POCT hematology analyzer

Abstract

Disclosed in the present application is a POCT hematology analyzer. The POCT hematology analyzer comprises: a cell counting assembly movable relative to a reagent kit, wherein the cell counting assembly comprises a main body provided with a front chamber and a rear chamber; a microporous sheet configured to isolate the front chamber from the rear chamber and provided with a micropore, the front chamber being in communication with the rear chamber by means of the micropore; and a first electrode, which penetrates and is arranged in the rear chamber and configured to be electrically connected to a test sample in the rear chamber, wherein the range of the shortest distance between the portion of the first electrode that penetrates and is arranged in the rear chamber and the micropore is 2-20 mm. By the above means, it is possible to prevent the first electrode from being too far away from or too close to the micropore, thereby reducing interference from other cells, minimizing bubble formation, and accordingly improving the accuracy of test results of the POCT hematology analyzer.

Description

POCT blood cell analyzer

[0001] Cross-reference to related applications

[0002] The present application claims priority to Chinese Patent Application No. 2024104267621, filed on April 10, 2024, entitled "POCT blood cell analyzer", Chinese Patent Application No. 202410444384X, filed on April 10, 2024, entitled "POCT blood cell analyzer", Chinese Patent Application No. 2024104307440, filed on April 10, 2024, entitled "POCT blood cell analyzer", Chinese Patent Application No. 2024207358825, filed on April 10, 2024, entitled "A POCT blood cell analyzer", Chinese Patent Application No. 2024207436434, filed on April 10, 2024, entitled "A POCT blood cell counter", the contents of which are incorporated herein by reference. TECHNICAL FIELD

[0003] The present application relates to the technical field of blood cell analysis, in particular to a POCT blood cell analyzer. BACKGROUND

[0004] The cell counter comprises a front cell, a front cell electrode, a rear cell, a rear cell electrode, and a gem hole sheet. The front cell is communicated with the rear cell through a gem hole of the gem hole sheet. One end of the rear cell electrode is arranged in the rear cell, and one end of the front cell electrode is arranged in the front cell. Among them, along the axial direction of the gem hole sheet, the distance between the rear cell electrode and the gem hole sheet is far, which may be interfered by other cells, resulting in low accuracy of the detection result of the cell counter. If the distance between the rear cell electrode and the gem hole sheet is too close, a narrow gap may be formed between the rear cell electrode and the gem hole sheet, and then bubbles are generated. When the size of the bubbles is close to that of the cells, the cell counting result may be larger, and the accuracy of the detection result of the cell counter is low.

[0005] SUMMARY

[0006] In view of the above problems, the present application provides a particle counting device and a POCT blood cell analyzer thereof, which can improve the accuracy of the detection result of the particle counting device.

[0007] In a first aspect, the present application provides a POCT blood cell analyzer, comprising a cell counting assembly movable relative to a reagent kit; the cell counting assembly comprises:

[0008] a main body provided with a front cavity and a rear cavity;

[0009] a micropore sheet for isolating the front cavity and the rear cavity, the micropore sheet being provided with micropores, and the front cavity and the rear cavity being communicated through the micropores;

[0010] a first electrode, penetrating into the rear cavity, the first electrode being configured to electrically connect to a detection sample in the rear cavity; a portion of the first electrode penetrating into the rear cavity has a shortest distance to the micropore in a range of 2-20 mm.

[0011] In a second aspect, the present application provides a POCT blood cell analyzer, comprising:

[0012] a main body, provided with a front cavity and a rear cavity;

[0013] a micropore sheet, configured to separate the front cavity and the rear cavity, the micropore sheet being provided with micropores, the front cavity and the rear cavity being communicated through the micropores;

[0014] a first electrode, penetrating into a side wall of the rear cavity, an axial direction of the first electrode being perpendicular to an axial direction of the micropore, the first electrode being configured to electrically connect to a detection sample in the rear cavity;

[0015] In some embodiments, along the axial direction of the micropore, the first electrode has a first distance to the micropore sheet, the first distance being in a range of 2-20 mm.

[0016] In some embodiments, along a radial direction of the micropore, an exposed portion of the first electrode in the rear cavity has a first length, the first length being in a range of 2-10 mm.

[0017] In some embodiments, the first length is in a range of 7-9 mm.

[0018] In some embodiments, the axial direction of the first electrode has a first intersection angle with the axial direction of the micropore, the first intersection angle being in a range of 80°-100°.

[0019] In some embodiments, the axial direction of the first electrode is perpendicular to the axial direction of the micropore.

[0020] In some embodiments, along the radial direction of the micropore, a free end of the first electrode has a second distance to a center of the micropore, the second distance being in a range of 0-1 mm.

[0021] In some embodiments, the cell counting assembly further comprises a second electrode, the second electrode being configured to electrically connect to a detection sample in the front cavity, along the axial direction of the micropore, the second electrode has a third distance to the micropore sheet, the third distance being in a range of 1-3 mm.

[0022] In some embodiments, the front chamber and the rear chamber have a partition plate therebetween, the partition plate is provided with the liquid inlet hole, the micro-hole sheet is arranged on a side of the partition plate facing the front chamber, and along an axial direction of the micro-hole, a projection of the micro-hole falls within the liquid inlet hole, and a diameter of the liquid inlet hole ranges from 1 mm to 5 mm.

[0023] In some embodiments, the cytometric assembly further comprises a first sealing ring arranged between the partition plate and the micro-hole sheet, an outer diameter of the first sealing ring ranges from 4 mm to 7 mm, and along the axial direction of the micro-hole, a thickness of the first sealing ring ranges from 1 mm to 2 mm.

[0024] In some embodiments, along the axial direction of the liquid inlet hole, a height of the liquid inlet hole ranges from 2 mm to 5 mm.

[0025] In some embodiments, the second electrode is provided with a first through hole along the axial direction of the micro-hole, the first through hole comprises a first hole section and a second hole section, the first hole section is arranged close to the micro-hole sheet relative to the second hole section, an inner diameter of the first hole section is smaller than an inner diameter of the second hole section, and in turn, an annular mesa is formed at a connection between the second hole section and the first hole section.

[0026] The cytometric assembly further comprises a pipette, one end of the pipette is arranged in the second hole section and abuts against the annular mesa, and the pipette is used to suck a detection sample from the kit.

[0027] In some embodiments, a ratio between the inner diameter of the pipette and the inner diameter of the first hole section ranges from 0.9 to 1.1.

[0028] In some embodiments, the cytometric assembly further comprises a second sealing ring, the second sealing ring is clamped between an end surface of the pipette and the annular mesa and abuts against a side peripheral wall of the second hole section.

[0029] In some embodiments, the cytometric assembly further comprises a pipette, the pipette is integrally formed with the second electrode.

[0030] In a second aspect, the present application provides a POCT blood cell analyzer, comprising:

[0031] a shell;

[0032] a loading seat for receiving a kit to be loaded;

[0033] a cytometric assembly arranged in the shell, the cytometric assembly being movable relative to the kit;

[0034] the cytometric assembly comprises:

[0035] a main body;

[0036] a liquid suction member cooperating with the main body to form a liquid suction channel for conveying liquid; the liquid suction channel is provided with a microporous sheet;

[0037] a liquid discharge member cooperating with the main body to form a liquid discharge channel for discharging liquid from the main body;

[0038] when the liquid suction channel is blocked, the cytometric component is configured to impact the liquid suction channel by gas in the main body, or to suck liquid by the liquid discharge member and impact the liquid suction channel by the liquid.

[0039] In some embodiments, after the liquid suction channel is impacted by the gas, and the liquid suction channel is blocked, the cytometric component is configured to suck liquid by the liquid discharge member and impact the liquid suction channel by the liquid.

[0040] In a third aspect, the present application provides a POCT blood cell analyzer, comprising:

[0041] a housing;

[0042] a loading seat for receiving a maintenance kit to be loaded, the maintenance kit comprising a plurality of cleaning liquid pools for storing cleaning liquid with different cleaning intensities;

[0043] a cytometric component arranged in the housing, the cytometric component being movable relative to the maintenance kit;

[0044] the cytometric component comprises:

[0045] a main body;

[0046] a liquid suction member cooperating with the main body to form a liquid suction channel for conveying liquid;

[0047] a liquid discharge member cooperating with the main body to form a liquid discharge channel for discharging liquid from the main body;

[0048] wherein the cytometric component is provided with a maintenance mode, in which the cytometric component is configured to suck the cleaning liquid from different cleaning liquid pools by the liquid suction member according to the cleaning intensity from high to low, and discharge the cleaning liquid in the main body to the maintenance kit by the liquid discharge member.

[0049] In a fourth aspect, the present application provides a POCT blood cell analyzer, comprising:

[0050] a housing;

[0051] a loading seat for receiving a kit to be loaded;

[0052] a cytometry component disposed in the housing, the cytometry component being movable relative to the cartridge;

[0053] the cytometry component comprises:

[0054] a main body provided with a front cavity and a rear cavity in communication;

[0055] a microporous sheet for isolating the front cavity and the rear cavity, the microporous sheet being provided with micropores, the front cavity and the rear cavity being in communication through the micropores;

[0056] a first electrode disposed in the rear cavity, the first electrode being used for electrical connection to a detection sample in the rear cavity;

[0057] a second electrode disposed in the front cavity, the second electrode being used for electrical connection to a detection sample in the front cavity;

[0058] a quick release member detachably connected with the main body, the quick release member being configured to cooperate with the main body to limit the microporous sheet and / or the second electrode in the front cavity.

[0059] In a fifth aspect, the application provides a POCT blood cell analyzer, comprising:

[0060] a housing;

[0061] a transfer mechanism disposed in the housing, the transfer mechanism being used for receiving and transferring a cartridge, the cartridge being used for storing a sample and / or a reagent;

[0062] a first driving member;

[0063] a cytometry component disposed in the housing, the cytometry component comprising:

[0064] a main body fixedly installed in the housing;

[0065] a suction and discharge assembly, the suction and discharge assembly being connected with the main body through a pipeline;

[0066] the first driving member being used for driving the suction and discharge assembly to move relative to the cartridge to complete a liquid suction and / or discharge operation.

[0067] Different from the prior art: the POCT blood cell analyzer of the application comprises: a main body provided with a front cavity and a rear cavity; a microporous sheet for isolating the front cavity and the rear cavity, the microporous sheet is provided with micropores, and the front cavity and the rear cavity are communicated through the micropores; a first electrode is arranged in the rear cavity, and the first electrode is used for electrically connecting the detection sample in the rear cavity; the shortest distance between the part of the first electrode arranged in the rear cavity and the micropore is 2-20mm. Compared with the distance between the rear pool electrode and the gemstone hole sheet in the prior art, by setting the shortest distance between the part of the first electrode arranged in the rear cavity and the micropore to be less than or equal to 20mm, the first electrode can be prevented from being too far away from the micropore, the interference of other cells can be reduced, and the accuracy of the detection result of the POCT blood cell analyzer can be improved. In addition, by setting the shortest distance between the part of the first electrode arranged in the rear cavity and the micropore to be greater than or equal to 2mm, the first electrode can be prevented from being too close to the micropore, the generation of bubbles can be reduced, and the accuracy of the detection result of the POCT blood cell analyzer can be improved. BRIEF DESCRIPTION OF DRAWINGS

[0068] In order to more clearly illustrate the technical solutions in the embodiments of the application, the drawings needed in the embodiment description will be briefly introduced. Obviously, the drawings in the following description are only some embodiments of the application, and other drawings can be obtained by those skilled in the art without creative labor.

