CN114112805A

CN114112805A - Blood cell analyzer

Info

Publication number: CN114112805A
Application number: CN202010905872.8A
Authority: CN
Inventors: 石汇林; 滕锦; 李晓强
Original assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Current assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Priority date: 2020-09-01
Filing date: 2020-09-01
Publication date: 2022-03-01

Abstract

The invention is suitable for the field of medical equipment, and discloses a blood cell analyzer which comprises a sampling component, an optical channel reaction tank, an optical detection unit, a hemoglobin detection unit, an impedance counting detection sample preparation unit, an impedance counting detection unit, a first reagent supply device, a second reagent supply device, a diluent supply device, a conveying pipeline assembly and a fluid power device, wherein the sampling component, the optical detection unit, the optical channel reaction tank, the hemoglobin detection unit, the impedance counting detection sample preparation unit, the impedance counting detection unit, the first reagent supply device, the second reagent supply device, the diluent supply device and the fluid power device are connected through the conveying pipeline assembly to form a liquid path system, the average gas consumption of the liquid path system is less than or equal to 2.0L/min in one detection period of completing hemoglobin detection, impedance counting detection and optical detection, the miniaturization and low-cost design of the instrument are realized.

Description

Blood cell analyzer

Technical Field

The invention relates to the field of medical equipment, in particular to a blood cell analyzer.

Background

The five-classification blood cell analyzer generally comprises a fluid power device which is mainly used for providing conveying power for samples and reagents to realize measurement. In the prior art, the design schemes of the fluid power device mainly include the following:

1) the fluid power device adopts an external air source scheme capable of providing a large flow: the scheme of adopting the external air source as the power source can provide high-pressure and large-flow power (generally, the no-load flow is more than 10L/min, and the pressure is more than 200 kPa), can drive the air cylinder, the pneumatic pressure stop valve, the pneumatic constant delivery pump and other parts to work, can drive the liquid storage tank to realize the functions of filling, supplying liquid, collecting waste liquid, draining and the like, has high execution speed of the driving part, and can support the high-air-consumption parts to work simultaneously (the average air consumption of the whole machine is more than 5L/min), so that the measuring speed of the machine type is high.

However, the scheme of using an external air source has an independent air source outside the machine, which brings a great increase in cost and volume, and has a matched conditioning element such as a dewatering air filter, a dryer, a precise pressure regulating valve, an overflow valve and the like inside the machine, which brings a very high instrument cost and makes the instrument have a very large volume. Therefore, this solution is generally only applied to high-end machines, which have high requirements on measuring speed.

2) The fluid power device adopts a scheme of a built-in small air source (air pump): the scheme of configuring a small air source in the machine as a power source can provide power with higher pressure and larger flow (generally providing no-load flow more than 2L/min, pressure more than 120 kPa), can drive parts such as a small air cylinder, a pneumatic pressure stop valve, a pneumatic metering pump and the like to work, and can drive and realize functions of filling and supplying liquid, collecting waste liquid, draining liquid and the like of a liquid storage tank. Due to the limited flow capacity of the miniature gas pump, an additional gas storage tank is generally required to support the simultaneous operation of the high gas consumption components. The air pump of the scheme has higher cost, and the volume of the instrument is still larger due to the need of a larger air storage tank or a pressure adjusting element; therefore, this solution is generally applied to medium end machines with high measurement speed requirements.

3) The fluid power device adopts a scheme of an injector: in this solution, all reagent dosing uses syringes, and when there are a large number of reagent types, the corresponding number of syringes is large, and the cost of the syringes is generally high and the size is large, so the solution still does not meet the requirements well in low cost and small design.

In summary, the conventional fluid power device design scheme generally has the problems of high cost and large volume, and is difficult to meet the design requirements of low instrument cost and small volume.

Disclosure of Invention

The invention aims to provide a blood cell analyzer, which aims to solve the technical problems of high air consumption, large volume and high cost of the existing blood cell analyzer.

In order to achieve the purpose, the invention provides the following scheme: a blood cell analyzer, comprising:

the sampling component is used for collecting a sample to be detected;

the optical channel reaction tank is used for providing a reaction site for the sample to be detected and the reagent so as to prepare and obtain optical detection sample liquid;

a first reagent supply device for supplying a reagent to the optical channel reaction cell;

an optical detection unit including a flow chamber having a detection zone for passage of the optical detection sample liquid under entrainment of a diluent, and an optical detection element for detecting the optical detection sample liquid entrained by the diluent passing through the detection zone;

the hemoglobin detection unit is used for providing a reaction field for the sample to be detected and the reagent so as to prepare a hemoglobin detection sample solution and detecting the concentration of hemoglobin in the hemoglobin detection sample solution;

a second reagent supplying means for supplying a reagent to the hemoglobin detecting unit;

the impedance counting detection sample preparation unit is used for providing a reaction field for the sample to be detected and the diluent so as to prepare an impedance counting detection sample;

the impedance counting detection unit is used for carrying out impedance counting detection on the impedance counting detection sample liquid;

a diluent supply device for supplying a diluent;

the fluid power device comprises a positive pressure providing unit, a negative pressure providing unit, a quantitative pump for optical detection and a quantitative pump for hemoglobin detection, wherein the quantitative pump for optical detection is respectively connected with the positive pressure providing unit, the negative pressure providing unit, the optical channel reaction pool and the first reagent providing device, so as to drive a reagent to be conveyed from the first reagent providing device into the optical channel reaction pool under the control of the positive pressure providing unit and the negative pressure providing unit; the quantitative pump for hemoglobin detection is respectively connected with the positive pressure providing unit, the negative pressure providing unit, the hemoglobin detection unit and the second reagent providing device, so as to drive a reagent to be conveyed from the second reagent providing device into the hemoglobin detection unit under the control of the positive pressure providing unit and the negative pressure providing unit;

the conveying pipeline assembly is connected with the hemoglobin detection unit, the impedance counting detection unit, the first reagent supply device, the second reagent supply device, the diluent supply device and the fluid power device to form a liquid path system, and the average gas consumption of the liquid path system is less than or equal to 2.0L/min in one detection period of completing hemoglobin detection, impedance counting detection and optical detection.

According to the blood cell analyzer provided by the invention, the scheme that the power source for driving the reagent to be conveyed is designed to be that the positive pressure providing unit and the negative pressure providing unit are respectively matched with the quantitative pump for optical detection and the quantitative pump for hemoglobin detection is adopted, and the design of large gas consumption components with high gas consumption or high output pressure such as a pneumatic pressure stop valve, a cylinder and the like is cancelled, so that the average gas consumption of the blood cell analyzer is controlled within a preset range in one detection period for completing hemoglobin detection, impedance counting detection and optical detection, the gas consumption requirement of the blood cell analyzer is greatly reduced, the volume and the cost of a pneumatic part of a fluid power device are reduced, and the miniaturization and low-cost design of the blood cell analyzer are favorably realized.

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 view of a fluid path system of a blood cell analyzer according to an embodiment of the present invention;

FIG. 2 is a schematic diagram of the connection of an optical channel reaction cell, an optical detection unit, a first reagent supply device and a fluid dynamic device according to one embodiment of the present invention;

FIG. 3 is a schematic diagram of the connection of the hemoglobin detecting unit, the impedance counting detecting unit, the second reagent supplying device, the fluid power device, the diluent supplying device and the diluent reservoir according to an embodiment of the present invention;

FIG. 4 is a schematic diagram of a positive pressure providing unit according to an embodiment of the present invention;

FIG. 5 is a schematic view of a negative pressure providing unit according to an embodiment of the present invention;

FIG. 6 is a schematic diagram of a positive pressure providing unit according to a second embodiment of the present invention;

FIG. 7 is a schematic view of a negative pressure providing unit according to a second embodiment of the present invention;

FIG. 8 is a schematic diagram of a positive pressure providing unit provided in the third embodiment of the present invention;

FIG. 9 is a schematic view of a negative pressure providing unit according to a third embodiment of the present invention;

FIG. 10 is a schematic view of a liquid path system of a blood cell analyzer according to a fifth embodiment of the present invention;

FIG. 11 is a schematic view of a fluid path system of a blood cell analyzer according to a sixth embodiment of the present invention;

FIG. 12 is a schematic view of a fluid path system of a blood cell analyzer according to a seventh embodiment of the present invention;

FIG. 13 is a schematic view of a fluid path system of a blood cell analyzer according to an eighth embodiment of the present invention;

FIG. 14 is a schematic view of a fluid path system of a blood cell analyzer according to a ninth embodiment of the present invention;

FIG. 15 is a schematic view of a liquid path system of a blood cell analyzer according to a tenth embodiment of the present invention;

fig. 16 is a schematic view of a negative pressure providing unit according to an eleventh embodiment of the present invention;

fig. 17 is a schematic view of a negative pressure providing unit according to a twelfth embodiment of the present invention;

fig. 18 is a schematic view of a pressure control apparatus according to a thirteenth embodiment of the present invention;

fig. 19 is a schematic view of a pressure control device according to a fourteenth embodiment of the present invention.

The reference numbers illustrate:

100. an optical channel reaction cell; 110. a first reaction tank; 120. a second reaction tank; 200. an optical detection unit; 210. a flow chamber; a. a first inlet; b. a second inlet; c. a first outlet; 220. an optical detection element; 300. a hemoglobin detection unit; 400. an impedance count detection unit; d. a second outlet; 500. a first reagent supply device; 510. a first reagent supply unit; 520. a second reagent supply unit; 530. a third reagent supply unit; 540. a fourth reagent supply unit; 600. a second reagent supply device; 610. a fifth reagent supply unit; 700. a delivery line assembly; 710. a first drain line; 711. a first drain control valve; 720. a second drain line; 730. a first delivery line; 731. a first control valve; 740. a second delivery line; 741. a second control valve; 750. a diluent delivery line; 751. a third control valve; 752. a fourth control valve; 760. a third delivery line; 761. a fifth control valve; 770. an optical sample preparation line; 771. a first sample preparation pipeline; 772. a second sample preparation line; 780. a first connecting line; 781. a sixth control valve; 790. a second connecting line; 791. a seventh control valve; 7100. a third connecting pipeline; 7101. an eighth control valve; 7110. an eleventh control valve; 7120. an impedance counting sample preparation pipeline; 7130. a fifth delivery line; 7131. a ninth control valve; 7140. a sixth delivery line; 7141. a tenth control valve; 7150. a third drain line; 7151. a third drain control valve; 7160. a fourth drain line; 7170. a fourth delivery line; 7171. a twelfth control valve; 800. a fluid power device; 810. a positive pressure supply unit; 811. a first air pump; 812. a first pressure sensor; 813. a first positive pressure control valve; 814. a first voltage stabilization member; 815. a positive pressure output pipeline; 820. a negative pressure providing unit; 821. a second air pump; 822. a second pressure sensor; 823. a first negative pressure control valve; 824. a second voltage stabilization member; 825. a negative pressure output pipeline; 826. a waste liquid tank; 827. a waste liquid barrel; 828. a negative pressure power source; 829. a first constant pressure control valve; 8210. a first external pipeline; 8211. a first atmospheric pressure pipeline; 8212. a first negative pressure line; 8213. a second negative pressure control valve; 830. a quantitative pump for optical detection; 831. a first fixed displacement pump; 832. a second fixed displacement pump; 833. a third fixed displacement pump; 834. a fourth fixed displacement pump; 840. a hemoglobin detection measuring pump; 850. a first gas path assembly; 851. a first air valve; 852. a second air valve; 853. a third air valve; 854. a fourth air valve; 860. a second gas path assembly; 861. a fifth air valve; 870. a third pressure sensor; 880. a third gas path assembly; 881. a sixth air valve; 890. a first syringe; 8100. a second syringe; 8120. a fourth gas path assembly; 8121. a seventh air valve; 8130. a sixth fixed displacement pump; 8140. a fifth gas path component; 8141. an eighth air valve; 8150. a seventh fixed displacement pump; 8160. a sixth gas path component; 8161. a ninth air valve; 8170. an eighth fixed displacement pump; 8180. a seventh gas path component; 8181. a tenth air valve; 900. a diluent supply device; 1000. a diluent reservoir; 1100. a pressure control device; 1103. a second positive pressure control valve; 1104. a third negative pressure control valve; 1105. a drain valve; 1106. a second atmospheric control valve; 1107. a second external pipeline; 1108. a second atmospheric pressure pipeline; 1109. a second negative pressure line; 1110. a positive pressure pipeline; 1200. a sampling component.

The implementation, functional features and advantages of the objects of the present invention will be further explained with reference to the accompanying drawings.

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 related to "first", "second", etc. in the present invention are 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 5, the blood cell analyzer according to the first embodiment of the present invention includes an optical channel reaction cell 100, an optical detection unit 200, a hemoglobin detection unit 300, an impedance count detection unit 400, a first reagent supply device 500, a second reagent supply device 600, a conveying pipeline assembly 700, a fluid power device 800, a diluent supply device 900, a diluent reservoir 1000, a sampling component 1200, and an impedance count detection sample preparation unit (in this embodiment, the hemoglobin detection unit 300 is also used as an impedance count detection sample preparation unit, that is, the impedance count detection sample preparation unit and the hemoglobin detection unit 300 are integrally disposed). The sampling part 1200, the optical detection unit 200, the optical channel reaction cell 100, the impedance counting detection sample preparation unit, the hemoglobin detection unit 300, the impedance counting detection unit 400, the first reagent supply device 500, the second reagent supply device 600, the diluent supply device 900 and the fluid dynamic device 800 are connected through the conveying pipeline assembly 700 to form a fluid path system, and one detection cycle of the fluid path system comprises impedance counting detection, hemoglobin detection and optical detection. The average gas consumption of the liquid path system is less than or equal to 2.0L/min in one detection period of finishing hemoglobin detection, impedance counting detection and optical detection.

