CN113008786A - Blood cell analyzer - Google Patents
Blood cell analyzer Download PDFInfo
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- CN113008786A CN113008786A CN201911330898.8A CN201911330898A CN113008786A CN 113008786 A CN113008786 A CN 113008786A CN 201911330898 A CN201911330898 A CN 201911330898A CN 113008786 A CN113008786 A CN 113008786A
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- 210000000601 blood cell Anatomy 0.000 title claims abstract description 22
- 230000005540 biological transmission Effects 0.000 claims abstract description 47
- 238000001514 detection method Methods 0.000 claims abstract description 43
- 238000002331 protein detection Methods 0.000 claims abstract description 34
- 239000003153 chemical reaction reagent Substances 0.000 claims abstract description 24
- 210000004369 blood Anatomy 0.000 claims abstract description 21
- 239000008280 blood Substances 0.000 claims abstract description 21
- 230000010365 information processing Effects 0.000 claims abstract description 14
- 238000005259 measurement Methods 0.000 claims abstract description 8
- 238000012545 processing Methods 0.000 claims abstract description 6
- 230000003287 optical effect Effects 0.000 claims description 88
- 210000004027 cell Anatomy 0.000 claims description 47
- 238000013214 routine measurement Methods 0.000 claims description 3
- 230000008033 biological extinction Effects 0.000 description 12
- 238000010586 diagram Methods 0.000 description 9
- 238000000034 method Methods 0.000 description 6
- 230000037361 pathway Effects 0.000 description 5
- 230000000694 effects Effects 0.000 description 4
- 102000004169 proteins and genes Human genes 0.000 description 4
- 108090000623 proteins and genes Proteins 0.000 description 4
- 239000012530 fluid Substances 0.000 description 3
- 239000013307 optical fiber Substances 0.000 description 2
- 230000002035 prolonged effect Effects 0.000 description 2
- 238000000790 scattering method Methods 0.000 description 2
- 102000008857 Ferritin Human genes 0.000 description 1
- 108050000784 Ferritin Proteins 0.000 description 1
- 238000008416 Ferritin Methods 0.000 description 1
- 206010018910 Haemolysis Diseases 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 238000004737 colorimetric analysis Methods 0.000 description 1
- 230000008094 contradictory effect Effects 0.000 description 1
- 230000008588 hemolysis Effects 0.000 description 1
- 230000001900 immune effect Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000004321 preservation Methods 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 239000000758 substrate Substances 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
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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
-
- 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
-
- 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
- G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
- G01N21/51—Scattering, i.e. diffuse reflection within a body or fluid inside a container, e.g. in an ampoule
-
- 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
- G01N21/59—Transmissivity
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
-
- 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
- G01N2021/0357—Sets of cuvettes
-
- 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
- G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
- G01N21/51—Scattering, i.e. diffuse reflection within a body or fluid inside a container, e.g. in an ampoule
- G01N2021/513—Cuvettes for scattering measurements
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- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Chemical & Material Sciences (AREA)
- Immunology (AREA)
- Analytical Chemistry (AREA)
- Biochemistry (AREA)
- General Health & Medical Sciences (AREA)
- General Physics & Mathematics (AREA)
- Physics & Mathematics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Hematology (AREA)
- Molecular Biology (AREA)
- Urology & Nephrology (AREA)
- Food Science & Technology (AREA)
- Medicinal Chemistry (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
The invention discloses a blood cell analyzer, which comprises a control and information processing module, a reagent collecting and distributing device, a protein detection device and a blood conventional measurement device. The protein detection device comprises a color comparison pool, at least two light path channels and a detection component. Each light path channel is used for generating a light beam to enter the color comparison pool, collecting transmitted light and/or scattered light of the light beam passing through the color comparison pool, and generating a transmitted electric signal according to the transmitted light and/or generating a scattered electric signal according to the scattered light; the detection component is used for acquiring solution information in the color comparison pool set according to the transmission electric signal and/or the scattering electric signal; the control and information processing module is used for controlling the reagent collecting and distributing device to collect the solution and distribute the solution, receiving the solution information output by the protein detection device and processing the solution information. Through the mode, the detection efficiency of the blood cell analyzer can be improved.
Description
Technical Field
The invention relates to the field of biological detection, in particular to a blood cell analyzer.
Background
The detection of specific proteins is a very hot clinical test item in recent years, including CRP, SAA and the like, and the detection principle is an optical colorimetric method.
The existing detection device generally only has one optical path, so that one detection device can only detect one solute of a group of solutions, and the whole detection efficiency is low.
Disclosure of Invention
The invention mainly provides a blood cell analyzer. The problem of detection device detection efficiency is low among the prior art is solved.
In order to solve the technical problems, the invention adopts a technical scheme that: there is provided a blood cell analyzer including: the device comprises a control and information processing module, a reagent collecting and distributing device, a protein detection device and a blood routine measuring device, wherein the reagent collecting and distributing device, the protein detection device and the blood routine measuring device are electrically connected with the control and information processing module; the reagent collecting and distributing device is used for collecting solution and distributing the collected solution to the protein detection device; the blood routine measuring device provides a measuring place for a sample and measures the sample to obtain measuring information of at least one blood routine parameter; the protein detection device comprises: a colorimetric pool group; each light path channel is used for generating a light beam to be incident into the color comparison pool, collecting transmitted light and/or scattered light of the light beam passing through the color comparison pool, and generating a transmitted electric signal according to the transmitted light and/or generating a scattered electric signal according to the scattered light; the detection component is used for acquiring solution information in the color comparison pool set according to the transmission electric signal and/or the scattering electric signal; the control and information processing module is used for controlling the reagent collecting and distributing device to collect solution and distribute solution, receiving and processing solution information output by the protein detection device, receiving and processing measurement information output by the blood routine measurement device.