[0069] Fig. 1 is a structural schematic diagram of a first embodiment of the POCT blood cell analyzer of the application;

[0070] Fig. 2 is a structural schematic diagram of a first embodiment of the cell counting component in Fig. 1;

[0071] Fig. 3 is a structural schematic diagram of a second embodiment of the cell counting component in Fig. 1;

[0072] Fig. 4 is a structural schematic diagram of a third embodiment of the cell counting component in Fig. 1;

[0073] Fig. 5 is a structural schematic diagram of a fourth embodiment of the cell counting component in Fig. 1;

[0074] Fig. 6 is a structural schematic diagram of a fifth embodiment of the cell counting component in Fig. 1;

[0075] Fig. 7 is a partially enlarged structural schematic diagram of region A in Fig. 2;

[0076] Fig. 8 is a simulation schematic diagram of the electric potential of the front cavity, the rear cavity, the micropore, the first electrode and the second electrode in Fig. 2;

[0077] Fig. 9 is a simulation schematic diagram of the electric field of the front cavity, the rear cavity, the micropore, the first electrode and the second electrode in Fig. 2;

[0078] Figure 10 is a simulation diagram of the electric field before the cells of the sample are detected in the microwell;

[0079] Figure 11 is a simulation diagram of the electric field in the microwell when the cells of the sample are detected;

[0080] Figure 12 is a simulation diagram of the electric field after the cells of the sample are detected in the microwell;

[0081] Figure 13 is a simulation diagram of the current density mode before, in and after the cells flow through the microwell;

[0082] Figure 14 is a simulation diagram of the first distance between the first electrode and the microwell;

[0083] Figure 15 is a simulation diagram of the first length of the exposed part of the first electrode in the back cavity;

[0084] Figure 16 is a frame diagram of a second embodiment of the POCT blood cell analyzer in Figure 1;

[0085] Figure 17 is a structure diagram of a third embodiment of the POCT blood cell analyzer of the present application;

[0086] Figure 18 is a structure diagram of a first embodiment of the cell counting assembly in Figure 17

[0087] Figure 19 is a structure diagram of a first embodiment of the maintenance kit in Figure 17;

[0088] Figure 20 is a structure diagram of a second embodiment of the maintenance kit in Figure 17;

[0089] Figure 21 is a structure diagram of a fourth embodiment of the POCT blood cell analyzer of the present application;

[0090] Figure 22 is a flow diagram of a first embodiment of the maintenance method of the POCT blood cell analyzer of the present application;

[0091] Figure 23 is a structure diagram of a third embodiment of the maintenance kit in Figure 17;

[0092] Figure 24 is a structure diagram of a fourth embodiment of the maintenance kit in Figure 17;

[0093] Figure 25 is a structure diagram of a partial enlargement of region A in Figure 18;

[0094] Figure 26 is a structure diagram of a first embodiment of the pressure mechanism of the present application;

[0095] Figure 27 is a structure diagram of a second embodiment of the pressure mechanism of the present application;

[0096] Figure 28 is a structure diagram of a fifth embodiment of the POCT blood cell analyzer of the present application;

[0097] FIG. 29 is a structural schematic diagram of a first embodiment of a cell counting assembly according to the present application;

[0098] FIG. 30 is a structural schematic diagram of a partial enlargement of region I in FIG. 29;

[0099] FIG. 31 is a structural schematic diagram of a first embodiment of a switch valve according to the present application;

[0100] FIG. 32 is a structural schematic diagram of a sixth embodiment of a POCT blood cell analyzer according to the present application;

[0101] FIG. 33 is a structural schematic diagram of a seventh embodiment of a POCT blood cell analyzer according to the present application;

[0102] FIG. 34 is a structural schematic diagram of a first embodiment of a cell counting assembly according to the present application;

[0103] FIG. 35 is a structural schematic diagram of a second embodiment of a cell counting assembly according to the present application;

[0104] FIG. 36 is a structural schematic diagram of an embodiment of a pressure building mechanism according to the present application;

[0105] FIG. 37 is a structural schematic diagram of an eighth embodiment of a POCT blood cell analyzer according to the present application. DETAILED DESCRIPTION

[0106] The embodiments of the technical solutions of the present application will be described in detail below with reference to the accompanying drawings. The following embodiments are only used to more clearly illustrate the technical solutions of the present application, and therefore only serve as examples, and cannot limit the protection scope of the present application.

[0107] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the present application belongs; the terms used herein are only for the purpose of describing specific embodiments and are not intended to limit the present application; the terms "include" and "have" and any variations thereof in the specification and claims of the present application and the above description of drawings are intended to cover non-exclusive inclusion.

[0108] In the description of the embodiments of the present application, the technical terms "first", "second", etc. are only used to distinguish different objects, and cannot be understood as indicating or implying relative importance or implicitly indicating the number, specific order or primary and secondary relationship of the indicated technical features. In the description of the embodiments of the present application, the meaning of "a plurality of" is two or more, unless otherwise explicitly specified.

[0109] Reference to“an embodiment” herein means that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the application. The appearances of the phrase“in an embodiment” in various places in the specification are not necessarily referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive of other embodiments. As will be apparent to those of ordinary skill in the art, embodiments described herein can be combined with other embodiments in accordance with the application.

[0110] In the description of the embodiments of the application, the term“and / or” only means an association relationship of the associated objects, which means that there can be three relationships, for example, A and / or B, which can mean that A exists alone, A and B exist together, and B exists alone. In addition, the character“ / ” herein generally means that the front and rear associated objects have an“or” relationship.

[0111] In the description of the embodiments of the application, the term“a plurality of” means more than two (including two), and similarly, “a plurality of groups” means more than two groups (including two groups), and “a plurality of pieces” means more than two pieces (including two pieces).

[0112] In the description of the embodiments of the application, the technical terms“center”,“longitudinal”,“transverse”,“length”,“width”,“thickness”,“upper”,“lower”,“front”,“rear”,“left”,“right”,“vertical”,“horizontal”,“top”,“bottom”,“inner”,“outer”,“clockwise”,“counterclockwise”,“axial”,“radial”,“circumferential” and the like indicate the orientation or positional relationship based on the orientation or positional relationship shown in the drawings, and are only for the convenience of describing the embodiments of the application and simplifying the description, and do not indicate or imply that the devices or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore cannot be understood as a limitation on the embodiments of the application.

[0113] In the description of the embodiments of the application, unless otherwise explicitly specified and limited, the technical terms“mounting”,“connection”,“connection”,“fixing” and the like should be understood broadly, for example, can be fixedly connected, or can be detachably connected, or can be integrated; can be mechanically connected, or can be electrically connected; can be directly connected, or can be indirectly connected through an intermediate medium; can be the internal communication of two elements or the interaction relationship between two elements. For those of ordinary skill in the art, the specific meaning of the above terms in the embodiments of the application can be understood according to the specific circumstances.

[0114] Please refer to FIG. 1, FIG. 2 and FIG. 7, FIG. 1 is a structural schematic diagram of a first embodiment of a POCT (point-of-care testing) blood cell analyzer according to the present application; FIG. 2 is a structural schematic diagram of a first embodiment of a cytometer component in FIG. 1; and FIG. 7 is a structural schematic diagram of a partial enlargement of region A in FIG. 2. The POCT blood cell analyzer 1 according to the present embodiment includes a cytometer component 10, and the cytometer component 10 can be relatively moved with a reagent box 20. The POCT blood cell analyzer 1 shown in FIG. 1 includes two cytometer components 10; in other embodiments, a person skilled in the art can design the number of cytometer components 10 according to actual needs, for example, the POCT blood cell analyzer 1 includes one cytometer component 10.

[0115] The relative movement of the cytometer component 10 and the reagent box 20 includes but is not limited to: the cytometer component 10 moves, and the reagent box 20 does not move; or the cytometer component 10 moves, and the reagent box 20 moves; or the cytometer component 10 does not move, and the reagent box 20 moves.

[0116] The cytometer component 10 includes a main body 11, a micropore sheet 12 and a first electrode 13. The main body 11 is provided with a front cavity 111 and a rear cavity 112, and the rear cavity 112 can also be referred to as a rear cell or a waste liquid cavity, etc.

[0117] The micropore sheet 12 is used to isolate the front cavity 111 and the rear cavity 112, and the micropore sheet 12 is provided with micropores 121. The front cavity 111 and the rear cavity 112 are communicated through the micropores 121. The micropore sheet 12 can also be referred to as a gemstone hole sheet, a gemstone sheet or a detection sheet, and the micropores 121 can also be referred to as gemstone holes or detection holes. For example, the detection sample in the front cavity 111 flows through the micropores 121 into the rear cavity 112 to allow the cells of the detection sample to flow through the micropores 121 one by one.

[0118] The first electrode 13 is arranged in the rear cavity 112, that is, the free end of the first electrode 13 is located in the rear cavity 112, and the other end of the first electrode 13 is located outside the rear cavity 112. The first electrode 13 can also be referred to as a rear cell electrode or a cathode.

[0119] Optionally, the free end of the first electrode 13 is electrically connected to the detection sample in the rear cavity 112. The detection sample flowing through the micropores 121 enters the rear cavity 112, and the free end of the first electrode 13 located in the rear cavity 112 is electrically connected to the detection sample in the rear cavity 112. The other end of the first electrode 13 located outside the rear cavity 112 is connected to an impedance detection circuit.

[0120] Optionally, the reagent box 20 is used to place the detection sample, and the cytometer component 10 is relatively moved with the reagent box 20 to suck the detection sample from the reagent box 20, so that the detection sample flows through the front cavity 111 and the micropores 121 into the rear cavity 112.

[0121] The shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 is in the range of 2-20 mm. The shortest distance L can be 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm, 16 mm, 17 mm, 18 mm, 19 mm, or 20 mm.

[0122] Alternatively, the shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 can be in the range of 4-12 mm. Alternatively, the shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 can be in the range of 4-16 mm. Alternatively, the shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 can be in the range of 6-16 mm.

[0123] Alternatively, the shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 refers to the shortest path of the cells of the sample liquid flowing from the microwell 121 to the portion of the first electrode 13 penetrating into the rear cavity 112.

[0124] As shown in FIG. 2, the microwell 121 has an axial direction Y and a radial direction X, the axial direction Y of the microwell 121 refers to the axial direction of the microwell 121, and the radial direction X of the microwell 121 refers to the direction of the radial plane of the microwell 121 passing through the axial center of the microwell 121.

[0125] In the case where the first electrode 13 is located above the microwell 121 and the axial direction of the first electrode 13 is perpendicular to the axial direction Y of the microwell 121, the shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 is a first distance L1, which refers to the distance between the first electrode 13 and the microwell 121 along the axial direction Y of the microwell 121.

[0126] As shown in FIGS. 3 and 4, in the case where the first electrode 13 is located above the microwell 121 and the axial direction of the first electrode 13 is perpendicular to the axial direction Y of the microwell 121, the shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 is the shortest straight-line distance between the microwell 121 and the first electrode 13.

[0127] As shown in FIG. 5, in the case where the first electrode 13 is located directly above the microwell 121 and the axial direction of the first electrode 13 is parallel to the axial direction Y of the microwell 121, the shortest distance L between the portion of the first electrode 13 penetrating into the rear cavity 112 and the microwell 121 is the shortest straight-line distance between the microwell 121 and the first electrode 13.

