Hematology analyzer

Abstract

The present invention is applicable to the field of medical equipment and discloses a blood cell analyzer, which includes a sampling component, an optical channel reaction pool, an optical detection unit, a hemoglobin detection unit, an impedance counting detection sample preparation unit, an impedance counting detection unit, a first reagent providing device, a second reagent providing device, a diluent providing device, a conveying pipeline assembly and a fluid power device. The sampling component, the optical detection unit, the optical channel reaction pool, the hemoglobin detection unit, the impedance counting detection sample preparation unit, the impedance counting detection unit, the first reagent providing device, the second reagent providing device, the diluent providing device and the fluid power device are connected through the conveying pipeline assembly to form a liquid circuit system. During a detection cycle of completing hemoglobin detection, impedance counting detection and optical detection, the average gas consumption of the liquid circuit system is less than or equal to 2.0 L / min, thereby achieving miniaturization and low-cost design of the instrument.

Description

Technical Field

[0001] The present invention relates to the field of medical equipment, and in particular to a blood cell analyzer. Background Art

[0002] Five-differentiation blood cell analyzers generally include a fluid power device, which is mainly used to provide power for transporting samples and reagents to achieve measurement. In the prior art, the design schemes of fluid power devices mainly include the following:

[0003] 1) The fluid power device adopts an external gas source solution that can provide a large flow rate: This solution using an external gas source as the power source can provide high pressure and large flow (generally providing a no-load flow rate greater than 10L / min and a pressure of more than 200kPa). It can drive components such as cylinders, pneumatic pressure-breaking valves, and pneumatic metering pumps, and can drive the filling and supply of liquid reservoirs, waste liquid collection and drainage, etc. Its driving components have a fast execution speed and can support high-gas-consuming components to work simultaneously (the average gas consumption of the whole machine is more than 5L / min). Therefore, this type of model has a fast measurement speed.

[0004] However, the use of an external air source not only significantly increases the cost and size of the instrument due to the independent air source, but also requires internal conditioning components such as a dehumidifier, air filter, dryer, precision pressure regulator, and relief valve, resulting in high instrument cost and a large size. Therefore, this solution is generally only used on high-end instruments with high measurement speed requirements.

[0005] 2) The fluid power device adopts a solution with a built-in small air source (air pump): This solution of configuring a small air source inside the machine as a power source can provide power with higher pressure and larger flow (generally providing a no-load flow of more than 2L / min and a pressure of more than 120kPa), can drive small cylinders, pneumatic pressure-breaking valves, pneumatic metering pumps and other components to work, and can drive functions such as filling and supplying liquid to the liquid reservoir, collecting and draining waste liquid. Due to the limited flow of miniaturized air pumps, it is generally necessary to add air tanks to support the simultaneous operation of high-gas-consuming components. The air pump cost of this solution is still relatively high, and since a larger air tank or pressure regulating element is required, the size of the instrument is still relatively large; therefore, this solution is generally used on mid-range machines with higher measurement speed requirements.

[0006] 3) The fluid power device uses a syringe solution: In this solution, all reagents are quantitatively delivered using syringes. When there are many types of reagents, the corresponding number of syringes will be large, and the cost of syringes is generally high and the volume is large. Therefore, this solution still cannot meet the needs in terms of low cost and miniaturization design.

[0007] In summary, existing fluid power device design solutions generally have the problems of high cost and large size, which makes it difficult to meet the design requirements of low cost and small size of instruments. Summary of the Invention

[0008] The object of the present invention is to provide a blood cell analyzer, which aims to solve the technical problems of existing blood cell analyzers such as high gas consumption, large volume and high cost.

[0009] To achieve the above object, the present invention provides a blood cell analyzer comprising:

[0010] A sampling component, used for collecting samples to be tested;

[0011] An optical channel reaction pool, which is used to provide a reaction site for the sample to be tested and the reagent to prepare an optical detection sample liquid;

[0012] a first reagent providing device, the first reagent providing device being used to provide reagents for the optical channel reaction cell;

[0013] an optical detection unit, the optical detection unit comprising a flow chamber and an optical detection element, the flow chamber having a detection zone for allowing the optical detection sample liquid to pass through while being carried by the diluent, and the optical detection element for detecting the optical detection sample liquid carried by the diluent through the detection zone;

[0014] A hemoglobin detection unit, which is used to provide a reaction site for the sample to be tested and the reagent to prepare a hemoglobin detection sample liquid, and to detect the hemoglobin concentration of the hemoglobin detection sample liquid;

[0015] a second reagent providing device, the second reagent providing device being used to provide reagents for the hemoglobin detection unit;

[0016] An impedance counting detection sample preparation unit, the impedance counting detection sample preparation unit is used to provide a reaction field for the sample to be tested and the diluent to prepare an impedance counting detection sample;

[0017] An impedance counting detection unit, configured to perform impedance counting detection on the impedance counting detection sample liquid;

[0018] a diluent providing device, the diluent providing device being used to provide a diluent;

[0019] a fluid power device, the fluid power device comprising a positive pressure providing unit, a negative pressure providing unit, a metering pump for optical detection, and a metering pump for hemoglobin detection; the metering pump for optical detection is respectively connected to the positive pressure providing unit, the negative pressure providing unit, the optical channel reaction pool, and the first reagent providing device, and is used to drive the reagent from the first reagent providing device to the optical channel reaction pool under the control of the positive pressure providing unit and the negative pressure providing unit; the metering pump for hemoglobin detection is respectively connected to the positive pressure providing unit, the negative pressure providing unit, the hemoglobin detection unit, and the second reagent providing device, and is used to drive the reagent from the second reagent providing device to the hemoglobin detection unit under the control of the positive pressure providing unit and the negative pressure providing unit;

[0020] The conveying pipeline assembly, the sampling component, the optical detection unit, the optical channel reaction pool, the hemoglobin detection unit, the impedance counting detection sample preparation unit, the impedance counting detection unit, the first reagent providing device, the second reagent providing device, the diluent providing device and the fluid power device are connected through the conveying pipeline assembly to form a liquid circuit system. The average gas consumption of the liquid circuit system is less than or equal to 2.0 L / min within a detection cycle of completing hemoglobin detection, impedance counting detection and optical detection.

[0021] The blood cell analyzer provided by the present invention eliminates the design of high-gas-consuming components such as pneumatic pressure-break valves and cylinders that consume large amounts of gas or have high output pressures by designing a power source for driving reagent delivery as a positive pressure providing unit and a negative pressure providing unit that cooperate with a metering pump for optical detection and a metering pump for hemoglobin detection, respectively. As a result, the average gas consumption of the blood cell analyzer within a detection cycle for completing hemoglobin detection, impedance counting detection, and optical detection is controlled within a predetermined range. This significantly reduces the gas consumption requirement of the blood cell analyzer, reduces the volume and cost of the pneumatic portion of the fluid power device, and facilitates the miniaturization and low-cost design of the blood cell analyzer. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on the structures shown in these drawings without paying any creative work.

[0023] Figure 1 Schematic diagram of the fluid path system of the blood cell analyzer provided in Example 1 of the present invention;

[0024] Figure 2 This is a schematic diagram of the connection between the optical channel reaction pool, the optical detection unit, the first reagent providing device, and the fluid dynamic device provided in the first embodiment of the present invention;

[0025] Figure 3 This is a schematic diagram of the connection between the hemoglobin detection unit, the impedance counting detection unit, the second reagent providing device, the fluid dynamic device, the diluent providing device, and the diluent storage tank provided in the first embodiment of the present invention;

[0026] Figure 4 Schematic diagram of a positive pressure providing unit provided in Example 1 of the present invention;

[0027] Figure 5 1 is a schematic diagram of a negative pressure providing unit provided in Example 1 of the present invention;

[0028] Figure 6 is a schematic diagram of a positive pressure providing unit provided in Embodiment 2 of the present invention;

[0029] Figure 7 Schematic diagram of a negative pressure providing unit provided in the second embodiment of the present invention;

[0030] Figure 8 This is a schematic diagram of a positive pressure providing unit provided in Example 3 of the present invention;

[0031] Figure 9 Schematic diagram of a negative pressure providing unit provided in the third embodiment of the present invention;

[0032] Figure 10 Schematic diagram of the fluid path system of the blood cell analyzer provided in the fifth embodiment of the present invention;

[0033] Figure 11 Schematic diagram of the fluid path system of the blood cell analyzer provided in Example 6 of the present invention;

[0034] Figure 12 Schematic diagram of the fluid path system of the blood cell analyzer provided in Example 7 of the present invention;

[0035] Figure 13 Schematic diagram of the fluid path system of the blood cell analyzer provided in Example 8 of the present invention;

[0036] Figure 14 Schematic diagram of the fluid path system of the blood cell analyzer provided in Example 9 of the present invention;

[0037] Figure 15 Schematic diagram of the fluid path system of the blood cell analyzer provided in the tenth embodiment of the present invention;

[0038] Figure 16 1 is a schematic diagram of a negative pressure providing unit provided in Example 11 of the present invention;

[0039] Figure 17 2 is a schematic diagram of a negative pressure providing unit provided in a twelfth embodiment of the present invention;

[0040] Figure 18 is a schematic diagram of a pressure control device provided in Example 13 of the present invention;

[0041] Figure 19 It is a schematic diagram of the pressure control device provided in Example 14 of the present invention.

[0042] Description of Figure Numbers:

[0043] 100, optical channel reaction pool; 110, first reaction pool; 120, second reaction pool; 200, optical detection unit; 210, flow chamber; a, first inlet; b, second inlet; c, first outlet; 220, optical detection element; 300, hemoglobin detection unit; 400, impedance counting detection unit; d, second outlet; 500, first reagent supply device; 510, first reagent supply unit; 520, second reagent supply unit; 530, third reagent supply unit; 540, fourth reagent supply unit; 600, second reagent supply device; 610, fifth reagent supply unit; 700, delivery pipeline assembly; 710, first discharge pipeline; 711, first discharge control valve; 720, second discharge Liquid pipeline; 730, first delivery pipeline; 731, first control valve; 740, second delivery pipeline; 741, second control valve; 750, diluent delivery pipeline; 751, third control valve; 752, fourth control valve; 760, third delivery pipeline; 761, fifth control valve; 770, optical sample preparation pipeline; 771, first sample preparation pipeline; 772, second sample preparation pipeline; 780, first connecting pipeline; 781, sixth control valve; 790, second connecting pipeline; 791, seventh control valve; 7100, third connecting pipeline; 7101, eighth control valve; 7110, eleventh control valve; 7120, impedance counting sample preparation pipeline; 7130, fifth delivery pipeline; 7131, Ninth control valve; 7140, sixth delivery pipeline; 7141, tenth control valve; 7150, third discharge pipeline; 7151, third discharge control valve; 7160, fourth discharge pipeline; 7170, fourth delivery pipeline; 7171, twelfth control valve; 800, fluid power device; 810, positive pressure providing unit; 811, first air pump; 812, first pressure sensor; 813, first positive pressure control valve; 814, first pressure stabilizing component; 815, positive pressure output pipeline; 820, negative pressure providing unit; 821, second air pump; 822, second pressure sensor; 823, first negative pressure control valve; 824, second pressure stabilizing component; 825, negative pressure output pipeline; 826, waste liquid tank; 827, waste liquid barrel ; 828, negative pressure power source; 829, first normal pressure control valve; 8210, first external pipeline; 8211, first normal pressure pipeline; 8212, first negative pressure pipeline; 8213, second negative pressure control valve; 830, quantitative pump for optical detection; 831, first quantitative pump; 832, second quantitative pump; 833, third quantitative pump; 834, fourth quantitative pump; 840, quantitative pump for hemoglobin detection; 850, first air circuit assembly; 851, first air valve; 852, second air valve; 853, third air valve; 854, fourth air valve; 860, second air circuit assembly; 861, fifth air valve; 870, third pressure sensor; 880, third air circuit assembly; 881, sixth air valve; 890, first syringe;8100, second syringe; 8120, fourth gas circuit assembly; 8121, seventh gas valve; 8130, sixth metering pump; 8140, fifth gas circuit assembly; 8141, eighth gas valve; 8150, seventh metering pump; 8160, sixth gas circuit assembly; 8161, ninth gas valve; 8170, eighth metering pump; 8180, seventh gas circuit assembly; 8181, tenth gas valve; 900, diluent supply device; 1000, diluent reservoir; 1100, pressure control device; 1103, second positive pressure control valve; 1104, third negative pressure control valve; 1105, drain valve; 1106, second normal pressure control valve; 1107, second external pipeline; 1108, second normal pressure pipeline; 1109, second negative pressure pipeline; 1110, positive pressure pipeline; 1200, sampling component.

[0044] The purpose, features and advantages of the present invention will be further described with reference to the accompanying drawings and in conjunction with the embodiments. DETAILED DESCRIPTION

[0045] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. All other embodiments obtained by ordinary technicians in this field based on the embodiments of the present invention without making any creative efforts shall fall within the scope of protection of the present invention.

[0046] It should be noted that all directional indications in the embodiments of the present invention (such as up, down, left, right, front, back, etc.) are only used to explain the relative position relationship and movement status of the various components in a certain specific posture. If the specific posture changes, the directional indication will also change accordingly.