According to an embodiment of the present invention, the set of color comparison cells includes at least two color comparison cells, and each color comparison cell is disposed corresponding to one of the optical path channels.
According to one embodiment of the present invention, the set of cuvettes comprises a cuvette, each of the optical channels is configured to generate a light beam of one wavelength to be incident on the cuvette and collect transmitted and/or scattered light through the cuvette; wherein, the wavelength of the light beam generated by each of the at least two light path channels is different from the wavelength of the light beam generated by the other light path channels.
According to an embodiment of the present invention, the light beams generated in the at least two light path channels are incident from different regions of the cuvette.
According to an embodiment of the present invention, the light beams generated by the at least two light path channels are incident on the colorimetric cell independently or simultaneously.
According to an embodiment of the present invention, the optical path channel includes: a light source for generating the light beam; the transmitted light collector is arranged on a light path of the light beam and is used for collecting the transmitted light of the light beam passing through the color comparison battery pack; and the scattered light collector and the optical axis of the light beam are arranged at a preset included angle and used for collecting the scattered light of the light beam passing through the color comparison cell group.
According to an embodiment of the present invention, an angle between the color cell set and the optical axis of the light beam is less than 90 ° or an angle between the light incident sidewall of the color cell set and the optical axis of the light beam is less than 90 °.
According to an embodiment of the present invention, the light beam is a converging light, the optical path further includes a first diaphragm, and the first diaphragm includes a transmission aperture, and the transmission aperture is disposed between the color comparison cell set and the transmission light collector and located on a beam waist of the light beam passing through the transmission aperture.
According to an embodiment of the present disclosure, the optical path further includes a second diaphragm and a third diaphragm sequentially disposed between the light source and the color comparison cell set, and an aperture of the second diaphragm is larger than an aperture of the third diaphragm.
According to an embodiment of the present invention, a distance between the aperture of the second diaphragm and the light source is greater than or equal to 5mm and less than or equal to 10 mm; the distance between the light hole of the third diaphragm and the light hole of the second diaphragm is greater than or equal to 30mm and less than or equal to 40 mm; the distance between the color comparison battery and the light hole of the third diaphragm is more than or equal to 2mm and less than or equal to 5 mm.
The invention has the beneficial effects that: different from the prior art, at least two light path channels are arranged in the protein detection device, each light path channel can generate light beams to be incident into the color comparison pool, the transmitted light and/or the scattered light of the light beams passing through the color comparison pool are collected, a transmitted electric signal can be generated according to the transmitted light and/or a scattered electric signal can be generated according to the scattered light, and then the solution information in the color comparison pool can be obtained according to the transmitted electric signal and/or the scattered electric signal by arranging a detection component. Therefore, one or more kinds of solution information can be detected for one or more groups of solutions, and the detection efficiency is greatly improved.
Drawings
In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the drawings needed to be used in the description of the embodiments are briefly introduced below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and other drawings can be obtained by those skilled in the art without inventive efforts, wherein:
FIG. 1 is a schematic configuration diagram of a first embodiment of a blood cell analyzer according to the present invention;
FIG. 2 is a schematic structural view of a first embodiment of the protein detection apparatus of FIG. 1;
FIG. 3 is a schematic structural view of a second embodiment of the protein detection apparatus of FIG. 1;
FIG. 4 is a schematic structural diagram of a first embodiment of the protein detection apparatus of FIG. 2, in which a light path channel is matched with a color cell set;
FIG. 5 is a schematic structural view of a third embodiment of the protein detection apparatus of FIG. 1;
FIG. 6 is a schematic view of a portion of the light source and cuvette of FIG. 4;
FIG. 7 is a schematic view of another partial structure of the light source and cuvette of FIG. 4;
FIG. 8 is a schematic structural diagram of a second embodiment of the protein detection apparatus shown in FIG. 2, in which one optical channel is matched with a cuvette;
FIG. 9 is a schematic structural diagram of a third embodiment of the protein detection apparatus shown in FIG. 2, in which one optical channel is matched with a cuvette;
FIG. 10 is a schematic structural diagram of a fourth embodiment of the protein detection apparatus shown in FIG. 2, in which one optical channel is matched with a cuvette;
FIG. 11 is a schematic structural diagram of a fifth embodiment of the protein detection apparatus shown in FIG. 2, in which one optical channel is matched with a cuvette;
FIG. 12 is a schematic structural diagram of the first embodiment of the protein detection apparatus shown in FIG. 2, in which at least two light path channels are matched with the colorimetric cells;
FIG. 13 is a schematic structural diagram of a second embodiment of the protein detection apparatus of FIG. 2 in which at least two optical channels are coupled to a cuvette;
FIG. 14 is a schematic structural diagram of a third embodiment of the protein detection apparatus shown in FIG. 2, in which at least two optical channels are matched with a cuvette.