[0128] As shown in FIG. 6, in the case that the first electrode 13 is arranged in parallel with the micro-hole 121 in the bottom wall of the rear cavity 112, the shortest distance L between the part of the first electrode 13 penetrating into the rear cavity 112 and the micro-hole 121 is the shortest path of the cells in the sample liquid flowing from the micro-hole 121 to the part of the first electrode 13 penetrating into the rear cavity 112.

[0129] The other components of the cell counting assembly 10 shown in FIGS. 3-6 are the same as those of the cell counting assembly 10 shown in FIG. 2, which will not be described here.

[0130] The distance between the rear pool electrode and the gem hole sheet in the prior art is far, which can be interfered by other cells; or the distance between the rear pool electrode and the gem hole sheet is close, which further generates bubbles, resulting in low accuracy of the detection result. Compared with the prior art, the shortest distance L between the part of the first electrode 13 penetrating into the rear cavity 112 and the micro-hole 121 is in the range of 2-20 mm, and the shortest distance L between the part of the first electrode 13 penetrating into the rear cavity 112 and the micro-hole 121 is less than or equal to 20 mm, which avoids that the first electrode 13 is too far from the micro-hole 121, reduces the interference of other cells, and improves the accuracy of the detection result of the POCT blood cell analyzer 1; in addition, by setting the shortest distance L between the part of the first electrode 13 penetrating into the rear cavity 112 and the micro-hole 121 to be greater than or equal to 2 mm, the first electrode 13 can be prevented from being too close to the micro-hole 121, bubbles can be reduced, and the accuracy of the detection result of the POCT blood cell analyzer 1 can be improved.

[0131] Please refer to FIGS. 1, 2 and 7, and FIG. 7 is a partially enlarged structural schematic view of the region A in FIG. 2. In the embodiment, the first electrode 13 penetrates into the side wall of the rear cavity 112, the free end of the first electrode 13 is located in the rear cavity 112, and the other end of the first electrode 13 is located outside the rear cavity 112.

[0132] The axis of the first electrode 13 is arranged to cross the axis Y of the micro-hole 121, for example, the axis of the first electrode 13 and the axis Y of the micro-hole 121 cross in space, so that the detection sample flowing through the micro-hole 121 contacts the first electrode 13.

[0133] The first electrode 13 is electrically connected to the detection sample in the rear cavity 112; the detection sample flowing through the micro-hole 121 enters the rear cavity 112, the free end of the first electrode 13 is electrically connected to the detection sample in the rear cavity 112, and the other end of the first electrode 13 is connected to the impedance detection circuit.

[0134] The first electrode 13 has a first distance L1 with the micropore 121 along the axial direction Y of the micropore 121, and the first distance L1 ranges from 2 mm to 20 mm. The first distance L1 between the first electrode 13 and the micropore 121 refers to the distance between the first electrode 13 and the end face of the micropore 121 close to the first electrode 13. The first distance L1 can be 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm, 16 mm, 17 mm, 18 mm, 19 mm, or 20 mm.

[0135] Alternatively, the first distance L1 can range from 4 mm to 12 mm. Alternatively, the first distance L1 can range from 4 mm to 16 mm. Alternatively, the first distance L1 can range from 6 mm to 16 mm.

[0136] The distance between the rear pool electrode and the gem hole sheet in the prior art is far, which can be interfered by other cells. Alternatively, the distance between the rear pool electrode and the gem hole sheet is close, which can generate bubbles and reduce the accuracy of the detection result. Compared with the prior art, the first electrode 13 has a first distance L1 with the micropore 121 along the axial direction Y of the micropore 121, and the first distance L1 ranges from 4 mm to 12 mm. The first distance L1 between the first electrode 13 and the micropore 121 is less than or equal to 12 mm, which can avoid the first electrode 13 being too far from the micropore 121, reduce the interference of other cells, and improve the accuracy of the detection result of the POCT blood cell analyzer 1. In addition, the first distance L1 between the first electrode 13 and the micropore 121 is greater than or equal to 4 mm, which can avoid the first electrode 13 being too close to the micropore 121, reduce the generation of bubbles, and improve the accuracy of the detection result of the POCT blood cell analyzer 1.

[0137] According to some embodiments of the present application, please continue to refer to FIGS. 2 and 7, the cell counting assembly 10 further comprises a second electrode 14 and a first sealing ring 15.

[0138] The second electrode 14 is electrically connected to the detection sample in the front cavity 111, for example, the second electrode 14 is arranged in the front cavity 111, so that the second electrode 14 is electrically connected to the detection sample in the front cavity 111. The second electrode 14 can also be referred to as a front pool electrode or an anode.

[0139] The main body 11 has a partition plate 113 between the front cavity 111 and the rear cavity 112. The partition plate 113 is provided with a liquid inlet hole 114 for communicating the front cavity 111 and the rear cavity 112. For example, the liquid inlet hole 114 is located at the bottom of the rear cavity 112.

[0140] The micropore sheet 12 is arranged on the side of the partition plate 113 facing the front cavity 111, i.e. the micropore sheet 12 is arranged in the front cavity 111. The detection sample in the front cavity 111 flows through the micropores 121 and the liquid inlet hole 114 in sequence, so that the detection sample flows into the rear cavity 112.

[0141] Optionally, the first sealing ring 15 is arranged between the partition plate 113 and the micropore sheet 12, and the first sealing ring 15 is used to seal the gap between the micropore sheet 12 and the main body 11, so as to prevent the detection sample in the front cavity 111 from entering the rear cavity 112 without flowing through the micropores 121.

[0142] Optionally, the micropores 121 and the liquid inlet hole 114 are coaxially arranged. In other embodiments, the micropores 121 can be arranged in different axes.

[0143] In the present application, the counting method of the cell counting assembly 10 is derived from the Coulter counting principle. The Coulter counting principle refers to the use of a small hole to connect two water reservoirs filled with electrolyte, and two electrodes are arranged on the two sides of the small hole and are connected to a direct current power supply. When a microsphere passes through the small hole, the microsphere replaces the position of the conductive fluid, thereby changing the resistance in the small hole. The change is reflected by the current pulse between the electrodes. Each pulse change corresponds to a microsphere passing through the small hole, and the amplitude of the pulse is proportional to the volume of the fluid replaced. The detection circuit processes the current signal output by the electrode, and the larger the relative change of the current signal, the easier the microsphere signal is detected. The size of the relative change reflects the size of the microsphere.

[0144] The front cavity 111 and the rear cavity 112 of the cell counting assembly 10 of the present application are connected through the micropores 121, and the front cavity 111 and the rear cavity 112 both store detection samples. The first electrode 13 is electrically connected to the detection sample in the rear cavity 112, and the second electrode 14 is electrically connected to the detection sample in the front cavity 111. The impedance detection circuit provides power for the first electrode 13 and the second electrode 14. When the cells of the detection sample pass through the micropores 121 one by one, the cells change the resistance of the micropores 121, which is reflected by the current pulse between the first electrode 13 and the second electrode 14. The cell counting assembly 10 detects and processes the current signal of the first electrode 13 and the second electrode 14 to count the cells in the detection sample.

[0145] According to some embodiments of the present application, the axis of the first electrode 13 and the axis Y of the micropore 121 have a first intersection angle. The axis of the first electrode 13 and the axis Y of the micropore 121 can intersect or not intersect. For example, the first intersection angle refers to the angle formed by the projection of the axis of the first electrode 13 onto the axis Y of the micropore 121 and the axis Y of the micropore 121.

[0146] The first intersection angle is 80°-100°. The first intersection angle can be 80°, 85°, 90°, 95° or 100°. For example, the first intersection angle is greater than or equal to 80° and less than 90°, as shown in FIG. 3; or the first intersection angle is greater than 90° and less than or equal to 100°, as shown in FIG. 4.

[0147] In the prior art, the angle between the axial direction of the back pool electrode and the axial direction of the gem hole is too small (for example, less than 80°), the flow channel formed by the back pool electrode and the pool wall of the back pool is too small, and the flow channel can generate fluctuations; the angle between the axial direction of the back pool electrode and the axial direction of the gem hole is too large (for example, greater than 100°), the flow channel formed by the back pool electrode and the pool wall of the back pool is too large, and the back pool needs a large amount of detection samples, resulting in poor detection result accuracy of the cell counting component. Compared with the prior art, the axial direction of the first electrode 13 and the axial direction Y of the microwell 121 have a first intersection angle in the embodiment, the first intersection angle is 80°-100°, which can reduce the fluctuations of the flow channel between the first electrode 13 and the microwell sheet 12, avoid the need for too many detection samples in the back cavity 112, and improve the detection result accuracy of the cell counting component 10.

[0148] Optionally, the axial direction of the first electrode 13 and the axial direction Y of the microwell 121 are perpendicular to each other, that is, the axial direction of the first electrode 13 is the same as the radial direction X of the microwell 121. The embodiment of the present application is described by taking the axial direction of the first electrode 13 and the axial direction Y of the microwell 121 as an example.

[0149] The axial direction of the first electrode 13 and the axial direction Y of the microwell 121 are perpendicular to each other in the embodiment, so that the electric field distribution between the first electrode 13 and the microwell 121 is more uniform, and the detection result accuracy of the cell counting component 10 is improved.

[0150] According to some embodiments of the present application, along the radial direction X of the microwell 121, the exposed part of the first electrode 13 in the back cavity 112 has a first length D1.

[0151] In the case where the axial direction of the first electrode 13 and the axial direction Y of the microwell 121 are perpendicular to each other, the axial direction of the first electrode 13 is the same as the radial direction X of the microwell 121, and the first length D1 of the exposed part of the first electrode 13 in the back cavity 112 is equal to the distance between the free end of the first electrode 13 and the side wall of the back cavity 112 (i.e., the side wall close to the first electrode 13).

[0152] The first length D1 is 2-10 mm, and the first length D1 can be 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm or 10 mm.

[0153] The first electrode 13, the second electrode 14 and the microwell 121 of the cell counting component 10 are simulated based on the counting method of the cell counting component 10. A two-dimensional model is established in advance, as shown in FIG. 1, the first electrode 13 and the second electrode 14 are located on the two sides of the microwell 121, which are equivalent to symmetric electrodes; the second electrode 14 has a third distance L3 from the microwell sheet 12, and the two-dimensional model is established on the premise of fixing the third distance L3 between the second electrode 14 and the microwell 121 (i.e. the third distance L3 is constant).

[0154] An impedance detection circuit (for example, a direct current power supply) is connected with the second electrode 14 and the first electrode 13, and used to provide a 5V voltage for the second electrode 14; the first electrode 13 is connected with the negative electrode of the impedance detection circuit, i.e. the voltage of the first electrode 13 is 0V.

[0155] Please refer to FIGS. 8-9, FIG. 8 is a simulation schematic diagram of the electric potential of the front cavity, the rear cavity, the microwell, the first electrode and the second electrode in FIG. 2; and FIG. 9 is a simulation schematic diagram of the electric field of the front cavity, the rear cavity, the microwell, the first electrode and the second electrode in FIG. 2. In FIGS. 8 and 9, the abscissa represents the distance between the first electrode 13 and the second electrode 14 and the microwell 121, and the ordinate represents the first length D1 of the exposed part of the first electrode 13 in the rear cavity 112 or the length of the second electrode 14 along the radial direction of the second electrode 14.