The blood cell analyzer of this embodiment provides a low-cost and miniaturized miniature gas circuit system design scheme, and the design that the gas circuit air consumption is great or need output pressure very high (cylinder and pneumatic pressure stop valve operating pressure is high) such as pneumatic pressure stop valve, cylinder, diluent liquid storage tank 1000 positive and negative pressure used alternately has been cancelled in this scheme, and the pneumatic drive scheme of constant delivery pump is considered in the key point to the demand reduction to pneumatic constant delivery pump, the blood cell analyzer that this embodiment provided, main gas consumption part is the constant delivery pump.

Preferably, the average gas consumption of the liquid path system in one detection period of completing hemoglobin detection, impedance counting detection and optical detection is less than or equal to 1.0L/min, namely: in the embodiment, the blood cell analyzer optimizes the gas path system (specifically, but not limited to, the optimization modes include, for example, reducing the volumes of the fixed displacement pump and the pipeline connected with the fixed displacement pump, arranging a gas valve for controlling the fixed displacement pump close to the fixed displacement pump, replacing a gas dynamic pressure cut-off valve with an electromagnetic valve, and replacing a scheme of alternately using a positive pressure power source and a negative pressure power source with a scheme of driving the diluent liquid storage tank 1000 to fill and supply liquid by using an injector and a positive pressure power source), so that the average gas consumption of the blood cell analyzer can reach less than or equal to 1.0L/min in a detection period.

As a preferred implementation scheme of the embodiment, the average gas consumption of the liquid path system is less than or equal to 0.5L/min in one detection period of completing hemoglobin detection, impedance counting detection and optical detection. That is, in this embodiment, the average gas consumption of the blood cell analyzer in a detection period may be less than or equal to 0.5L/min by further optimizing the gas path system (specifically, but not limited to, the following modes, for example, reducing the volumes of the fixed displacement pump and the pipeline connected thereto, disposing a gas valve for controlling the fixed displacement pump close to the fixed displacement pump, replacing the gas dynamic pressure cut-off valve with an electromagnetic valve, and replacing the scheme of alternately using the positive pressure power source and the negative pressure power source with the scheme of driving the diluent reservoir 1000 to fill and supply liquid with the injector and the positive pressure power source).

The optical channel reaction cell 100 is used for providing a reaction field for a sample and a reagent to be detected so as to prepare an optical detection sample solution. In this embodiment, the sample to be detected is a blood sample, and the optical detection sample solution includes a reticulocyte detection sample solution and a leukocyte classification detection sample solution. Of course, as alternative embodiments, the optical detection of the sample liquid is not limited thereto, for example: the optical detection sample solution can also only comprise one of reticulocyte detection sample solution and leukocyte classification detection sample solution, or the optical detection sample solution can also comprise other sample solutions which are not the reticulocyte detection sample solution and the leukocyte classification detection sample solution, and in specific application, the optical detection sample solution can be correspondingly designed according to the requirements of actual detection items.

The optical channel reaction cell 100 comprises a first reaction cell 110 and a second reaction cell 120, the first reaction cell 110 and the second reaction cell 120 are two independent reaction cells, and the first reaction cell 110 is used for providing reaction sites for a sample to be detected and a reagent to prepare a reticulocyte detection sample solution; the second reaction cell 120 is used for providing a reaction field for the sample and the reagent to be detected so as to prepare and obtain a sample solution for classifying and detecting leukocytes. In the embodiment, the reticulocyte detection sample solution and the leukocyte classification detection sample solution are respectively prepared in two mutually independent reaction tanks, so that the problem of cross contamination caused by reagent residues in the process of sharing the reaction tanks can be avoided; on the other hand, the leukocyte classification detection sample liquid and the reticulocyte detection sample liquid can be prepared simultaneously, and the detection efficiency is improved. Of course, as an alternative embodiment, the reticulocyte assay sample solution and the leukocyte differential assay sample solution can be incubated in the same reaction chamber, i.e., the optical channel reaction chamber 100 includes only one reaction chamber (e.g., the first reaction chamber 110), and in consideration of the problem of residual cross-contamination of the fluorescence reagent between the optical channels, in this alternative embodiment, the leukocyte differential assay does not use a fluorescence platform (e.g., a chemical staining platform, a hemolytic agent, but no fluorescence staining), and the reticulocyte assay uses a fluorescence platform, so that the reaction chamber used for both the leukocyte differential assay and the reticulocyte assay has no residual cross-contamination of the fluorescence reagent.

The first reagent supplying means 500 is used to supply the optical channel reaction cell 100 with a reagent. In this embodiment, the first reagent supplying apparatus 500 includes a first reagent supplying unit 510, a second reagent supplying unit 520, a third reagent supplying unit 530, and a fourth reagent supplying unit 540.

The first reagent supplying unit 510 and the third reagent supplying unit 530 are respectively connected to the first reaction cell 110 to respectively supply the third reagent and the fifth reagent to the first reaction cell 110. As a preferred embodiment of the present embodiment, one of the third reagent and the fifth reagent is a fluorescent reagent, and the other is a diluting reagent, the fluorescent reagent is used for enabling the optical detection element 220 to obtain a fluorescent signal during the reticulocyte detection, and the diluting reagent is mainly used for diluting the sample to be detected; of course, in a specific application, as an alternative embodiment, the fluorescence reagent and the dilution reagent may be replaced by a reagent (for convenience of description, this embodiment is referred to as a first reagent) having both fluorescence and dilution functions, and in this alternative embodiment, only one reagent providing unit is connected to the first reaction chamber 110, for example, the first reagent providing unit 510, and the first reagent providing unit 510 is connected to the first reaction chamber 110 for providing the first reagent to the first reaction chamber 110.

The second reagent supplying unit 520 and the fourth reagent supplying unit 540 are connected to the second reaction cell 120, respectively, to supply the fourth reagent and the sixth reagent to the second reaction cell 120, respectively. One of the second reagent and the fourth reagent is a hemolytic agent capable of lysing erythrocytes in the sample to be tested and capable of distinguishing different leukocyte types, and the other reagent is a reagent capable of staining leukocytes. As a preferred embodiment of this embodiment, one of the second reagent and the fourth reagent is a hemolytic agent, and the other is a fluorescent staining reagent; of course, in a specific application, the hemolytic agent and the fluorescence staining reagent may be replaced by a reagent (for convenience of description, this embodiment is referred to as a second reagent) having both the erythrocyte lysis function and the fluorescence staining function, and in this alternative embodiment, only one reagent providing unit is connected to the second reaction chamber 120, for example, the second reagent providing unit 520, and the second reagent providing unit 520 is connected to the second reaction chamber 120 for providing the second reagent to the second reaction chamber 110; alternatively, the fluorescent staining reagent may be replaced with a chemical staining reagent.

The optical detection unit 200 includes a flow cell 210 and an optical detection element 220, the flow cell 210 having a detection region, a first inlet a, a second inlet b, and a first outlet c, the first inlet a, the second inlet b, and the first outlet c communicating with the detection region, respectively. The detection area is used for allowing the optical detection sample liquid to pass through under the wrapping of the diluent.

The optical detection element 220 is used for detecting the optical detection sample liquid passing through the detection area and being entrained by the diluent. In the reticulocyte detection, the optical detection element 220 may perform reticulocyte detection on the reticulocyte detection sample solution wrapped by the sheath solution (in this embodiment, the sheath solution is formed by using a diluent solution) and passing through the detection region, and obtain a reticulocyte detection result according to the scattered light signal and the fluorescence signal; in the classifying detection of leukocytes, the optical detection element 220 can perform classifying detection of leukocytes on the leukocyte classifying detection sample solution passing through the detection region and being wrapped by the sheath solution. The optical detection element 220 may include a light source, a forward scattered light signal collection means disposed on the optical axis, a side scattered light signal collection means disposed on the side of the optical axis, and a fluorescent signal collection means.

The impedance counting detection unit 400 is used for performing impedance counting detection on the impedance counting detection sample liquid. Impedance counting detection may include red blood cell number detection and/or platelet count detection. The impedance counting detection sample can be prepared by reacting a sample to be detected with a diluent.

The hemoglobin detecting unit 300 is used for providing a reaction field for the sample and the reagent to be detected, so as to prepare a hemoglobin detecting sample solution, and for detecting the concentration of hemoglobin in the hemoglobin detecting sample solution. In this embodiment, the hemoglobin detecting unit 300 is also used as an impedance counting detecting sample preparing unit, that is, the hemoglobin detecting unit 300 is also used to provide a reaction field for the sample to be detected and the diluent so as to prepare an impedance counting detecting sample solution. During specific operation, a sample to be detected and diluent can be added into the hemoglobin detection unit 300 to prepare an impedance counting detection sample, and then part of the impedance counting detection sample is pumped away; then, the reagent is added to the hemoglobin detecting unit 300 to prepare a hemoglobin detection sample. Of course, in alternative embodiments, the impedance counting test sample fluid does not have to be generated in the hemoglobin test cell 300, for example: the impedance counting detection sample liquid can also be generated in the impedance counting detection unit 400, that is, the impedance counting detection sample preparation unit and the impedance counting detection unit 400 are integrally arranged; alternatively, the impedance count detection sample preparation unit may be provided independently of the hemoglobin detection unit 300 and the impedance count detection unit 400.

The second reagent supplying means 600 is for supplying the reagent to the hemoglobin detecting unit 300. In this embodiment, the second reagent supplying apparatus 600 includes a fifth reagent supplying unit 610, and the fifth reagent supplying unit 610 is connected to the hemoglobin detecting unit 300 to supply a seventh reagent to the hemoglobin detecting unit 300. The seventh reagent is, for example, a hemolytic agent capable of lysing red blood cells in the blood sample, releasing hemoglobin in the red blood cells, and converting the hemoglobin into methemoglobin. In an alternative embodiment, the reagent used in the differential leukocyte measurement and the reagent used in the hemoglobin measurement may also be the same hemolytic agent, i.e., the second reagent providing unit 520 and the fifth reagent providing unit 610 are the same reagent providing unit.

The fluid dynamic device 800 includes a positive pressure providing unit 810, a negative pressure providing unit 820, a quantitative pump 830 for optical detection, a quantitative pump 840 for hemoglobin detection, a first air path component 850, and a second air path component 860, wherein the positive pressure providing unit 810 can output a positive pressure value, and the negative pressure providing unit 820 can output a negative pressure value. The optical detection quantitative pump 830 is connected to the positive pressure supply unit 810 and the negative pressure supply unit 820 through the first air channel block 850, the hemoglobin detection quantitative pump 840 is connected to the positive pressure supply unit 810 and the negative pressure supply unit 820 through the second air channel block 860, and the total volume of the optical detection quantitative pump 830, the first air channel block 850, the hemoglobin detection quantitative pump 840, and the second air channel block 860 is 30mL or less.

Preferably, the positive pressure output by the positive pressure providing unit 810 is less than or equal to 120kpa, that is, in this embodiment, the positive pressure less than or equal to 120kpa can meet the positive pressure working requirement of the gas path system, so that the miniaturization design of the gas path system is facilitated.

Preferably, the positive pressure output by the positive pressure providing unit 810 is less than or equal to 90kpa, that is, in the further optimization scheme of this embodiment, the positive pressure less than or equal to 90kpa can meet the positive pressure working requirement of the gas path system, so that the further miniaturization design of the gas path system is facilitated.

As a preferred embodiment of this embodiment, the positive pressure providing unit 810 outputs a positive pressure less than or equal to 50 kpa; the negative pressure providing unit 820 outputs negative pressure greater than or equal to-30 kpa, that is, in the preferred embodiment of the present embodiment, the positive pressure is less than or equal to 50kpa, and the negative pressure is greater than or equal to-30 kpa, so as to meet the positive pressure working requirement of the air path system, which is favorable for further miniaturization design of the air path system.

The quantitative pump 830 for optical detection is connected to the optical channel reaction cell 100 and the first reagent supplying apparatus 500 in addition to the positive pressure supplying unit 810 and the negative pressure supplying unit 820, and is used for driving the reagent to be transferred from the first reagent supplying apparatus 500 into the optical channel reaction cell 100 under the control of the positive pressure supplying unit 810 and the negative pressure supplying unit 820.

In this embodiment, since the first reagent supplying apparatus 500 includes four reagent supplying units (the first reagent supplying unit 510, the second reagent supplying unit 520, the third reagent supplying unit 530, and the fourth reagent supplying unit 540), the optical detection quantitative pump 830 includes four quantitative pumps, that is, the optical detection quantitative pump 830 includes the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, and the fourth quantitative pump 834.

The first quantitative pump 831 is connected to the positive pressure output pipeline 815, the negative pressure output pipeline 825, the first reaction cell 110, and the first reagent supply unit 510, respectively, for driving the third reagent to be supplied from the first reagent supply unit 510 into the first reaction cell 110, and the third quantitative pump 833 is connected to the positive pressure output pipeline 815, the negative pressure output pipeline 825, the first reaction cell 110, and the third reagent supply unit 530, respectively, for driving the fifth reagent to be supplied from the third reagent supply unit 530 into the first reaction cell 110. In this embodiment, two metering pumps are connected to the first reaction tank 110; of course, in a specific application, if the fluorescence reagent and the dilution reagent (i.e., the third reagent and the fifth reagent) for reacting the sample for forming a reticulocyte detection are replaced by a reagent (i.e., the first reagent) having both fluorescence and dilution functions, only one dosing pump corresponding to the reagent supply unit connected to the first reaction cell 110 is required, for example, only the first dosing pump 831 needs to be connected to the first reaction cell 110, and the third dosing pump 833 does not need to be provided.