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, if directional indications (such as up, down, left, right, front, and back … …) are involved in the embodiment of the present invention, the directional indications are only used to explain the relative positional relationship between the components, the movement situation, and the like in a specific posture (as shown in the drawing), and if the specific posture is changed, the directional indications are changed accordingly.
In addition, if there is a description of "first", "second", etc. in an embodiment of the present invention, the description of "first", "second", etc. is for descriptive purposes only and is 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.
Referring to fig. 1-14, the present invention provides a blood cell analyzer 1, wherein the blood cell analyzer 1 includes a protein detection device 10, a control and information processing module 20, a reagent collecting and distributing device 30, and a blood routine measuring device 40. And the protein detection device 10, the reagent collecting and distributing device 30 and the blood routine measuring device 40 are all electrically connected with the control and information processing module 20.
In particular embodiments, reagent collection and dispensing device 30 is used to collect a solution and dispense the collected solution to protein detection device 10.
In a particular embodiment, the blood routine measuring device 40 provides a measurement site for the sample and measures the sample to obtain measurement information for at least one blood routine parameter.
As shown in fig. 2-14, the protein detection apparatus 10 includes a color cell set 100, a light path channel 200, and a detection component 300.
The number of the optical path channels 200 is at least two, and specifically may be two, three, or more, which is not limited herein. Each optical channel 200 can be used to generate and transmit a light beam into the cell stack 100, and then collect the transmitted and/or scattered light of the light beam after passing through the cell stack 100. And further may generate a transmitted electrical signal from the transmitted light and/or a scattered electrical signal from the scattered light.
The detection assembly 300 can then obtain information about the solution in the cell stack 100 based on the transmitted electrical signal and/or the scattered electrical signal.
In a specific scenario, the color cell stack 100 may be specifically configured to contain a solution dispensed by the reagent collecting and dispensing device 30, when a light beam generated by the optical path channel 200 enters the color cell stack 100, a part of the light beam may be directly transmitted to form transmitted light, a part of the light beam may be scattered by the solution to form scattered light, and the transmitted light or the scattered light carries information about the solution, so that solution information may be determined according to a transmitted electrical signal generated by the transmitted light and/or a scattered telecommunication generated by the transmitted light.
The control and information processing module 20 is used for controlling the reagent collecting and distributing device 30 to collect the solution and distribute the solution, and receiving the solution information output by the protein detecting device 10 and processing the solution information. And can also be used to receive and process measurement information output by the blood routine measuring device 40. The solution information and the measurement information can be further processed, and then the whole detection result is output.
In the above embodiment, at least two optical path channels 200 are provided, and each optical path channel 200 can generate a light beam to enter the color cell set 100, collect transmitted light and/or scattered light of the light beam after passing through the color cell set 100, and can generate a transmitted electrical signal according to the transmitted light and/or generate a scattered electrical signal according to the scattered light, and then further, the detection component 300 can obtain solution information in the color cell set 100 according to the transmitted electrical signal and/or the scattered electrical signal. Therefore, one or more kinds of solution information can be detected for one or more groups of solutions, and the detection efficiency is greatly improved.
In a specific embodiment, the blood cell analyzer 1 may further include a reagent bottle storage device for providing a low-temperature preservation environment for the solution, so that the solution is well preserved and is not easily deteriorated.
In particular embodiments, the solution may specifically be an antibody reagent, a hemolysis reagent, and the like, including but not limited to an immunological reagent, such as a CRP reagent, a SAA reagent, a ferritin reagent, and the like.
In an embodiment, the blood cell analyzer 1 may further include a sample collection and distribution device and a fluid path support device electrically connected to the control and information processing module 20. The control and information processing module 20 can control the sample collection and distribution device for collecting and distributing samples to the blood routine measuring device 40. The blood routine measuring device 40 is used for providing a measuring place for the dispensed sample, and measuring the dispensed sample to obtain measurement information of at least one blood routine parameter. The sample collection and distribution device comprises a sample needle and a hydrodynamic device such as a syringe, a dosing pump, etc., and the sample is mainly a blood-related sample. The fluid path support device is used for providing fluid path support for the sample collection and distribution device, the reagent collection and distribution device 30, the blood routine measurement device 40 and the protein detection device 10.
As shown in FIG. 3, the color comparison cell set 100 comprises at least two color comparison cells 110, and each color comparison cell 110 is disposed corresponding to one optical path channel 200. I.e., one cuvette 110 corresponds to one optical channel 200.
In a specific embodiment, for example, if there are two optical channels 200, there may be two colorimetric cells 110, and each colorimetric cell 110 corresponds to one optical channel 200.
In a specific scenario, at least two cuvettes 110 may contain the same solution or different solutions, and are not limited herein.
In a specific scenario, different optical paths 200 may detect the same solute of a solution, and may also detect different solutes, which is not limited herein.
As shown in fig. 4, the light path channel 200 includes a light source 210 and a transmitted light collector 220 and/or a scattered light collector 230. The light source 210 is configured to generate a light beam and emit the light beam into the color cell set 100, and the transmission light collector 220 is disposed on a light path of the light beam generated by the light source 210 of the same light path channel 200 and configured to collect transmission light of the light beam after passing through the color cell set 110. The scattered light collector 230 is disposed at a predetermined angle with respect to the optical axis of the light beam, and is configured to collect scattered light of the light beam passing through the color cell stack 100.