[0156] In the simulation, the voltage of the second electrode 14 is 5V, the front cavity 111 and the rear cavity 112 store detection samples, the first electrode 13 is electrically connected with the detection sample in the rear cavity 112, the second electrode 14 is electrically connected with the detection sample in the front cavity 111, the third distance L3 between the second electrode 14 and the microwell 121 is about 2.5mm, the first distance L1 between the first electrode 13 and the microwell 121 is about 10.5mm, and the first length D1 of the exposed part of the first electrode 13 in the rear cavity 112 is 5mm.

[0157] As can be seen from FIGS. 8-9, the first electrode 13 and the second electrode 14 are located on the opposite sides of the microwell sheet 12, which are similar to symmetric electrodes; the closer to the position of the first electrode 13 and the position of the second electrode 14, the more concentrated the electric field lines are, the smaller the diameter of the microwell 121 of the microwell sheet 12 is, and the more concentrated the electric field lines in the microwell 121 are; the electric potential of the front cavity 111 and the electric potential of the rear cavity 112 are approximately uniform, and the microwell 121 has a potential difference.

[0158] The simulation is based on Figs. 8 and 9; see Figs. 10-12, Fig. 10 is a schematic diagram of the electric field mode of the cells of the detection sample before the micro-hole; Fig. 11 is a schematic diagram of the electric field mode of the cells of the detection sample in the micro-hole; and Fig. 12 is a schematic diagram of the electric field mode of the cells of the detection sample after the micro-hole. In Fig. 10, the cells are located in the front cavity 111, in Fig. 11, the cells are located in the micro-hole 121, and in Fig. 12, the cells are located in the rear cavity 112; the right column in Figs. 10, 11 and 12 represents the size of the electric field mode. It can be seen from Figs. 10-12 that the electric field mode changes most when the cells of the detection sample flow through the micro-hole 121, i.e., when the cells are located in the micro-hole 121.

[0159] See Fig. 13, which is a schematic diagram of the current density mode of the cells before, during and after flowing through the micro-hole; the vertical coordinate in Fig. 13 represents the current density mode, and the horizontal coordinate in Fig. 13 represents the distance through which the cells flow. The current density mode in the micro-hole 121 is represented by the current density mode, the cells are located in the micro-hole 121, and the current density mode changes most, i.e., the current density is large.

[0160] Based on Figs. 10-13, a two-dimensional model is established, i.e., simulation is performed based on Figs. 10-13, Figs. 14 and 15 are obtained, Fig. 14 is a schematic diagram of the simulation of the first distance between the first electrode and the micro-hole, and Fig. 15 is a schematic diagram of the simulation of the first length of the exposed part of the first electrode in the rear cavity.

[0161] As shown in Fig. 14, when the third distance L3 between the second electrode 14 and the micro-hole 121 remains unchanged, and the first length D1 of the exposed part of the first electrode 13 in the rear cavity 112 remains unchanged, the main factor affecting the electric field distribution between the first electrode 13 and the micro-hole 121 and the structural design of the cell counting assembly 10 is the first distance L1 between the first electrode 13 and the micro-hole 121; by changing the first distance L1 between the first electrode 13 and the micro-hole 121, and obtaining the current density mode change amount when the first distance L1 is at different values. The horizontal coordinate in Fig. 14 represents the first distance L1 between the first electrode 13 and the micro-hole 121, and the vertical coordinate in Fig. 14 represents the current density mode change amount; the greater the current density mode change amount, the higher the accuracy of the detection result of the cell counting assembly 10. It can be seen from Fig. 14 that the range of the first distance L1 is 2-20 mm, i.e., the first distance L1 can be 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm, 16 mm, 17 mm, 18 mm, 19 mm or 20 mm.

[0162] The horizontal coordinate in Fig. 14 can also represent the shortest distance L between the part of the first electrode 13 penetrating into the rear cavity 112 and the micro-hole 121, which will not be described again.

[0163] In combination with FIG. 14, the first distance L1 ranges from 2-20 mm, and the corresponding current density modulus variation is large, so it can be concluded that the first distance L1 ranges from 2-20 mm, which can reduce the interference of other cells and improve the detection result accuracy of the cytometry component 10.

[0164] When the first distance L1 ranges from 2-4 mm, the current density modulus variation slowly increases with the increase of the first distance L1; when the first distance L1 ranges from 4-10 mm, the current density modulus variation quickly increases with the increase of the first distance L1; when the first distance L1 ranges from 10-16 mm, the current density modulus variation slowly decreases with the increase of the first distance L1; when the first distance L1 ranges from 16-20 mm, the current density modulus variation quickly decreases with the increase of the first distance L1. Therefore, the first distance L1 can range from 4-12 mm. Alternatively, the first distance L1 can range from 4-16 mm. Alternatively, the first distance L1 can range from 6-16 mm. When the first distance L1 ranges from 8-10 mm, the current density modulus variation is larger, and the detection result accuracy of the cytometry component 10 is higher.

[0165] Based on the simulation diagram shown in FIG. 14, the first distance L1 between the first electrode and the micropore sheet can be 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm, 16 mm, 17 mm, 18 mm, 19 mm, or 20 mm.

[0166] As shown in FIG. 15, when the third distance L3 between the second electrode 14 and the micropore 121 remains unchanged, and the first distance L1 between the first electrode and the micropore sheet remains unchanged, the main factor affecting the electric field distribution between the first electrode 13 and the micropore 121 and the structural design of the cytometry component 10 is the first length D1 of the exposed part of the first electrode 13 in the rear cavity 112. By changing the first length D1 of the exposed part of the first electrode 13 in the rear cavity 112, and obtaining the current density modulus variation when the first length D1 is at different values. The abscissa of FIG. 15 represents the first length D1 of the exposed part of the first electrode 13 in the rear cavity 112, and the ordinate of FIG. 15 represents the current density modulus variation; the larger the current density modulus variation, the higher the detection result accuracy of the cytometry component 10. The first length D1 of the present application ranges from 2-10 mm, and the first length D1 can be 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, or 10 mm.

[0167] In combination with FIG. 15, the first length D1 ranges from 2 mm to 10 mm, and the corresponding current density modulus variation is large, so it can be concluded that the first length D1 ranges from 2 mm to 10 mm, which can reduce other cell interference and improve the detection result accuracy of the cytometry component 10.

[0168] When the first length D1 ranges from 2 mm to 8 mm, the current density modulus variation increases with the increase of the first length D1; when the first length D1 ranges from 8 mm to 10 mm, the current density modulus variation decreases with the increase of the first length D1; therefore, compared with the first length D1 ranging from 2 mm to 7 mm or 9 mm to 10 mm, when the first length D1 ranges from 7 mm to 9 mm, the current density modulus variation is larger, and the detection result accuracy of the cytometry component 10 is higher. When the first length D1 is 8 mm, the current density modulus variation is the largest, and the detection result accuracy of the cytometry component 10 is the highest.

[0169] Based on the simulation diagram shown in FIG. 15, the first length D1 of the exposed part of the first electrode 13 in the rear cavity 112 can be 8 mm, 7 mm, 9 mm, 6 mm, 10 mm, 5 mm, 4 mm, 3 mm or 2 mm.

[0170] In combination with FIGS. 14-15, it can be concluded that the first distance L1 ranges from 2 mm to 20 mm, and the first length D1 ranges from 2 mm to 10 mm, which can reduce other cell interference and improve the detection result accuracy of the cytometry component 10.

[0171] According to some embodiments of the present application, as shown in FIG. 2, in the case where the axial direction of the first electrode 13 and the axial direction Y of the microwell 121 are perpendicular to each other, along the radial direction X of the microwell 121, the free end of the first electrode 13 to the center of the microwell 121 has a second distance L2, and the second distance L2 ranges from 0 mm to 1 mm. Wherein, the second distance L2 can be 0 mm, 0.5 mm or 1 mm.

[0172] When the second distance L2 is 0 mm, that is, the free end of the first electrode 13 is aligned with the center of the microwell 121 along the radial direction X of the microwell 121, so that the electric field distribution between the free end of the first electrode 13 and the center of the microwell 121 is more uniform.

[0173] The second distance L2 of the free end of the first electrode 13 to the center of the microwell 121 in the embodiment ranges from 0 mm to 1 mm, and the relative position of the center of the microwell 121 and the free end of the first electrode 13 is used to make the electric field distribution between the free end of the first electrode 13 and the center of the microwell 121 more uniform, and improve the detection result accuracy of the cytometry component 10.

[0174] According to some embodiments of the present application, as shown in FIG. 2 and FIG. 7, along the axial direction Y of the micropore 121, the second electrode 14 and the micropore sheet 12 have a third distance L3, and the third distance L3 ranges from 1 mm to 3 mm; the third distance L3 can be 1 mm, 2 mm, or 3 mm.

[0175] Optionally, the cytometry component 10 further comprises a third sealing ring 16, which is arranged between the second electrode 14 and the micropore sheet 12 to seal the second electrode 14 and the micropore sheet 12. In this embodiment, the front cavity 111 can refer to the space formed between the micropore sheet 12, the third sealing ring 16, and the second electrode 14; for example, along the axial direction Y of the micropore 121, the height of the front cavity 111 is the same as the height of the third sealing ring 16.

[0176] The third distance L3 of this embodiment ranges from 1 mm to 3 mm, so as to arrange the third sealing ring 16 between the second electrode 14 and the micropore sheet 12 to seal the second electrode 14 and the micropore sheet 12.

[0177] According to some embodiments of the present application, along the axial direction Y of the micropore 121, the projection of the micropore 121 falls into the liquid inlet hole 114.

[0178] As shown in FIG. 8 and FIG. 9, the electric field lines of the front cavity 111 and the electric field lines of the rear cavity 112 are not completely uniform, so that the cells of the detection sample flowing through the micropore 121 from different positions will produce different current signals; in order to improve the detection accuracy of the cytometry component 10, the cells of the detection sample need to pass through the front cavity 111 and the micropore 121 along a straight line to enter the rear cavity 112.

[0179] The projection of the micropore 121 of this embodiment falls into the liquid inlet hole 114, that is, the micropore 121 is arranged corresponding to the liquid inlet hole 114, so as to ensure the consistency of the cells of the detection sample flowing through the micropore 121 and improve the detection accuracy of the cytometry component 10.

[0180] The diameter of the liquid inlet hole 114 ranges from 1 mm to 5 mm; the diameter of the liquid inlet hole 114 can be 1 mm, 2 mm, 3 mm, 4 mm, or 5 mm.

[0181] The diameter of the liquid inlet hole 114 of this embodiment ranges from 1 mm to 5 mm, so as to facilitate the projection of the micropore 121 falling into the liquid inlet hole 114 along the axial direction Y of the micropore 121, ensure the consistency of the cells of the detection sample flowing through the micropore 121, and improve the detection accuracy of the cytometry component 10.

[0182] Optionally, along the axial direction of the liquid inlet hole 114, the height of the liquid inlet hole 114 ranges from 2 mm to 5 mm; the height of the liquid inlet hole 114 can be 2 mm, 3 mm, 4 mm, or 5 mm.

[0183] The axial direction of the liquid inlet hole 114 is the same as the axial direction Y of the micropore 121; in the axial direction Y of the micropore 121, the height of the liquid inlet hole 114 ranges from 2 mm to 5 mm, which can improve the stability of the cells of the detection sample flowing through the micropore 121.

