spot 14 that semiconductor laser light resource 1 forms in detection zone 123 is oval, and said oval-shaped minor axis is the flow direction of blood cell, and minor axis length is less than two leukocytic diameters; Hot spot 14 is corresponding to forming oval major axis dimension less than the aperture of detecting hole 124, otherwise can shine on the interior rib of flow chamber 12, produces a large amount of parasitic lights, is unfavorable for the detection of signal.
Said photodetection unit 13 comprises second condenser lens 4; Produce fluorescence and scattered light after in flow chamber 12, detecting the irradiation that the blood cell that flows through in the hole 124 receives oval hot spot; Said fluorescence and scattered light are collected by second condenser lens 4 on perpendicular to the optical propagation direction of semiconductor laser light resource 1, and second condenser lens, 4 collected angular ranges are 70 ~ 100 degree.On the convergence light path of second condenser lens 4, dichroic beamsplitter 5 is set, dichroic beamsplitter 5 can be with the fluorescence transmission of collecting, and can be with the scattered light reflection output of collecting.Therefore, on the fluorescence transmitted light path of dichroic beamsplitter 5, be provided with first photodetector 8, on the reflected light path of dichroic beamsplitter 5, be provided with second photodetector 10.Because fluorescence signal is very faint, in order to reduce the bias light of fluorescence, before getting into first photodetector 8, filter out, to improve the contrast of fluorescence signal with the composition of a long logical color filter 6 with non-fluorescence; Be provided with first diaphragm 7 with logical color filter 6 of duration and 8 of first photodetectors, can eliminate parasitic light, improve signal to noise ratio (S/N ratio) through first diaphragm 7.5 of second photodetector 10 and dichroic beamsplitters are provided with second diaphragm 9.Fig. 7 has provided a wavelength of fluorescence and has arrived 850nm at 650nm, the curve of spectrum instance of the logical color filter 6 of the length that the irradiates light wavelength is adopted when 635nm.After first photodetector 8 and second photodetector 10 receive fluorescence signal and scattered light signal respectively; Convert corresponding light signal into blood cell and analyze electric signal output, and with in said blood cell analytic signal input signal processing and the data analysis unit 200.Fluorescence that hot spot 14 is produced according to five types of cells in the blood cell and scattered light different, signal Processing and data analysis unit 200 can be exported corresponding leukocyte analysis structure.Said second photodetector 10 can adopt photodiode, and first photodetector 8 can adopt photomultiplier.
Like Fig. 8 and shown in Figure 9: be the concrete implementation structure synoptic diagram of the utility model.The overall optical electric transducer is positioned on the substrate 20.One end of said substrate 20 is provided with light source assembly 30; Light source assembly 30 comprises semiconductor laser light resource 1, laser alignment lens 2 and first condenser lens 3; Said light source assembly 30 1 sides are equipped with flow chamber 12 through flow chamber seat 40, and the detection zone 123 of flow chamber 12 is positioned on the propagation light path of light source assembly 30.A side of corresponding flow chamber seat 40 is provided with lens mount 50 on the substrate 20, and said lens mount 50 is perpendicular to light source assembly 30 optical propagation directions; Be provided with second condenser lens 4 in the lens mount 50, lens mount 50 can be done the adjusting of three translational degree of freedom.Substrate 20 is provided with first probe assembly 60 corresponding to the other end that light source assembly 30 and flow chamber seat 40 are set; Said first probe assembly 60 comprises long logical color filter 6, first diaphragm 7 and first photoelectric sensor 8; 50 of first probe assembly 60 and lens mounts are provided with dichroic assembly 70; Be provided with dichroic beamsplitter 5 in the said dichroic assembly 70, the fluorescence printing opacity light path of dichroic beamsplitter 5 is corresponding with first probe assembly 60; The scattered light reflected light path of dichroic beamsplitter 5 is provided with second detector assembly, 80, the second detector assemblies 80 and comprises second diaphragm 9 and second photodetector 10.Wherein light source assembly 30 can be on substrate 20 be rotated adjusting, with optical system for alignment; Flow chamber seat 40 can carry out one-dimensional translation on substrate regulates, and regulates direction perpendicular to the laser propagation direction; Lens mount 50 is connected with flow chamber seat 40, and can on flow chamber seat 40, carry out three-dimensional translating and regulate; First detector assembly is fixed on the substrate 20 with screw thread; The dichroscope assembly is fixed on the substrate 20 with screw thread; Second detector assembly 80 can carry out two-dimensional translation on substrate 20 regulates.