[0047] It should also be noted that when an element is referred to as being "fixed to" or "disposed on" another element, it may be directly on the other element or there may be an intervening element. When an element is referred to as being "connected to" another element, it may be directly connected to the other element or indirectly connected to the other element through an intervening element.

[0048] In addition, the descriptions of "first", "second", etc. in the present invention are for descriptive purposes only and should not be understood as indicating or implying their relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features defined as "first" or "second" may explicitly or implicitly include at least one of such features. In addition, the technical solutions between the various embodiments can be combined with each other, but this must be based on the fact that they can be implemented by ordinary technicians in this field. When the combination of technical solutions is contradictory or cannot be implemented, it should be deemed that such combination of technical solutions does not exist and is not within the scope of protection required by the present invention.

[0049] Example 1:

[0050] like Figure 1-5 As shown, the blood cell analyzer provided in the first embodiment of the present invention includes an optical channel reaction pool 100, an optical detection unit 200, a hemoglobin detection unit 300, an impedance counting detection unit 400, a first reagent providing device 500, a second reagent providing device 600, a delivery pipeline assembly 700, a fluid power device 800, a diluent providing device 900, a diluent reservoir 1000, a sampling component 1200 and an impedance counting detection sample preparation unit (in this embodiment, the hemoglobin detection unit 300 is also used as the impedance counting detection sample preparation unit, that is, the impedance counting detection sample preparation unit and the hemoglobin detection unit 300 are integrated). The sampling component 1200, optical detection unit 200, optical channel reaction cell 100, impedance counting detection sample preparation unit, hemoglobin detection unit 300, impedance counting detection unit 400, first reagent supply device 500, second reagent supply device 600, diluent supply device 900, and fluid dynamic device 800 are connected via a delivery pipeline assembly 700 to form a fluidic system. A single detection cycle of the fluidic system includes impedance counting detection, hemoglobin detection, and optical detection. During a single detection cycle of hemoglobin detection, impedance counting detection, and optical detection, the average gas consumption of the fluidic system is less than or equal to 2.0 L / min.

[0051] The blood cell analyzer of this embodiment proposes a low-cost and miniaturized micro-air circuit system design. This design eliminates designs such as the pneumatic pressure-off valve, the cylinder, and the alternating positive and negative pressures of the diluent reservoir 1000, which consume a lot of air or require very high output pressure (the cylinder and the pneumatic pressure-off valve have high operating pressures). Instead, the focus is on the pneumatic drive solution for the metering pump, thereby reducing the demand for the pneumatic metering pump. In other words, the main air-consuming component of the blood cell analyzer provided by this embodiment is the metering pump.

[0052] Preferably, the average gas consumption of the liquid circuit system is less than or equal to 1.0 L / min within one detection cycle when completing hemoglobin detection, impedance counting detection and optical detection. That is, in this embodiment, by optimizing the gas circuit system (specific optimization methods include but are not limited to the methods listed below, for example: reducing the volume of the metering pump and the pipeline connected thereto; arranging the air valve used to control the metering pump close to the metering pump; replacing the pneumatic pressure-breaking valve with an electromagnetic valve; using a syringe and a positive pressure power source to drive the diluent reservoir 1000 to fill and supply liquid instead of using a positive and negative pressure power source alternately), the average gas consumption of the blood cell analyzer within one detection cycle can be less than or equal to 1.0 L / min.

[0053] As a preferred embodiment of this embodiment, the average gas consumption of the liquid circuit system during one detection cycle of completing hemoglobin detection, impedance counting detection, and optical detection is less than or equal to 0.5 L / min. That is, in this embodiment, by further optimizing the gas circuit system (specific optimization methods include but are not limited to the methods listed below, such as: reducing the volume of the metering pump and the pipeline connected thereto; locating the air valve used to control the metering pump close to the metering pump; replacing the pneumatic pressure-off valve with a solenoid valve; and using a syringe and a positive pressure power source to drive the diluent reservoir 1000 to fill and supply the diluent instead of using a positive and negative pressure power source alternately), the average gas consumption of the blood cell analyzer during one detection cycle can be reduced to less than or equal to 0.5 L / min.

[0054] The optical channel reaction pool 100 is used to provide a reaction site for the sample to be tested and the reagents to prepare a sample solution for optical detection. In this embodiment, the sample to be tested is a blood sample, and the sample solution for optical detection includes a sample solution for reticulocyte detection and a sample solution for white blood cell differential detection. Of course, as an alternative embodiment, the sample solution for optical detection is not limited to this. For example, the sample solution for optical detection may include only one of the sample solution for reticulocyte detection and the sample solution for white blood cell differential detection, or the sample solution for optical detection may include other sample solutions other than the sample solution for reticulocyte detection and the sample solution for white blood cell differential detection. In specific applications, the design can be adapted according to the actual detection project requirements.

[0055] The optical channel reaction pool 100 includes a first reaction pool 110 and a second reaction pool 120. The first reaction pool 110 and the second reaction pool 120 are two independent reaction pools. The first reaction pool 110 is used to provide a reaction site for the sample to be tested and the reagent to prepare the reticulocyte detection sample solution; the second reaction pool 120 is used to provide a reaction site for the sample to be tested and the reagent to prepare the white blood cell differential detection sample solution. In this embodiment, the reticulocyte detection sample solution and the white blood cell differential detection sample solution are prepared in two independent reaction pools. This not only avoids cross-contamination caused by reagent residue when the reaction pools are shared, but also allows the white blood cell differential detection sample solution and the reticulocyte detection sample solution to be prepared simultaneously, thereby improving detection efficiency. Of course, as an alternative embodiment, the reticulocyte detection sample liquid and the white blood cell classification detection sample liquid can also be incubated and generated in the same reaction pool, that is, the optical channel reaction pool 100 only includes one reaction pool (for example, the first reaction pool 110). Taking into account the problem of cross-contamination of fluorescent reagent residues between optical channels, in this alternative embodiment, the fluorescent platform is not used in the white blood cell classification detection (for example, a chemical staining platform is used, a hemolytic agent is used, but no fluorescent staining), and the reticulocyte detection uses a fluorescent platform. In this way, the white blood cell classification detection and the reticulocyte detection share a reaction pool without cross-contamination of fluorescent reagent residues.

[0056] The first reagent supply device 500 is used to provide reagents for the optical channel reaction cell 100. In this embodiment, the first reagent supply device 500 includes a first reagent supply unit 510, a second reagent supply unit 520, a third reagent supply unit 530 and a fourth reagent supply unit 540.

[0057] The first reagent providing unit 510 and the third reagent providing unit 530 are respectively connected to the first reaction pool 110 to respectively provide the third reagent and the fifth reagent to the first reaction pool 110. As a preferred embodiment of this 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 to enable the optical detection element 220 to obtain a fluorescent signal during reticulocyte detection, and the diluting reagent is mainly used to dilute the sample to be tested. Of course, in specific applications, as an alternative embodiment, the fluorescent reagent and the diluting reagent can also be replaced by a reagent having both fluorescent and diluting effects (for the convenience of distinguishing descriptions, referred to as the first reagent in this embodiment). In this alternative embodiment, there is only one reagent providing unit connected to the first reaction pool 110, such as the first reagent providing unit 510. The first reagent providing unit 510 is connected to the first reaction pool 110 to provide the first reagent to the first reaction pool 110.

[0058] The second reagent providing unit 520 and the fourth reagent providing unit 540 are respectively connected to the second reaction pool 120 to respectively provide the fourth reagent and the sixth reagent to the second reaction pool 120. One of the second reagent and the fourth reagent is a hemolytic agent that can dissolve red blood cells in the sample to be tested and can distinguish different types of white blood cells, and the other is a reagent that can stain white blood cells. 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, as an alternative embodiment, the hemolytic agent and the fluorescent staining reagent can also be replaced by a reagent that has both the function of dissolving red blood cells and the function of fluorescent staining (for the convenience of distinguishing and describing, this embodiment is referred to as the second reagent). In this alternative embodiment, there is only one reagent providing unit connected to the second reaction pool 120, such as the second reagent providing unit 520. The second reagent providing unit 520 is connected to the second reaction pool 120 and is used to provide the second reagent to the second reaction pool 110; alternatively, the fluorescent staining reagent can also be replaced by a chemical staining reagent.

[0059] The optical detection unit 200 includes a flow chamber 210 and an optical detection element 220. The flow chamber 210 has a detection zone, 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 are respectively connected to the detection zone. The detection zone is used for optical detection sample liquid to pass through under the influence of diluent.

[0060] The optical detection element 220 is used to detect the optical detection sample liquid carried by the diluent through the detection zone. During reticulocyte detection, the optical detection element 220 can perform reticulocyte detection on the reticulocyte detection sample liquid carried by the sheath fluid (in this embodiment, the diluent is used to form the sheath fluid) through the detection zone, and obtain the reticulocyte detection result based on the scattered light signal and the fluorescence signal. During white blood cell classification detection, the optical detection element 220 can perform white blood cell classification detection on the white blood cell classification detection sample liquid carried by the sheath fluid through the detection zone. The optical detection element 220 may include a light source, a forward scattered light signal collection device disposed on the optical axis, a side scattered light signal collection device disposed to the side of the optical axis, and a fluorescence signal collection device.

[0061] The impedance counting detection unit 400 is used to perform impedance counting detection on the impedance counting detection sample liquid. The impedance counting detection may include red blood cell count detection and / or platelet count detection. The impedance counting detection sample can be prepared by reacting the sample to be tested with a diluent.

[0062] The hemoglobin detection unit 300 is used to provide a reaction site for the sample to be tested and the reagent to prepare the hemoglobin detection sample liquid, and to perform hemoglobin concentration detection on the hemoglobin detection sample liquid. In this embodiment, the hemoglobin detection unit 300 is also used as an impedance counting detection sample preparation unit, that is, the hemoglobin detection unit 300 is also used to provide a reaction site for the sample to be tested and the diluent to prepare the impedance counting detection sample liquid. During specific operation, the sample to be tested and the diluent can be first added to the hemoglobin detection unit 300 to prepare the impedance counting detection sample, and then part of the impedance counting detection sample can be withdrawn; and then the reagent can be added to the hemoglobin detection unit 300 to prepare the hemoglobin detection sample. Of course, as an alternative implementation scheme, the impedance counting detection sample liquid does not necessarily have to be generated in the hemoglobin detection unit 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 integrated together; or, the impedance counting detection sample preparation unit can also be set independently of the hemoglobin detection unit 300 and the impedance counting detection unit 400.

[0063] The second reagent providing device 600 is used to provide reagents for the hemoglobin detection unit 300. In this embodiment, the second reagent providing device 600 includes a fifth reagent providing unit 610, which is connected to the hemoglobin detection unit 300 to provide a seventh reagent for the hemoglobin detection unit 300. The seventh reagent is, for example, a hemolytic agent that can dissolve red blood cells in a blood sample, release hemoglobin in the red blood cells, and convert hemoglobin into methemoglobin. In an alternative embodiment, the reagent used in the white blood cell classification test and the reagent used in the hemoglobin test can also be the same hemolytic agent, that is, the second reagent providing unit 520 and the fifth reagent providing unit 610 are the same reagent providing unit.

[0064] The fluid dynamic device 800 includes a positive pressure providing unit 810, a negative pressure providing unit 820, a metering pump for optical detection 830, a metering pump for hemoglobin detection 840, a first air circuit assembly 850, and a second air circuit assembly 860. 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 metering pump for optical detection 830 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively through the first air circuit assembly 850, and the metering pump for hemoglobin detection 840 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively through the second air circuit assembly 860. The total volume of the metering pump for optical detection 830, the first air circuit assembly 850, the metering pump for hemoglobin detection 840, and the second air circuit assembly 860 is less than or equal to 30 mL.

[0065] Preferably, the positive pressure output by the positive pressure providing unit 810 is less than or equal to 120 kPa, that is, in this embodiment, a positive pressure less than or equal to 120 kPa can meet the positive pressure working requirements of the air path system, thereby facilitating the miniaturization design of the air path system.

[0066] Preferably, the positive pressure output by the positive pressure providing unit 810 is less than or equal to 90 kPa, that is, in a further optimization scheme of this embodiment, a positive pressure less than or equal to 90 kPa can meet the positive pressure working requirements of the air path system, thereby facilitating further miniaturization design of the air path system.

[0067] As a preferred implementation scheme of this embodiment, the positive pressure output by the positive pressure providing unit 810 is less than or equal to 50 kPa; the negative pressure output by the negative pressure providing unit 820 is greater than or equal to -30 kPa, that is, in the preferred implementation scheme of this embodiment, the positive pressure is less than or equal to 50 kPa and the negative pressure is greater than or equal to -30 kPa, which can meet the positive pressure working requirements of the air path system, and is conducive to the further miniaturization design of the air path system.

[0068] In addition to being connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 , the optical detection metering pump 830 is also connected to the optical channel reaction pool 100 and the first reagent providing device 500 , so as to drive the reagent from the first reagent providing device 500 to the optical channel reaction pool 100 under the control of the positive pressure providing unit 810 and the negative pressure providing unit 820 .