The second quantitative pump 832 is respectively connected with the positive pressure output pipeline 815, the negative pressure output pipeline 825, the second reaction cell 120 and the second reagent providing unit 520 for driving the fourth reagent to be delivered from the second reagent providing unit 520 into the second reaction cell 120. The fourth quantitative pump 834 is connected to the positive pressure output line 815, the negative pressure output line 825, the second reaction cell 120, and the fourth reagent supplying unit 540, respectively, for driving the sixth reagent to be transferred from the fourth reagent supplying unit 540 into the second reaction cell 120. In this embodiment, two metering pumps are connected to the second reaction tank 120; of course, in a specific application, if the hemolytic agent and the staining reagent (i.e., the fourth reagent and the sixth reagent) for the classification test sample for generating leukocytes are replaced by a reagent (i.e., the second reagent) having both hemolytic action and staining action, only one quantitative pump corresponding to the reagent supply unit connected to the second reaction cell 120 is required, for example, only the second quantitative pump 832 connected to the second reaction cell 120 is required, and the fourth quantitative pump 834 is not required.

The first air path assembly 850 includes a first air valve 851, a second air valve 852, a third air valve 853, and a fourth air valve 854, and the first quantitative pump 831 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 through the first air valve 851, respectively. The first air valve 851 is used to control the conduction state of the first constant volume pump 831 with the positive pressure providing unit 810 and the negative pressure providing unit 820. In a specific application, when the first constant delivery pump 831 is driven to work by positive pressure, the first air valve 851 is opened, and the first air valve 851 is regulated to switch to a state that the first constant delivery pump 831 is conducted with the positive pressure providing unit 810; when the first constant delivery pump 831 needs to be driven by negative pressure to work, the first air valve 851 is opened, and the first air valve 851 is regulated to switch to a state that the first constant delivery pump 831 is conducted with the negative pressure providing unit 820.

The second constant delivery pump 832 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 through the second air valve 852, respectively. The second air valve 852 is used for controlling the conduction state of the second constant delivery pump 832 and the positive pressure providing unit 810 and the negative pressure providing unit 820, and the control principle thereof can refer to the control principle that the first air valve 851 controls the conduction of the first constant delivery pump 831 and the positive pressure providing unit 810 and the negative pressure providing unit 820, respectively, and will not be described in detail herein.

The third quantitative pump 833 is connected to the positive pressure supply unit 810 and the negative pressure supply unit 820 through the third air valve 853, respectively. The third air valve 853 is used to control the conduction state of the third quantitative pump 833 with the positive pressure providing unit 810 and the negative pressure providing unit 820, and the control principle thereof can refer to the control principle that the first air valve 851 controls the conduction of the first quantitative pump 831 with the positive pressure providing unit 810 and the negative pressure providing unit 820, which will not be described in detail herein.

The fourth quantitative pump 834 is connected to the positive pressure supply unit 810 and the negative pressure supply unit 820 through a fourth air valve 854, respectively. The fourth air valve 854 is used for controlling the conduction state of the fourth quantitative pump 834 and the positive pressure providing unit 810 and the negative pressure providing unit 820, and the control principle thereof can refer to the control principle that the first air valve 851 controls the conduction of the first quantitative pump 831 and the positive pressure providing unit 810 and the negative pressure providing unit 820, which will not be described in detail herein.

The hemoglobin detection quantitative pump 840 is connected to the hemoglobin detection unit 300 and the second reagent supply device 600 in addition to the positive pressure supply unit 810 and the negative pressure supply unit 820, and drives the reagent to be transferred from the second reagent supply device 600 into the hemoglobin detection unit 300 under the control of the positive pressure supply unit 810 and the negative pressure supply unit 820.

The second air channel assembly 860 includes a fifth air valve 861, and the hemoglobin detecting quantitative pump 840 is connected to the positive pressure supply unit 810 and the negative pressure supply unit 820 through the fifth air valve 861, respectively. The fifth air valve 861 is used for controlling the conduction state of the fifth constant displacement pump and the positive pressure providing unit 810 and the negative pressure providing unit 820, and the control principle thereof can refer to the control principle that the first air valve 851 controls the conduction of the first constant displacement pump 831 with the positive pressure providing unit 810 and the negative pressure providing unit 820, respectively, and therefore, the detailed description thereof is omitted.

In this embodiment, the positive pressure providing unit 810 and the negative pressure providing unit 820 are all one, and the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834, and the hemoglobin detection quantitative pump 840 are connected to the same positive pressure providing unit 810 and the same negative pressure providing unit 820, respectively.

Preferably, the total volume of the quantitative pump for optical detection 830, the first air channel assembly 850, the quantitative pump for hemoglobin detection 840 and the second air channel assembly 860 is less than or equal to 20mL, which is favorable for further reducing the average air consumption of the blood cell analyzer in one detection period.

More preferably, the total volume of the quantitative pump for optical detection 830, the first air channel assembly 850, the quantitative pump for hemoglobin detection 840 and the second air channel assembly 860 is less than or equal to 15mL, which is favorable for further reducing the average air consumption of the blood cell analyzer in one detection period.

As a preferred embodiment of this embodiment, the total volume of the quantitative pump for optical detection 830, the first air channel assembly 850, the quantitative pump for hemoglobin detection 840 and the second air channel assembly 860 is less than or equal to 10mL, which is favorable for further reducing the average air consumption of the blood cell analyzer in one detection period.

In the preferred embodiment of this embodiment, the volumes of the optical detection quantitative pump 830 and the hemoglobin detection quantitative pump 840 and the common gas path pipeline (the pipeline between the quantitative pump and the gas valve) connected to them are small, and the total volume is less than 10 mL. In terms of layout, in the present embodiment, it is preferable that control gas valves for controlling the optical detection dosing pumps 830 and the hemoglobin detection dosing pumps 840 are respectively provided close to the dosing pumps, so that the gas consumption of the common line when the positive pressure and the negative pressure are switched can be further reduced.

Preferably, the length of the connecting line between each gas valve and the dosing pump is less than or equal to 20cm, namely: the connecting pipeline between the first air valve 851 and the first quantitative pump 831 is less than or equal to 20 cm; the connecting pipeline between the second air valve 852 and the second dosing pump 832 is less than or equal to 20 cm; a connecting pipeline between the third air valve 853 and the third fixed displacement pump 833 is less than or equal to 20 cm; a connecting pipeline between the fourth air valve 854 and the fourth quantitative pump 834 is less than or equal to 20 cm; the connecting pipeline between the fifth air valve 861 and the hemoglobin detection quantitative pump 840 is less than or equal to 20cm, so that the control air valves of each optical detection quantitative pump 830 and the hemoglobin detection quantitative pump 840 are respectively arranged close to each quantitative pump, and the air consumption of a common pipeline during positive and negative pressure switching is reduced, and further, the working air consumption of the quantitative pump can be below 0.3L/min in one detection period of completing hemoglobin detection, impedance counting detection and optical detection of a liquid path system.

The positive pressure providing unit 810 includes a first air pump 811, a first pressure sensor 812, a first positive pressure control valve 813, a first pressure stabilizing member 814, and a positive pressure output pipeline 815, wherein one end of the positive pressure output pipeline 815 is connected to the optical detection quantitative pump 830 and the hemoglobin detection quantitative pump 840, respectively, the other end of the positive pressure output pipeline 815 is connected to the first air pump 811 through the first positive pressure control valve 813, and the first pressure sensor 812 is disposed between the first positive pressure control valve 813 and the positive pressure output pipeline 815 for detecting the air pressure in the positive pressure output pipeline 815. In this embodiment, the positive pressure output pipeline 815 is connected to the first dosing pump 831, the second dosing pump 832, the third dosing pump 833, the fourth dosing pump 834 and the hemoglobin detection dosing pump 840 through the first air valve 851, the second air valve 852, the third air valve 853, the fourth dosing pump 854 and the fifth air valve 861, respectively, and the positive pressure output pipeline 815, the first dosing pump 831, the second dosing pump 832, the third dosing pump 833, the fourth dosing pump 834 and the hemoglobin detection dosing pump 840 can be controlled to be connected to and disconnected from each other by controlling the first air valve 851, the second air valve 852, the third air valve 853, the fourth air valve 854 and the fifth air valve 861.

The first pressure-stabilizing unit 814 is connected between the positive pressure output pipe 815 and the first positive pressure control valve 813, and the first pressure sensor 812 is connected between the first pressure-stabilizing unit 814 and the first positive pressure control valve 813. The first pressure stabilizing unit 814 is mainly used to act as a pressure stabilizing function when the instantaneous pushed liquid consumption of the dosing pump (for example, the first dosing pump 831, the second dosing pump 832, the third dosing pump 833, the fourth dosing pump 834, or the hemoglobin detection dosing pump 840) is high.

In this embodiment, the first pressure-stabilizing component 814 is a positive pressure air chamber. In a particular application, a positive pressure (e.g., 50kPa, etc.) may be established inside the positive pressure gas chamber by the first gas pump 811, depending on system requirements.

Preferably, the volume of the positive pressure air chamber (the first pressure stabilizing part 814) is between 80mL and 200mL, so that the positive pressure output requirement of the air path system of the blood cell analyzer can be met, and the volume of the blood cell analyzer can be reduced. In the embodiment, the positive pressure air chamber with the volume of 80-200 mL is adopted, so that the positive pressure output requirement of the air path system of the blood cell analyzer can be met, and therefore, the air consumption and the positive pressure of the blood cell analyzer provided by the embodiment are very small.

More preferably, the positive pressure gas chamber has a volume of between 100mL and 130 mL. Therefore, the size of the positive pressure air chamber can be further optimized on the premise that the positive pressure output meets the air consumption requirement and is stable and reliable.

As a preferred embodiment of this embodiment, the volume of the positive pressure air chamber is about 120 mL.

Preferably, the first air pump 811 is a micro air pump, and the no-load flow of the first air pump 811 is less than or equal to 4L/min, so that the positive pressure output requirement of the air path system of the blood cell analyzer can be met, and the volume and the cost of the blood cell analyzer can be reduced. In the embodiment, the first air pump 811 with the no-load flow rate less than or equal to 4L/min is adopted, so that the positive pressure output requirement of the air path system of the blood cell analyzer can be met, and the air consumption and the positive pressure of the blood cell analyzer provided by the embodiment are very small.

As a preferred embodiment of this embodiment, the no-load flow rate of the first air pump 811 is 3L/min to 4L/min; alternatively, as another preferred embodiment of this embodiment, the idle flow rate of the first air pump 811 is less than or equal to 2L/min.

Preferably, the maximum length of the first air pump 811 is less than or equal to 80mm, so that the volume and cost of the first air pump 811 can be reduced on the premise of ensuring that the negative pressure output meets the air consumption requirement and the negative pressure output is stable and reliable.

As a preferred embodiment of this embodiment, the external contour of the first air pump 811 is substantially cylindrical, the outer diameter of the first air pump 811 is less than or equal to 30mm, and the length of the first air pump 811 is less than or equal to 80 mm; as another preferred embodiment of this embodiment, the outer contour of the first air pump 811 is substantially rectangular, the width and height of the first air pump 811 are both less than or equal to 30mm, and the length of the first air pump 811 is less than or equal to 80 mm. Of course, in a specific application, the shape of the first air pump 811 is not limited thereto, and it is only necessary to ensure that the maximum length thereof is less than or equal to 80 mm.

The negative pressure supply unit 820 includes a second air pump 821, a second pressure sensor 822, a first negative pressure control valve 823, a second pressure stabilizing member 824, and a negative pressure output pipeline 825, one end of the negative pressure output pipeline 825 is connected to the optical detection quantitative pump 830 and the hemoglobin detection quantitative pump 840, the other end of the negative pressure output pipeline 825 is connected to the second air pump 821 through the first negative pressure control valve 823, and the second pressure sensor 822 is disposed between the first negative pressure control valve 823 and the negative pressure output pipeline 825 for detecting the gas pressure in the negative pressure output pipeline 825. In this embodiment, the negative pressure output pipeline 825 is connected to the first dosing pump 831, the second dosing pump 832, the third dosing pump 833, the fourth dosing pump 834 and the hemoglobin detection dosing pump 840 through the first air valve 851, the second air valve 852, the third air valve 853, the fourth air valve 854 and the fifth air valve 861, respectively, and the on/off of the pipeline connected between the negative pressure output pipeline 825 and the first dosing pump 831, the second dosing pump 832, the third dosing pump 833, the fourth dosing pump 834 and the hemoglobin detection dosing pump 840 can be controlled by controlling the first air valve 851, the second air valve 852, the third air valve 853, the fourth air valve 854 and the fifth air valve 861, respectively.

The second pressure stabilizing member 824 is connected between the negative pressure output pipe 825 and the first negative pressure control valve 823, and the second pressure sensor 822 is connected between the second pressure stabilizing member 824 and the first negative pressure control valve 823. The second pressure stabilizing unit 824 is mainly used to stabilize the pressure when the instantaneous gas consumption of the measurement pump (for example, the first measurement pump 831, the second measurement pump 832, the third measurement pump 833, the fourth measurement pump 834, or the hemoglobin detection measurement pump 840) is high.

In this embodiment, the second pressure stabilizing member 824 is a negative pressure chamber. In a specific application, a negative pressure (e.g., -40kPa, etc.) can be established inside the negative pressure air chamber by the second air pump 821 according to the system requirements.