Specifically, the detection assembly 300 is coupled to the transmitted light collector 220 and/or the scattered light collector 230.
As shown in fig. 5, each optical channel 200 includes an independent light source 210, and at least two color cells 110 of the color cell set 100 are respectively in one-to-one correspondence with the light beams generated by the light sources 210 of at least two optical channels 200. Similarly, the transmitted light collector 220 and/or the scattered light collector 230 are independent and respectively correspond to at least two colorimetric cells 110.
In another embodiment, a plurality of or all of the at least two light paths 200 may share the light source 210, and the light source 210 may emit a plurality of light beams with different angles to be incident on the at least two colorimetric cells 110, thereby saving the cost and volume of the light source 210.
In other embodiments, the light source 210 and the at least two cuvettes 110 may be connected by optical fibers, so that the light beams of the same light source 210 can be incident on the at least two cuvettes 110.
In a particular embodiment, the color cell stack 100 is at an angle of less than 90 ° to the optical axis of the light beam. Specifically, each cell 110 makes an angle of less than 90 ° with the optical axis of the light beam incident on the cell 110.
In another embodiment, the light-incident sidewall 111 of the cell stack 100 is angled less than 90 ° from the optical axis of the light beam. Specifically, the included angle between the light incident sidewall 111 of each cuvette 110 and the optical axis of the light beam incident to the cuvette 110 may be smaller than 90 °.
The following takes a colorimetric cell 110 and an optical channel 200 as an example:
in one embodiment, as shown in fig. 6, the entire cuvette 110 may be a regular cylinder, and the entire cuvette 110 is disposed at an oblique angle with respect to the optical axis.
In another embodiment, as shown in fig. 7, the light-incident sidewall 111 of the cuvette 110 is inclined with respect to the bottom wall 112 of the cuvette 110, such that the light-incident sidewall 111 is inclined with respect to the optical axis when the cuvette 110 is disposed horizontally with respect to the optical axis.
As shown in fig. 6 and 7, the inclination angle α of the inclination is 1 ° or more and 5 ° or less.
In an exemplary embodiment, the light beam generated by the light source 210 is a concentrated light.
In the above embodiment, the light source 210 generates the light beam as the convergent light, so that most of the light beam entering the colorimetric pool 110 is not vertically incident, and thus the primary reflection of the colorimetric pool 110 on the light beam can be reduced, and further the primary reflection of the colorimetric pool 110 on the light beam can be further reduced by obliquely arranging the optical axes of the colorimetric pool 110 and the light beam, and further the light beam reflected by the colorimetric pool 110 enters the light source 210, so that the loss of the light source 210 is reduced, and the service life of the light source 210 is further prolonged. Furthermore, if the light beam is reflected into the light source 210, the stability of the output power of the light source 210 is directly affected, and the stability of the whole detection result is further affected.
In an embodiment, the optical path 200 may include only the transmitted light collector 220, only the scattered light collector 230, or both the transmitted light collector 220 and the scattered light collector 230.
For embodiments in which both the transmitted light collector 220 and the scattered light collector 230 are included, the detection of the solution in the cuvette 110 typically includes a scattering method and a transmission method, wherein the scattering method is suitable for scenes with low solution concentration and the transmission method is suitable for scenes with high solution concentration.
The transmission concentration value and the scattering concentration value of the solution in the cuvette 110 are respectively obtained through the transmission electric signal generated by the transmission light collector 220 and the scattering electric signal generated by the scattering light collector 230, and are compared with the preset concentration value, if the transmission concentration value and the scattering concentration value are higher than the preset concentration value, that is, the solution can be considered as a high value, the transmission concentration value is adopted as the final detection result. And if the concentration value is lower than the preset concentration value, namely the solution can be considered as a low value, adopting the scattering concentration value as a final detection result.
Therefore, by arranging the transmitted light collector 220 for collecting the transmitted light passing through the cuvette 110 and the scattered light collector 230 for collecting the scattered light passing through the cuvette 110, the transmission concentration value and the transmission concentration value of the solution in the cuvette 110 can be detected, and further the transmission concentration value or the scattering concentration value can be selected as the final detection result according to the detection result, thereby ensuring that the optimal detection result can be ensured no matter the solution is a high-concentration solution or a low-concentration solution.
In a specific embodiment, at least two of the optical paths 200 in the same protein detection apparatus 10 may be the same or different. Are not limited herein.
In a specific scenario, each of the at least two optical paths 200 may include a transmitted light collector 220 and a scattered light collector 230.
In another specific scenario, for at least two optical paths 200 in the same protein detection apparatus 10, one optical path 200 of the at least two optical paths 200 includes both the transmitted light collector 220 and the scattered light collector 230, and one optical path 200 of the at least two optical paths 200 may include only the transmitted light collector 220 or only the scattered light collector 230.
Referring to fig. 8, the optical path channel 200 further includes a first diaphragm 240, the first diaphragm 240 includes a transmission aperture 241, and the transmission aperture 241 is disposed between the cuvette 110 and the transmission light collector 220 and located at the beam waist position of the light beam.