Like Fig. 1 ~ shown in Figure 9: during use, the position of adjustment light irradiation unit 11 and flow chamber 12 makes the focal beam spot 14 of light irradiation unit 11 be positioned at detection zone 123 central parts of flow chamber 12.During work, in flow chamber 12, inject sheath fluid and sample liquid through inhaling appearance and liquid road control module 300, sample liquid is through in the 126 input flow chambers 12 of sample liquid input field, and sheath fluid is positioned at the outside of sample liquid, can form sheath fluid parcel sample liquid.Behind commutating zone 121 and accelerating region 122, sheath fluid is gone into the indentation of sample hydraulic pressure in the detection zone 123, makes the blood cell in the sample liquid can pass through detection zone 123 one by one.Semiconductor laser light resource 1 in the light irradiation unit 11 forms focal beam spot 14 through the laser alignment lens 2 and first condenser lens 3 and shines on detection zone 123 hot spot 14 ovalizes.When having blood cell to pass through in the detection zone 123, blood cell can produce side scattered light and fluorescence respectively through after the irradiation of oval hot spot 14.The fluorescence that produces is collected through second condenser lens 4, dichroic beamsplitter 5, long logical color filter 6, first diaphragm 7 and first photodetector 8, and first photodetector 8 converts the fluorescence signal of collecting into electric signal output; Produced simultaneously sideswipe light is collected through second condenser lens 4, dichroic beamsplitter 5, second diaphragm 9 and second photodetector 10, and second photodetector 10 is electric signal output with the side scattered light conversion of signals of collecting.Signal Processing and data analysis unit 200 receive the electric signal of first photodetector 8 and 10 outputs of second photodetector simultaneously, and different fluorescence and the scattered lights of hot spot 14 generations detected leucocyte according to five classification cells in the different leucocytes; Realized the detection of single blood cell in the sample liquid.After detecting last blood cell, forming statistical property is exactly the general characteristic of this sample liquid.
Inject sheath fluid and sample liquid in the utility model flow chamber 12 simultaneously, sample liquid gets into detection zone 123 under sheath fluid parcel and compression, and blood cell is one by one through detection zone 123; The oval hot spot 14 that light irradiation unit 11 focuses on back formation is radiated on the blood cell; And generation side scattered light and fluorescence; Said fluorescence receives through first photodetector 8 and converts electric signal into, and side scattered light receives through second photodetector 10 and converts electric signal into; Signal Processing and data analysis unit 200 are handled back output leucocyte check and analysis result according to the electric signal of first photodetector 8 and second photodetector 10; During sampling analysis, forward scattering light is not participated in cytological classification, forward scattering light is not received and surveys, and has simplified the detection system structure; Reduce production and maintenance cost, made system stability improve compact conformation simultaneously; Easy to install, improved accuracy of detection, safe and reliable.
Claims (10)
1. one kind is used for the photoelectric sensor that blood cell is analyzed; It is characterized in that: comprise allowing sheath fluid and the logical flow chamber (12) of sample flow; Said sample liquid is when flowing in flow chamber (12) under the parcel of sheath fluid, and sample liquid inner blood cell can pass through the detection zone (123) of flow chamber (12) end one by one; Flow chamber (12) is provided with light irradiation unit (11) and photodetection unit (13) corresponding to the end that detection zone (123) is set; During blood cell in focal beam spot (14) the irradiating and detecting district (123) that said light irradiation unit (11) forms; Photodetection unit (13) can receive scattered light and the fluorescence that produces through blood cell, and said photodetection unit (13) converts scattered light that receives and fluorescence the output of into blood cell analytic signal.
2. the photoelectric sensor that is used for the blood cell analysis according to claim 1; It is characterized in that: said flow chamber (12) comprises the chamber body of being processed by optically transparent material (125); Said chamber body (125) is provided with commutating zone (121) corresponding to the other end that detection zone (123) is set, and the center of said commutating zone (121) is provided with sample liquid input field (126); Said commutating zone (121) is connected with detection zone (123) through accelerating region (122).