[0069] In this embodiment, since the first reagent providing device 500 includes four reagent providing units (respectively, the first reagent providing unit 510, the second reagent providing unit 520, the third reagent providing unit 530 and the fourth reagent providing unit 540), the metering pump 830 for optical detection correspondingly includes four metering pumps, that is, the metering pump 830 for optical detection includes a first metering pump 831, a second metering pump 832, a third metering pump 833 and a fourth metering pump 834.

[0070] The first metering pump 831 is respectively connected to the positive pressure output pipeline 815, the negative pressure output pipeline 825, the first reaction tank 110, and the first reagent supply unit 510 to drive the third reagent from the first reagent supply unit 510 to be transported into the first reaction tank 110. The third metering pump 833 is respectively connected to the positive pressure output pipeline 815, the negative pressure output pipeline 825, the first reaction tank 110 and the third reagent supply unit 530 to drive the fifth reagent from the third reagent supply unit 530 to be transported into the first reaction tank 110. In this embodiment, there are two metering pumps connected to the first reaction tank 110; of course, in specific applications, if the fluorescent reagent and the dilution reagent (i.e., the third reagent and the fifth reagent) used to react and generate the reticulocyte detection sample are replaced by a reagent (i.e., the first reagent) that has both fluorescent and dilution effects, then since there is only one reagent providing unit connected to the first reaction tank 110, only one metering pump corresponding to the first reaction tank 110 is required. For example, only the first metering pump 831 needs to be connected to the first reaction tank 110, and there is no need to set the third metering pump 833.

[0071] The second metering pump 832 is connected to the positive pressure output pipeline 815, the negative pressure output pipeline 825, the second reaction cell 120, and the second reagent supply unit 520, respectively, to drive the fourth reagent from the second reagent supply unit 520 to be delivered into the second reaction cell 120. The fourth metering pump 834 is connected to the positive pressure output pipeline 815, the negative pressure output pipeline 825, the second reaction cell 120, and the fourth reagent supply unit 540, respectively, to drive the sixth reagent from the fourth reagent supply unit 540 to be delivered into the second reaction cell 120. In this embodiment, there are two metering pumps connected to the second reaction tank 120; of course, in specific applications, if the hemolytic agent and the staining reagent (i.e., the fourth reagent and the sixth reagent) used to react and generate the white blood cell classification detection sample are replaced by a reagent (i.e., the second reagent) that has both hemolytic and staining effects, then since there is only one reagent providing unit connected to the second reaction tank 120, only one metering pump corresponding to the second reaction tank 120 is needed. For example, only the second metering pump 832 needs to be connected to the second reaction tank 120, and there is no need to set up the fourth metering pump 834.

[0072] The first air circuit assembly 850 includes a first air valve 851, a second air valve 852, a third air valve 853, and a fourth air valve 854. The first metering pump 831 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively through the first air valve 851. The first air valve 851 is used to control the conduction state between the first metering pump 831 and the positive pressure providing unit 810 and the negative pressure providing unit 820. In a specific application, when positive pressure is required to drive the first metering pump 831 to work, the first air valve 851 is opened and the first air valve 851 is regulated to switch to a state in which the first metering pump 831 is in conduction with the positive pressure providing unit 810; when negative pressure is required to drive the first metering pump 831 to work, the first air valve 851 is opened and the first air valve 851 is regulated to switch to a state in which the first metering pump 831 is in conduction with the negative pressure providing unit 820.

[0073] The second metering pump 832 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively through the second air valve 852. The second air valve 852 is used to control the conduction state between the second metering pump 832 and the positive pressure providing unit 810 and the negative pressure providing unit 820. The control principle thereof can be referred to the control principle of the first air valve 851 controlling the conduction state between the first metering pump 831 and the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively, and will not be described in detail here.

[0074] The third metering pump 833 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively through the third air valve 853. The third air valve 853 is used to control the conduction state between the third metering pump 833 and the positive pressure providing unit 810 and the negative pressure providing unit 820. The control principle thereof can be referred to the control principle of the first air valve 851 controlling the conduction state between the first metering pump 831 and the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively, and will not be described in detail here.

[0075] The fourth metering pump 834 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively through the fourth air valve 854. The fourth air valve 854 is used to control the conduction state between the fourth metering pump 834 and the positive pressure providing unit 810 and the negative pressure providing unit 820. The control principle thereof can be referred to the control principle of the first air valve 851 controlling the conduction state between the first metering pump 831 and the positive pressure providing unit 810 and the negative pressure providing unit 820 respectively, and will not be described in detail here.

[0076] In addition to being connected to the positive pressure providing unit 810 and the negative pressure providing unit 820, the hemoglobin detection metering pump 840 is also connected to the hemoglobin detection unit 300 and the second reagent providing device 600, so as to drive the reagent from the second reagent providing device 600 to the hemoglobin detection unit 300 under the control of the positive pressure providing unit 810 and the negative pressure providing unit 820.

[0077] The second air circuit assembly 860 includes a fifth air valve 861, through which the hemoglobin detection metering pump 840 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820, respectively. The fifth air valve 861 is used to control the communication between the fifth metering pump and the positive pressure providing unit 810 and the negative pressure providing unit 820. The control principle of the fifth air valve 861 can be referred to the control principle of the first air valve 851 controlling the communication between the first metering pump 831 and the positive pressure providing unit 810 and the negative pressure providing unit 820, respectively, and will not be described in detail here.

[0078] In this embodiment, the number of positive pressure providing units 810 and negative pressure providing units 820 is one, and the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection are respectively connected to the same positive pressure providing unit 810 and the same negative pressure providing unit 820.

[0079] Preferably, the total volume of the optical detection quantitative pump 830, the first gas circuit assembly 850, the hemoglobin detection quantitative pump 840 and the second gas circuit assembly 860 is less than or equal to 20 mL, which helps to further reduce the average gas consumption of the blood cell analyzer in one detection cycle.

[0080] More preferably, the total volume of the quantitative pump 830 for optical detection, the first gas circuit assembly 850, the quantitative pump 840 for hemoglobin detection and the second gas circuit assembly 860 is less than or equal to 15 mL, which helps to further reduce the average gas consumption of the blood cell analyzer in one detection cycle.

[0081] As a preferred implementation scheme of this embodiment, the total volume of the quantitative pump 830 for optical detection, the first gas circuit assembly 850, the quantitative pump 840 for hemoglobin detection, and the second gas circuit assembly 860 is less than or equal to 10 mL. This helps to further reduce the average gas consumption of the blood cell analyzer during one detection cycle.

[0082] In a preferred embodiment of this embodiment, the volume of each optical detection metering pump 830 and hemoglobin detection metering pump 840, as well as their connected common gas pipeline (the pipeline between the metering pump and the air valve), is very small, with a total volume of less than 10 mL. In terms of layout, this embodiment preferably places the control air valves used to control each optical detection metering pump 830 and hemoglobin detection metering pump 840 close to each metering pump. This further reduces gas consumption in the common pipeline during positive and negative pressure switching.

[0083] Preferably, the length of the connecting pipeline between each air valve and the metering pump is less than or equal to 20 cm, that is: the connecting pipeline between the first air valve 851 and the first metering pump 831 is less than or equal to 20 cm; the connecting pipeline between the second air valve 852 and the second metering pump 832 is less than or equal to 20 cm; the connecting pipeline between the third air valve 853 and the third metering pump 833 is less than or equal to 20 cm; the connecting pipeline between the fourth air valve 854 and the fourth metering pump 834 is less than or equal to 20 cm; the connecting pipeline between the fifth air valve 861 and the metering pump 840 for hemoglobin detection is less than or equal to 20 cm. In this way, the control air valves of each metering pump 830 for optical detection and the metering pump 840 for hemoglobin detection can be respectively arranged close to each metering pump, thereby reducing the gas consumption of the common pipeline when switching between positive and negative pressure, and thus making the working gas consumption of the metering pump of the liquid system less than 0.3 L / min within a detection cycle of completing hemoglobin detection, impedance counting detection and optical detection.

[0084] 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 component 814 and a positive pressure output pipeline 815. One end of the positive pressure output pipeline 815 is respectively connected to the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection, and 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. The first pressure sensor 812 is arranged between the first positive pressure control valve 813 and the positive pressure output pipeline 815 for detecting the gas pressure in the positive pressure output pipeline 815. In this embodiment, the positive pressure output pipeline 815 is connected to the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection 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. 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 connection and disconnection of the connecting pipelines between the positive pressure output pipeline 815 and the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection can be controlled respectively.

[0085] The first pressure stabilizing component 814 is connected between the positive pressure output pipeline 815 and the first positive pressure control valve 813, and the first pressure sensor 812 is connected between the first pressure stabilizing component 814 and the first positive pressure control valve 813. The first pressure stabilizing component 814 is mainly used to stabilize the pressure when the metering pump (e.g., the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834, or the hemoglobin detection metering pump 840) has a high instantaneous gas consumption when pushing liquid.

[0086] In this embodiment, the first pressure stabilizing component 814 is a positive pressure air chamber. In specific applications, according to system requirements, the first air pump 811 can establish a positive pressure (eg, 50 kPa) inside the positive pressure air chamber.

[0087] Preferably, the volume of the positive pressure chamber (first pressure stabilizing component 814) is between 80 mL and 200 mL. This not only meets the positive pressure output requirements of the blood cell analyzer's air circuit system, but also helps reduce the size of the blood cell analyzer. This embodiment uses a positive pressure chamber with a volume of 80 mL to 200 mL to meet the positive pressure output requirements of the blood cell analyzer's air circuit system. Therefore, the blood cell analyzer provided by this embodiment has very low gas consumption and positive pressure.

[0088] More preferably, the volume of the positive pressure chamber is between 100 mL and 130 mL. This can facilitate further optimization of the size of the positive pressure chamber while ensuring that the positive pressure output meets the gas consumption requirements and that the positive pressure output is stable and reliable.

[0089] As a preferred implementation scheme of this embodiment, the volume of the positive pressure chamber is about 120 mL.

[0090] Preferably, the first air pump 811 is a micro air pump with a no-load flow rate of less than or equal to 4 L / min. This not only meets the positive pressure output requirements of the blood cell analyzer's air circuit system, but also helps reduce the size and cost of the blood cell analyzer. This embodiment uses a first air pump 811 with a no-load flow rate of less than or equal to 4 L / min to meet the positive pressure output requirements of the blood cell analyzer's air circuit system. This further demonstrates that the blood cell analyzer provided by this embodiment has very low air consumption and positive pressure.

[0091] As a preferred implementation scheme of this embodiment, the no-load flow rate of the first air pump 811 is 3L / min to 4L / min; or, as another preferred implementation scheme of this embodiment, the no-load flow rate of the first air pump 811 is less than or equal to 2L / min.

[0092] Preferably, the maximum length of the first air pump 811 is less than or equal to 80 mm. In this way, the volume and cost of the first air pump 811 can be reduced while ensuring that the negative pressure output meets the gas consumption requirements and the negative pressure output is stable and reliable.

[0093] As a preferred embodiment of this embodiment, the outer contour of the first air pump 811 is generally cylindrical, the outer diameter of the first air pump 811 is less than or equal to 30 mm, 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 generally rectangular, the width and height of the first air pump 811 are both less than or equal to 30 mm, and the length of the first air pump 811 is less than or equal to 80 mm. Of course, in specific applications, the shape of the first air pump 811 is not limited to this, as long as its maximum length is less than or equal to 80 mm.

[0094] The negative pressure providing unit 820 includes a second air pump 821, a second pressure sensor 822, a first negative pressure control valve 823, a second pressure stabilizing component 824 and a negative pressure output pipeline 825. One end of the negative pressure output pipeline 825 is respectively connected to the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection, and 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. The second pressure sensor 822 is arranged 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 metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection 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. 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 connection and disconnection of the connecting pipelines between the negative pressure output pipeline 825 and the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection can be controlled respectively.

[0095] The second pressure stabilizing component 824 is connected between the negative pressure output pipeline 825 and the first negative pressure control valve 823, and the second pressure sensor 822 is connected between the second pressure stabilizing component 824 and the first negative pressure control valve 823. The second pressure stabilizing component 824 is mainly used to stabilize the pressure when the metering pump (e.g., the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834, or the hemoglobin detection metering pump 840) has a high instantaneous air consumption during liquid aspiration.

[0096] In this embodiment, the second pressure stabilizing component 824 is a negative pressure chamber. In specific applications, according to system requirements, the second air pump 821 can establish a negative pressure (eg, -40 kPa) inside the negative pressure chamber.

[0097] Preferably, the volume of the negative pressure chamber (second pressure stabilizing component 824) is between 80 mL and 200 mL. This not only meets the negative pressure output requirements of the blood cell analyzer's air circuit system, but also helps reduce the size of the blood cell analyzer. This embodiment uses a negative pressure chamber with a volume of 80 mL to 200 mL to meet the negative pressure output requirements of the blood cell analyzer's air circuit system. As can be seen, the blood cell analyzer provided by this embodiment has very low gas consumption and negative pressure.