Specifically, after the light beam enters the cuvette 110, a portion of the light beam directly transmits through the cuvette 110 and is transmitted along the original light path, a portion of the light beam is scattered by the solution of the cuvette 110, the collected light path required to be collected by the transmitted light collector 220 is a portion directly transmitting through the cuvette 110 and generating a transmitted electrical signal, and if the stray light scattered by the inner wall of the cuvette 110 is collected by the transmitted light collector 220, the stray light does not carry any signal of the solution of the cuvette 110, the accuracy of the transmitted electrical signal is affected, and the detection result is ultimately affected. According to the invention, the light beams converging light are adopted, the transmission light hole 241 is arranged at the beam waist position of the light beams, and as the part from the light path of the light beams to the beam waist position is gradually narrowed, compared with a parallel light path, the light path is narrowed, which means less stray light can be parallel to the light path, and further, the transmission light hole 241 is arranged at the beam waist position, so that only the light along the light path of the originally converging light beams can pass through the transmission light hole 241 and be collected by the transmission light collector 220, and most of the stray light can be blocked, therefore, the stray light collected by the transmission light collector 220 can be reduced, and the accuracy of the detection result is greatly improved.
In a specific embodiment, the transmission light hole 241 may be a circular light hole, and the diameter of the transmission light hole 241 is equal to the beam waist diameter of the converged light beam.
In other embodiments, the diameter of the transmission light aperture 241 may also be reduced according to the light intensity of the transmission light that needs to be collected by the transmission light collector 220.
In other embodiments, the diameter of the light transmitting hole 241 may be further increased according to assembly tolerance, and the like, which are not limited herein.
As shown in fig. 8, the first diaphragm 240 further includes a scattered light hole 242, the scattered light hole 242 is disposed between the cuvette 110 and the scattered light collector 230, and the scattered light hole is an elliptical light hole. Wherein the major axis of the scattered light aperture is determined by the upper and lower limits of the scattered light that needs to be collected by the scattered light collector 230, and the minor axis of the scattered light aperture is equal to the diameter of the converged light beam when entering the cuvette 110.
The scattered light entering the scattered light collector 230 through the scattered light hole 242 can satisfy a certain angle consistency by arranging the scattered light hole 242, so as to improve the accuracy of the detection result.
As shown in fig. 9, the optical channel 200 further includes a first extinction groove (not shown), a first lens 250, a second extinction groove (not shown), and a second lens 260.
The first extinction groove and the first lens 250 are sequentially arranged between the transmission light hole 241 and the transmission light collector 220, the first extinction groove and the first lens 250 are matched to further eliminate stray light entering the transmission light collector 220, and further, the light spot entering the transmission light collector 220 can be controlled by arranging the first lens 250, so that the size of the light spot can be restricted, and the light spot has better shape and size when being collected by the transmission light collector 220.
The second extinction groove and the second lens 260 are sequentially disposed between the scattered light aperture 242 and the scattered light collector 230, and the second extinction groove and the second lens 260 cooperate to eliminate stray light entering the transmitted light collector 220 and can restrict the size of a light spot, so as to improve the accuracy of a detection result.
As shown in fig. 10, the optical channel 200 further includes a second diaphragm 270 and a third diaphragm 280 sequentially disposed between the light source 210 and the cuvette 110. And the aperture of the second diaphragm 270 is larger than that of the third diaphragm 280.
In a specific embodiment, the aperture of the second diaphragm 270 is greater than or equal to 5mm, less than or equal to 10mm from the light source 210. Specifically, the distance from the light exit hole of the light source 210 is greater than or equal to 5mm, and less than or equal to 10 mm. Specifically, it may be 5mm, 7mm or 10mm, and is not particularly limited herein.
The distance between the light hole of the third diaphragm 280 and the light hole of the second diaphragm 270 is greater than or equal to 30mm and less than or equal to 40 mm; specifically, it may be 30mm, 35mm or 40mm, and is not particularly limited herein. The distance between the aperture of the color comparison pool 100 and the third diaphragm 280 is greater than or equal to 2mm and less than or equal to 5 mm. Specifically, the distance between the light holes of the cuvette 110 and the third diaphragm 280 in the cuvette set 100 is greater than or equal to 2mm and less than or equal to 5 mm. Specifically, it may be 2mm, 4mm or 5mm, and is not particularly limited herein.
Specifically, the converged light beam can be constrained by keeping the aperture of the second diaphragm 270 and the aperture of the third diaphragm 280 consistent with the optical path change of the converged light beam. On the other hand, the stray light generated by the light source 10 itself or the optical cavity between the light source 10 and the third diaphragm 280 can be prevented from entering the cuvette 110, and further, because the aperture of the third diaphragm 280 is small, the influence of the stray light reflected by the cuvette 110 and the transmitted light collector 220 on the light source 10 can be further reduced, so that the light source 10 is protected.
As shown in fig. 11, the light path 200 further includes a base 290, wherein the light source 210, the transmitted light collector 220 and the scattered light collector 230 are disposed on the base 290. In other embodiments, other optical components of the optical path 200, such as the first diaphragm 240, the second diaphragm 270, the third diaphragm 280, the first extinction groove, the first lens 250, the second extinction groove, and the second lens 260, may also be disposed on the substrate 290, which is not limited herein.