3. the photoelectric sensor that is used for the blood cell analysis according to claim 2; It is characterized in that: hole (124) formation detection zone (123) is detected through being provided with in the center of an end in the said chamber body (125), and the axis of the axis in said detection hole (124) and chamber body (125) is located along the same line; Said detection hole (124) is rectangular or square, and the aperture of detecting hole (124) is 200 μ m ~ 400 μ m.
4. the photoelectric sensor that is used for the blood cell analysis according to claim 1 is characterized in that: the Reynolds number of the interior sheath fluid fluid layer stream of said flow chamber (12) is less than 2300.
5. the photoelectric sensor that is used for the blood cell analysis according to claim 1; It is characterized in that: said light irradiation unit (11) comprises at least one semiconductor laser light resource (1); Be provided with laser alignment lens (2) and first condenser lens (3) on the light ray propagation direction of said semiconductor laser light resource (1) successively, the light that semiconductor laser light resource (1) penetrates focuses on the center that back focus is positioned at detection zone (123) through laser alignment lens (2) and first condenser lens (3).
6. the photoelectric sensor that is used for the blood cell analysis according to claim 1; It is characterized in that: said photodetection unit (13) comprises second condenser lens (4), and said second condenser lens (4) is positioned on the light ray propagation direction perpendicular to light irradiation unit (11); Second condenser lens (4) is assembled light path and is provided with dichroic beamsplitter (5); The reflected light path of said dichroic beamsplitter (5) is provided with second photodetector (10), and the transmitted light path of dichroic beamsplitter (5) is provided with first photodetector (8).
7. the photoelectric sensor that is used for the blood cell analysis according to claim 6; It is characterized in that: be provided with long logical color filter (6) and first diaphragm (7) between said first photodetector (8) and dichroic beamsplitter (5), said length is led to the contiguous dichroic beamsplitter (5) of color filter (6).
8. the photoelectric sensor that is used for the blood cell analysis according to claim 6 is characterized in that: be provided with second diaphragm (9) between said second photodetector (10) and dichroic beamsplitter (5).
9. according to claim 1 or the 5 described photoelectric sensors that are used for the blood cell analysis; It is characterized in that: said light irradiation unit (11) is radiated at hot spot (14) ovalize of detection zone (123) center; The flow direction that the corresponding oval short-axis direction of said hot spot (14) is a blood cell in the sample liquid, said oval minor axis length is less than two leukocytic diameters; The corresponding oval major axis of hot spot (14) is less than detection zone (123) width.
10. the photoelectric sensor that is used for the blood cell analysis according to claim 1; It is characterized in that: said flow chamber (12) is provided with inhales appearance and road control module at night (300), and the output terminal of said photo detecting unit (13) links to each other with data analysis unit (200) with signal Processing.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2011202412493U CN202177574U (en) | 2011-07-08 | 2011-07-08 | Photoelectric sensor for blood cell analysis |
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| Application Number | Priority Date | Filing Date | Title |
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| CN2011202412493U CN202177574U (en) | 2011-07-08 | 2011-07-08 | Photoelectric sensor for blood cell analysis |
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| CN202177574U true CN202177574U (en) | 2012-03-28 |
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| CN2011202412493U Expired - Fee Related CN202177574U (en) | 2011-07-08 | 2011-07-08 | Photoelectric sensor for blood cell analysis |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105628660A (en) * | 2015-12-29 | 2016-06-01 | 大连理工大学 | Passive microvalve POCT chip |
| CN108120666A (en) * | 2017-11-07 | 2018-06-05 | 山东卓越生物技术股份有限公司 | For the Optical devices of blood cell analysis |
| CN115015178A (en) * | 2022-08-05 | 2022-09-06 | 天津迈科隆生物科技有限公司 | Optical detection device and blood analyzer |
-
2011
- 2011-07-08 CN CN2011202412493U patent/CN202177574U/en not_active Expired - Fee Related
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105628660A (en) * | 2015-12-29 | 2016-06-01 | 大连理工大学 | Passive microvalve POCT chip |
| CN105628660B (en) * | 2015-12-29 | 2018-04-10 | 大连理工大学 | A kind of passive micro-valve POCT chips |
| CN108120666A (en) * | 2017-11-07 | 2018-06-05 | 山东卓越生物技术股份有限公司 | For the Optical devices of blood cell analysis |
| CN115015178A (en) * | 2022-08-05 | 2022-09-06 | 天津迈科隆生物科技有限公司 | Optical detection device and blood analyzer |
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Granted publication date: 20120328 Termination date: 20120708 |