Preferably, the volume of the negative pressure air chamber (the second pressure stabilizing member 824) is between 80mL and 200mL, so that the negative pressure output requirement of the air path system of the blood cell analyzer can be met, and the volume of the blood cell analyzer can be reduced. In the embodiment, the negative pressure air chamber with the volume of 80-200 mL is adopted, so that the negative pressure output requirement of the air path system of the blood cell analyzer can be met, and therefore, the air consumption and the negative pressure of the blood cell analyzer provided by the embodiment are very small.

More preferably, the volume of the negative pressure air chamber is between 100mL and 130 mL. Therefore, on the premise that the negative pressure output is guaranteed to meet the air consumption requirement and the negative pressure output is stable and reliable, the size of the negative pressure air chamber can be further optimized.

As a preferred embodiment of this embodiment, the volume of the negative pressure air chamber is about 120 mL.

Preferably, the second air pump 821 is a micro air pump, and the no-load flow of the second air pump 821 is less than or equal to 4L/min, so that the negative pressure output requirement of the air path system of the blood cell analyzer can be met, and the volume and the cost of the blood cell analyzer can be reduced. In this embodiment, the second air pump 821 with the idle flow rate less than or equal to 4L/min is adopted, so that the negative pressure output requirement of the air path system of the blood cell analyzer can be met, and thus, the air consumption and the positive pressure of the blood cell analyzer provided by this embodiment are very small.

As a preferred embodiment of this embodiment, the no-load flow rate of the second air pump 821 is 3L/min to 4L/min; alternatively, as another preferred embodiment of this embodiment, the idle flow rate of the second air pump 821 is less than or equal to 2L/min.

Preferably, the maximum length of the second air pump 821 is less than or equal to 80mm, so that the volume and cost of the second air pump 821 can be reduced on the premise of ensuring that the negative pressure output meets the air consumption requirement and the negative pressure output is stable and reliable.

As a preferred embodiment of this embodiment, the external contour of the second air pump 821 is substantially cylindrical, the external diameter of the second air pump 821 is less than or equal to 30mm, and the length of the second air pump 821 is less than or equal to 80 mm; as another preferred embodiment of this embodiment, the outer contour of the second air pump 821 is substantially rectangular, the width and height of the second air pump 821 are both less than or equal to 30mm, and the length of the second air pump 821 is less than or equal to 80 mm. Of course, in a specific application, the shape of the second air pump 821 is not limited thereto, and it is only required to ensure that the maximum length thereof is less than or equal to 80 mm.

In this embodiment, the impedance counting detection unit 400 includes a sheath flow impedance front cell, a sheath flow impedance rear cell, a gem hole for communicating the sheath flow impedance front cell with the sheath flow impedance rear cell, and a second outlet d communicated with the sheath flow impedance rear cell, the negative pressure air chamber is further time-division multiplexed for collecting the waste liquid at the first outlet c of the optical channel flow chamber 210 and the waste liquid at the second outlet d of the sheath flow impedance rear cell, the negative pressure air chamber is also used as a waste liquid pool, the conveying pipeline assembly 700 includes a first liquid discharge pipeline 710 connected between the flow chamber 210 and the negative pressure air chamber, and a second liquid discharge pipeline 720 connected between the impedance counting detection unit 400 and the negative pressure air chamber. The first drain line 710 is provided with a first drain control valve 711. Of course, as an alternative embodiment, only one of the first outlet c of the flow cell 210 and the second outlet d of the impedance count detecting unit 400 may be connected to the negative pressure air chamber, and the other may be connected to a waste liquid collecting device independent of the negative pressure air chamber.

In a specific application, when the quantitative pump (for example, the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834, or the quantitative pump 840 for hemoglobin detection) is driven to operate, the negative pressure air chamber maintains a certain negative pressure; and when waste liquid is collected, the negative pressure air chamber keeps normal pressure and is communicated with the atmosphere.

In this embodiment, the conveying pipeline assembly 700 further includes a first conveying pipeline 730 and a second conveying pipeline 740, the fluid power device 800 further includes a third pressure sensor 870 and a third air channel assembly 880, the first conveying pipeline 730 is connected between the diluent reservoir 1000 and the impedance counting detection unit 400, the second conveying pipeline 740 is connected between the diluent reservoir 1000 and the diluent providing device 900, the positive pressure providing unit 810 is connected to the diluent reservoir 1000 through the third air channel assembly 880 for driving the diluent to be conveyed from the diluent reservoir 1000 to the impedance counting detection unit 400, so that the impedance counting detection sample flows in the impedance counting detection unit 400 under entrainment of the diluent, and the third pressure sensor 870 is connected to the diluent reservoir 1000 for detecting the air pressure in the diluent reservoir 1000. The third air path assembly 880 includes a sixth air valve 881, a first control valve 731 is disposed on the first conveying pipeline 730, and a second control valve 741 is disposed on the second conveying pipeline 740.

The diluent reservoir 1000 is normally at a positive pressure, and when the diluent reservoir 1000 consumes a certain amount of diluent, it is necessary to build up a pressure in the diluent reservoir 1000, and since the amount of the diluent consumed by the diluent reservoir 1000 is less than 10mL, the gas consumption is extremely low, and is less than 0.1L/min.

The fluid dynamic device 800 further comprises a first syringe 890, the transfer line assembly 700 further comprises a diluent transfer line 750 connected between the first syringe 890 and the flow chamber 210, the diluent providing device 900 and the second transfer line 740 are respectively connected to the diluent transfer line 750, the first syringe 890 is configured to drive the diluent to be transferred from the diluent transfer line 750 to the flow chamber 210 so as to allow the optical detection sample solution to pass through the detection area under the entrainment of the diluent, and the first syringe 890 is configured to drive the diluent to be transferred from the diluent providing device 900 to the diluent reservoir 1000 through the second transfer line 740. The diluent feed line 750 is provided with a third control valve 751 and a fourth control valve 752, the third control valve 751 is provided between the first syringe 890 and the fourth control valve 752, and the diluent supply unit 900 is connected to the third control valve 751. In this embodiment, the first syringe 890 is used for filling the diluent reservoir 1000 to provide power, the positive pressure providing unit 810 is used for supplying liquid to the impedance counting detection unit 400 by the diluent reservoir 1000, and compared with the scheme of alternately switching and driving the diluent reservoir 1000 to fill and supply liquid by positive and negative pressures, the embodiment can simplify the regulation and control structure of the gas path system and reduce the gas consumption of the gas path system.

The transfer line assembly 700 further includes a third transfer line 760, one end of the third transfer line 760 is connected to the hemoglobin detecting unit 300, and the other end is connected to the diluent transfer line 750, and the first injector 890 is further configured to drive the diluent to be transferred from the third transfer line 760 to the hemoglobin detecting unit 300. The third transfer line 760 is provided with a fifth control valve 761. The hemoglobin detection quantitative pump 840 and the fifth reagent supply unit 610 are both connected to the hemoglobin detection unit 300 through the third transfer line 760, and the connection point of the hemoglobin detection quantitative pump 840 and the fifth reagent supply unit 610 to the third transfer line 760 is located between the hemoglobin detection unit 300 and the fifth control valve 761.

The delivery circuit assembly 700 also includes an optical sample preparation circuit 770, and the fluid power device 800 also includes a second syringe 8100, the range of the first syringe 890 being greater than the range of the second syringe 8100. The optical sample preparation pipeline 770 is connected to the optical channel reaction cell 100, the flow chamber 210, the second injector 8100 and the first injector 890, the first injector 890 is further configured to drive the optical detection sample fluid to be transported from the optical channel reaction cell 100 to the optical sample preparation pipeline 770, and the second injector 8100 is configured to drive the optical detection sample fluid to be transported from the optical sample preparation pipeline 770 to the flow chamber 210.

In this embodiment, the optical sample preparation pipeline 770 includes a first sample preparation pipeline 771 and a second sample preparation pipeline 772, the transport pipeline assembly 700 further includes a first connection equipment pipeline 780, a second connection equipment pipeline 790 and a third connection equipment pipeline 7100, one end of the first sample preparation pipeline 771 is connected with the first reaction cell 110, the other end is connected with the flow chamber 210 and the second connection equipment pipeline 790 respectively, one end of the second sample preparation pipeline 772 is connected with the second reaction cell 120, the other end is connected with the flow chamber 210 and the second connection equipment pipeline 790 respectively, the first syringe 890 is connected with the first sample preparation pipeline 771 and the second sample preparation pipeline 772 through the second connection equipment pipeline 790, and the second syringe 8100 is connected with the first sample preparation pipeline 771 and the second sample preparation pipeline 772 through an eleventh control valve 7110 respectively. A sixth control valve 781 is arranged on the first connecting equipment pipeline 780, a seventh control valve 791 is arranged on the second connecting equipment pipeline 790, and an eighth control valve 7101 is arranged on the third connecting equipment pipeline 7100. The second transfer line 740 and the third transfer line 760 are connected to the diluent transfer line 750 through the second connection preparation line 790. The connection point of the second connection preparation line 790 and the diluent delivery line 750 is located between the first injector 890 and the third control valve 751.

In this embodiment, the delivery tubing assembly 700 further includes an impedance count sample preparation tubing 7120, the impedance count sample preparation tubing 7120 is connected to the hemoglobin detection unit 300, the impedance count detection unit 400, the second injector 8100, and the first injector 890, the first injector 890 is further configured to drive the impedance count detection sample liquid to be delivered from the hemoglobin detection unit 300 to the impedance count sample preparation tubing 7120, and the second injector 8100 is further configured to drive the impedance count detection sample liquid to be delivered from the impedance count sample preparation tubing 7120 to the impedance count detection unit 400.

In this embodiment, the sample pushing injector for pushing the optical detection sample liquid and the sample pushing injector for pushing the impedance counting detection sample liquid are the same injector (i.e., the second injector 8100), which can simplify the power system and reduce the volume and cost of the instrument; of course, in a specific application, as an alternative embodiment, the second syringe 8100 for pushing the optical detection sample liquid and the second syringe 8100 for pushing the impedance counting detection sample liquid can also be designed as two mutually independent syringes.

The conveying pipeline assembly 700 further includes a fifth conveying pipeline 7130 and a sixth conveying pipeline 7140, one end of the impedance count sample preparation pipeline 7120 is connected to one end of the impedance count detection unit 400 and one end of the fifth conveying pipeline 7130, the other end of the impedance count sample preparation pipeline 7120 is connected to the third conveying pipeline 760 through the sixth conveying pipeline 7140, and the other end of the fifth conveying pipeline 7130 is connected to the first syringe 890 through the second connection preparation pipeline 790 and the diluent conveying pipeline 750 in sequence. A ninth control valve 7131 is provided on the fifth delivery line 7130, and a tenth control valve 7141 is provided on the sixth delivery line 7140.

Preferably, in this embodiment, the second injector 8100 is further connected to the sampling component 1200 for driving the sampling component 1200 to suck the sample to be detected (i.e. sample), and for driving the sample to be detected in the sampling component 1200 to be respectively delivered to the optical channel reaction cell 100, the impedance counting detection sample preparation unit, and the hemoglobin detection unit 300 for reaction (i.e. sample separation). The sampling member 1200 may be a sampling needle or a sampling pipette, etc. The blood cell analyzer further includes a power element (not shown) for driving the movement of the sampling part 1200, and the sampling part 1200 can be moved to a sample storage container (e.g., a test tube, etc.) to perform sampling by the driving of the power element, and then moved to the optical channel reaction cell 100 and the hemoglobin detecting unit 300 by the driving of the power element, respectively, and perform sample division by the driving of the second syringe 8100.

The embodiment can greatly reduce the cost and the volume of the instrument by multiplexing the two syringes in a time-sharing way, and is favorable for realizing the low-cost and miniaturized design of the blood cell analyzer. In this embodiment, the driving power device for the diluent and the sample in the liquid path system has only two injectors, and one micro-upgrading injector (i.e., the second injector 8100) is used for providing power for sampling, sample separation and sample pushing; one milliupgrading syringe (i.e., the first syringe 890) is used to provide power for diluent delivery and sample preparation, wherein the first syringe 890 is used to provide power for diluent delivery, including for sample dilution, cuvette/sampling channel/sample preparation, etc., where the diluent is passed through the sample, diluent reservoir 1000 filling, optical detection of sheath fluid, etc., and the first syringe 890 is used to provide power for sample preparation, including sample preparation for optical detection of sample fluid and impedance counting detection of sample fluid.

In this embodiment, each air valve in the air path system is an electromagnetic valve. In this embodiment, the air valves in the air path system include a first air valve 851, a second air valve 852, a third air valve 853, a fourth air valve 854, a fifth air valve 861, a sixth air valve 881, a first positive pressure control valve 813, and a first negative pressure control valve 823, that is, the first air valve 851, the second air valve 852, the third air valve 853, the fourth air valve 854, the fifth air valve 861, the sixth air valve 881, the first positive pressure control valve 813, and the first negative pressure control valve 823 are all solenoid valves. In the embodiment, the design scheme that the electromagnetic valve replaces a pneumatic pressure-break valve is adopted, and the pneumatic pressure-break valve which is a component with large air consumption and high output pressure is omitted, so that the air consumption requirement of the blood cell analyzer is effectively reduced, the miniaturization design of the blood cell analyzer is facilitated, and the miniaturization and low-cost design of the blood cell analyzer is finally facilitated.