As shown in fig. 12, the cell set 100 includes a cell 110, and each optical path channel 200 is used to generate a light beam of one wavelength to be incident on the cell 110 and collect the transmitted and/or scattered light through the cell. And the wavelength of the light beam generated by each of the at least two optical paths 200 is different from the wavelengths of the light beams generated by the other optical paths.
That is, in the specific embodiment, each of the at least two optical paths 200 generates a light beam of one wavelength and the wavelength of the light beam generated by each of the optical paths 200 is different.
Specifically, for the same optical path 200, only the light beam generated by the optical path 200 is collected, and the light beams generated by other optical paths 200 are not collected, and the collection may specifically depend on the identification of the wavelength.
In one embodiment, each of the optical pathways 200 is independent of the other, and the light beams generated by at least two of the optical pathways 200 are incident from different regions of the cuvette 110. I.e., the light beams generated by the respective light path channels 200 are incident from different regions of the cuvette 110.
As shown in fig. 12 and 13, the optical path 200 includes a light source 210 and a transmitted light collector 220 and/or a scattered light collector 230. The light sources 210 of the multiple light paths 200 generate light beams with one wavelength to be incident on the same cuvette 110, and since the wavelengths of the light beams generated by each light source 210 are different, the transmitted light collector 220 and/or the scattered light collector 230 can selectively collect light beams according to the wavelengths, so as to collect only the light beams generated by the light sources 210 of the light paths 200.
As shown in fig. 12, in an embodiment, the number of the optical path channels 200 may be three, the three optical path channels 200 are arranged in an array, and specifically include three light sources 210, three light beams generated by the three light sources 210 are incident from different areas of the cuvette 110, three transmission light collectors 220 are respectively and correspondingly arranged on the optical paths of the light beams generated by the three light sources 210 and are respectively used for collecting the transmission light of the light beams generated by the corresponding light sources 210 via the cuvette 110, and three scattered light collectors 230 are also respectively and correspondingly arranged and are respectively used for collecting the scattered light of the light beams generated by the light sources 210 via the cuvette 110.
In a specific embodiment, filters may be disposed in front of the collection channels of the transmission light collector 220 and the scattered light collector 230, so that the transmission light collector 220 and the scattered light collector 230 only collect light beams with corresponding wavelengths.
In another embodiment, the at least two optical pathways 200 may share a light source 210, and the light source 210 may be configured to emit light beams of different wavelengths from different regions of the cuvette 110 by means of optical fibers or the like.
In another embodiment, the at least two optical pathways 200 may share the light source 210, and the light source 210 may generate a light beam incident into the cuvette 110, and the light beam may include light of multiple wavelengths.
In a specific scenario, as shown in fig. 14, the two optical pathways 200 share a light source 210 and produce a light beam containing two wavelengths that is incident on the cuvette 110. The two transmissive light collectors 220 may be disposed on the light path of the light beam corresponding to each wavelength, and specifically, the first selective transflective film 221 may be disposed between the two transmissive light collectors 220 of the color cell 110 to filter or reflect light with different wavelengths. Specifically, the first selective transflective film 221 may be disposed at a predetermined angle with respect to an optical axis of the light beam, when the transmitted light of two wavelengths passes through the first selective transflective film 221, the transmitted light of one wavelength may be reflected to enter another optical path, the corresponding transmitted light collector 220 may be disposed on the optical path to collect the transmitted light of the wavelength, and the transmitted light of another intermediate wavelength may directly pass through the first selective transflective film 221 to be transmitted along the original optical path and collected by the transmitted light collector 220 disposed on the optical path. Similarly, the scattered light collector 230 can collect the scattered light with corresponding wavelength by disposing a second selective transflective film 231 between the two scattered light collectors 230 and the cuvette 110.
By the above method, the number of the light sources 210 and the volume requirement of the cuvette 110 can be reduced, and further, the volume and the cost of the whole device can be reduced.
In a particular embodiment, the light beams generated by the at least two light paths 200 are incident on the cuvette 110 independently or simultaneously. That is, only one light beam generated by one optical path 200 may be used for detecting the color cell 110, or a plurality of optical paths 200 may generate light beams with various wavelengths and detect the color cell 110 at the same time.
In a specific scenario, the detection of the solution may specifically be detection of a solute in the solution, such as a protein or other solutes, and for different solutes, the sensitivities of the light beams with different wavelengths are different, so that when a certain solute needs to be detected, the light beam with the optimal wavelength may be selected to detect the colorimetric pool 110, thereby improving the detection effect. Furthermore, the light beams with different wavelengths are adopted to detect the color pool 110, and the light beams with different wavelengths do not interfere with each other, so that the solution in the color pool 110 can be simultaneously detected for multiple solutes without being detected one by one, and the detection speed can be greatly increased.