[0184] According to some embodiments of the present application, the outer diameter of the first sealing ring 15 ranges from 4 mm to 7 mm, and the outer diameter of the first sealing ring 15 can be 4 mm, 5 mm, 6 mm or 7 mm. In the axial direction Y of the micropore 121, the thickness of the first sealing ring 15 ranges from 1 mm to 2 mm, and the thickness of the first sealing ring 15 can be 1 mm, 1.5 mm or 2 mm.

[0185] The outer diameter of the first sealing ring 15 of the present embodiment ranges from 4 mm to 7 mm; in the axial direction Y of the micropore 121, the thickness of the first sealing ring 15 ranges from 1 mm to 2 mm; which ensures the consistency of the cells of the detection sample flowing through the micropore 121, and improves the detection accuracy of the cytometric component 10.

[0186] According to some embodiments of the present application, as shown in FIGS. 1, 2 and 7, the second electrode 14 of the present embodiment is provided with a first through hole 141 in the axial direction Y of the micropore 121.

[0187] The first through hole 141 includes a first hole section 142 and a second hole section 143, and the first hole section 142 is arranged closer to the micropore sheet 12 relative to the second hole section 143; the inner diameter of the first hole section 142 is smaller than the inner diameter of the second hole section 143, and in turn forms an annular mesa 144 at the connection between the second hole section 143 and the first hole section 142.

[0188] The cytometric component 10 of the present embodiment further includes a pipette 17 and a connecting piece 18, one end of the pipette 17 is arranged in the second hole section 143 and abuts against the annular mesa 144. The pipette 17 communicates with the front cavity 111 through the first hole section 142, and the pipette 17 is used to suck the detection sample from the reagent box 20, so that the detection sample flows through the pipette 17 and the first hole section 142 into the front cavity 111.

[0189] The main body 11 is provided with a through hole 118, and the connecting piece 18 is arranged in the through hole 118, and the connecting piece 18 is used to electrically connect with the second electrode 14, so that the impedance detection circuit supplies power to the second electrode 14 through the connecting piece 18. For example, the second electrode 14 is provided with a threaded hole, and one end of the connecting piece 18 is provided with a thread matched with the threaded hole, and the one end of the connecting piece 18 is arranged in the threaded hole.

[0190] Optionally, the ratio of the inner diameter of the pipette 17 to the inner diameter of the first hole section 142 ranges from 0.9 to 1.1. The ratio of the inner diameter of the pipette 17 to the inner diameter of the first hole section 142 can be 0.9, 1 or 1.1.

[0191] The ratio of the inner diameter of the pipette 17 to the inner diameter of the first hole section 142 is between 0.9-1.1, which can ensure the consistency of the cells of the detection sample flowing through the micropores 121, and improve the detection accuracy of the cytometer assembly 10.

[0192] Optionally, referring to FIGS. 2 and 7, the first through-hole 141 further includes a third hole section 145, the third hole section 145 is arranged close to the micropore sheet 12 relative to the first hole section 142; the inner diameter of the first hole section 142 is smaller than the inner diameter of the third hole section 145. The micropore sheet 12, the third sealing ring 16, and the third hole section 145 of the second electrode 14 form the front cavity 111.

[0193] According to some embodiments of the present application, referring to FIGS. 2 and 7, the cytometer assembly 10 of the present embodiment further includes a second sealing ring 19, the second sealing ring 19 is clamped between the end face of the pipette 17 and the annular mesa 144, and abuts against the side peripheral wall of the second hole section 143.

[0194] The second sealing ring 19 of the present embodiment is clamped between the end face of the pipette 17 and the annular mesa 144, and abuts against the side peripheral wall of the second hole section 143, which can seal the end face of the pipette 17 and the second electrode 14 through the second sealing ring 19, and avoid the detection sample from overflowing from the second electrode 14.

[0195] Optionally, the cytometer assembly 10 of the present embodiment further includes a drainage pipe 115 and a pressure interface 116, wherein the partition plate 113 is provided with a drainage hole 117, the drainage hole 117 is arranged spaced apart from the liquid inlet hole 114, the drainage pipe 115 communicates with the drainage hole 117; the drainage pipe 115 discharges the detection sample that has completed counting from the rear cavity 112. The pressure interface 116 is arranged at the top of the rear cavity 112 to build pressure in the rear cavity 112.

[0196] According to some embodiments of the present application, the difference between the cytometer assembly 10 shown in FIG. 2 and the cytometer assembly of the present embodiment is that the cytometer assembly of the present embodiment further includes a pipette (not shown in the figure), the pipette is integrally formed with the second electrode. That is, at least part of the pipette of the present embodiment is used as the second electrode, that is, the pipette and the second electrode are the same component, which can reduce the components of the cytometer assembly and reduce the cost.

[0197] The present application further provides a POCT blood cell analyzer 1, as shown in FIGS. 1, 2, 7 and 16, the POCT blood cell analyzer 1 includes a pressure building assembly 101, a moving assembly 102, and the cytometer assembly 10 of the above embodiments.

[0198] The cell counting assembly 10 can be arranged on the moving assembly 102, and the moving assembly 102 is used to drive the cell counting assembly 10 to move, so that the cell counting assembly 10 moves relative to the reagent box 20; and the pressure building assembly 101 is connected with the cell counting assembly 10 through a pipeline.

[0199] When the POCT blood cell analyzer 1 works, the moving assembly 102 drives the cell counting assembly 10 to move, so that the cell counting assembly 10 is located on the reagent box 20; the pressure building assembly 101 builds negative pressure on the rear cavity 112 through the pressure interface 116; under the action of the negative pressure, the cell counting assembly 10 sucks the detection sample from the reagent box 20, and the detection sample flows through the pipette 17, the second electrode 14, the microporous sheet 12 and the liquid inlet hole 114 into the rear cavity 112. When the first electrode 13 is electrically connected with the detection sample in the rear cavity 112, the cell counting assembly 10 counts the detection sample through the first electrode 13 and the second electrode 14.

[0200] When the cell counting assembly 10 completes counting, the pressure building assembly 101 builds positive pressure on the rear cavity 112 through the pressure interface 116; under the action of the positive pressure, the detection sample in the rear cavity 112 flows through the liquid outlet hole 117 and the liquid outlet pipe 115 and is discharged.

[0201] As described above, the shortest distance L between the part of the first electrode 13 arranged in the rear cavity 112 and the micropore 121 is 2-20 mm, and the shortest distance L between the part of the first electrode 13 arranged in the rear cavity 112 and the micropore 121 is less than or equal to 20 mm, so that the first electrode 13 is not too far away from the micropore 121, other cell interference is reduced, and the accuracy of the detection result of the POCT blood cell analyzer 1 is improved; in addition, by setting the shortest distance L between the part of the first electrode 13 arranged in the rear cavity 112 and the micropore 12 to be greater than or equal to 2 mm, the first electrode 13 can be prevented from being too close to the micropore 121, bubbles can be reduced, and the accuracy of the detection result of the POCT blood cell analyzer 1 is improved.

[0202] Please refer to FIG. 17 and FIG. 18, FIG. 17 is a structural schematic diagram of a third embodiment of the POCT blood cell analyzer of the present application; and FIG. 18 is a structural schematic diagram of a first embodiment of the cell counting assembly in FIG. 17.

[0203] The POCT blood cell analyzer 1 of the embodiment includes a shell (not shown in the figure), a loading seat (not shown in the figure) and a cell counting assembly 10. The cell counting assembly 10 can also be referred to as a blood cell counting mechanism or a blood cell counting pool.

[0204] The cell counting assembly 10 is arranged in the shell, and the loading seat is used for receiving the maintenance kit 40. For example, the loading seat is arranged in the shell, and when the loading seat receives the maintenance kit 40, the loading seat moves out of the shell, so that the maintenance kit 40 is placed on the loading seat and the maintenance kit 40 is moved into the shell, thereby realizing that the loading seat receives the maintenance kit 40.

[0205] The cell counting assembly 10 can move relative to the maintenance kit 40. Specifically, the cell counting assembly 10 moves, and the maintenance kit 40 does not move; or the cell counting assembly 10 moves, and the maintenance kit 40 moves; or the cell counting assembly 10 does not move, and the maintenance kit 40 moves.

[0206] The maintenance kit 40 includes a plurality of cleaning liquid pools 21, and the plurality of cleaning liquid pools 21 are used for storing cleaning liquids with different cleaning intensities. For example, the plurality of cleaning liquid pools 21 are arranged adjacent to each other in order from high to low cleaning intensity, or the plurality of cleaning liquid pools 21 are arranged randomly.

[0207] The cell counting assembly 10 of the embodiment includes a main body 11, a liquid suction member 110, and a liquid discharge member 120. The liquid suction member 110 cooperates with the main body 11 to form a liquid suction channel for conveying liquid, and the liquid discharge member 120 cooperates with the main body 11 to form a liquid discharge channel for discharging liquid from the main body. The liquid suction member 110 can be the liquid suction tube 17 of the above embodiment, and the liquid discharge member 120 can be the liquid discharge tube 115 of the above embodiment.

[0208] Optionally, the main body 11 is provided with an inner cavity 130, and the inner cavity 130 is in communication with the liquid discharge channel and the liquid suction channel, respectively. The inner cavity 130 can also be referred to as a rear cavity or a rear pool, that is, the inner cavity 130 can be the rear cavity 112 of the above embodiment.

[0209] The cell counting assembly 10 is pre-provided with a maintenance mode. Specifically, when the detection number of the cell counting assembly 10 reaches a preset number, or the POCT blood cell analyzer 1 appears abnormal, or before the POCT blood cell analyzer 1 is started or turned off, or the POCT blood cell analyzer 1 prompts that maintenance is needed, the cell counting assembly 10 enters the maintenance mode. The detection number of the cell counting assembly 10 refers to the number of times that the cell counting assembly 10 completes counting detection on the detection liquid. The abnormality of the POCT blood cell analyzer 1 includes but is not limited to that the microporous sheet 12 of the cell counting assembly 10 is blocked or the liquid suction channel is blocked.

[0210] The cell counting assembly 10 is pre-provided with a maintenance mode, and it is not necessary to be provided with a maintenance mode; when the cell counting assembly 10 meets the maintenance condition, the cell counting assembly 10 performs automatic maintenance, which also belongs to the maintenance mode of the present application.

[0211] In the maintenance mode, the cytometry component 10 is arranged to draw the cleaning liquid from the different cleaning liquid pools 21 through the liquid suction member 110 according to the cleaning intensity from high to low, and discharge the cleaning liquid in the main body 11 to the maintenance reagent box 40 through the liquid discharge member 120.

[0212] For example, when the cytometry component 10 enters the maintenance mode, the cytometry component 10 draws the cleaning liquid from the cleaning liquid pool 21 with the highest cleaning intensity through the liquid suction member 110, and discharges the cleaning liquid in the main body 11 to the maintenance reagent box 40 through the liquid discharge member 120. The cytometry component 10 draws the cleaning liquid from the cleaning liquid pool 21 with the higher cleaning intensity through the liquid suction member 110, and discharges the cleaning liquid in the main body 11 to the maintenance reagent box 40 through the liquid discharge member 120. The cytometry component 10 draws the cleaning liquid from the cleaning liquid pool 21 with the weakest cleaning intensity through the liquid suction member 110, and discharges the cleaning liquid in the main body 11 to the maintenance reagent box 40 through the liquid discharge member 120.