[0098] More preferably, the volume of the negative pressure chamber is between 100 mL and 130 mL. This can facilitate further optimization of the size of the negative pressure chamber while ensuring that the negative pressure output meets the gas consumption requirements and that the negative pressure output is stable and reliable.

[0099] As a preferred implementation scheme of this embodiment, the volume of the negative pressure chamber is about 120 mL.

[0100] Preferably, the second air pump 821 is a micro air pump with a no-load flow rate of less than or equal to 4 L / min. This not only meets the negative pressure output requirements of the blood cell analyzer's air circuit system, but also helps reduce the size and cost of the blood cell analyzer. This embodiment uses a second air pump 821 with a no-load flow rate of less than or equal to 4 L / min to meet the negative pressure output requirements of the blood cell analyzer's air circuit system. This further demonstrates that the blood cell analyzer provided by this embodiment has very low air consumption and positive pressure.

[0101] As a preferred implementation scheme of this embodiment, the no-load flow rate of the second air pump 821 is 3L / min to 4L / min; or, as another preferred implementation scheme of this embodiment, the no-load flow rate of the second air pump 821 is less than or equal to 2L / min.

[0102] Preferably, the maximum length of the second air pump 821 is less than or equal to 80 mm. In this way, the volume and cost of the second air pump 821 can be reduced while ensuring that the negative pressure output meets the gas consumption requirements and the negative pressure output is stable and reliable.

[0103] As a preferred embodiment of this embodiment, the outer contour of the second air pump 821 is generally cylindrical, the outer diameter of the second air pump 821 is less than or equal to 30 mm, 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 generally rectangular, the width and height of the second air pump 821 are both less than or equal to 30 mm, and the length of the second air pump 821 is less than or equal to 80 mm. Of course, in specific applications, the shape of the second air pump 821 is not limited to this, as long as its maximum length is less than or equal to 80 mm.

[0104] In this embodiment, the impedance counting detection unit 400 comprises a sheath flow impedance forecell, a sheath flow impedance postcell, a jewel hole for connecting the sheath flow impedance forecell and the sheath flow impedance postcell, and a second outlet d connected to the sheath flow impedance postcell. The negative pressure chamber also serves as a waste liquid reservoir for collecting waste liquid from the first outlet c of the optical channel flow chamber 210 and the second outlet d of the sheath flow impedance postcell. The delivery pipeline assembly 700 includes a first drain line 710 connected between the flow chamber 210 and the negative pressure chamber, and a second drain line 720 connected between the impedance counting detection unit 400 and the negative pressure chamber. A first drain control valve 711 is provided on the first drain line 710. Alternatively, only one of the first outlet c of the flow chamber 210 and the second outlet d of the impedance counting detection unit 400 may be connected to the negative pressure chamber, while the other may be connected to a waste liquid collection device independent of the negative pressure chamber.

[0105] In specific applications, when driving the metering pump (for example, the first metering pump 831 or the second metering pump 832 or the third metering pump 833 or the fourth metering pump 834 or the metering pump 840 for hemoglobin detection), the negative pressure chamber maintains a certain negative pressure; when collecting waste liquid, the negative pressure chamber maintains normal pressure and is connected to the atmosphere.

[0106] In this embodiment, the delivery pipeline assembly 700 also includes a first delivery pipeline 730 and a second delivery pipeline 740, and the fluid power device 800 also includes a third pressure sensor 870 and a third air circuit assembly 880. The first delivery pipeline 730 is connected between the diluent reservoir 1000 and the impedance counting detection unit 400, and the second delivery 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 circuit assembly 880 to drive the diluent from the diluent reservoir 1000 to be transported into the impedance counting detection unit 400, so that the impedance counting detection sample flows in the impedance counting detection unit 400 under the influence of the diluent. The third pressure sensor 870 is connected to the diluent reservoir 1000 for detecting the air pressure in the diluent reservoir 1000. The third gas circuit assembly 880 includes a sixth gas valve 881 , the first delivery pipeline 730 is provided with a first control valve 731 , and the second delivery pipeline 740 is provided with a second control valve 741 .

[0107] The diluent reservoir 1000 is normally at positive pressure. When the diluent reservoir 1000 consumes a certain amount of diluent, pressure needs to be built into the diluent reservoir 1000. Since the liquid consumption of the diluent reservoir 1000 is less than 10 mL, its gas consumption is extremely low, less than 0.1 L / min.

[0108] The fluid dynamic device 800 also includes a first syringe 890. The delivery pipeline assembly 700 also includes a diluent delivery pipeline 750 connected between the first syringe 890 and the flow chamber 210. The diluent supplying device 900 and the second delivery pipeline 740 are respectively connected to the diluent delivery pipeline 750. The first syringe 890 is used to drive the diluent from the diluent delivery pipeline 750 to the flow chamber 210, so that the optical detection sample liquid passes through the detection zone under the influence of the diluent. The first syringe 890 is also used to drive the diluent from the diluent supplying device 900 through the second delivery pipeline 740 to the diluent reservoir 1000. The diluent delivery pipeline 750 is provided with a third control valve 751 and a fourth control valve 752. The third control valve 751 is located between the first syringe 890 and the fourth control valve 752. The diluent supplying device 900 is connected to the third control valve 751. In this embodiment, the filling of the diluent reservoir 1000 is powered by the first syringe 890, and the supply of liquid from the diluent reservoir 1000 to the impedance counting detection unit 400 is powered by the positive pressure providing unit 810. Compared with the solution of using alternating positive and negative pressure to drive the filling and supply of liquid to the diluent reservoir 1000, this embodiment can simplify the control structure of the gas circuit system and reduce the gas consumption of the gas circuit system.

[0109] The delivery pipeline assembly 700 also includes a third delivery pipeline 760, one end of which is connected to the hemoglobin detection unit 300 and the other end is connected to the diluent delivery pipeline 750. The first syringe 890 is also used to drive the diluent from the third delivery pipeline 760 into the hemoglobin detection unit 300. A fifth control valve 761 is provided on the third delivery pipeline 760. The hemoglobin detection metering pump 840 and the fifth reagent supply unit 610 are both connected to the hemoglobin detection unit 300 via the third delivery pipeline 760, and the connection point between the hemoglobin detection metering pump 840 and the fifth reagent supply unit 610 and the third delivery pipeline 760 is located between the hemoglobin detection unit 300 and the fifth control valve 761.

[0110] The delivery pipeline assembly 700 also includes an optical sample preparation pipeline 770, and the fluid dynamic device 800 also includes a second syringe 8100. The range of the first syringe 890 is greater than that 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 syringe 8100, and the first syringe 890, respectively. The first syringe 890 is further used to drive the optical detection sample liquid from the optical channel reaction cell 100 into the optical sample preparation pipeline 770, and the second syringe 8100 is used to drive the optical detection sample liquid from the optical sample preparation pipeline 770 into the flow chamber 210.

[0111] In this embodiment, the optical sample preparation pipeline 770 includes a first sample preparation pipeline 771 and a second sample preparation pipeline 772. The delivery pipeline assembly 700 also includes a first connecting pipeline 780, a second connecting pipeline 790, and a third connecting pipeline 7100. One end of the first sample preparation pipeline 771 is connected to the first reaction pool 110, and the other end is respectively connected to the flow chamber 210 and the second connecting pipeline 790. One end of the second sample preparation pipeline 772 is connected to the second reaction pool 120, and the other end is respectively connected to the flow chamber 210 and the second connecting pipeline 790. The first syringe 890 is connected to the first sample preparation pipeline 771 and the second sample preparation pipeline 772 through the second connecting pipeline 790. The second syringe 8100 is connected to the first sample preparation pipeline 771 and the second sample preparation pipeline 772 through the eleventh control valve 7110. The first connecting line 780 is provided with a sixth control valve 781, the second connecting line 790 is provided with a seventh control valve 791, and the third connecting line 7100 is provided with an eighth control valve 7101. The second delivery line 740 and the third delivery line 760 are both connected to the diluent delivery line 750 via the second connecting line 790. The connection point between the second connecting line 790 and the diluent delivery line 750 is located between the first syringe 890 and the third control valve 751.

[0112] In this embodiment, the delivery pipeline assembly 700 also includes an impedance counting sample preparation pipeline 7120, which is respectively connected to the hemoglobin detection unit 300, the impedance counting detection unit 400, the second syringe 8100 and the first syringe 890. The first syringe 890 is also used to drive the impedance counting detection sample liquid from the hemoglobin detection unit 300 to the impedance counting sample preparation pipeline 7120, and the second syringe 8100 is also used to drive the impedance counting detection sample liquid from the impedance counting sample preparation pipeline 7120 to the impedance counting detection unit 400.

[0113] In this embodiment, the sample pushing syringe used to push the sample liquid for optical detection and the sample pushing syringe used to push the sample liquid for impedance counting detection are the same syringe (i.e., the second syringe 8100), which can simplify the power system and reduce the size and cost of the instrument; of course, in specific applications, as an alternative implementation scheme, the second syringe 8100 for pushing the sample liquid for optical detection and the second syringe 8100 for pushing the sample liquid for impedance counting detection can also be designed as two independent syringes.

[0114] The delivery pipeline assembly 700 also includes a fifth delivery pipeline 7130 and a sixth delivery pipeline 7140. One end of the impedance counting sample preparation pipeline 7120 is connected to the impedance counting detection unit 400 and one end of the fifth delivery pipeline 7130, respectively. The other end of the impedance counting sample preparation pipeline 7120 is connected to the third delivery pipeline 760 via the sixth delivery pipeline 7140. The other end of the fifth delivery pipeline 7130 is connected to the first syringe 890 via the second connection pipeline 790 and the diluent delivery pipeline 750. A ninth control valve 7131 is provided on the fifth delivery pipeline 7130, and a tenth control valve 7141 is provided on the sixth delivery pipeline 7140.

[0115] Preferably, in this embodiment, the second syringe 8100 is also connected to the sampling component 1200 to drive the sampling component 1200 to absorb the sample to be tested (i.e., sampling), and to drive the sample to be tested in the sampling component 1200 to be transported to the optical channel reaction pool 100, the impedance counting detection sample preparation unit and the hemoglobin detection unit 300 for reaction (i.e., sample splitting). The sampling component 1200 can be a sampling needle or a sampling pipette, etc. The blood cell analyzer also includes a power element (not shown) for driving the sampling component 1200 to move. The sampling component 1200 can be moved to a sample storage container (such as a test tube, etc.) for sampling under the drive of the power element, and then moved to the optical channel reaction pool 100 and the hemoglobin detection unit 300 respectively under the drive of the power element, and sample splitting is performed under the drive of the second syringe 8100.

[0116] This embodiment can significantly reduce the cost and size of the instrument by time-sharing multiplexing of two syringes, which is conducive to achieving a low-cost and miniaturized design of the blood cell analyzer. In this embodiment, the liquid circuit system has only two syringes for driving the diluent and sample. A microliter-level syringe (i.e., the second syringe 8100) is used to provide power for sampling, sample separation, and sample pushing; and a milliliter-level syringe (i.e., the first syringe 890) is used to provide power for diluent delivery and sample preparation. The first syringe 890 is mainly used for diluent delivery, including providing power for sample dilution, cleaning of the reaction pool / sampling channel / sample preparation, filling the diluent reservoir 1000, optical detection sheath fluid pushing, and other all aspects of diluent delivery. The first syringe 890 is used to provide power for sample preparation, including providing power for sample preparation for optical detection and impedance counting detection.

[0117] In this embodiment, each air valve in the air circuit system is a solenoid valve. In this embodiment, the air valves in the air circuit system include 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. 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 this embodiment, the design scheme of using solenoid valves instead of air-break and pressure-break valves eliminates the need for pneumatic pressure-break valves, which consume a lot of air and have a high output pressure. This effectively reduces the air consumption requirement of the blood cell analyzer, thereby facilitating the miniaturization design of the blood cell analyzer, and ultimately facilitating the miniaturization and low-cost design of the blood cell analyzer.

[0118] The delivery pipeline assembly 700 includes a plurality of control valves for controlling the operation of the fluid circuit system, and each of the control valves is a solenoid valve. In this embodiment, the control valves on the delivery pipeline 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 discharge 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 discharge control valve 711, the ninth control valve 7131, and the tenth control valve 7141 are all solenoid valves. In this embodiment, a solenoid valve is used instead of a pneumatic or pressure-off valve. Since the pneumatic or pressure-off valve, which consumes a large amount of gas and has a high output pressure, is eliminated, the gas consumption requirement of the blood cell analyzer is effectively reduced, thereby facilitating the miniaturization of the blood cell analyzer and ultimately facilitating the miniaturization and low-cost design of the blood cell analyzer.

[0119] The blood cell analyzer of this embodiment has an extremely low gas consumption in its gas circuit system (in a preferred embodiment, it can reach below 0.5 L / min) and requires a relatively low operating pressure (in a preferred embodiment, the positive pressure can reach below 90 kPa and the negative pressure can reach above -30 kPa). This can be supported by a miniaturized and extremely low-cost micropump, and no complex conditioning system is required. The gas circuit system can be miniaturized, thus achieving the goal of low cost and miniaturization of the instrument.