The delivery line assembly 700 includes a plurality of control valves for controlling the operation of the fluid path system, and each of the control valves is a solenoid valve. In this embodiment, the control valves on the delivery line assembly 700 for controlling the operation of the fluid circuit system include a first control valve 731, a second control valve 741, a third control valve 751, a fourth control valve 752, a fifth control valve 761, a sixth control valve 781, a seventh control valve 791, an eighth control valve 7101, a first drain control valve 711, a ninth control valve 7131 and a tenth control valve 7141, that is, the first control valve 731, the second control valve 741, the third control valve 751, the fourth control valve 752, the fifth control valve 761, the sixth control valve 781, the seventh control valve 791, the eighth control valve 7101, the first drain control valve 711, the ninth control valve 7131 and the tenth control valve 7141 are all solenoid valves. In the embodiment, the design scheme that the electromagnetic valve replaces a pneumatic pressure-break valve is adopted, and the pneumatic pressure-break valve which is a component with large air consumption and high output pressure is omitted, so that the air consumption requirement of the blood cell analyzer is effectively reduced, the miniaturization design of the blood cell analyzer is facilitated, and the miniaturization and low-cost design of the blood cell analyzer is finally facilitated.

The blood cell analyzer of the embodiment has the advantages that the air consumption of the air path system is extremely low (in an optimal scheme, the air consumption can reach below 0.5L/min), the working pressure required to be provided is also low (in an optimal scheme, the positive pressure can reach below 90kpa, and the negative pressure can reach above-30 kpa), the micro pump with miniaturization and extremely low cost can be selected for supporting realization, meanwhile, a complex conditioning and regulating system is not required, and the air path system can realize miniaturization, so that the purposes of low cost and miniaturization of the instrument are achieved.

In this embodiment, the working flow of one detection cycle of the blood cell analyzer is as follows:

1) the first air pump 811 builds pressure to the positive pressure air chamber, the first pressure sensor 812 monitors the pressure of the positive pressure air chamber, and the pressure building is stopped when the pressure of the positive pressure air chamber is monitored to reach a target pressure; meanwhile, the second air pump 821 builds pressure to the negative pressure air chamber, the second pressure sensor 822 monitors the pressure of the negative pressure air chamber, and the pressure building is stopped when the pressure of the negative pressure air chamber reaches the target pressure;

2) a sampling system sucks a sample to be detected from a test tube, a first quantitative pump 831 and a third quantitative pump 833 respectively add a third reagent and a fifth reagent into the first reaction tank 110, a second quantitative pump 832 and a fourth quantitative pump 834 respectively add a fourth reagent and a sixth reagent into the second reaction tank 120, and simultaneously the sampling system respectively adds the sample to be detected into the first reaction tank 110 and the second reaction tank 120 to carry out sample incubation reaction so as to respectively prepare a reticulocyte detection sample solution and a leukocyte classification detection sample solution;

3) opening the third control valve 751 and the fifth control valve 761, the first injector 890 adding the diluent to the hemoglobin detection unit 300, and simultaneously adding the sample to be detected to the hemoglobin detection unit 300 by the sampling system to prepare an impedance counting detection sample solution (i.e., the diluted sample to be detected);

4) opening the third control valve 751, valve 4 and valve 6, sucking the impedance count detection sample liquid from the hemoglobin detection unit 300 through the first syringe 890 into the impedance count sample preparation line 7120; then, the hemoglobin detection quantitative pump 840 adds a seventh reagent to the hemoglobin detection unit 300 to perform a sample incubation reaction to prepare a hemoglobin detection sample solution;

5) the hemoglobin detecting unit 300 starts measuring the hemoglobin concentration of the hemoglobin detection sample liquid; the impedance counting detection unit 400 is driven by the diluent reservoir 1000 to provide diluent by the positive pressure providing unit 810, and simultaneously the second syringe 8100 pushes the impedance counting detection sample liquid in the impedance counting sample preparation pipeline 7120 into the gem hole of the impedance counting detection unit 400 to start measuring the impedance counting of the impedance counting detection sample liquid;

6) opening the third control valve 751, the seventh control valve 791 and the eighth control valve 7101, and drawing the leukocyte fraction detection sample solution from the second reaction cell 120 through the first syringe 890 into the second sample preparation line 772;

7) the third control valve 751, the fourth control valve 752 and the first drainage control valve 711 are opened, the first injector 890 pushes the sheath fluid into the flow chamber 210, the regulating valve 14-1 is opened, and the second injector 8100 pushes the leukocyte classification detection sample fluid into the flow chamber 210 to start leukocyte classification measurement;

8) draining the waste liquid in the second reaction cell 120, and cleaning the optical sample preparation pipe 770 (the seventh control valve 791, the eighth control valve 7101 to the channel of the second reaction cell 120) and the second reaction cell 120;

9) opening the third control valve 751, the sixth control valve 781 and the seventh control valve 791, sucking the reticulocyte detection sample solution from the first reaction cell 110 into the first sample preparation line 771 through the first syringe 890;

10) the third control valve 751, the fourth control valve 752 and the first drain control valve 711 are opened, the first injector 890 pushes the sheath fluid into the flow chamber 210, the eleventh control valve 7110 is opened, the second injector 8100 pushes the leukocyte classification test sample fluid into the flow chamber 210, and the leukocyte classification measurement is started;

11) emptying the waste liquid in the first reaction cell 110 and the hemoglobin detecting unit 300, and cleaning the first reaction cell 110 and the hemoglobin detecting unit 300; purging the impedance count sample preparation tubing 7120 and the first sample preparation tubing 771, the sampling system, the flow cell 210, and the impedance count detection unit 400;

12) opening the second control valve 741 and the third control valve 751, filling the diluent reservoir 1000 with the first syringe 890;

13) finishing the measurement;

example two:

referring to fig. 4 to 7, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the positive pressure providing unit 810 and the negative pressure providing unit 820 have different structural schemes. In the first embodiment, the positive pressure providing unit 810 and the negative pressure providing unit 820 each include a gas chamber; in this embodiment, the air chambers of the positive pressure providing unit 810 and the negative pressure providing unit 820 are eliminated, that is, the positive pressure providing unit 810 does not include the positive pressure air chamber, and the negative pressure providing unit 820 does not include the negative pressure air chamber.

In this embodiment, one port of the first air pump 811 is connected to the atmospheric pressure, the other port is connected to the positive pressure output pipe 815 via the first positive pressure control valve 813, and the first pressure sensor 812 is provided between the first positive pressure control valve 813 and the positive pressure output pipe 815. One port of the second air pump 821 is connected to atmospheric pressure, the other port is connected to the negative pressure output pipeline 825 through a first negative pressure control valve 823, and the second pressure sensor 822 is provided between the first negative pressure control valve 823 and the negative pressure output pipeline 825.

Compared with the first embodiment, since the positive pressure air chamber and the negative pressure air chamber are omitted in the present embodiment, the volume of the blood cell analyzer can be further reduced in the present embodiment compared with the first embodiment, but after the positive pressure air chamber and the negative pressure air chamber are omitted, the pressure fluctuation range of the positive pressure providing unit 810 and the negative pressure providing unit 820 for driving the

quantitative pumps

830 and 840 for optical detection is slightly large, the performance is reduced, and the requirements can still be met.

In this embodiment, the arrangement of the positive pressure air chamber and the negative pressure air chamber is eliminated at the same time, but as an alternative embodiment, only one of the positive pressure air chamber and the negative pressure air chamber may be eliminated.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed correspondingly with reference to the embodiment, and will not be described in detail herein.

Example three:

referring to fig. 4, 5, 8 and 9, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the first voltage stabilization part 814 and the second voltage stabilization part 824 are differently arranged. In the first embodiment, the first pressure-stabilizing component 814 is a positive pressure air chamber; the second pressure stabilizing member 824 is a negative pressure air chamber; in this embodiment, the first pressure-stabilizing component 814 is a first air storage tube; the second pressure-stabilizing member 824 is a second air storage tube, i.e. the present embodiment also eliminates the arrangement of the positive pressure air chamber and the negative pressure air chamber, and uses a section of air tube to replace the air chamber.

In this embodiment, one port of the first air pump 811 is connected to the atmospheric pressure, the other port is connected to a first air receiver through a first positive pressure control valve 813, a first pressure sensor 812 is provided between the first positive pressure control valve 813 and the first air receiver, and an end of the first air receiver remote from the first positive pressure control valve 813 is connected to a positive pressure output pipe 815. One interface of the second air pump 821 is connected with the atmospheric pressure, the other interface is connected with a first air storage pipe through a first negative pressure control valve 823, the second pressure sensor 822 is arranged between the first negative pressure control valve 823 and the first air storage pipe, and the end part of the second air storage pipe far away from the first negative pressure control valve 823 is connected with a negative pressure output pipeline 825.

In this embodiment, the first and second gas reservoirs can play a role of stabilizing pressure when the positive pressure providing unit 810, the negative pressure providing unit 820 build pressure and drive the optical detection quantitative pump 830 and the hemoglobin detection quantitative pump 840 to work, and the gas tube can be placed at a suitable position selected according to the layout of the blood cell analyzer, which occupies a smaller space than the gas chamber.

Of course, this embodiment can also be understood as adding the first air storage tube and the second air storage tube to the second embodiment.

In the embodiment, the arrangement of a positive pressure air chamber and a negative pressure air chamber is simultaneously cancelled, and the first air storage pipe and the second air storage pipe are respectively used for replacing the positive pressure air chamber and the negative pressure air chamber; of course, as an alternative embodiment, only one of the positive pressure air chamber and the negative pressure air chamber may be eliminated, and only one of the first air storage pipe and the second air storage pipe may be provided.

Example four:

the blood cell analyzer provided in this embodiment is different from the first to third embodiments mainly in that: the positive pressure supply units 810 and the negative pressure supply units 820 are different in number. In the first to third embodiments, only one positive pressure providing unit 810 and one negative pressure providing unit 820 are provided, and the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834 and the hemoglobin detection quantitative pump 840 are respectively connected to the same positive pressure providing unit 810 and the same negative pressure providing unit 820; in this embodiment, the number of the positive pressure providing units 810 and the number of the negative pressure providing units 820 are at least two, and at least two of the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834, and the hemoglobin detection quantitative pump 840 are connected to different positive pressure providing units 810 and different negative pressure providing units 820, respectively.

As a preferred embodiment of this embodiment, the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834, and the hemoglobin detection quantitative pump 840 are connected to the independent positive pressure providing units 810, and are connected to the independent negative pressure providing units 820, respectively, for example: the first quantitative pump 831 is connected with the first positive pressure providing unit 810 and the first negative pressure providing unit 820; the second constant delivery pump 832 is connected with the second positive pressure providing unit 810 and the second negative pressure providing unit 820; the third quantitative pump 833 is connected to the third positive pressure supply unit 810 and the third negative pressure supply unit 820, and the fourth quantitative pump 834 is connected to the fourth positive pressure supply unit 810 and the fourth negative pressure supply unit 820; the hemoglobin detection quantitative pump 840 is connected to the fifth positive pressure providing unit 810 and the fifth negative pressure providing unit 820, the first positive pressure providing unit 810, the second positive pressure providing unit 810, the third positive pressure providing unit 810, the fourth positive pressure providing unit 810, and the fifth positive pressure providing unit 810 are independent devices, and the first negative pressure providing unit 820, the second negative pressure providing unit 820, the third negative pressure providing unit 820, the fourth negative pressure providing unit 820, and the fifth negative pressure providing unit 820 are independent devices.

In the solution of this embodiment, a plurality of low-cost micro air pump access air paths are added to drive the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection respectively to accelerate the pressure building speed, so as to avoid the problem of long pressure stabilization time after the quantitative pumps are switched after the positive pressure air chamber of the positive pressure providing unit 810 and the negative pressure air chamber of the negative pressure providing unit 820 are cancelled in the second embodiment and the third embodiment. Therefore, the solution of the present embodiment is preferably suitable for being combined into the second embodiment and the third embodiment to realize the optimization and improvement of the second embodiment and the third embodiment.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to the first to third embodiments, and will not be described in detail herein.

Example five:

referring to fig. 1 to 3 and fig. 10, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the first outlet c of the optical detection unit 200 and the second outlet d of the impedance counting detection unit 400 have different waste liquid discharge schemes. In the first embodiment, the negative pressure air chamber is also used in a waste liquid pool, and the waste liquid flowing out from the first outlet c of the optical detection unit 200 and the waste liquid flowing out from the second outlet d of the impedance counting detection unit 400 are both discharged to the negative pressure air chamber; in this embodiment, the waste liquid flowing out of the first outlet c of the optical detection unit 200 and/or the waste liquid flowing out of the second outlet d of the impedance count detection unit 400 is discharged to the optical channel reaction cell 100.

As a preferred embodiment of this embodiment, the waste liquid flowing out of the first outlet c of the optical detection unit 200 is discharged to the second reaction cell 120, and the waste liquid flowing out of the second outlet d of the impedance count detection unit 400 is discharged to the first reaction cell 110. The transfer line assembly 700 further includes a third drain line 7150 and a fourth drain line 7160, the third drain line 7150 is connected between the flow cell 210 and the second reaction cell 120, and the fourth drain line 7160 is connected between the impedance counter detecting unit 400 and the first reaction cell 110. A third drain control valve 7151 is provided in the third drain line 7150.