[0213] In the maintenance mode, the cytometry component 10 is arranged to draw the cleaning liquid from the different cleaning liquid pools 21 through the liquid suction member 110 according to the cleaning intensity from high to low, and discharge the cleaning liquid in the main body 11 to the maintenance reagent box 40 through the liquid discharge member 120. In the maintenance mode, the cytometry component 10 is cleaned multiple times according to the cleaning intensity from high to low, so that the cytometry component 10 is cleaned and maintained, the waste liquid residues in the inner cavity 130, the liquid suction channel and the liquid discharge channel of the main body 11 are reduced, and the detection result accuracy of the POCT blood cell analyzer 1 is improved. In addition, the micro-hole sheet 12 of the cytometry component 10 is cleaned multiple times according to the cleaning intensity from high to low, so that the probability of hole blockage of the micro-hole sheet 12 is reduced, the frequency of replacing the micro-hole sheet 12 is reduced, and the cost is reduced. In addition, in the maintenance mode, the cytometry component 10 is cleaned multiple times according to the cleaning intensity from high to low, so that the cleaning effect of the cytometry component 10 is improved, and the detection result accuracy of the POCT blood cell analyzer 1 is improved.

[0214] According to some embodiments of the present application, please refer to FIGS. 17-19, FIG. 19 is a structural schematic diagram of the first embodiment of the maintenance reagent box in FIG. 17. The plurality of cleaning liquid pools 21 of the embodiment include a first cleaning liquid pool 211, a second cleaning liquid pool 212 and a third cleaning liquid pool 213, which are sequentially arranged along the extension direction of the maintenance reagent box 40.

[0215] The cleaning intensity of the cleaning liquid in the first cleaning liquid pool 211 is greater than the cleaning intensity of the cleaning liquid in the second cleaning liquid pool 212, and the cleaning intensity of the cleaning liquid in the second cleaning liquid pool 212 is greater than or equal to the cleaning intensity of the cleaning liquid in the third cleaning liquid pool 213.

[0216] For example, the cleaning liquid in the first cleaning liquid pool 211 is a strong alkaline cleaning liquid, the cleaning liquid in the second cleaning liquid pool 212 is a weak acid cleaning liquid, and the cleaning liquid in the third cleaning liquid pool 213 is pure water; or the cleaning liquid in the first cleaning liquid pool 211 is a strong alkaline cleaning liquid, the cleaning liquid in the second cleaning liquid pool 212 is pure water, and the cleaning liquid in the third cleaning liquid pool 213 is pure water.

[0217] The cell counting assembly 10 sequentially sucks the cleaning liquid from the first cleaning liquid pool 211, the second cleaning liquid pool 212 and the third cleaning liquid pool 213 through the liquid suction member 110.

[0218] Specifically, in the maintenance mode, the cell counting assembly 10 sucks the cleaning liquid from the first cleaning liquid pool 211 through the liquid suction member 110 to soak the inner cavity 130 to remove foreign matters in the inner cavity 130, and discharges the cleaning liquid in the inner cavity 130 of the main body 11 to the maintenance kit 40 through the liquid discharge member 120. The cell counting assembly 10 sucks the cleaning liquid from the second cleaning liquid pool 212 through the liquid suction member 110 to clean the inner cavity 130, and discharges the cleaning liquid in the inner cavity 130 of the main body 11 to the maintenance kit 40 through the liquid discharge member 120. The cell counting assembly 10 sucks the cleaning liquid from the third cleaning liquid pool 213 through the liquid suction member 110 to clean the inner cavity 130, and discharges the cleaning liquid in the inner cavity 130 of the main body 11 to the maintenance kit 40 through the liquid discharge member 120.

[0219] The cell counting assembly 10 of the embodiment sequentially sucks the cleaning liquid from the first cleaning liquid pool 211, the second cleaning liquid pool 212 and the third cleaning liquid pool 213 through the liquid suction member 110, wherein the cleaning strength of the cleaning liquid in the first cleaning liquid pool 211 is greater than the cleaning strength of the cleaning liquid in the second cleaning liquid pool 212, and the cleaning strength of the cleaning liquid in the second cleaning liquid pool 212 is greater than or equal to the cleaning strength of the cleaning liquid in the third cleaning liquid pool 213. The liquid suction channel, the inner cavity 130 and the liquid discharge channel can be cleaned from high to low according to the cleaning strength, the cleaning effect of the cell counting assembly 10 is improved, the cleaning liquid residue is reduced, and the detection result accuracy of the POCT blood cell analyzer 1 is improved.

[0220] According to some embodiments of the present application, the cell counting assembly 10 of the embodiment is configured to discharge the cleaning liquid in the main body 11 to the cleaning liquid pool 21 from which the cleaning liquid has been sucked through the liquid discharge member 120.

[0221] The cell counting assembly 10 sucks the cleaning liquid from the cleaning liquid pool 21 through the liquid suction member 110, and then discharges the cleaning liquid in the main body 11 to the cleaning liquid pool 21 through the liquid discharge member 120.

[0222] For example, the cell counting assembly 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 is inserted into the first washing liquid pool 211, and the cell counting assembly 10 sucks the washing liquid from the first washing liquid pool 211 through the liquid suction member 110. When the liquid suction member 110 finishes sucking the washing liquid from the first washing liquid pool 211, the cell counting assembly 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 is inserted into the second washing liquid pool 212, the liquid discharge member 120 is inserted into the first washing liquid pool 211, and the cell counting assembly 10 discharges the washing liquid in the main body 11 to the first washing liquid pool 211 through the liquid discharge member 120, thereby completing the first washing of the cell counting assembly 10. The cell counting assembly 10 sucks the washing liquid from the second washing liquid pool 212 through the liquid suction member 110. When the liquid suction member 110 finishes sucking the washing liquid from the second washing liquid pool 212, the cell counting assembly 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 is inserted into the third washing liquid pool 213, the liquid discharge member 120 is inserted into the second washing liquid pool 212, and the cell counting assembly 10 discharges the washing liquid in the main body 11 to the second washing liquid pool 212 through the liquid discharge member 120, thereby completing the second washing of the cell counting assembly 10. The cell counting assembly 10 sucks the washing liquid from the third washing liquid pool 213 through the liquid suction member 110 and discharges the washing liquid in the main body 11 to the second washing liquid pool 212 through the liquid discharge member 120, or the cell counting assembly 10 can be moved relative to the maintenance kit 40 so that the liquid discharge member 120 is inserted into the third washing liquid pool 213 and discharges the washing liquid in the main body 11 to the third washing liquid pool 213 through the liquid discharge member 120, thereby completing the third washing of the cell counting assembly 10.

[0223] Optionally, when the liquid suction member 110 of the cell counting assembly 10 is inserted into the first washing liquid pool 211, the liquid discharge member 120 of the cell counting assembly 10 is located outside the first washing liquid pool 211, for example, the liquid discharge member 120 is located on the side of the first washing liquid pool 211 away from the second washing liquid pool 212.

[0224] Optionally, the cytometric component 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 and the liquid discharge member 120 are inserted into the first cleaning liquid pool 211, cleaning liquid is sucked from the first cleaning liquid pool 211 by the liquid suction member 110, and cleaning liquid in the main body 11 is discharged to the first cleaning liquid pool 211 by the liquid discharge member 120, thereby completing the first cleaning of the cytometric component 10. The cytometric component 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 and the liquid discharge member 120 are inserted into the second cleaning liquid pool 212, cleaning liquid is sucked from the second cleaning liquid pool 212 by the liquid suction member 110, and cleaning liquid in the main body 11 is discharged to the second cleaning liquid pool 212 by the liquid discharge member 120, thereby completing the second cleaning of the cytometric component 10. The cytometric component 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 and the liquid discharge member 120 are inserted into the third cleaning liquid pool 213, cleaning liquid is sucked from the third cleaning liquid pool 213 by the liquid suction member 110, and cleaning liquid in the main body 11 is discharged to the third cleaning liquid pool 213 by the liquid discharge member 120, thereby completing the third cleaning of the cytometric component 10.

[0225] The cytometric component 10 of the embodiment is arranged to discharge cleaning liquid in the main body 11 to the cleaning liquid pool 21 from which the cleaning liquid has been sucked by the liquid discharge member 120, without discharging the cleaning liquid in the main body 11 to the waste liquid pool, which is simple in operation and improves the detection efficiency of the POCT blood cell analyzer 1. In addition, the maintenance kit 40 does not need to be additionally provided with a waste liquid pool, which reduces the volume of the maintenance kit 40 and reduces the cost.

[0226] According to some embodiments of the present application, the plurality of cleaning liquid pools 21 of the embodiment are arranged in order of decreasing cleaning strength, for example, the plurality of cleaning liquid pools 21 include the first cleaning liquid pool 211, the second cleaning liquid pool 212, and the third cleaning liquid pool 213, and the first cleaning liquid pool 211, the second cleaning liquid pool 212, and the third cleaning liquid pool 213 are arranged in order of decreasing cleaning strength.

[0227] The cytometric component 10 is arranged to insert the liquid suction member 110 into the current cleaning liquid pool 21 from which cleaning liquid is currently being sucked, while inserting the liquid discharge member 120 into the previous cleaning liquid pool 21 adjacent to the current cleaning liquid pool 21 from which cleaning liquid has been sucked.

[0228] For example, the suction member 110 of the cytometric component 10 is inserted into the second washing liquid pool 212 while the discharge member 120 is inserted into the first washing liquid pool 211, where the second washing liquid pool 212 is the current washing liquid pool 21 from which the washing liquid is currently being sucked, and the first washing liquid pool 211 is the previous washing liquid pool 21 adjacent to the current washing liquid pool 21 from which the washing liquid has been sucked; or the suction member 110 of the cytometric component 10 is inserted into the third washing liquid pool 213 while the discharge member 120 is inserted into the second washing liquid pool 212, where the third washing liquid pool 213 is the current washing liquid pool 21 from which the washing liquid is currently being sucked, and the second washing liquid pool 212 is the previous washing liquid pool 21 adjacent to the current washing liquid pool 21 from which the washing liquid has been sucked.

[0229] The plurality of washing liquid pools 21 of the embodiment are arranged in order of decreasing washing strength, and the cytometric component 10 is configured to insert the suction member 110 into the current washing liquid pool 21 from which the washing liquid is currently being sucked while inserting the discharge member 120 into the previous washing liquid pool 21 adjacent to the current washing liquid pool 21 from which the washing liquid has been sucked, which is simple to operate and improves the detection efficiency of the POCT blood cell analyzer 1. In addition, the maintenance reagent box 40 does not need to be additionally provided with a waste liquid pool, which reduces the volume of the maintenance reagent box 40 and reduces the cost.

[0230] According to some embodiments of the present application, please refer to FIG. 17, FIG. 18 and FIG. 20, FIG. 20 is a structural schematic diagram of the second embodiment of the maintenance reagent box in FIG. 17. The maintenance reagent box 40 of the embodiment further comprises a first waste liquid pool 22 adjacent to the washing liquid pool 21 with the strongest washing strength.

[0231] Specifically, the plurality of washing liquid pools 21 comprises a first washing liquid pool 211, a second washing liquid pool 212 and a third washing liquid pool 213, which are arranged in order along the extension direction of the maintenance reagent box 40. The washing strength of the washing liquid in the first washing liquid pool 211 is greater than the washing strength of the washing liquid in the second washing liquid pool 212, and the washing strength of the washing liquid in the second washing liquid pool 212 is greater than or equal to the washing strength of the washing liquid in the third washing liquid pool 213. The first waste liquid pool 22 is arranged on the side of the first washing liquid pool 211 away from the second washing liquid pool 212.