[0120] In this embodiment, the workflow of a detection cycle of the blood cell analyzer is as follows:

[0121] 1) The first air pump 811 builds pressure in the positive-pressure chamber, and the first pressure sensor 812 monitors the pressure of the positive-pressure chamber. When the pressure of the positive-pressure chamber reaches the target pressure, the pressure building stops. Simultaneously, the second air pump 821 builds pressure in the negative-pressure chamber, and the second pressure sensor 822 monitors the pressure of the negative-pressure chamber. When the pressure of the negative-pressure chamber reaches the target pressure, the pressure building stops.

[0122] 2) The sampling system draws the sample to be tested from the test tube, and the first metering pump 831 and the third metering pump 833 respectively add the third reagent and the fifth reagent to the first reaction well 110. The second metering pump 832 and the fourth metering pump 834 respectively add the fourth reagent and the sixth reagent to the second reaction well 120. Simultaneously, the sampling system adds the sample to be tested to the first reaction well 110 and the second reaction well 120 for sample incubation reaction, thereby preparing a reticulocyte detection sample solution and a leukocyte differential detection sample solution, respectively.

[0123] 3) The third control valve 751 and the fifth control valve 761 are opened, and the first syringe 890 adds the diluent to the hemoglobin detection unit 300. Simultaneously, the sampling system adds the sample to be tested to the hemoglobin detection unit 300 to prepare the impedance counting detection sample solution (i.e., the diluted sample to be tested);

[0124] 4) Open the third control valve 751, valve 4, and valve 6, and draw the impedance counting test sample solution from the hemoglobin detection unit 300 into the impedance counting sample preparation line 7120 via the first syringe 890; then, the hemoglobin detection dosing pump 840 adds the seventh reagent to the hemoglobin detection unit 300 for sample incubation reaction to prepare the hemoglobin detection sample solution;

[0125] 5) The hemoglobin detection unit 300 starts measuring the hemoglobin concentration of the hemoglobin detection sample solution; the impedance counting detection unit 400 receives diluent from the diluent reservoir 1000 under the drive of the positive pressure providing unit 810. Simultaneously, the second syringe 8100 pushes the impedance counting detection sample solution in the impedance counting sample preparation pipeline 7120 into the jewel hole of the impedance counting detection unit 400 to start measuring the impedance of the impedance counting detection sample solution;

[0126] 6) Open the third control valve 751, the seventh control valve 791, and the eighth control valve 7101, and draw the white blood cell differential detection sample liquid from the second reaction pool 120 into the second sample preparation pipeline 772 through the first syringe 890;

[0127] 7) The third control valve 751, the fourth control valve 752, and the first drain control valve 711 are opened, and the first syringe 890 pushes the sheath fluid into the flow chamber 210. Simultaneously, the control valve 14-1 is opened, and the second syringe 8100 pushes the white blood cell differential test sample liquid into the flow chamber 210, starting the white blood cell differential measurement.

[0128] 8) Draining the waste liquid in the second reaction tank 120 and cleaning the optical sample preparation pipeline 770 (the passage from the seventh control valve 791 and the eighth control valve 7101 to the second reaction tank 120) and the second reaction tank 120;

[0129] 9) Open the third control valve 751 , the sixth control valve 781 , and the seventh control valve 791 , and draw the reticulocyte detection sample solution from the first reaction pool 110 into the first sample preparation pipeline 771 through the first syringe 890 ;

[0130] 10) The third control valve 751, the fourth control valve 752, and the first drain control valve 711 are opened, and the first syringe 890 pushes the sheath fluid into the flow chamber 210. Simultaneously, the eleventh control valve 7110 is opened, and the second syringe 8100 pushes the white blood cell differential test sample solution into the flow chamber 210, starting the white blood cell differential measurement.

[0131] 11) Draining the waste liquid from the first reaction tank 110 and the hemoglobin detection unit 300, and cleaning the first reaction tank 110 and the hemoglobin detection unit 300; cleaning the impedance counting sample preparation pipeline 7120 and the first sample preparation pipeline 771, the sampling system, the flow chamber 210, and the impedance counting detection unit 400;

[0132] 12) Open the second control valve 741 and the third control valve 751 and use the first syringe 890 to fill the diluent reservoir 1000;

[0133] 13) Measurement ends;

[0134] Example 2:

[0135] Reference Figure 4-7 As shown, the hematology analyzer provided in this embodiment differs from the first embodiment primarily in the structural solutions of the positive pressure providing unit 810 and the negative pressure providing unit 820. In the first embodiment, both the positive pressure providing unit 810 and the negative pressure providing unit 820 include air chambers; however, 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 a positive pressure air chamber, and the negative pressure providing unit 820 does not include a negative pressure air chamber.

[0136] In this embodiment, one interface of the first air pump 811 is connected to atmospheric pressure, and the other interface is connected to a positive pressure output pipeline 815 via a first positive pressure control valve 813. A first pressure sensor 812 is disposed between the first positive pressure control valve 813 and the positive pressure output pipeline 815. One interface of the second air pump 821 is connected to atmospheric pressure, and the other interface is connected to a negative pressure output pipeline 825 via a first negative pressure control valve 823. A second pressure sensor 822 is disposed between the first negative pressure control valve 823 and the negative pressure output pipeline 825.

[0137] Compared to the first embodiment, since the positive pressure chamber and the negative pressure chamber are eliminated in the present embodiment, the volume of the blood cell analyzer can be further reduced compared to the first embodiment. However, without the positive pressure chamber and the negative pressure chamber, the pressure fluctuation range of the positive pressure providing unit 810 and the negative pressure providing unit 820 used to drive the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection is slightly larger, and the performance is reduced, but it can still meet the requirements.

[0138] This embodiment eliminates both the positive pressure chamber and the negative pressure chamber. Of course, as an alternative implementation, it is also possible to eliminate only one of the positive pressure chamber and the negative pressure chamber.

[0139] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of the first embodiment and will not be described in detail here.

[0140] Example 3:

[0141] Reference Figure 4 、 Figure 5 、 Figure 8 and Figure 9 As shown, the main difference between the blood cell analyzer provided in this embodiment and that in the first embodiment lies in the different configurations of the first pressure-stabilizing component 814 and the second pressure-stabilizing component 824. In the first embodiment, the first pressure-stabilizing component 814 is a positive-pressure air chamber, and the second pressure-stabilizing component 824 is a negative-pressure air chamber. In this embodiment, the first pressure-stabilizing component 814 is a first air storage tube, and the second pressure-stabilizing component 824 is a second air storage tube. This means that this embodiment also eliminates the positive-pressure and negative-pressure air chambers, replacing the air chambers with a section of air pipe.

[0142] In this embodiment, one interface of the first air pump 811 is connected to atmospheric pressure, and the other interface is connected to the first air storage pipe via a first positive pressure control valve 813. A first pressure sensor 812 is disposed between the first positive pressure control valve 813 and the first air storage pipe, and the end of the first air storage pipe away from the first positive pressure control valve 813 is connected to a positive pressure output pipeline 815. One interface of the second air pump 821 is connected to atmospheric pressure, and the other interface is connected to the first air storage pipe via a first negative pressure control valve 823. A second pressure sensor 822 is disposed between the first negative pressure control valve 823 and the first air storage pipe, and the end of the second air storage pipe away from the first negative pressure control valve 823 is connected to a negative pressure output pipeline 825.

[0143] In this embodiment, the first gas storage tube and the second gas storage tube can stabilize the pressure when the positive pressure providing unit 810 and the negative pressure providing unit 820 build pressure and drive the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection. The air tube can be placed in a suitable position according to the layout of the blood cell analyzer, and it occupies less space than the air chamber.

[0144] Of course, this embodiment can also be understood as adding the first gas storage pipe and the second gas storage pipe on the basis of the second embodiment.

[0145] In this embodiment, the positive pressure air chamber and the negative pressure air chamber are simultaneously eliminated, and are replaced by the first air storage pipe and the second air storage pipe respectively; of course, as an alternative implementation scheme, only one of the positive pressure air chamber and the negative pressure air chamber can be eliminated, and only one of the first air storage pipe and the second air storage pipe can be set accordingly.

[0146] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of the first embodiment and will not be described in detail here.

[0147] Example 4:

[0148] The main difference between the blood cell analyzer provided in this embodiment and those in embodiments 1 to 3 is that the number of positive pressure providing units 810 and negative pressure providing units 820 is different. In embodiments 1 to 3, only one positive pressure providing unit 810 and one negative pressure providing unit 820 are provided, and the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834, and the metering pump for hemoglobin detection 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 positive pressure providing units 810 and the number of negative pressure providing units 820 are both at least two, and at least two of the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834, and the metering pump for hemoglobin detection 840 are respectively connected to different positive pressure providing units 810 and different negative pressure providing units 820.

[0149] As a preferred embodiment of this embodiment, the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection are respectively connected to the independent positive pressure providing units 810, and are respectively connected to the independent negative pressure providing units 820. For example, the first metering pump 831 is connected to the first positive pressure providing unit 810 and the first negative pressure providing unit 820; the second metering pump 832 is connected to the second positive pressure providing unit 810 and the second negative pressure providing unit 820; the third metering pump 833 is connected to the third positive pressure providing unit 810 and the third negative pressure providing unit 820. , the fourth metering pump 834 is connected to the fourth positive pressure providing unit 810 and the fourth negative pressure providing unit 820; the metering pump 840 for hemoglobin detection 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.

[0150] This embodiment's solution, by adding multiple low-cost micro-pumps to the air circuit to drive the optical detection metering pump 830 and the hemoglobin detection metering pump 840, respectively, to accelerate pressure buildup, thereby avoiding the long pressure stabilization time required after the metering pumps switch after eliminating the positive pressure chamber of the positive pressure providing unit 810 and the negative pressure chamber of the negative pressure providing unit 820, as in the second and third embodiments. Therefore, this embodiment's solution is preferably suitable for incorporation into the second and third embodiments to achieve optimization and improvement over these two embodiments.

[0151] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of embodiments 1 to 3 and will not be described in detail here.

[0152] Embodiment 5:

[0153] Reference Figure 1-3 and Figure 10As shown, the main difference between the blood cell analyzer provided in this embodiment and the first embodiment lies in the different waste liquid discharge schemes of the first outlet c of the optical detection unit 200 and the second outlet d of the impedance counting detection unit 400. In the first embodiment, the negative pressure chamber is also used as a waste liquid pool, and 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 counting detection unit 400 are both discharged into the negative pressure 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 counting detection unit 400 are discharged into the optical channel reaction pool 100.

[0154] As a preferred embodiment of this embodiment, waste liquid flowing out of the first outlet c of the optical detection unit 200 is discharged into the second reaction tank 120, and waste liquid flowing out of the second outlet d of the impedance counting detection unit 400 is discharged into the first reaction tank 110. The delivery pipeline assembly 700 also includes a third drainage pipeline 7150 and a fourth drainage pipeline 7160. The third drainage pipeline 7150 is connected between the flow chamber 210 and the second reaction tank 120, and the fourth drainage pipeline 7160 is connected between the impedance counting detection unit 400 and the first reaction tank 110. The third drainage pipeline 7150 is provided with a third drainage control valve 7151.

[0155] This embodiment can also be understood as a solution to the problem of waste liquid discharge from 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 chamber and the negative pressure chamber are eliminated in Examples 2 to 4. Of course, the solution to this technical problem 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 tank 120 and discharging the waste liquid flowing out of the second outlet d of the impedance counting detection unit 400 to the first reaction tank 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 counting detection unit 400 can be both discharged to the first reaction tank 110 or both discharged to the second reaction tank 120, that is, the third drainage pipeline 7150 and the fourth drainage pipeline 7160 are 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 from the first outlet c of the optical detection unit 200 can be discharged into the first reaction tank 110, and the waste liquid flowing out from the second outlet d of the impedance counting detection unit 400 can be discharged into the second reaction tank 120, that is, the third drain pipe 7150 is connected to the first reaction tank 110, and the fourth drain pipe 7160 is connected to the second reaction tank 120; or, as another alternative embodiment, one or two independent waste liquid tanks can 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 counting detection unit 400 can be discharged into the waste liquid tank, and the other can be discharged into the waste liquid tank or the first reaction tank 110 or the second reaction tank 120.

[0156] Preferably, the third liquid discharge pipeline 7150 and the fourth liquid discharge pipeline 7160 are both solenoid valves, which is conducive to the miniaturized design of the gas path system of the blood cell analyzer.

[0157] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of the first to fourth embodiments and will not be described in detail here.

[0158] Example 6:

[0159] Reference Figure 1-3 and Figure 11As shown, the difference between the blood cell analyzer provided in this embodiment and the embodiment 1 mainly lies in: the setting scheme of the air valves used to control the conductive state of the connecting pipelines between the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection and the positive pressure providing unit 810 and the negative pressure providing unit 820 is different. In Example 1, the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection are respectively connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825 through independent air valves; while in this embodiment, at least two of the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection 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 valve parts of the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834 and the metering pump 840 for hemoglobin detection are merged into one air valve control or all are merged into one air valve control. In specific applications, whether to merge the control valves can be determined based on whether there are conflicts in the working time periods of the metering pumps in the measurement process. After the valves are merged, the gas consumption will increase to a certain extent when the metering pumps are working. However, as long as the volume of the pipeline between the valves and the metering pumps is reasonably controlled, the gas consumption will still be within a very low range.