The present embodiment can also be understood as being used to solve the waste liquid discharge problem of the first outlet c of the optical detection unit 200 and the second outlet d of the impedance counting detection unit 400 after the positive pressure air chamber and the negative pressure air chamber are eliminated in the second to fourth embodiments. Of course, for solving this technical problem, it is not limited to discharging the waste liquid flowing out of the first outlet c of the optical detection unit 200 to the second reaction cell 120, and discharging the waste liquid flowing out of the second outlet d of the impedance count detection unit 400 to the first reaction cell 110, for example: as an alternative embodiment, the waste liquid flowing out of the first outlet c of the optical detection unit 200 and the waste liquid flowing out of the second outlet d of the impedance count detection unit 400 may be both discharged to the first reaction tank 110 or both discharged to the second reaction tank 120, i.e., the third drain line 7150 and the fourth drain line 7160 may be both connected to the first reaction tank 110 or both connected to the second reaction tank 120; or, as another alternative embodiment, the waste liquid flowing out of the first outlet c of the optical detection unit 200 may be discharged to the first reaction cell 110, and the waste liquid flowing out of the second outlet d of the impedance count detection unit 400 may be discharged to the second reaction cell 120, i.e., the third drain line 7150 is connected to the first reaction cell 110, and the fourth drain line 7160 is connected to the second reaction cell 120; still alternatively, as still another alternative embodiment, one or two separate waste liquid pools may be added, and one of the waste liquid flowing out from the first outlet c of the optical detection unit 200 and the waste liquid flowing out from the second outlet d of the impedance count detection unit 400 may be discharged to the waste liquid pool, and the other may be discharged to the waste liquid pool or the first reaction cell 110 or the second reaction cell 120.

Preferably, the third drain line 7150 and the fourth drain line 7160 are both solenoid valves, which is beneficial to the miniaturization design of the air path system of the blood cell analyzer.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to the first to fourth embodiments, and will not be described in detail herein.

Example six:

referring to fig. 1 to 3 and fig. 11, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the air valve arrangement schemes for controlling the conduction states of the connection pipes of the optical detection dosing pump 830 and the hemoglobin detection dosing pump 840, the positive pressure supply unit 810, and the negative pressure supply unit 820 are different. In the first embodiment, the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834, and the hemoglobin detection quantitative pump 840 are connected to the positive pressure output line 815 and the negative pressure output line 825 through air valves that are independent of each other, respectively; in this embodiment, at least two of the first dosing pump 831, the second dosing pump 832, the third dosing pump 833, the fourth dosing pump 834 and the hemoglobin detection dosing pump 840 are respectively connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825 through the same air valve, that is, in this embodiment, the control air valves of the first dosing pump 831, the second dosing pump 832, the third dosing pump 833, the fourth dosing pump 834 and the hemoglobin detection dosing pump 840 are combined into one air valve control or all are combined into one air valve control. In specific application, whether a control air valve is combined or not can be determined according to whether interval conflict exists in the working time period of each quantitative pump in the measurement process; after the air valves are combined, the air consumption can be increased to a certain extent when the quantitative pump works, but the air consumption is still in a very low range as long as the pipeline volume between the air valves and the quantitative pump is reasonably controlled.

As a preferred embodiment of this embodiment, the first air path assembly 850 includes a first air valve 851 and a second air valve 852, the second air path assembly 860 includes a fifth air valve 861, and the first dosing pump 831 and the second dosing pump 832 are respectively connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825 via the first air valve 851; the third quantitative pump 833 and the fourth quantitative pump 834 are respectively connected with the positive pressure output pipeline 815 and the negative pressure output pipeline 825 through a second air valve 852; the hemoglobin detection quantitative pump 840 is connected to the positive pressure output line 815 and the negative pressure output line 825 via a fifth air valve 861, respectively. This preferred embodiment corresponds to combining the control valves of the two constant delivery pumps connected to the first reaction tank 110 into one, and combining the control valves of the two constant delivery pumps connected to the second reaction tank 120 into one. Compared with the first embodiment, the present embodiment has two air valves reduced.

As another preferred embodiment of this embodiment, the first air path assembly 850 includes a first air valve 851, the second air path assembly 860 is connected to the first air valve 851, and the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834 and the hemoglobin detection quantitative pump 840 are respectively connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825 through the first air valve 851. In the preferred embodiment, the control air valves of the first quantitative pump 831, the second quantitative pump 832, the third quantitative pump 833, the fourth quantitative pump 834 and the hemoglobin detection quantitative pump 840 are all combined into one. Compared with the first embodiment, the present embodiment has four air valves.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to the first to fifth embodiments, and will not be described in detail herein.

Example seven:

referring to fig. 1 to 3 and 12, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the diluent reservoir 1000 has different filling power settings. In the first embodiment, the diluent reservoir 1000 is filled using a first syringe 890; in this embodiment, the diluent reservoir 1000 is filled with power by the negative pressure providing unit 820.

In this embodiment, the transportation pipeline assembly 700 still includes a diluent transportation pipeline 750, the fluid power device 800 further includes a fourth air path assembly 8120, the diluent transportation pipeline 750 is connected between the first injector 890 and the flow chamber 210, the diluent providing device 900 is respectively connected with the second transportation pipeline 740 and the diluent transportation pipeline 750 (in the first embodiment, the second transportation pipeline 740 is indirectly connected with the diluent providing device 900 through the diluent transportation pipeline 750; in the present embodiment, the second transportation pipeline 740 is directly connected with the diluent providing device 900), the first injector 890 is used for driving the diluent to be transported from the diluent transportation pipeline 750 to the flow chamber 210 so as to make the optical detection sample liquid pass through the detection area under the entrainment of the diluent, the negative pressure providing unit 820 is connected to the diluent reservoir 1000 through a fourth air path assembly 8120 for driving the diluent to be delivered from the diluent providing device 900 to the diluent reservoir 1000 through a second delivery pipe 740. The fourth air path component 8120 includes a seventh air valve 8121, and by controlling the seventh air valve 8121, the communication state between the negative pressure providing unit 820 and the diluent reservoir 1000 can be controlled.

In this embodiment, according to the design of the measurement process, the diluent reservoir 1000 is filled with a negative pressure, and the filling interval may be selected in a time period when the first air pump 811 and the second air pump 821 are idle (i.e., the first air pump 811 and the second air pump 821 are not in a time period when the control of the operation of the optical detection quantitative pump 830 and the operation of the hemoglobin detection quantitative pump 840). Compared with the first embodiment, the average air consumption of the system of the embodiment is increased, but the normal operation of the micro air channel system is not affected.

Preferably, the seventh air valve 8121 is an electromagnetic valve, which facilitates the miniaturization design of the air channel system of the blood cell analyzer.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to the first to sixth embodiments, and will not be described in detail herein.

Example eight:

referring to fig. 1 to 3 and fig. 13, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the power supply scheme for the hemoglobin test cell 300 plus diluent is different. In the first embodiment, the hemoglobin detecting unit 300 is powered by a first syringe 890; in this embodiment, the hemoglobin detecting unit 300 and the diluent are powered by a quantitative pump in cooperation with the positive pressure providing unit 810 and the negative pressure providing unit 820.

In this embodiment, the conveying pipeline assembly 700 further includes a fourth conveying pipeline 7170, the fluid power apparatus 800 further includes a sixth dosing pump 8130 and a fifth air channel assembly 8140, the sixth dosing pump 8130 is respectively connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 through the fifth air channel assembly 8140, and is respectively connected to the hemoglobin detecting unit 300 and the diluent providing device 900 through the fourth conveying pipeline 7170, so as to drive the diluent to be conveyed from the diluent providing device 900 to the hemoglobin detecting unit 300 through the fourth conveying pipeline 7170 under the control of the positive pressure providing unit 810 and the negative pressure providing unit 820. The fifth air path assembly 8140 includes an eighth air valve 8141, and by controlling the eighth air valve 8141, the conduction states of the sixth fixed displacement pump 8130, the positive pressure providing unit 810 and the negative pressure providing unit 820 can be controlled.

A twelfth control valve 7171 is arranged on the fourth conveying pipeline 7170, and the diluent supply device 900, the hemoglobin detection unit 300 and the sixth dosing pump 8130 are respectively connected with the twelfth control valve 7171. The twelfth control valve 7171 is used for controlling the connection and disconnection of the diluent supply device 900, the sixth dosing pump 8130 and the hemoglobin detection unit 300.

As a preferred embodiment of this embodiment, the sixth dosing pump 8130 has a range of 1 mL. Of course, in a specific application, the range of the sixth quantitative pump 8130 is not limited thereto, and may be greater than 1mL or less than 1 mL.

Compared with the first embodiment, the present embodiment will increase a certain cost and layout space; and the average air consumption of the air path system is increased to some extent (less than 0.1L/min), but the air path system still has extremely low air consumption, and the normal work of the micro air path system is not influenced.

Preferably, a connecting pipeline between the eighth air valve 8141 and the sixth fixed displacement pump 8130 is less than or equal to 20cm, so that the control air valve of the sixth fixed displacement pump 8130 can be arranged close to the sixth fixed displacement pump 8130, and the air consumption of a common pipeline during positive and negative pressure switching is favorably reduced.

Preferably, the eighth air valve 8141 and the twelfth control valve 7171 are both solenoid valves, which is beneficial to the miniaturization design of the air channel system of the blood cell analyzer.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to the first to seventh embodiments, and will not be described in detail herein.

Example nine:

referring to fig. 1 to 3 and fig. 14, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the power supply scheme for optical detection sample preparation is different. In the first embodiment, the first syringe 890 is used to provide power for preparing the optical detection sample, that is, the first syringe 890 is used to drive the optical detection sample solution to be transported from the optical channel reaction cell 100 to the optical sample preparation pipeline 770; in this embodiment, a quantitative pump is used in conjunction with the negative pressure providing unit 820 to provide power for preparing the optical detection sample.

In this embodiment, the fluid power apparatus 800 further includes a seventh quantitative pump 8150 and a sixth air path component 8160, the optical sample preparation pipeline 770 is respectively connected to the optical channel reaction cell 100, the flow chamber 210, the second injector 8100 and the seventh quantitative pump 8150, the seventh quantitative pump 8150 is further respectively connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 through the sixth air path component 8160, the seventh quantitative pump 8150 is configured to drive the optical detection sample liquid to be transported from the optical channel reaction cell 100 to the optical sample preparation pipeline 770 under the control of the negative pressure providing unit 820, and the second injector 8100 is configured to drive the optical detection sample liquid to be transported from the optical sample preparation pipeline 770 to the flow chamber 210. The fifth air path assembly 8140 includes a ninth air valve 8161, and by controlling the ninth air valve 8161, the communication states of the seventh quantitative pump 8150, the positive pressure providing unit 810 and the negative pressure providing unit 820 can be controlled.

Preferably, a connecting pipeline between the ninth air valve 8161 and the seventh quantitative pump 8150 is less than or equal to 20cm, so that the control air valve of the seventh quantitative pump 8150 can be arranged close to the seventh quantitative pump 8150, and the air consumption of a common pipeline during the switching of positive pressure and negative pressure is reduced.

Preferably, the ninth air valve 8161 is an electromagnetic valve, which facilitates the miniaturization design of the air channel system of the blood cell analyzer.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed correspondingly according to the first to eighth embodiments, and will not be described in detail herein.

Example ten:

referring to fig. 1 to 3 and fig. 15, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the power supply scheme for impedance counting detection sample liquid preparation is different. In the first embodiment, the first syringe 890 is used to provide power for the preparation of the impedance counting test sample fluid, i.e., the first syringe 890 is multiplexed with driving the impedance counting test sample fluid to be transported from the hemoglobin detection unit 300 into the impedance counting sample preparation tubing 7120; in the present embodiment, a quantitative pump is used in conjunction with the negative pressure providing unit 820 to provide power for preparing the sample liquid for impedance counting detection.

In this embodiment, the fluid power apparatus 800 further includes an eighth quantitative pump 8170 and a seventh gas circuit assembly 8180, the impedance count sample preparation pipeline 7120 is respectively connected to the hemoglobin detection unit 300, the impedance count detection unit 400, the second injector 8100 and the eighth quantitative pump 8170, the eighth quantitative pump 8170 is further respectively connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 through the seventh gas circuit assembly 8180, the eighth quantitative pump 8170 is configured to drive the impedance count detection sample liquid to be conveyed from the hemoglobin detection unit 300 to the impedance count sample preparation pipeline 7120 under the control of the negative pressure providing unit 820, and the second injector 8100 is configured to drive the impedance count detection sample liquid to be conveyed from the impedance count sample preparation pipeline 7120 to the impedance count detection unit 400. The seventh air channel assembly 8180 includes a tenth air valve 8181, and by controlling the tenth air valve 8181, the conduction states of the eighth fixed displacement pump 8170, the positive pressure providing unit 810 and the negative pressure providing unit 820 can be controlled.

In the first embodiment, one end of the fifth transport pipeline 7130 is connected to the impedance count sample preparation pipeline 7120 and the impedance count detection unit 400, respectively, and the other end of the fifth transport pipeline 7130 is connected to the first syringe 890 through the second connection preparation pipeline 790 and the diluent transport pipeline 750 in sequence; in this embodiment, one end of the fifth delivery line 7130 is still connected to the impedance count sample preparation line 7120 and the impedance count detection unit 400, the other end of the fifth delivery line 7130 is connected to the eighth quantitative pump 8170, and the ninth control valve 7131 of the fifth delivery line 7130 is connected to the waste liquid tank 826.

Preferably, a connecting pipeline between the tenth air valve 8181 and the eighth fixed displacement pump 8170 is less than or equal to 20cm, so that the control air valve of the eighth fixed displacement pump 8170 can be arranged close to the eighth fixed displacement pump 8170, and the air consumption of a common pipeline during the switching of positive pressure and negative pressure is reduced.