[0232] The cytometric component 10 is configured to insert the suction member 110 into the washing liquid pool 21 with the strongest washing strength while inserting the discharge member 120 into the first waste liquid pool 22.

[0233] In the maintenance mode, the liquid suction member 110 is inserted into the first cleaning liquid pool 211, and the liquid discharge member 120 is inserted into the first waste liquid pool 22 at the same time, the cell counting component 10 sucks the cleaning liquid in the first cleaning liquid pool 211 through the liquid suction member 110, and discharges the cleaning liquid in the inner cavity 130 to the first waste liquid pool 22 through the liquid discharge member 120, thereby completing the first cleaning of the cell counting component 10. The cell counting component 10 can be moved relative to the maintenance kit 40, the liquid suction member 110 is inserted into the second cleaning liquid pool 212, and the liquid discharge member 120 is inserted into the first cleaning liquid pool 211 at the same time, the cell counting component 10 sucks the cleaning liquid in the second cleaning liquid pool 212 through the liquid suction member 110, and discharges the cleaning liquid in the inner cavity 130 to the first cleaning liquid pool 211 through the liquid discharge member 120, thereby completing the second cleaning of the cell counting component 10. The cell counting component 10 can be moved relative to the maintenance kit 40, the liquid suction member 110 is inserted into the third cleaning liquid pool 213, and the liquid discharge member 120 is inserted into the second cleaning liquid pool 212 at the same time, the cell counting component 10 sucks the cleaning liquid in the third cleaning liquid pool 213 through the liquid suction member 110, and discharges the cleaning liquid in the inner cavity 130 to the second cleaning liquid pool 212 through the liquid discharge member 120, thereby completing the third cleaning of the cell counting component 10.

[0234] Optionally, the interval distance between the liquid suction member 110 and the liquid discharge member 120 is equal to the distance between the central axis of the first waste liquid pool 22 and the central axis of the first cleaning liquid pool 211, or the distance between the central axis of the first cleaning liquid pool 211 and the central axis of the second cleaning liquid pool 212, or the distance between the central axis of the second cleaning liquid pool 212 and the central axis of the third cleaning liquid pool 213.

[0235] The maintenance kit 40 of the embodiment further comprises the first waste liquid pool 22 adjacent to the cleaning liquid pool 21 with the strongest cleaning strength, and the cell counting component 10 is arranged to insert the liquid suction member 110 into the cleaning liquid pool 21 with the strongest cleaning strength while inserting the liquid discharge member 120 into the first waste liquid pool 22. The cleaning liquid in the inner cavity 130 can be discharged to the first waste liquid pool 22 through the liquid discharge member 120, which is simple to operate and improves the detection efficiency of the POCT blood cell analyzer 1. By arranging the first waste liquid pool 22, the liquid can be discharged without moving to the second cleaning liquid pool 212 when the first cleaning liquid pool 211 sucks the cleaning liquid for cleaning, the liquid can be discharged without moving to the third cleaning liquid pool 213 when the second cleaning liquid pool 212 sucks the cleaning liquid for cleaning, and the liquid can be directly discharged when the third cleaning liquid pool 213 sucks the cleaning liquid for cleaning. Considering that a small amount of cleaning liquid will also be discharged through the liquid suction channel when discharging the liquid, compared with the first embodiment, the cleaning liquid in the first cleaning liquid pool 211 will not be discharged to the second cleaning liquid pool 212 through the liquid suction member 110, and the cleaning liquid in the second cleaning liquid pool 212 will not be discharged to the third cleaning liquid pool 213 through the liquid suction member 110, thereby making the cleaning more thorough.

[0236] According to some embodiments of the present application, the cell counting assembly 10 is arranged to sequentially increase the liquid amount of the washing liquid sequentially drawn by the liquid suction member 110 from the different washing liquid pools 21 according to the washing intensity from high to low.

[0237] As shown in FIG. 17 and FIG. 20, the liquid amount of the washing liquid drawn by the liquid suction member 110 from the first washing liquid pool 211 is a first liquid amount, the liquid amount of the washing liquid drawn by the liquid suction member 110 from the second washing liquid pool 212 is a second liquid amount, the liquid amount of the washing liquid drawn by the liquid suction member 110 from the third washing liquid pool 213 is a third liquid amount, the second liquid amount is greater than the first liquid amount, and the third liquid amount is greater than the second liquid amount.

[0238] The cell counting assembly 10 is arranged to sequentially increase the liquid amount of the washing liquid sequentially drawn by the liquid suction member 110 from the different washing liquid pools 21 according to the washing intensity from high to low; by sequentially increasing the liquid amount of the washing liquid drawn by the liquid suction member 110 according to the washing intensity from high to low, the washing liquid of the previous washing can be washed, the side wall of the inner cavity 130 is prevented from remaining the washing liquid of the previous washing, and the washing effect of the cell counting assembly 10 is improved.

[0239] According to some embodiments of the present application, the POCT blood cell analyzer 1 performs self-checking on the cell counting assembly 10 and selectively re-enters the maintenance mode or generates an alarm according to the self-checking result, i.e., after the third washing of the cell counting assembly 10 is completed, the cell counting assembly 10 is subjected to self-checking.

[0240] For example, after the third washing of the cell counting assembly 10 is completed, the POCT blood cell analyzer 1 performs self-checking on the cell counting assembly 10; in response to the self-checking result being failed, when the maintenance mode is selected to be re-entered, the cell counting assembly 10 is subjected to the maintenance mode again based on the maintenance mode of the above-mentioned embodiments, which will not be described herein again. In response to the self-checking result being failed after the cell counting assembly 10 is subjected to the re-maintenance mode, the POCT blood cell analyzer 1 generates an alarm to remind the user to replace the microwell sheet 12 of the cell counting assembly 10.

[0241] Optionally, after the microwell sheet 12 of the cell counting assembly 10 is replaced, the cell counting assembly 10 is re-entered into the maintenance mode.

[0242] Optionally, the self-checking of the cytometric component 10 refers to establishing a negative pressure value preset pressure value in the inner cavity 130 of the main body 11, sucking air or liquid by the liquid suction member 110 of the cytometric component 10, reading the pressure value of the inner cavity 130 after a preset interval, and calculating the difference between the preset pressure value and the pressure value. In response to the difference being within the preset range, the self-checking result is passed; in response to the difference not being within the preset range, the self-checking result is failed.

[0243] The POCT blood cell analyzer 1 of the embodiment performs self-checking on the cytometric component 10 and selectively re-enters the maintenance mode or issues an alarm according to the self-checking result; the cytometric component 10 can be self-checked to ensure that the cytometric component 10 meets the detection conditions and improve the accuracy of the detection result of the POCT blood cell analyzer 1.

[0244] According to some embodiments of the present application, as shown in FIG. 18 and FIG. 21, FIG. 21 is a structural schematic diagram of a fourth embodiment of the POCT blood cell analyzer of the present application. The loading seat of the POCT blood cell analyzer 1 of the embodiment is also used to receive the loading of the detection reagent kit 30, and the cytometric component 10 of the POCT blood cell analyzer 1 of the embodiment is the same as the cytometric component 10 of the above-mentioned embodiments, which will not be described here.

[0245] The POCT blood cell analyzer 1 of the present application includes two parallelly arranged cytometric components 10. In other embodiments, the POCT blood cell analyzer 1 can be provided with other numbers of cytometric components 10, for example, the POCT blood cell analyzer 1 includes one cytometric component 10 or three cytometric components 10.

[0246] The cytometric component 10 of the embodiment is provided with a detection mode, in which the cytometric component 10 sucks the detection liquid from the detection reagent kit 30 through the liquid suction member 110 and discharges the detection liquid in the main body 11 to the detection reagent kit 30 through the liquid discharge member 120.

[0247] For example, the detection reagent kit 30 includes a detection liquid pool 31, a detection cleaning liquid pool 32 and a detection waste liquid pool 33 arranged in sequence. In the detection mode, the liquid suction member 110 is inserted into the detection liquid pool 31 at the same time that the liquid discharge member 120 is inserted into the detection cleaning liquid pool 32, the cytometric component 10 sucks the detection liquid from the detection liquid pool 31 through the liquid suction member 110 to count the cell particles in the detection liquid; when the counting of the cytometric component 10 is completed, the cytometric component 10 can be moved relative to the detection reagent kit 30, the liquid suction member 110 is inserted into the detection cleaning liquid pool 32 at the same time that the liquid discharge member 120 is inserted into the detection waste liquid pool 33, and the cytometric component 10 discharges the detection liquid in the main body 11 to the detection waste liquid pool 33 through the liquid discharge member 120.

[0248] Optionally, in the detection mode, the liquid suction member 110 is inserted into the detection liquid pool 31 while the liquid discharge member 120 is inserted into the detection liquid pool 31, and the cell counting assembly 10 sucks the detection liquid from the detection liquid pool 31 through the liquid suction member 110 to count the cell particles in the detection liquid; when the counting is completed by the cell counting assembly 10, the cell counting assembly 10 discharges the detection liquid in the main body 11 to the detection liquid pool 31 through the liquid discharge member 120.

[0249] The cell counting assembly 10 of the embodiment is provided with a detection mode, in which the cell counting assembly 10 sucks the detection liquid from the detection kit 30 through the liquid suction member 110 and discharges the detection liquid in the main body 11 to the detection kit 30 through the liquid discharge member 120; and the counting of the detection liquid can be realized.

[0250] According to some embodiments of the present application, as shown in FIGS. 18 and 21, the cell counting assembly 10 of the embodiment also sucks the washing liquid from the detection kit 30 through the liquid suction member 110 and discharges the washing liquid in the main body 11 to the detection kit 30 through the liquid discharge member 120.

[0251] Optionally, when the counting is completed by the cell counting assembly 10, the cell counting assembly 10 can be moved relative to the detection kit 30, the liquid suction member 110 is inserted into the detection washing liquid pool 32 while the liquid discharge member 120 is inserted into the detection waste liquid pool 33, and the cell counting assembly 10 discharges the detection liquid in the main body 11 to the detection waste liquid pool 33 through the liquid discharge member 120. The cell counting assembly 10 also sucks the washing liquid from the detection washing liquid pool 32 through the liquid suction member 110 to wash the inner cavity 130 of the main body 11, and discharges the washing liquid in the main body 11 to the detection waste liquid pool 33 through the liquid discharge member 120.

[0252] Optionally, when the counting is completed by the cell counting assembly 10, the cell counting assembly 10 can be moved relative to the detection kit 30, the liquid suction member 110 is inserted into the detection washing liquid pool 32 while the liquid discharge member 120 is inserted into the detection washing liquid pool 32, and the cell counting assembly 10 sucks the washing liquid from the detection washing liquid pool 32 through the liquid suction member 110 to wash the inner cavity 130 of the main body 11, and discharges the washing liquid in the main body 11 to the detection washing liquid pool 32 through the liquid discharge member 120. In other embodiments, the detection kit 30 can be provided only with the detection liquid pool 31 and the detection washing liquid pool 32 to suck or discharge the detection liquid in the detection liquid pool 31 and the washing liquid in the detection washing liquid pool 32.

[0253] The cell counting assembly 10 of the embodiment also sucks the cleaning liquid from the detection kit 30 through the liquid suction member 110 and discharges the cleaning liquid in the main body 11 to the detection kit 30 through the liquid discharge member 120; the cell counting assembly 10 can be cleaned after the counting is completed, so as to reduce the pollution of the detection liquid and improve the detection result accuracy of the POCT blood cell analyzer 1.