A description of a specific scenario is made with respect to the overall structure of the blood cell analyzer 1:
the control and information processing module 20 controls the reagent collecting and distributing device 30 to collect the solution and distribute the collected solution, which may be specifically distributed to each cuvette 110 in the cuvette set 100 of the protein detecting device 10. The light source 210 emits a converged light beam, the converged light beam sequentially passes through the second diaphragm 270 and the third diaphragm 280, the second diaphragm 270 and the third diaphragm 280 restrict the converged light beam through respective light holes, so that the converged light beam is incident into the cuvette 110 according to a required cross-sectional size, because the cuvette 110 has a certain inclination with the optical axis of the converged light beam, the converged light beam is not easily reflected back to the light source 210 along the original path, and part of the light beam reflected toward the light source 210 is blocked by the second diaphragm 270 and the third diaphragm 280, so as to protect the light source 210, the part of the converged light beam incident into the cuvette 100 is scattered due to the inner wall of the cuvette 100 to form stray light, part of the light beam directly transmits through the cuvette 100 to form transmitted light, and part of the light beam forms scattered light due to the influence of a solution in the cuvette 100.
The transmitted light sequentially passes through the transmission aperture 241 of the first diaphragm 240, the first extinction groove and the first lens 250 and is collected by the transmitted light collector 220, specifically, on one hand, since the light path of the converged light beam is gradually narrowed in the propagation process, stray light and scattered light parallel to the converged light beam can be reduced, and further, the transmission aperture 241 is arranged at the beam waist position of the converged light beam to ensure that only the light beam coincident with the light path of the converged light beam can penetrate through the transmission aperture 241, then, the stray light entering the transmitted light collector 220 is further eliminated through the cooperation of the first extinction groove and the first lens 250, and the light beam is constrained by the first lens 250, so that the transmitted light collector 220 has a better shape and size when being collected. In the above-mentioned structure, on the one hand can reduce the light beam and reflect back to light source 210 to protect light source 210, improve the stability of the light beam that assembles that light source 210 launches, and then improve detection effect, on the other hand is through handling stray light etc. to reduce stray light etc. and enter into transmission light collector 300, thereby reduce the influence of stray light to the detection, thereby improve detection effect.
The scattered light sequentially passes through the scattered light aperture 242, the second extinction groove and the second lens 260 of the first diaphragm 240 and is collected by the scattered light collector 230, the angle consistency of the scattered light entering the scattered light collector 230 can be ensured through the scattered light aperture 242, the stray light is reduced through the second extinction groove and the second lens 260, and therefore the whole detection effect can be improved.
In a specific embodiment, in the case that the protein detection apparatus 10 includes a plurality of optical paths 200, each of the plurality of optical paths 200 may operate according to the above-mentioned scenario, or may operate differently from the above-mentioned scenario, but the specific operation principle is similar, and is specifically determined according to the type of the component.
In summary, the invention provides a blood cell analyzer, which can detect one or more kinds of solution information of one or more groups of solutions by arranging a plurality of light path channels in a protein detection device of the blood cell analyzer, thereby greatly improving the detection efficiency; on one hand, the light beam is set to be convergent light, a certain inclination angle is arranged between the colorimetric pool group and the optical axis of the light beam, and the second diaphragm and the third diaphragm are further arranged, so that the light beam cannot be reflected on the original path to damage the light source when entering the colorimetric pool, and the service life of the light source is prolonged; on one hand, the first diaphragm is arranged, and the transmission light hole of the first diaphragm is arranged at the beam waist position of the light beam, so that the influence of stray light on the transmission light collector is reduced, and the detection precision is improved; on the one hand, the light beams generated by the light path channels are set to different wavelengths, so that the light path channels can be detected by the same colorimetric pool, and the detection rate is increased.
The above description is only an embodiment of the present invention, and not intended to limit the scope of the present invention, and all modifications of equivalent structures and equivalent processes performed by the present specification and drawings, or directly or indirectly applied to other related technical fields, are included in the scope of the present invention.
Claims (10)
1. A blood cell analyzer, comprising: the device comprises a control and information processing module, a reagent collecting and distributing device, a protein detection device and a blood routine measuring device, wherein the reagent collecting and distributing device, the protein detection device and the blood routine measuring device are electrically connected with the control and information processing module;
the reagent collecting and distributing device is used for collecting solution and distributing the collected solution to the protein detection device;
the blood routine measuring device provides a measuring place for a sample and measures the sample to obtain measuring information of at least one blood routine parameter;
the protein detection device comprises:
a colorimetric pool group;
each light path channel is used for generating a light beam to be incident into the color comparison pool, collecting transmitted light and/or scattered light of the light beam passing through the color comparison pool, and generating a transmitted electric signal according to the transmitted light and/or generating a scattered electric signal according to the scattered light;
the detection component is used for acquiring solution information in the color comparison pool set according to the transmission electric signal and/or the scattering electric signal;
the control and information processing module is used for controlling the reagent collecting and distributing device to collect solution and distribute solution, receiving and processing solution information output by the protein detection device, receiving and processing measurement information output by the blood routine measurement device.
2. The blood cell analyzer of claim 1, wherein the cuvette set includes at least two cuvettes, each cuvette being disposed corresponding to one of the optical paths.
3. The hematology analyzer of claim 1, wherein the set of cuvettes includes one cuvette, each of the optical paths for generating a light beam of one wavelength to be incident on the cuvette and collecting transmitted and/or scattered light through the cuvette;
wherein, the wavelength of the light beam generated by each of the at least two light path channels is different from the wavelength of the light beam generated by the other light path channels.