Preferably, the tenth air valve 8181 is an electromagnetic valve, which facilitates the miniaturization design of the air channel system of the blood cell analyzer.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to the first to ninth embodiments, and will not be described in detail herein.

Example eleven:

referring to fig. 5 and 16, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the arrangement scheme of the negative pressure providing unit 820 is different. In the first embodiment, the negative pressure providing unit 820 is used to generate negative pressure and the negative pressure air chamber can be reused for collecting waste liquid; in this embodiment, the negative pressure providing unit 820 can be reused to generate a normal pressure environment (standard atmospheric pressure) in addition to generating negative pressure and reusing for collecting waste liquid.

In this embodiment, the negative pressure providing unit 820 includes a waste liquid tank 826, a waste liquid barrel 827, a negative pressure power source 828, a first constant pressure control valve 829, a first external pipeline 8210, at least one first constant pressure pipeline 8211 and at least one first negative pressure pipeline 8212, the first constant pressure control valve 829 is connected to the waste liquid tank 826 and the atmospheric pressure through the first external pipeline 8210 for setting the waste liquid tank 826 to a constant pressure environment, the negative pressure power source 828 is connected to the waste liquid tank 826 for setting the waste liquid tank 826 to a negative pressure environment, the waste liquid tank 826 is connected to the flow chamber 210 and/or the impedance counting detection unit 400 through the first constant pressure pipeline 8211 for collecting waste liquid discharged from the flow chamber 210 and/or the impedance counting detection unit 400, the waste liquid tank 826 is connected to the optical detection quantitative pump 830 and/or the hemoglobin detection quantitative pump 840 through a first negative pressure pipeline 8212 so as to provide negative pressure driving power for the optical detection quantitative pump 830 and/or the hemoglobin detection quantitative pump 840.

Preferably, in this embodiment, the waste liquid tank 826 is connected to a plurality of first normal pressure pipelines 8211 and a plurality of first negative pressure pipelines 8212, and the internal pressure of the waste liquid can be switched according to the functional requirements, and the internal pressure can be respectively communicated with different pipelines.

In this embodiment, the negative pressure power source 828 is a peristaltic pump. The negative pressure power source 828 is connected between the waste liquid tank 826 and the waste liquid barrel 827, namely: one interface of the negative pressure power source 828 is connected with the waste liquid pool 826, and the other interface is connected with the waste liquid barrel 827.

In this embodiment, it can also be understood as a multiplexing design scheme for the waste liquid pool 826, that is, a scheme in which the waste liquid pool 826 can be set to different pressures for time-sharing multiplexing according to functional requirements, so that the cost and volume of the blood cell analyzer can be reduced.

In specific application, the waste liquid tank 826 can be set to be normal pressure and negative pressure according to the measurement function process of the blood analyzer, and different functions are realized in different measurement stages, so that the requirement of reusing the waste liquid tank 826 is met, and the cost and the volume of the instrument are reduced; for example: in the optical detection, when the waste liquid at the first outlet c of the flow chamber 210 needs to be discharged to the waste liquid tank 826, the first constant pressure control valve 829 connected to the waste liquid tank 826 is opened to maintain the interior of the waste liquid tank 826 in a constant pressure environment; when the waste liquid tank 826 is required to serve as a negative pressure chamber for supplying negative pressure to the diaphragm type quantitative pumps (for example, the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection), the first normal pressure control valve 829 is closed and the negative pressure power source 828 is turned on to place the waste liquid tank 826 in a negative pressure environment and supply suction power to the diaphragm type quantitative pumps.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed in accordance with one to ten embodiments, and will not be described in detail herein.

Example twelve:

referring to fig. 16 and 17, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the arrangement of the negative pressure power source 828 is different. In the eleventh embodiment, the negative pressure power source 828 is a peristaltic pump; in this embodiment, the negative pressure power source 828 is an injector.

In this embodiment, the negative pressure providing unit 820 further includes a second negative pressure control valve 8213, and the second negative pressure control valve 8213 is connected to the negative pressure power source 828, the waste liquid tank 827, and the waste liquid tank 826, respectively. By controlling the second negative pressure control valve 8213, the on-off of the connecting pipeline among the negative pressure power source 828, the waste liquid barrel 827 and the waste liquid tank 826 can be controlled.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to the first to eleventh embodiments, and will not be described in detail herein.

Example thirteen:

referring to fig. 1 to 5 and fig. 18, the blood cell analyzer according to the present embodiment is different from the first embodiment mainly in that: the blood cell analyzer according to this embodiment further includes a pressure control device 1100, the positive pressure supply unit 810 and the negative pressure supply unit 820 are connected to the quantitative pump 830 for optical detection and/or the quantitative pump 840 for hemoglobin detection via the pressure control device 1100, the pressure control device 1100 includes a waste liquid tank 826, a waste liquid tank 827, a second positive pressure control valve 1103 and a third negative pressure control valve 1104, the waste liquid tank is connected with the waste liquid tank 826 through the second external pipeline 1107 to set the waste liquid tank 826 to be a normal pressure environment, the second positive pressure control valve 1103 is connected between the waste liquid tank 826 and the positive pressure providing unit 810 to set the waste liquid tank 826 to be a positive pressure environment, and the third negative pressure control valve 1104 is connected between the waste liquid tank 826 and the negative pressure providing unit 820 to set the waste liquid tank 826 to be a negative pressure environment; a drain valve 1105 connecting between the bottom of the waste liquid tank 826 and the waste liquid tank 827 for discharging waste liquid from the waste liquid tank 826 in cooperation with the positive pressure supply unit 810 and the second positive pressure control valve 1103; the waste liquid tank 826 is connected to the flow chamber 210 and/or the impedance counting detection unit 400 through a second normal pressure pipe 1108, respectively, for collecting waste liquid discharged from the flow chamber 210 and/or the impedance counting detection unit 400, and the waste liquid tank 826 is connected to the optical detection quantitative pump 830 and/or the hemoglobin detection quantitative pump 840 through a second negative pressure pipe 1109, for supplying negative pressure driving power to the optical detection quantitative pump 830 and/or the hemoglobin detection quantitative pump 840.

In a specific application, when the third negative pressure control valve 1104 is opened, the waste liquid tank 826 can be set to a negative pressure environment, so that a negative pressure power source 828 can be provided for the second negative pressure pipeline 1109 connected with the waste liquid tank 826; when the second atmospheric control valve 1106 is opened, the waste liquid tank 826 can be set to be in an atmospheric environment so as to meet the pressure requirement of a second atmospheric pipeline 1108 connected with the waste liquid tank 826; when the second positive pressure control valve 1103 and the drain valve 1105 are opened, the waste liquid tank 826 may be switched to a positive pressure environment to drain the waste liquid in the waste liquid tank 826 to the outside of the machine.

In this embodiment, the waste liquid pool 826 can also be set to a scheme of time-sharing multiplexing with different pressures according to the functional requirements, so that the cost and the volume of the blood cell analyzer can be reduced.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed correspondingly to the first to twelfth embodiments, and will not be described in detail herein.

Example fourteen:

referring to fig. 18 and 19, the blood cell analyzer according to the present embodiment is different from the thirteenth embodiment mainly in that: in this embodiment, on the basis of the thirteenth embodiment, the pressure control apparatus 1100 further includes at least one positive pressure pipeline 1110, and the waste liquid tank 826 is connected to the optical detection quantitative pump 830 and/or the hemoglobin detection quantitative pump 840 through the positive pressure pipeline 1110 to provide positive pressure driving power for the optical detection quantitative pump 830 and/or the hemoglobin detection quantitative pump 840. In a specific application, the second positive pressure control valve 1103 may be opened to switch the waste liquid tank 826 to a positive pressure environment according to functional requirements.

In addition to the above differences, the other parts of the blood cell analyzer provided in this embodiment can be designed according to embodiments one to thirteen, 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

1. A blood cell analyzer, comprising:

the sampling component is used for collecting a sample to be detected;

a diluent supply device for supplying a diluent;

2. The blood cell analyzer of claim 1, wherein the fluid circuit system has an average gas consumption of less than or equal to 1.0L/min during a detection cycle of hemoglobin detection, impedance counting detection, and optical detection.

3. The blood cell analyzer of claim 2, wherein the fluid circuit system has an average gas consumption of 0.5L/min or less during a detection cycle of hemoglobin detection, impedance counting detection, and optical detection.

4. The blood cell analyzer of any one of claims 1 to 3, wherein the fluid dynamic device further comprises a first air channel assembly and a second air channel assembly, the positive pressure supply unit and the negative pressure supply unit are respectively connected to the quantitative pump for optical detection through the first air channel assembly, the positive pressure supply unit and the negative pressure supply unit are respectively connected to the quantitative pump for hemoglobin detection through the second air channel assembly, and a total volume of the quantitative pump for optical detection, the first air channel assembly, the quantitative pump for hemoglobin detection, and the second air channel assembly is less than or equal to 20 mL.

5. The blood cell analyzer of claim 4, wherein a total volume of the optical detection dosing pump, the first air channel assembly, the hemoglobin detection dosing pump, and the second air channel assembly is less than or equal to 15 mL.

6. The blood cell analyzer of claim 5, wherein a total volume of the optical detection dosing pump, the first air channel assembly, the hemoglobin detection dosing pump, and the second air channel assembly is less than or equal to 10 mL.

7. The blood cell analyzer of any one of claims 1 to 6, wherein the positive pressure providing unit outputs a positive pressure of 120kpa or less.

8. The blood cell analyzer of claim 7, wherein the positive pressure providing unit outputs a positive pressure less than or equal to 50 kpa; and/or the negative pressure providing unit outputs negative pressure greater than or equal to-30 kpa.

9. The blood cell analyzer of any one of claims 1 to 8, wherein the positive pressure supply unit includes a first air pump, a first positive pressure control valve, and a positive pressure output line, one end of the positive pressure output line being connected to the optical detection quantitative pump and the hemoglobin detection quantitative pump, respectively, and the other end of the positive pressure output line being connected to the first air pump through the first positive pressure control valve;

the negative pressure providing unit comprises a second air pump, a first negative pressure control valve and a negative pressure output pipeline, one end of the negative pressure output pipeline is respectively connected with the quantitative pump for optical detection and the quantitative pump for hemoglobin detection, and the other end of the negative pressure output pipeline is connected with the second air pump through the first negative pressure control valve;

and the no-load flow of the first air pump and the no-load flow of the second air pump are both less than or equal to 4L/min.

10. The blood cell analyzer of claim 9, wherein the no-load flow rate of the first air pump and the no-load flow rate of the second air pump are both 3L/min to 4L/min; or the idle-load flow of the first air pump and the idle-load flow of the second air pump are both less than or equal to 2L/min.

11. The blood cell analyzer of claim 9 or 10, wherein the maximum length of the first air pump and the maximum length of the second air pump are both less than or equal to 80 mm.

12. The blood cell analyzer of any one of claims 9 to 11, wherein the positive pressure supply unit further comprises a first pressure stabilizing part connected between the positive pressure output line and the first positive pressure control valve;

the negative pressure providing unit further comprises a second pressure stabilizing component connected between the negative pressure output pipeline and the first negative pressure control valve.

13. The blood cell analyzer of claim 12, wherein the first pressure-stabilizing member is a positive pressure gas chamber; the second pressure stabilizing component is a negative pressure air chamber, and the volume of the positive pressure air chamber and the volume of the negative pressure air chamber are both 80 mL-200 mL.

14. The blood cell analyzer of claim 13, wherein the volume of said positive pressure gas chamber and the volume of said negative pressure gas chamber are both between 100mL _ and 130mL _.

15. The blood cell analyzer of claim 13 or 14, wherein the negative pressure gas chamber also serves as a waste liquid pool, and the transfer line assembly includes a first drain line connected between the flow chamber and the negative pressure gas chamber and/or a second drain line connected between the impedance count detection unit and the negative pressure gas chamber.

16. The blood cell analyzer of claim 12, wherein the first pressure-stabilizing member is a first gas-storing tube; the second pressure stabilizing component is a second air storage pipe.

17. The blood cell analyzer of any one of claims 9 to 11 or 16, wherein the number of the positive pressure supplying units and the number of the negative pressure supplying units are both at least two, the number of the quantitative pumps for optical detection is at least two, and at least two of each of the quantitative pumps for optical detection and the quantitative pumps for hemoglobin detection are connected to different ones of the positive pressure supplying units and different ones of the negative pressure supplying units, respectively.

18. The blood cell analyzer of claim 17, wherein each of the quantitative pumps for optical detection is connected to the positive pressure providing units, which are independent of each other, one by one, and is connected to the negative pressure providing units, which are independent of each other, one by one.

19. The blood cell analyzer of any one of claims 1 to 18, the optical channel reaction cell includes a first reaction cell and a second reaction cell, the first reagent supply device includes a first reagent supply unit and a second reagent supply unit, the quantitative pump for optical detection comprises a first quantitative pump and a second quantitative pump, the first quantitative pump is respectively connected with the positive pressure providing unit, the negative pressure providing unit, the first reaction cell and the first reagent providing unit so as to drive a first reagent to be conveyed from the first reagent providing unit to the first reaction cell, the second quantitative pump is respectively connected with the positive pressure providing unit, the negative pressure providing unit, the second reaction pool and the second reagent providing unit and is used for driving a second reagent to be conveyed from the second reagent providing unit to the second reaction pool.