[0160] As a preferred embodiment of this embodiment, the first gas circuit assembly 850 includes a first gas valve 851 and a second gas valve 852, and the second gas circuit assembly 860 includes a fifth gas valve 861. The first metering pump 831 and the second metering pump 832 are both connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825, respectively, through the first gas valve 851; the third metering pump 833 and the fourth metering pump 834 are both connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825, respectively, through the second gas valve 852; and the hemoglobin detection metering pump 840 is connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825, respectively, through the fifth gas valve 861. This preferred embodiment is equivalent to merging the control valves of the two metering pumps connected to the first reaction tank 110 into one, and merging the control valves of the two metering pumps connected to the second reaction tank 120 into one. Compared to Example 1, this embodiment reduces two gas valves.

[0161] As another preferred embodiment of this embodiment, the first air circuit assembly 850 includes a first air valve 851, and the second air circuit assembly 860 is connected to the first air valve 851. The first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834, and the hemoglobin detection metering pump 840 are all connected to the positive pressure output pipeline 815 and the negative pressure output pipeline 825 respectively through the first air valve 851. This preferred embodiment is equivalent to combining the control air valves of the first metering pump 831, the second metering pump 832, the third metering pump 833, the fourth metering pump 834, and the hemoglobin detection metering pump 840 into a single one. Compared to the first embodiment, this embodiment reduces the number of air valves by four.

[0162] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of embodiments 1 to 5 and will not be described in detail here.

[0163] Embodiment seven:

[0164] Reference Figure 1-3 and Figure 12 As shown, the main difference between the blood cell analyzer provided in this embodiment and the first embodiment lies in the different power settings for filling the diluent reservoir 1000. In the first embodiment, the diluent reservoir 1000 is powered by the first syringe 890; in this embodiment, the diluent reservoir 1000 is powered by the negative pressure providing unit 820.

[0165] In this embodiment, the delivery pipeline assembly 700 still includes the diluent delivery pipeline 750, and the fluid power device 800 also includes a fourth air circuit assembly 8120. The diluent delivery pipeline 750 is connected between the first syringe 890 and the flow chamber 210. The diluent providing device 900 is connected to the second delivery pipeline 740 and the diluent delivery pipeline 750, respectively (in the first embodiment, the second delivery pipeline 740 is indirectly connected to the diluent providing device 900 via the diluent delivery pipeline 750; in this embodiment, the second delivery pipeline 740 is directly connected to the diluent providing device 900). The first syringe 890 is used to drive the diluent from the diluent delivery pipeline 750 to the flow chamber 210, so that the optical detection sample liquid passes through the detection area under the influence of the diluent. The negative pressure providing unit 820 is connected to the diluent reservoir 1000 through the fourth air circuit assembly 8120 to drive the diluent from the diluent providing device 900 through the second delivery pipeline 740 to the diluent reservoir 1000. The fourth gas circuit assembly 8120 includes a seventh gas valve 8121 . By controlling the seventh gas valve 8121 , the communication state between the negative pressure providing unit 820 and the diluent storage tank 1000 can be controlled.

[0166] In this embodiment, based on the design of the measurement process, the diluent reservoir 1000 is filled with negative pressure, and the filling interval can be selected during the time period when the first air pump 811 and the second air pump 821 are idle (i.e., the time period when the first air pump 811 and the second air pump 821 are not controlling the quantitative pump 830 for optical detection and the quantitative pump 840 for hemoglobin detection). Compared to the first embodiment, the average gas consumption of the system in this embodiment is increased, but this does not affect the normal operation of the micro-gas circuit system.

[0167] Preferably, the seventh gas valve 8121 is a solenoid valve, which is conducive to the miniaturized design of the gas path system of the blood cell analyzer.

[0168] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of the first to sixth embodiments and will not be described in detail here.

[0169] Embodiment 8:

[0170] Reference Figure 1-3 and Figure 13 As shown, the main difference between the blood cell analyzer provided in this embodiment and the first embodiment lies in the different power supply schemes for adding diluent to the hemoglobin detection unit 300. In the first embodiment, the hemoglobin detection unit 300 was powered by a first syringe 890; in this embodiment, the hemoglobin detection unit 300 is powered by a metering pump in conjunction with a positive pressure providing unit 810 and a negative pressure providing unit 820.

[0171] In this embodiment, the delivery pipeline assembly 700 further includes a fourth delivery pipeline 7170, and the fluid power device 800 further includes a sixth metering pump 8130 and a fifth air circuit assembly 8140. The sixth metering pump 8130 is connected to the positive pressure providing unit 810 and the negative pressure providing unit 820, respectively, through the fifth air circuit assembly 8140, and is also connected to the hemoglobin detection unit 300 and the diluent providing device 900, respectively, through the fourth delivery pipeline 7170. Under the control of the positive pressure providing unit 810 and the negative pressure providing unit 820, the sixth metering pump 8130 drives the diluent from the diluent providing device 900 through the fourth delivery pipeline 7170 to the hemoglobin detection unit 300. The fifth air circuit assembly 8140 includes an eighth air valve 8141. By controlling the eighth air valve 8141, the communication state between the sixth metering pump 8130 and the positive pressure providing unit 810 and the negative pressure providing unit 820 can be controlled.

[0172] A twelfth control valve 7171 is provided on the fourth delivery pipeline 7170. The diluent supply device 900, the hemoglobin detection unit 300, and the sixth metering pump 8130 are respectively connected to the twelfth control valve 7171. The twelfth control valve 7171 is used to control the connection between the diluent supply device 900, the sixth metering pump 8130, and the hemoglobin detection unit 300.

[0173] As a preferred embodiment of this embodiment, the range of the sixth metering pump 8130 is 1 mL. Of course, in specific applications, the range of the sixth metering pump 8130 is not limited thereto and can be greater than 1 mL or less than 1 mL.

[0174] Compared with the first embodiment, this embodiment will increase the cost and layout space to a certain extent; and the average gas consumption of the gas circuit system will increase (less than 0.1L / min), but it is still extremely low and will not affect the normal operation of the micro gas circuit system.

[0175] Preferably, the connecting pipeline between the eighth air valve 8141 and the sixth metering pump 8130 is less than or equal to 20 cm. In this way, the control air valve of the sixth metering pump 8130 can be set close to the sixth metering pump 8130, which is conducive to reducing the gas consumption of the common pipeline when switching between positive and negative pressure.

[0176] Preferably, the eighth gas valve 8141 and the twelfth control valve 7171 are both solenoid valves, which is conducive to the miniaturized design of the gas path system of the blood cell analyzer.

[0177] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of Embodiments 1 to 7 and will not be described in detail here.

[0178] Embodiment 9:

[0179] Reference Figure 1-3 and Figure 14 As shown, the main difference between the blood cell analyzer provided in this embodiment and that in the first embodiment lies in the different power supply schemes for optical detection sample preparation. In the first embodiment, a first syringe 890 is used to provide power for optical detection sample preparation. That is, the first syringe 890 is also used to drive the optical detection sample liquid from the optical channel reaction cell 100 to the optical sample preparation pipeline 770. In contrast, in this embodiment, a metering pump and a negative pressure supply unit 820 are used to provide power for optical detection sample preparation.

[0180] In this embodiment, the fluid dynamic device 800 further includes a seventh metering pump 8150 and a sixth gas circuit assembly 8160. The optical sample preparation pipeline 770 is respectively connected to the optical channel reaction cell 100, the flow chamber 210, the second syringe 8100, and the seventh metering pump 8150. The seventh metering pump 8150 is further connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 via the sixth gas circuit assembly 8160. The seventh metering pump 8150 is used to drive the optical detection sample liquid from the optical channel reaction cell 100 into the optical sample preparation pipeline 770 under the control of the negative pressure providing unit 820. The second syringe 8100 is used to drive the optical detection sample liquid from the optical sample preparation pipeline 770 into the flow chamber 210. The fifth gas circuit assembly 8140 includes a ninth gas valve 8161. By controlling the ninth gas valve 8161, the communication state between the seventh metering pump 8150 and the positive pressure providing unit 810 and the negative pressure providing unit 820 can be controlled.

[0181] Preferably, the connecting pipeline between the ninth air valve 8161 and the seventh metering pump 8150 is less than or equal to 20 cm. In this way, the control air valve of the seventh metering pump 8150 can be set close to the seventh metering pump 8150, thereby reducing the gas consumption of the common pipeline when switching between positive and negative pressure.

[0182] Preferably, the ninth gas valve 8161 is a solenoid valve, which is conducive to the miniaturized design of the gas path system of the blood cell analyzer.

[0183] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of Embodiments 1 to 8 and will not be described in detail here.

[0184] Embodiment 10:

[0185] Reference Figure 1-3 and Figure 15 As shown, the main difference between the blood cell analyzer provided in this embodiment and that in the first embodiment lies in the different power supply schemes for preparing the sample solution for impedance counting detection. In the first embodiment, a first syringe 890 is used to provide power for preparing the sample solution for impedance counting detection. That is, the first syringe 890 is used to drive the sample solution for impedance counting detection from the hemoglobin detection unit 300 to the impedance counting sample preparation pipeline 7120. In contrast, in this embodiment, a quantitative pump and a negative pressure providing unit 820 are used in conjunction to provide power for preparing the sample solution for impedance counting detection.

[0186] In this embodiment, the fluid power device 800 also includes an eighth metering pump 8170 and a seventh air circuit assembly 8180. The impedance counting sample preparation pipeline 7120 is respectively connected to the hemoglobin detection unit 300, the impedance counting detection unit 400, the second syringe 8100 and the eighth metering pump 8170. The eighth metering pump 8170 is also connected to the positive pressure providing unit 810 and the negative pressure providing unit 820 through the seventh air circuit assembly 8180. The eighth metering pump 8170 is used to drive the impedance counting detection sample liquid from the hemoglobin detection unit 300 to the impedance counting sample preparation pipeline 7120 under the control of the negative pressure providing unit 820. The second syringe 8100 is used to drive the impedance counting detection sample liquid from the impedance counting sample preparation pipeline 7120 to the impedance counting detection unit 400. The seventh gas circuit assembly 8180 includes a tenth gas valve 8181 . By controlling the tenth gas valve 8181 , the conduction state between the eighth metering pump 8170 and the positive pressure providing unit 810 and the negative pressure providing unit 820 can be controlled.

[0187] In Example 1, one end of the fifth delivery pipeline 7130 is respectively connected to the impedance counting sample preparation pipeline 7120 and the impedance counting detection unit 400, and the other end of the fifth delivery pipeline 7130 is connected to the first syringe 890 through the second connecting pipeline 790 and the diluent delivery pipeline 750 in sequence; while in this embodiment, one end of the fifth delivery pipeline 7130 is still respectively connected to the impedance counting sample preparation pipeline 7120 and the impedance counting detection unit 400, and the other end of the fifth delivery pipeline 7130 is connected to the eighth metering pump 8170, and the ninth control valve 7131 on the fifth delivery pipeline 7130 is connected to the waste liquid pool 826.

[0188] Preferably, the connecting pipeline between the tenth air valve 8181 and the eighth metering pump 8170 is less than or equal to 20 cm. In this way, the control air valve of the eighth metering pump 8170 can be set close to the eighth metering pump 8170, which is conducive to reducing the gas consumption of the common pipeline when switching between positive and negative pressure.

[0189] Preferably, the tenth gas valve 8181 is a solenoid valve, which is conducive to the miniaturized design of the gas path system of the blood cell analyzer.

[0190] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of Embodiments 1 to 9 and will not be described in detail here.

[0191] Example 11:

[0192] Reference Figure 5 and Figure 16As shown, the main difference between the blood cell analyzer provided in this embodiment and the first embodiment lies in the different configuration of the negative pressure providing unit 820. In the first embodiment, the negative pressure providing unit 820 is used to generate negative pressure, and the negative pressure chamber can be reused to collect waste liquid. In this embodiment, in addition to generating negative pressure and being reused to collect waste liquid, the negative pressure providing unit 820 can also be reused to generate a normal pressure environment (standard atmospheric pressure).

[0193] In this embodiment, the negative pressure providing unit 820 includes a waste liquid pool 826, a waste liquid barrel 827, a negative pressure power source 828, a first normal pressure control valve 829, a first external pipe 8210, at least one first normal pressure pipe 8211 and at least one first negative pressure pipe 8212. The first normal pressure control valve 829 is connected to the waste liquid pool 826 and the atmospheric pressure through the first external pipe 8210 to set the waste liquid pool 826 to a normal pressure environment. The negative pressure power source 828 is connected to the waste liquid pool 826 to set the waste liquid pool 826 to a normal pressure environment. 6 is set to a negative pressure environment, the waste liquid pool 826 is connected to the flow chamber 210 and / or the impedance counting detection unit 400 through the first normal pressure pipeline 8211 for collecting waste liquid discharged from the flow chamber 210 and / or the impedance counting detection unit 400, and the waste liquid pool 826 is connected to the optical detection metering pump 830 and / or the hemoglobin detection metering pump 840 through the first negative pressure pipeline 8212 for providing negative pressure driving power for the optical detection metering pump 830 and / or the hemoglobin detection metering pump 840.