4. The blood cell analyzer of claim 3, wherein the light beams generated in the at least two light path channels are incident from different regions of the cuvette.
5. The blood cell analyzer of claim 3, wherein the light beams generated by the at least two light path channels are incident on the cuvette independently or simultaneously.
6. The blood cell analyzer of claims 1-5, wherein the optical path channel comprises:
a light source for generating the light beam;
the transmitted light collector is arranged on a light path of the light beam and is used for collecting the transmitted light of the light beam passing through the color comparison battery pack; and/or
And the scattered light collector is arranged at a preset included angle with the optical axis of the light beam and is used for collecting the scattered light of the light beam passing through the color comparison cell group.
7. The hematology analyzer of claim 6, wherein the cuvette is at an angle of less than 90 ° to the optical axis of the light beam or the cuvette entrance sidewall is at an angle of less than 90 ° to the optical axis of the light beam.
8. The hematology analyzer of claim 6, wherein the light beam is a converging light, and the optical channel further comprises a first aperture, wherein the first aperture comprises a transmitting aperture, and the transmitting aperture is disposed between the color cell set and the transmitting light collector and located at a beam waist of the light beam passing through the transmitting aperture.
9. The blood cell analyzer of claim 8, wherein the light path channel further comprises a second diaphragm and a third diaphragm sequentially disposed between the light source and the color cell set, and the aperture of the second diaphragm is larger than that of the third diaphragm.
10. The blood cell analyzer of claim 8, wherein the distance between the aperture of the second diaphragm and the light source is greater than or equal to 5mm, and less than or equal to 10 mm; the distance between the light hole of the third diaphragm and the light hole of the second diaphragm is greater than or equal to 30mm and less than or equal to 40 mm; the distance between the color comparison battery and the light hole of the third diaphragm is more than or equal to 2mm and less than or equal to 5 mm.
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| CN201911330898.8A CN113008786A (en) | 2019-12-20 | 2019-12-20 | Blood cell analyzer |
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| CN201911330898.8A CN113008786A (en) | 2019-12-20 | 2019-12-20 | Blood cell analyzer |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113777076A (en) * | 2021-08-30 | 2021-12-10 | 四川南格尔生物科技有限公司 | Sensor and method for online real-time concentration monitoring |
| CN113984663A (en) * | 2021-10-28 | 2022-01-28 | 中国人民解放军海军特色医学中心 | Optical detection device and working method thereof |
| CN116106524A (en) * | 2023-04-11 | 2023-05-12 | 深圳市帝迈生物技术有限公司 | Blood analysis device |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN203595662U (en) * | 2013-09-30 | 2014-05-14 | 江苏英诺华医疗技术有限公司 | Photoelectric detection device with multiple detection positions |
| CN204101456U (en) * | 2014-06-24 | 2015-01-14 | 江苏英诺华医疗技术有限公司 | A kind of optical detection apparatus of applicable automatic clinical chemistry analyzer |
| US20150138552A1 (en) * | 2012-05-25 | 2015-05-21 | Kowa Company, Ltd. | Apparatus and method for measuring physiologically active substance of biological origin |
| CN108088816A (en) * | 2018-01-23 | 2018-05-29 | 深圳市国赛生物技术有限公司 | Small-sized specific protein analyzer |
| CN108732135A (en) * | 2017-11-20 | 2018-11-02 | 重庆中元汇吉生物技术有限公司 | A kind of blood cell and analysis of protein device |
| CN212364039U (en) * | 2019-12-20 | 2021-01-15 | 深圳市帝迈生物技术有限公司 | Blood cell analyzer |
-
2019
- 2019-12-20 CN CN201911330898.8A patent/CN113008786A/en active Pending
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20150138552A1 (en) * | 2012-05-25 | 2015-05-21 | Kowa Company, Ltd. | Apparatus and method for measuring physiologically active substance of biological origin |
| CN203595662U (en) * | 2013-09-30 | 2014-05-14 | 江苏英诺华医疗技术有限公司 | Photoelectric detection device with multiple detection positions |
| CN204101456U (en) * | 2014-06-24 | 2015-01-14 | 江苏英诺华医疗技术有限公司 | A kind of optical detection apparatus of applicable automatic clinical chemistry analyzer |
| CN108732135A (en) * | 2017-11-20 | 2018-11-02 | 重庆中元汇吉生物技术有限公司 | A kind of blood cell and analysis of protein device |
| CN108088816A (en) * | 2018-01-23 | 2018-05-29 | 深圳市国赛生物技术有限公司 | Small-sized specific protein analyzer |
| CN212364039U (en) * | 2019-12-20 | 2021-01-15 | 深圳市帝迈生物技术有限公司 | Blood cell analyzer |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113777076A (en) * | 2021-08-30 | 2021-12-10 | 四川南格尔生物科技有限公司 | Sensor and method for online real-time concentration monitoring |
| CN113984663A (en) * | 2021-10-28 | 2022-01-28 | 中国人民解放军海军特色医学中心 | Optical detection device and working method thereof |
| CN116106524A (en) * | 2023-04-11 | 2023-05-12 | 深圳市帝迈生物技术有限公司 | Blood analysis device |
| CN116106524B (en) * | 2023-04-11 | 2023-08-25 | 深圳市帝迈生物技术有限公司 | blood analysis device |
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