20. The blood cell analyzer of any one of claims 1 to 18, wherein the optical channel reaction cell includes a first reaction cell and a second reaction cell, the first reagent supplying device includes a first reagent supplying unit, a second reagent supplying unit, a third reagent supplying unit and a fourth reagent supplying unit, the quantitative pump for optical detection includes a first quantitative pump, a second quantitative pump, a third quantitative pump and a fourth quantitative pump, the first quantitative pump is respectively connected with the positive pressure supplying unit, the negative pressure supplying unit, the first reaction cell, the first reagent supplying unit for driving a third reagent to be transferred from the first reagent supplying unit into the first reaction cell, and the second quantitative pump is respectively connected with the positive pressure supplying unit, the negative pressure supplying unit, the second reaction cell and the second reagent supplying unit for driving a second reagent to be transferred from the fourth reagent supplying unit into the first reaction cell The second reaction tank;

the third quantitative pump is respectively connected with the positive pressure providing unit, the negative pressure providing unit, the first reaction tank and the third reagent providing unit for driving a fifth reagent to be conveyed into the first reaction tank from the third reagent providing unit, and the fourth quantitative pump is respectively connected with the positive pressure providing unit, the negative pressure providing unit, the second reaction tank and the fourth reagent providing unit for driving a sixth reagent to be conveyed into the second reaction tank from the fourth reagent providing unit.

21. The blood cell analyzer of claim 20, wherein the fluid power device further comprises a first air channel assembly and a second air channel assembly, the quantitative pump for optical detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the first air channel assembly, the quantitative pump for hemoglobin detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the second air channel assembly, the first air channel assembly comprises a first air valve, a second air valve, a third air valve and a fourth air valve, the second air channel assembly comprises a fifth air valve, and the first quantitative pump is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the first air valve; the second quantitative pump is respectively connected with the positive pressure providing unit and the negative pressure providing unit through the second air valve; the third quantitative pump is respectively connected with the positive pressure providing unit and the negative pressure providing unit through the third air valve; the fourth fixed displacement pump is respectively connected with the positive pressure providing unit and the negative pressure providing unit through the fourth air valve; the hemoglobin detection quantitative pump is respectively connected with the positive pressure providing unit and the negative pressure providing unit through the fifth air valve.

22. The blood cell analyzer of claim 20, wherein at least two of the first quantitative pump, the second quantitative pump, the third quantitative pump, the fourth quantitative pump, and the hemoglobin detection quantitative pump are connected to the positive pressure supply unit and the negative pressure supply unit, respectively, through the same air valve.

23. The blood cell analyzer of claim 22, wherein the fluid dynamic device further comprises a first air channel assembly and a second air channel assembly, the quantitative pump for optical detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the first air channel assembly, the quantitative pump for hemoglobin detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the second air channel assembly, the first air channel assembly comprises a first air valve and a second air valve, the second air channel assembly comprises a fifth air valve, and the first quantitative pump and the second quantitative pump are respectively connected to the positive pressure providing unit and the negative pressure providing unit through the first air valve; the third quantitative pump and the fourth quantitative pump are respectively connected with the positive pressure providing unit and the negative pressure providing unit through the second air valve; the hemoglobin detection quantitative pump is respectively connected with the positive pressure providing unit and the negative pressure providing unit through the fifth air valve.

24. The blood cell analyzer of claim 22, wherein the fluid dynamic device further comprises a first air channel assembly and a second air channel assembly, the quantitative pump for optical detection is connected to the positive pressure providing unit and the negative pressure providing unit through the first air channel assembly, the quantitative pump for hemoglobin detection is connected to the positive pressure providing unit and the negative pressure providing unit through the second air channel assembly, the first air channel assembly comprises a first air valve, the second air channel assembly is connected to the first air valve, and the first quantitative pump, the second quantitative pump, the third quantitative pump, the fourth quantitative pump and the quantitative pump for hemoglobin detection are all connected to the positive pressure providing unit and the negative pressure providing unit through the first air valve.

25. The blood cell analyzer of any one of claims 21 to 24, wherein the length of the connection line between each of the gas valves and the dosing pump is less than or equal to 20 cm; and/or the presence of a gas in the atmosphere,

each air valve is an electromagnetic valve.

26. The hematology analyzer of any one of claims 1 to 25, wherein the hematology analyzer further includes a diluent reservoir, the delivery line assembly further includes a first delivery line and a second delivery line, the fluid power device further includes a third air line assembly, the first delivery line is connected between the diluent reservoir and the impedance count detection unit, the second delivery line is connected between the diluent reservoir and the diluent providing device, and the positive pressure providing unit is connected to the diluent reservoir through the third air line assembly for driving diluent to be delivered from the diluent reservoir into the impedance count detection unit to flow the impedance count detection sample within the impedance count detection unit under entrainment of the diluent.

27. The hematology analyzer of claim 26 wherein the fluid power device further includes a first syringe, the transfer line assembly further includes a diluent transfer line connected between the first syringe and the flow chamber, the diluent supply and the second transfer lines are respectively connected to the diluent transfer line, the first syringe is configured to drive transfer of diluent from the diluent transfer line to the flow chamber to pass the optical test sample fluid through the test area under entrainment of the diluent, and the first syringe is configured to drive transfer of diluent from the diluent supply to the diluent reservoir.

28. The blood cell analyzer of claim 26, wherein the fluid power device further comprises a first syringe and a fourth air circuit assembly, the delivery line assembly further comprises a diluent delivery line connected between the first syringe and the flow chamber, the diluent providing device is respectively connected to the second delivery line and the diluent delivery line, the first syringe is configured to drive a diluent to be delivered from the diluent delivery line to the flow chamber so that the optical detection sample solution passes through the detection region under the entrainment of the diluent, and the negative pressure providing unit is connected to the diluent reservoir through the fourth air circuit assembly so as to drive a diluent to be delivered from the diluent providing device to the diluent reservoir.

29. The blood cell analyzer of claim 27 or 28, wherein the delivery line assembly further comprises a third delivery line, one end of the third delivery line is connected to the hemoglobin detection unit, the other end of the third delivery line is connected to the diluent delivery line, and the first syringe is further configured to drive the diluent to be delivered from the third delivery line into the hemoglobin detection unit.

30. The blood cell analyzer of claim 27 or 28, wherein the conveying line assembly further comprises a fourth conveying line, and the fluid power device further comprises a sixth quantitative pump and a fifth gas line assembly, the sixth quantitative pump is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the fifth gas line assembly, and is respectively connected to the hemoglobin detecting unit and the diluent providing device through the fourth conveying line assembly, so as to drive the diluent to be conveyed from the diluent providing device to the hemoglobin detecting unit under the control of the positive pressure providing unit and the negative pressure providing unit.

31. The hematology analyzer of claim 27 or 28 wherein the transfer line assembly further includes an optical sample preparation line, the fluid dynamic device further including a second injector, the range of the first injector being greater than the range of the second injector, the optical sample preparation line being connected to the optical channel reaction cell, the flow chamber, the second injector and the first injector, respectively, the first injector further being configured to drive transfer of the optical test sample fluid from the optical channel reaction cell into the optical sample preparation line, the second injector being configured to drive transfer of the optical test sample fluid from the optical sample preparation line into the flow chamber.

32. The blood cell analyzer of claim 27 or 28, wherein said transfer line assembly further comprises an optical sample preparation line, the fluid power device further includes a second injector, a seventh fixed displacement pump, and a sixth gas path component, the range of the first injector is greater than the range of the second injector, the optical sample preparation pipeline is respectively connected with the optical channel reaction cell, the flow chamber, the second injector and the seventh quantitative pump, the seventh fixed displacement pump is also respectively connected with the positive pressure providing unit and the negative pressure providing unit through the sixth air path component, the seventh quantitative pump is used for driving the optical detection sample liquid to be conveyed from the optical channel reaction cell to the optical sample preparation pipeline under the control of the negative pressure providing unit, the second injector is used for driving the optical detection sample liquid to be conveyed from the optical sample preparation pipeline to the flowing chamber.

33. The blood cell analyzer of claim 27 or 28, wherein the impedance count test sample preparation unit is integrally provided with the hemoglobin detection unit, the hemoglobin detection unit further provides a reaction field for the sample to be measured and the diluent to prepare the impedance count test sample solution, the transfer line assembly further includes an impedance count sample preparation line, the fluid power device further includes a second syringe, the range of the first syringe is larger than that of the second syringe, the impedance count sample preparation line is connected to the hemoglobin detection unit, the impedance count test unit, the second syringe and the first syringe, respectively, and the first syringe is further configured to drive the transfer of the impedance count test sample solution from the hemoglobin detection unit to the impedance count sample preparation line, the second injector is used for driving the impedance counting detection sample liquid to be conveyed from the impedance counting sample preparation pipeline to the impedance counting detection unit.

34. The blood cell analyzer of claim 27 or 28, wherein the impedance count detection sample preparation unit is integrally disposed with the hemoglobin detection unit, the hemoglobin detection unit is further configured to provide a reaction field for the sample to be detected and the diluent to prepare the impedance count detection sample solution, the delivery line assembly further includes an impedance count sample preparation line, the fluid power device further includes a second syringe, an eighth quantitative pump and a seventh gas path assembly, the range of the first syringe is greater than that of the second syringe, the impedance count sample preparation line is respectively connected to the hemoglobin detection unit, the impedance count detection unit, the second syringe and the eighth quantitative pump, and the eighth quantitative pump is respectively connected to the positive pressure providing unit through the seventh gas path assembly, The negative pressure providing unit is used for driving the impedance counting detection sample liquid to be conveyed from the hemoglobin detection unit to the impedance counting sample preparation pipeline under the control of the negative pressure providing unit, and the second injector is used for driving the impedance counting detection sample liquid to be conveyed from the impedance counting sample preparation pipeline to the impedance counting detection unit.

35. The blood cell analyzer of any one of claims 31 to 34, wherein the second injector is further connected to the sampling unit for driving the sampling unit to aspirate the sample to be tested and for driving the sample to be tested in the sampling unit to be respectively transferred to the hemoglobin detecting unit, the optical channel reaction cell and the impedance counting detection sample preparation unit for reaction.

36. The blood cell analyzer of any one of claims 1 to 35, wherein the transfer line assembly includes a plurality of control valves for controlling operation of the fluid path system, and each of the control valves is a solenoid valve.

37. The blood cell analyzer of any one of claims 1 to 8 or 19 to 36, wherein the negative pressure providing unit includes a waste liquid pool, a negative pressure power source, a first atmospheric pressure control valve, a first external pipeline, at least one first atmospheric pressure pipeline, and at least one first negative pressure pipeline, the first atmospheric pressure control valve connects the waste liquid pool and atmospheric pressure through the first external pipeline for setting the waste liquid pool to an atmospheric pressure environment, the negative pressure power source connects the waste liquid pool for setting the waste liquid pool to a negative pressure environment, the waste liquid pool connects the flow chamber and/or the impedance count detection unit through the first atmospheric pressure pipeline for collecting waste liquid discharged from the flow chamber and/or the impedance count detection unit, and the waste liquid pool connects the optical detection quantitative pump and/or the hemoglobin detection quantitative pump through the first negative pressure pipeline for use And providing negative pressure driving power for the quantitative pump for optical detection and/or the quantitative pump for hemoglobin detection.

38. The blood cell analyzer of claim 37, wherein the negative pressure power source is a peristaltic pump, the negative pressure providing unit further comprises a waste liquid tank, the negative pressure power source is connected between the waste liquid tank and the waste liquid tank; alternatively, the first and second electrodes may be,

the negative pressure power source is an injector, the negative pressure providing unit further comprises a waste liquid barrel and a second negative pressure control valve, and the second negative pressure control valve is respectively connected with the negative pressure power source, the waste liquid barrel and the waste liquid pool and used for controlling the connection and disconnection of pipelines among the negative pressure power source, the waste liquid barrel and the waste liquid pool.

39. The blood cell analyzer of any one of claims 1 to 8 or 19 to 36, further comprising a pressure control device, wherein the positive pressure providing unit and the negative pressure providing unit are connected to the quantitative pump for optical detection and/or the quantitative pump for hemoglobin detection through the pressure control device, the pressure control device comprises a waste liquid pool, a waste liquid bucket, a second positive pressure control valve, a third negative pressure control valve, a drain valve, a second normal pressure control valve, a second external connection pipeline, at least one second normal pressure pipeline, and at least one second negative pressure pipeline, the second normal pressure control valve is connected to the waste liquid pool and atmospheric pressure through the second external connection pipeline for setting the waste liquid pool to a normal pressure environment, the second positive pressure control valve is connected between the waste liquid pool and the positive pressure providing unit for setting the waste liquid pool to a positive pressure environment, the third negative pressure control valve is connected between the waste liquid tank and the negative pressure providing unit for setting the waste liquid tank to a negative pressure environment, the drain valve is connected between the bottom of the waste liquid pool and the waste liquid barrel and is used for being matched with the positive pressure providing unit and the second positive pressure control valve to discharge waste liquid out of the waste liquid pool, the waste liquid pool is respectively connected with the flow chamber and/or the impedance counting detection unit through the second normal-pressure pipeline so as to be used for collecting waste liquid discharged from the flow chamber and/or the impedance counting detection unit, and the waste liquid pool is connected with the quantitative pump for optical detection and/or the quantitative pump for hemoglobin detection through the second negative pressure pipeline so as to provide negative pressure driving power for the quantitative pump for optical detection and/or the quantitative pump for hemoglobin detection.

40. The blood cell analyzer of claim 39, wherein the pressure control device further comprises at least one positive pressure pipeline, and the waste liquid pool is connected to the quantitative pump for optical detection and/or the quantitative pump for hemoglobin detection through the positive pressure pipeline so as to provide positive pressure driving power for the quantitative pump for optical detection and/or the quantitative pump for hemoglobin detection.