[0194] Preferably, in this embodiment, the waste liquid pool 826 is connected to multiple first normal pressure pipelines 8211 and multiple first negative pressure pipelines 8212, and the pressure inside the waste liquid can be switched according to functional needs and connected to different pipelines respectively.

[0195] In this embodiment, the negative pressure power source 828 is a peristaltic pump and is connected between the waste liquid pool 826 and the waste liquid barrel 827 , that is, one interface of the negative pressure power source 828 is connected to the waste liquid pool 826 and the other interface is connected to the waste liquid barrel 827 .

[0196] This embodiment can also be understood as a reuse design scheme for the waste liquid pool 826, that is, the waste liquid pool 826 can be set to a time-sharing reuse scheme with different pressures according to functional requirements, thereby reducing the cost and size of the blood cell analyzer.

[0197] In specific applications, the waste liquid pool 826 can be set to normal pressure and negative pressure according to the measurement function process of the blood analyzer, and different functions can be realized in different measurement stages to meet the needs of reusing the waste liquid pool 826 and reduce the cost and volume of the instrument; for example: in optical detection, when the waste liquid from the first outlet c of the flow chamber 210 needs to be discharged to the waste liquid pool 826, the first normal pressure control valve 829 connected to the waste liquid pool 826 is opened to maintain the normal pressure environment in the waste liquid pool 826; when the waste liquid pool 826 is needed as a negative pressure air chamber to provide negative pressure to the diaphragm metering pump (such as the metering pump 830 for optical detection, the metering pump 840 for hemoglobin detection), the first normal pressure control valve 829 is closed, and the negative pressure power source 828 is turned on at the same time to set the waste liquid pool 826 to a negative pressure environment to provide suction power to the diaphragm metering pump.

[0198] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of Embodiments 1 to 10 and will not be described in detail here.

[0199] Example 12:

[0200] Reference Figure 16 and Figure 17 As shown, the main difference between the blood cell analyzer provided in this embodiment and the eleventh embodiment is the different arrangement of the negative pressure power source 828. In the eleventh embodiment, the negative pressure power source 828 is a peristaltic pump; while in this embodiment, the negative pressure power source 828 is a syringe.

[0201] In this embodiment, the negative pressure providing unit 820 further includes a second negative pressure control valve 8213, which is respectively connected to the negative pressure power source 828, the waste liquid barrel 827, and the waste liquid pool 826. By controlling the second negative pressure control valve 8213, the connection and disconnection of the connecting pipelines between the negative pressure power source 828, the waste liquid barrel 827, and the waste liquid pool 826 can be controlled.

[0202] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of the first to eleventh embodiments and will not be described in detail here.

[0203] Example 13:

[0204] Reference Figure 1-5 and Figure 18As shown, the difference between the blood cell analyzer provided in this embodiment and the embodiment 1 is mainly that: the blood cell analyzer provided in this embodiment further includes a pressure control device 1100, the positive pressure providing unit 810 and the negative pressure providing unit 820 are connected to the quantitative pump 830 for optical detection and / or the quantitative pump 840 for hemoglobin detection through the pressure control device 1100, the pressure control device 1100 includes a waste liquid pool 826, a waste liquid barrel 827, a second positive pressure control valve 1103, a third negative pressure control valve 1104, a drain valve 1105, a second normal pressure control valve 1106, a second external pipe 1107, at least one second normal pressure pipe 1108 and at least one second negative pressure pipe 1109, the second normal pressure control valve 1106 connects the waste liquid pool 826 and atmospheric pressure through the second external pipe 1107 to set the waste liquid pool 826 to a normal pressure environment, the second positive pressure control valve 1103 is connected between the waste liquid pool 826 and the positive pressure control valve 1103, and the third negative pressure control valve 1104 is connected to the drain valve 1105. The positive pressure supply unit 810 is used to set the waste liquid pool 826 to a positive pressure environment. The third negative pressure control valve 1104 is connected between the waste liquid pool 826 and the negative pressure supply unit 820 to set the waste liquid pool 826 to a negative pressure environment. The drain valve 1105 is connected between the bottom of the waste liquid pool 826 and the waste liquid barrel 827 to cooperate with the positive pressure supply unit 810 and the second positive pressure control valve 1103 to discharge the waste liquid out of the waste liquid pool 826. The waste liquid pool 826 is connected to the negative pressure supply unit 810 and the second positive pressure control valve 1103 to discharge the waste liquid out of the waste liquid pool 826. The normal pressure pipeline 1108 is respectively connected to the flow chamber 210 and / or the impedance counting detection unit 400 for collecting waste liquid discharged from the flow chamber 210 and / or the impedance counting detection unit 400, and the waste liquid pool 826 is connected to the metering pump 830 for optical detection and / or the metering pump 840 for hemoglobin detection through the second negative pressure pipeline 1109 for providing negative pressure driving power for the metering pump 830 for optical detection and / or the metering pump 840 for hemoglobin detection.

[0205] In specific applications, 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 the second negative pressure pipeline 1109 connected to the waste liquid tank 826 can be provided with a negative pressure power source 828; when the second normal pressure control valve 1106 is opened, the waste liquid tank 826 can be set to a normal pressure environment to meet the pressure requirement of the second normal pressure pipeline 1108 connected to 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 can be switched to a positive pressure environment to discharge the waste liquid in the waste liquid tank 826 to the outside of the machine.

[0206] In this embodiment, the waste liquid pool 826 can also be set to a time-sharing multiplexing scheme with different pressures according to functional requirements, thereby reducing the cost and volume of the blood cell analyzer.

[0207] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of Embodiments 1 to 12 and will not be described in detail here.

[0208] Example 14:

[0209] Reference Figure 18 and Figure 19 As shown, the hematology analyzer provided in this embodiment differs from that in Example 13 primarily in that, in addition to Example 13, the pressure control device 1100 in this embodiment further includes at least one positive pressure line 1110. The waste liquid reservoir 826 is connected to the optical detection metering pump 830 and / or the hemoglobin detection metering pump 840 via the positive pressure line 1110 to provide positive pressure driving power for the optical detection metering pump 830 and / or the hemoglobin detection metering pump 840. In specific applications, the waste liquid reservoir 826 can be switched to a positive pressure environment by opening the second positive pressure control valve 1103, depending on functional requirements.

[0210] Apart from the above differences, other parts of the blood cell analyzer provided in this embodiment can be designed with reference to the corresponding parts of Embodiments 1 to 13 and will not be described in detail here.

[0211] The above description is only a preferred embodiment of the present invention and does not limit the patent scope of the present invention. Any equivalent structural transformation made by using the contents of the present description and drawings under the inventive concept of the present invention, or directly / indirectly applied in other related technical fields, is included in the patent protection scope of the present invention.

Claims

1. A blood cell analyzer, characterized in that: include: A sampling component, used for collecting samples to be tested; An optical channel reaction pool, which is used to provide a reaction site for the sample to be tested and the reagent to prepare an optical detection sample liquid; a first reagent providing device, the first reagent providing device being used to provide reagents for the optical channel reaction cell; an optical detection unit, the optical detection unit comprising a flow chamber and an optical detection element, the flow chamber having a detection zone for allowing the optical detection sample liquid to pass through while being carried by the diluent, and the optical detection element for detecting the optical detection sample liquid carried by the diluent through the detection zone; A hemoglobin detection unit, which is used to provide a reaction site for the sample to be tested and the reagent to prepare a hemoglobin detection sample liquid, and to detect the hemoglobin concentration of the hemoglobin detection sample liquid; a second reagent providing device, the second reagent providing device being used to provide reagents for the hemoglobin detection unit; An impedance counting detection sample preparation unit, the impedance counting detection sample preparation unit is used to provide a reaction field for the sample to be tested and the diluent to prepare an impedance counting detection sample; An impedance counting detection unit, configured to perform impedance counting detection on the impedance counting detection sample liquid; a diluent providing device, the diluent providing device being used to provide a diluent; a fluid power device, the fluid power device comprising a positive pressure providing unit, a negative pressure providing unit, a metering pump for optical detection, and a metering pump for hemoglobin detection; the metering pump for optical detection is respectively connected to the positive pressure providing unit, the negative pressure providing unit, the optical channel reaction pool, and the first reagent providing device, and is used to drive the reagent from the first reagent providing device to the optical channel reaction pool under the control of the positive pressure providing unit and the negative pressure providing unit; the metering pump for hemoglobin detection is respectively connected to the positive pressure providing unit, the negative pressure providing unit, the hemoglobin detection unit, and the second reagent providing device, and is used to drive the reagent from the second reagent providing device to the hemoglobin detection unit under the control of the positive pressure providing unit and the negative pressure providing unit; The conveying pipeline assembly, the sampling component, the optical detection unit, the optical channel reaction pool, the hemoglobin detection unit, the impedance counting detection sample preparation unit, the impedance counting detection unit, the first reagent providing device, the second reagent providing device, the diluent providing device and the fluid power device are connected through the conveying pipeline assembly to form a liquid circuit system. The average gas consumption of the liquid circuit system is less than or equal to 2.0 L / min within a detection cycle of completing hemoglobin detection, impedance counting detection and optical detection.

2. The blood cell analyzer according to claim 1, wherein The average gas consumption of the liquid system during one detection cycle of completing hemoglobin detection, impedance counting detection and optical detection is less than or equal to 1.0 L / min.

3. The blood cell analyzer according to claim 2, wherein: The average gas consumption of the liquid circuit system during one detection cycle of completing hemoglobin detection, impedance counting detection and optical detection is less than or equal to 0.5 L / min.

4. The blood cell analyzer according to any one of claims 1 to 3, wherein: The fluid power device also includes a first air circuit assembly and a second air circuit 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 circuit assembly, and 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 circuit assembly. The total volume of the quantitative pump for optical detection, the first air circuit assembly, the quantitative pump for hemoglobin detection and the second air circuit assembly is less than or equal to 20 mL.

5. The blood cell analyzer according to claim 4, wherein: The total volume of the quantitative pump for optical detection, the first gas circuit component, the quantitative pump for hemoglobin detection, and the second gas circuit component is less than or equal to 15 mL.

6. The blood cell analyzer according to claim 5, wherein: The total volume of the quantitative pump for optical detection, the first gas circuit component, the quantitative pump for hemoglobin detection, and the second gas circuit component is less than or equal to 10 mL.

7. The blood cell analyzer according to any one of claims 1 to 3, characterized in that: The positive pressure output by the positive pressure providing unit is less than or equal to 120 kPa.

8. The blood cell analyzer according to claim 7, wherein The positive pressure output by the positive pressure providing unit is less than or equal to 50 kPa; and / or the negative pressure output by the negative pressure providing unit is greater than or equal to -30 kPa.

9. The blood cell analyzer according to any one of claims 1 to 3, characterized in that: The positive pressure providing unit includes a first air pump, a first positive pressure control valve and a positive pressure output pipeline, one end of the positive pressure output pipeline is connected to the quantitative pump for optical detection and the quantitative pump for hemoglobin detection respectively, and the other end of the positive pressure output pipeline is connected to the first air pump through the first positive pressure control valve; The negative pressure providing unit includes 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 connected to the quantitative pump for optical detection and the quantitative pump for hemoglobin detection respectively, and the other end of the negative pressure output pipeline is connected to the second air pump through the first negative pressure control valve; The no-load flow rate of the first air pump and the no-load flow rate of the second air pump are both less than or equal to 4 L / min.

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

11. The blood cell analyzer according to claim 9, 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 according to claim 9, wherein: The positive pressure providing unit further includes a first pressure stabilizing component connected between the positive pressure output pipeline and the first positive pressure control valve; The negative pressure providing unit further includes a second pressure stabilizing component connected between the negative pressure output pipeline and the first negative pressure control valve.

13. The blood cell analyzer according to claim 12, wherein: The first pressure stabilizing component is a positive pressure air 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 between 80 mL and 200 mL.

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

15. The blood cell analyzer according to claim 13, wherein: The negative pressure chamber is also used as a waste liquid pool, and the delivery pipeline assembly includes a first drainage pipeline connected between the flow chamber and the negative pressure chamber and / or a second drainage pipeline connected between the impedance counting detection unit and the negative pressure chamber.

16. The blood cell analyzer according to claim 12, wherein: The first pressure stabilizing component is a first gas storage pipe; the second pressure stabilizing component is a second gas storage pipe.

17. The blood cell analyzer according to claim 9, wherein: The number of the positive pressure providing units and the number of the negative pressure providing units are both at least two, the number of the quantitative pumps for optical detection is at least two, and at least two of the quantitative pumps for optical detection and the quantitative pumps for hemoglobin detection are respectively connected to different positive pressure providing units and different negative pressure providing units.

18. The blood cell analyzer according to claim 17, wherein: Each of the optical detection metering pumps is connected one-to-one with the mutually independent positive pressure providing units, and is also connected one-to-one with the mutually independent negative pressure providing units.

19. The blood cell analyzer according to any one of claims 1 to 3, characterized in that: The optical channel reaction pool includes a first reaction pool and a second reaction pool, the first reagent supply device includes a first reagent supply unit and a second reagent supply unit, and the quantitative pump for optical detection includes a first quantitative pump and a second quantitative pump. The first quantitative pump is respectively connected to the positive pressure supply unit, the negative pressure supply unit, the first reaction pool, and the first reagent supply unit to drive the first reagent from the first reagent supply unit to the first reaction pool, and the second quantitative pump is respectively connected to the positive pressure supply unit, the negative pressure supply unit, the second reaction pool, and the second reagent supply unit to drive the second reagent from the second reagent supply unit to the second reaction pool.

20. The blood cell analyzer according to any one of claims 1 to 3, characterized in that: The optical channel reaction pool includes a first reaction pool and a second reaction pool, the first reagent supply device includes a first reagent supply unit, a second reagent supply unit, a third reagent supply unit and a fourth reagent supply unit, and the optical detection metering pump includes a first metering pump, a second metering pump, a third metering pump and a fourth metering pump, the first metering pump is respectively connected to the positive pressure supply unit, the negative pressure supply unit, the first reaction pool and the first reagent supply unit to drive the third reagent from the first reagent supply unit to the first reaction pool, and the second metering pump is respectively connected to the positive pressure supply unit, the negative pressure supply unit, the second reaction pool and the second reagent supply unit to drive the second reagent from the fourth reagent supply unit to the second reaction pool; The third metering pump is respectively connected to the positive pressure providing unit, the negative pressure providing unit, the first reaction tank and the third reagent providing unit to drive the fifth reagent from the third reagent providing unit to the first reaction tank, and the fourth metering pump is respectively connected to the positive pressure providing unit, the negative pressure providing unit, the second reaction tank and the fourth reagent providing unit to drive the sixth reagent from the fourth reagent providing unit to the second reaction tank.

21. The blood cell analyzer according to claim 20, wherein: The fluid power device also includes a first air circuit assembly and a second air circuit 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 circuit assembly, and 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 circuit assembly. The first air circuit assembly includes a first air valve, a second air valve, a third air valve and a fourth air valve, and the second air circuit assembly includes a fifth air valve. 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 to the positive pressure providing unit and the negative pressure providing unit through the second air valve; the third quantitative pump is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the third air valve; the fourth quantitative pump is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the fourth air valve; the quantitative pump for hemoglobin detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the fifth air valve.

22. The blood cell analyzer according to claim 20, wherein: At least two of the first metering pump, the second metering pump, the third metering pump, the fourth metering pump and the metering pump for hemoglobin detection are respectively connected to the positive pressure providing unit and the negative pressure providing unit through the same air valve.

23. The blood cell analyzer according to claim 22, wherein: The fluid power device also includes a first air circuit assembly and a second air circuit assembly. The metering pump for optical detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the first air circuit assembly, and the metering pump for hemoglobin detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the second air circuit assembly. The first air circuit assembly includes a first air valve and a second air valve, and the second air circuit assembly includes a fifth air valve. The first metering pump and the second metering pump are respectively connected to the positive pressure providing unit and the negative pressure providing unit through the first air valve; the third metering pump and the fourth metering pump are respectively connected to the positive pressure providing unit and the negative pressure providing unit through the second air valve; the metering pump for hemoglobin detection is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the fifth air valve.

24. The blood cell analyzer according to claim 22, wherein: The fluid power device also includes a first air circuit assembly and a second air circuit 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 circuit 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 circuit assembly. The first air circuit assembly includes a first air valve, and the second air circuit assembly is connected to the first air valve. 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 respectively connected to the positive pressure providing unit and the negative pressure providing unit through the first air valve.

25. The blood cell analyzer according to claim 21, wherein The length of the connecting pipe between each of the air valves and the metering pump is less than or equal to 20 cm; and / or, Each of the gas valves is a solenoid valve.

26. The blood cell analyzer according to claim 1, wherein The blood cell analyzer also includes a diluent reservoir, the delivery pipeline assembly also includes a first delivery pipeline and a second delivery pipeline, the fluid power device also includes a third air circuit assembly, the first delivery pipeline is connected between the diluent reservoir and the impedance counting detection unit, the second delivery pipeline 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 circuit assembly to drive the diluent from the diluent reservoir to the impedance counting detection unit, so that the impedance counting detection sample flows in the impedance counting detection unit under the influence of the diluent.

27. The blood cell analyzer according to claim 26, wherein: The fluid power device also includes a first syringe, and the delivery pipeline assembly also includes a diluent delivery pipeline connected between the first syringe and the flow chamber. The diluent providing device and the second delivery pipeline are respectively connected to the diluent delivery pipeline. The first syringe is used to drive the diluent from the diluent delivery pipeline to the flow chamber so that the optical detection sample liquid passes through the detection area under the influence of the diluent, and the first syringe is used to drive the diluent from the diluent providing device to the diluent storage tank.

28. The blood cell analyzer according to claim 26, wherein: The fluid power device also includes a first syringe and a fourth air circuit assembly. The delivery pipeline assembly also includes a diluent delivery pipeline. The diluent delivery pipeline is connected between the first syringe and the flow chamber. The diluent providing device is connected to the second delivery pipeline and the diluent delivery pipeline respectively. The first syringe is used to drive the diluent from the diluent delivery pipeline to the flow chamber so that the optical detection sample liquid passes through the detection area under the influence of the diluent. The negative pressure providing unit is connected to the diluent reservoir through the fourth air circuit assembly to drive the diluent from the diluent providing device to the diluent reservoir.

29. The blood cell analyzer according to claim 27 or 28, wherein: The delivery pipeline assembly also includes a third delivery pipeline, one end of which is connected to the hemoglobin detection unit and the other end is connected to the diluent delivery pipeline. The first syringe is also used to drive the diluent from the third delivery pipeline to the hemoglobin detection unit.

30. The blood cell analyzer according to claim 27 or 28, wherein: The delivery pipeline assembly also includes a fourth delivery pipeline, and the fluid power device also includes a sixth metering pump and a fifth air circuit assembly. The sixth metering pump is respectively connected to the positive pressure providing unit and the negative pressure providing unit through the fifth air circuit assembly, and is respectively connected to the hemoglobin detection unit and the diluent providing device through the fourth delivery pipeline, so as to drive the diluent from the diluent providing device to be delivered to the hemoglobin detection unit under the control of the positive pressure providing unit and the negative pressure providing unit.

31. The blood cell analyzer according to claim 27 or 28, wherein: The delivery pipeline assembly further includes an optical sample preparation pipeline, and the fluid dynamic device further includes a second syringe. The measuring range of the first syringe is greater than that of the second syringe. The optical sample preparation pipeline is connected to the optical channel reaction pool, the flow chamber, the second syringe, and the first syringe respectively. The first syringe is further used to drive the optical detection sample liquid from the optical channel reaction pool to the optical sample preparation pipeline, and the second syringe is used to drive the optical detection sample liquid from the optical sample preparation pipeline to the flow chamber.

32. The blood cell analyzer according to claim 27 or 28, wherein: The delivery pipeline assembly also includes an optical sample preparation pipeline. The fluid dynamic device also includes a second syringe, a seventh metering pump, and a sixth gas circuit assembly. The measurement range of the first syringe is greater than that of the second syringe. The optical sample preparation pipeline is respectively connected to the optical channel reaction pool, the flow chamber, the second syringe, and the seventh metering pump. The seventh metering pump is also respectively connected to the positive pressure providing unit and the negative pressure providing unit through the sixth gas circuit assembly. The seventh metering pump is used to drive the optical detection sample liquid from the optical channel reaction pool to the optical sample preparation pipeline under the control of the negative pressure providing unit. The second syringe is used to drive the optical detection sample liquid from the optical sample preparation pipeline to the flow chamber.

33. The blood cell analyzer according to claim 27 or 28, wherein: The impedance counting detection sample preparation unit is integrated with the hemoglobin detection unit. The hemoglobin detection unit is also used to provide a reaction field for the sample to be tested and the diluent to prepare the impedance counting detection sample liquid. The delivery pipeline assembly also includes an impedance counting sample preparation pipeline. The fluid power device also includes a second syringe. The range of the first syringe is greater than the range of the second syringe. The impedance counting sample preparation pipeline is respectively connected to the hemoglobin detection unit, the impedance counting detection unit, the second syringe and the first syringe. The first syringe is also used to drive the impedance counting detection sample liquid from the hemoglobin detection unit to the impedance counting sample preparation pipeline. The second syringe is used to drive the impedance counting detection sample liquid from the impedance counting sample preparation pipeline to the impedance counting detection unit.

34. The blood cell analyzer according to claim 27 or 28, wherein: The impedance counting detection sample preparation unit is integrally arranged with the hemoglobin detection unit. The hemoglobin detection unit is also used to provide a reaction field for the sample to be tested and the diluent to prepare the impedance counting detection sample liquid. The delivery pipeline assembly also includes an impedance counting sample preparation pipeline. The fluid power device also includes a second syringe, an eighth metering pump and a seventh air circuit assembly. The range of the first syringe is greater than the range of the second syringe. The impedance counting sample preparation pipeline is respectively connected to the hemoglobin detection unit, the impedance counting detection unit, the second syringe and the eighth metering pump. The eighth metering pump is also connected to the positive pressure providing unit and the negative pressure providing unit respectively through the seventh air circuit assembly. The eighth metering pump is used to drive the impedance counting detection sample liquid from the hemoglobin detection unit to the impedance counting sample preparation pipeline under the control of the negative pressure providing unit. The second syringe is used to drive the impedance counting detection sample liquid from the impedance counting sample preparation pipeline to the impedance counting detection unit.

35. The blood cell analyzer according to claim 31, wherein The second syringe is also connected to the sampling component to drive the sampling component to absorb the sample to be tested, and to drive the sample to be tested in the sampling component to be transported to the hemoglobin detection unit, the optical channel reaction pool and the impedance counting detection sample preparation unit for reaction.

36. The blood cell analyzer according to any one of claims 1 to 3, characterized in that: The delivery pipeline assembly includes a plurality of control valves for controlling the operation of the fluid system, and each of the control valves is a solenoid valve.

37. The blood cell analyzer according to any one of claims 1 to 3, wherein: The negative pressure providing unit includes a waste liquid pool, a negative pressure power source, a first normal pressure control valve, a first external pipeline, at least one first normal pressure pipeline and at least one first negative pressure pipeline. The first normal pressure control valve is connected to the waste liquid pool and the atmospheric pressure through the first external pipeline to set the waste liquid pool to a normal pressure environment. The negative pressure power source is connected to the waste liquid pool to set the waste liquid pool to a negative pressure environment. The waste liquid pool is connected to the flow chamber and / or the impedance counting detection unit through the first normal pressure pipeline to collect waste liquid discharged from the flow chamber and / or the impedance counting detection unit, and the waste liquid pool is connected to the optical detection metering pump and / or the hemoglobin detection metering pump through the first negative pressure pipeline to provide negative pressure driving power for the optical detection metering pump and / or the hemoglobin detection metering pump.

38. The blood cell analyzer according to claim 37, wherein: The negative pressure power source is a peristaltic pump, the negative pressure providing unit further includes a waste liquid barrel, and the negative pressure power source is connected between the waste liquid pool and the waste liquid barrel; or, The negative pressure power source is a syringe, and the negative pressure providing unit also includes a waste liquid barrel and a second negative pressure control valve. The second negative pressure control valve is respectively connected to the negative pressure power source, the waste liquid barrel and the waste liquid pool to control the on-off of the pipelines between the negative pressure power source, the waste liquid barrel and the waste liquid pool.

39. The blood cell analyzer according to any one of claims 1 to 3, wherein: The blood cell analyzer also includes a pressure control device, 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 includes a waste liquid pool, a waste liquid barrel, a second positive pressure control valve, a third negative pressure control valve, a drain valve, a second normal pressure control valve, a second external 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 pipeline to set 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 to set the waste liquid pool to a positive pressure environment, the third negative pressure The control valve is connected between the waste liquid pool and the negative pressure providing unit to place the waste liquid pool in a negative pressure environment, the drain valve is connected between the bottom of the waste liquid pool and the waste liquid barrel to cooperate with the positive pressure providing unit and the second positive pressure control valve to discharge the waste liquid out of the waste liquid pool, the waste liquid pool is connected to the flow chamber and / or the impedance counting detection unit through the second normal pressure pipeline to collect the waste liquid discharged from the flow chamber and / or the impedance counting detection unit, and the waste liquid pool is connected to the optical detection metering pump and / or the hemoglobin detection metering pump through the second negative pressure pipeline to provide negative pressure driving power for the optical detection metering pump and / or the hemoglobin detection metering pump.

40. The blood cell analyzer according to claim 39, wherein The pressure control device also includes 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 to provide positive pressure driving power for the quantitative pump for optical detection and / or the quantitative pump for hemoglobin detection.

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