[0254] Please refer to FIGS. 17-22, and FIG. 22 is a flowchart of a first embodiment of the maintenance method of the POCT blood cell analyzer. The maintenance method of the embodiment is applied to the POCT blood cell analyzer 1 of the above-mentioned embodiments, and the maintenance method comprises the following steps:

[0255] S601: In response to the cell counting assembly 10 in the maintenance mode, the maintenance kit 40 is loaded into the loading seat of the cell counting assembly 10.

[0256] In response to the cell counting assembly 10 in the maintenance mode, the maintenance kit 40 is loaded into the loading seat of the cell counting assembly 10, and the loading seat receives the maintenance kit 40 so that the maintenance kit 40 is located in the housing. The maintenance kit 40 is the same as the maintenance kit 40 of the above-mentioned embodiments, and will not be described here again.

[0257] In other embodiments, the maintenance kit 40 can be loaded into the loading seat of the cell counting assembly 10 before the cell counting assembly 10 is in the maintenance mode.

[0258] S602: The cleaning liquid is sucked from different cleaning liquid pools 21 through the liquid suction member 110 in the order of the cleaning intensity from high to low, and the cleaning liquid in the main body 11 is discharged to the maintenance kit 40 through the liquid discharge member 120.

[0259] The cell counting assembly 10 is arranged to suck the cleaning liquid from different cleaning liquid pools 21 through the liquid suction member 110 in the order of the cleaning intensity from high to low, and discharge the cleaning liquid in the main body 11 to the maintenance kit 40 through the liquid discharge member 120, which is the same as the above-mentioned embodiments and will not be described here again.

[0260] S603: The cell counting assembly 10 is self-checked, and selectively re-enters the maintenance mode or generates an alarm according to the self-checking result.

[0261] The cell counting assembly 10 is self-checked, and the self-checking result is obtained. In response to the self-checking result failing, the maintenance mode is selected to be re-entered, and the step S602 is returned, which will not be described here again. In response to the self-checking result failing after the cell counting assembly 10 completes the re-maintenance mode, the POCT blood cell analyzer 1 generates an alarm to remind the user to replace the microporous sheet 12 of the cell counting assembly 10. In response to the self-checking result passing, the maintenance mode is ended.

[0262] The embodiment realizes the cleaning maintenance of the cytometric component 10 by cleaning the cytometric component 10 multiple times in the maintenance mode according to the cleaning intensity from high to low, and improves the detection result accuracy of the POCT blood cell analyzer 1.

[0263] According to some embodiments of the present application, please refer to FIG. 18 and FIG. 25, FIG. 25 is a partially enlarged structural schematic diagram of region A in FIG. 18. The main body 11 of the embodiment is further provided with a front cavity 111, and the cytometric component 10 further includes a micropore sheet 12, a first electrode 13, a second electrode 14, a liquid inlet hole 114, a liquid outlet hole 117, a pressure interface 116, and a switch valve 119.

[0264] The micropore sheet 12 is used to isolate the front cavity 111 and the inner cavity 130, and the micropore sheet 12 is provided with micropores 121, and the front cavity 111 and the inner cavity 130 are communicated through the micropores 121. The micropore sheet 12 can also be called a gem hole sheet, a gem sheet or a detection sheet, and the micropore 121 can also be called a gem hole or a detection hole. For example, the detection liquid in the front cavity 111 flows through the micropores 121 into the inner cavity 130 to allow the cells of the detection liquid to flow through the micropores 121 one by one.

[0265] Optionally, the liquid suction member 110, the front cavity 111, the micropore 121 and the liquid inlet hole 114 form the liquid suction channel of the present application, and the liquid discharge member 120, the switch valve 119 and the liquid outlet hole 117 form the liquid discharge channel of the present application.

[0266] The first electrode 13 is arranged in the inner cavity 130, that is, the free end of the first electrode 13 is located in the inner cavity 130, and the other end of the first electrode 13 is located outside the inner cavity 130; the first electrode 13 can also be called a back cell electrode or a cathode.

[0267] Optionally, the free end of the first electrode 13 is electrically connected to the detection liquid in the inner cavity 130; the detection liquid flowing through the micropore 121 enters the inner cavity 130, the free end of the first electrode 13 located in the inner cavity 130 is electrically connected to the detection liquid in the inner cavity 130, and the other end of the first electrode 13 located outside the inner cavity 130 is connected to the impedance detection circuit.

[0268] The second electrode 14 is arranged in the front cavity 111, and the second electrode 14 is electrically connected to the detection liquid in the front cavity 111.

[0269] Optionally, the bottom wall of the inner cavity 130 is arranged in an inclined manner, and in the direction of gravity, the side of the bottom wall of the inner cavity 130 close to the liquid suction member 110 (for example, the liquid inlet hole 114) is higher than the side of the bottom wall of the inner cavity 130 close to the liquid discharge member 120 (for example, the liquid discharge hole 117), so that the liquid in the inner cavity 130 flows to the side of the bottom wall of the inner cavity 130 close to the liquid discharge member 120, and then the liquid in the inner cavity 130 can be discharged from the liquid discharge member 120. The pressure interface 116 is arranged at the top of the inner cavity 130 to build pressure (positive pressure or negative pressure) in the inner cavity 130.

[0270] Please continue to refer to FIGS. 17, 18 and 25, the POCT blood cell analyzer 1 of the embodiment includes a shell, a loading seat and a cytometry assembly 10.

[0271] The loading seat is used to receive the loading of a cartridge, and the cartridge is used to carry a liquid; the cytometry assembly 10 is movable relative to the cartridge. Specifically, the cytometry assembly 10 moves, and the cartridge does not move; or the cytometry assembly 10 moves, and the cartridge moves; or the cytometry assembly 10 does not move, and the cartridge moves.

[0272] The cartridge includes but is not limited to a maintenance cartridge 40, a detection cartridge 30 or other cartridges carrying a liquid. In other embodiments, the cartridge can also be replaced by other objects carrying a liquid, such as a reagent bottle used to carry a liquid. The liquid carried by the cartridge includes but is not limited to a cleaning liquid or a detection liquid; the following is described by taking the cartridge as the maintenance cartridge 40.

[0273] The cytometry assembly 10 is arranged in the shell, and the loading seat is used to receive the loading of the maintenance cartridge 40. For example, the loading seat is arranged in the shell, and when the loading seat receives the loading of the maintenance cartridge 40, the loading seat moves out of the shell, so that the maintenance cartridge 40 is placed on the loading seat and the maintenance cartridge 40 is moved into the shell, thereby realizing that the loading seat receives the loading of the maintenance cartridge 40.

[0274] The cytometry assembly 10 is movable relative to the maintenance cartridge 40. Specifically, the cytometry assembly 10 moves, and the maintenance cartridge 40 does not move; or the cytometry assembly 10 moves, and the maintenance cartridge 40 moves; or the cytometry assembly 10 does not move, and the maintenance cartridge 40 moves.

[0275] The cytometry assembly 10 of the embodiment includes a main body 11, a liquid suction member 110 and a liquid discharge member 120. The liquid suction member 110 cooperates with the main body 11 to form a liquid suction channel for conveying a liquid, and a microporous sheet 12 is arranged in the liquid suction channel; the liquid discharge member 120 cooperates with the main body 11 to form a liquid discharge channel for discharging the liquid of the main body.

[0276] Optionally, the main body 11 is provided with an inner cavity 130, which is in communication with the liquid discharge channel and the liquid suction channel respectively. The inner cavity 130 can also be referred to as a rear cavity or a rear pool.

[0277] When the liquid suction channel is blocked, the cytometric assembly 10 is configured to impact the liquid suction channel by gas; or, the liquid suction channel is impacted by liquid, i.e., the liquid suction channel is impacted by liquid sucked by the liquid discharge member 120 from the maintenance kit 40.

[0278] The liquid suction channel is blocked means that the micropore sheet 12 in the liquid suction channel is blocked or the liquid suction member 110 is blocked, so that the liquid suction channel is difficult or unable to suck liquid.

[0279] Specifically, when the liquid suction channel is blocked, the cytometric assembly 10 impacts the liquid suction channel by gas. For example, when the liquid suction channel is blocked, the liquid discharge channel is controlled to be closed, and the inner cavity 130 of the main body 11 is established to be positive pressure, so that the liquid suction channel is impacted by gas in the inner cavity 130.

[0280] Alternatively, when the liquid suction channel is blocked, the cytometric assembly 10 sucks liquid from the maintenance kit 40 by the liquid discharge member 120, and the liquid suction channel is impacted by liquid. The free end of the liquid discharge member 120 and the free end of the liquid suction member 110 of the cytometric assembly 10 are located below the liquid level of the liquid in the maintenance kit 40. For example, when the liquid suction channel is blocked, the liquid discharge member 120 is inserted into the maintenance kit 40, the liquid discharge channel is controlled to be open, and the inner cavity 130 of the main body 11 is established to be negative pressure, so that the liquid is sucked from the maintenance kit 40 by the liquid discharge member 120; the liquid discharge channel is controlled to be closed, and the inner cavity 130 of the main body 11 is established to be positive pressure, so that the liquid suction channel is impacted by liquid in the inner cavity 130.

[0281] When the liquid suction channel is blocked, the cytometric assembly 10 is configured to impact the liquid suction channel by gas; or, the liquid suction channel is impacted by liquid, i.e., the liquid suction channel is impacted by liquid sucked by the liquid discharge member 120 from the maintenance kit 40.

[0282] According to some embodiments of the present application, as shown in FIGS. 17 and 18, when the liquid suction channel is blocked after the liquid suction channel is impacted by the gas, the cell counting assembly 10 is configured to suck the liquid from the liquid discharge member 120 and impact the liquid suction channel by the liquid.

[0283] When the liquid suction channel is blocked, the cell counting assembly 10 is configured to impact the liquid suction channel by the gas. When the liquid suction channel is still blocked after the cell counting assembly 10 impacts the liquid suction channel by the gas, the cell counting assembly 10 is configured to suck the liquid from the maintenance kit 40 by the liquid discharge member 120 and impact the liquid suction channel by the liquid.

[0284] When the liquid suction channel is blocked after the liquid suction channel is impacted by the gas, the cell counting assembly 10 is configured to suck the liquid from the maintenance kit 40 by the liquid discharge member 120 and impact the liquid suction channel by the liquid. The liquid suction channel is impacted twice by the gas and the liquid, which can improve the effect of impacting the liquid suction channel and improve the accuracy of the detection result of the POCT blood cell analyzer 1. In addition, the POCT blood cell analyzer 1 does not need to increase other components, which can reduce the cost.

[0285] According to some embodiments of the present application, the maintenance kit 40 of the present embodiment includes a backflush liquid pool for carrying the liquid. The cell counting assembly 10 is configured to suck the liquid from the backflush liquid pool by the liquid discharge member 120 and impact the liquid suction channel by the liquid.

[0286] When the liquid suction channel is blocked, the cell counting assembly 10 is configured to suck the liquid from the backflush liquid pool by the liquid discharge member 120 and impact the liquid suction channel by the liquid. The liquid suction channel is impacted by the liquid from the backflush liquid pool, which can improve the accuracy of the detection result of the POCT blood cell analyzer 1. In addition, the POCT blood cell analyzer 1 does not need to increase other components, which can reduce the cost.

[0287] According to some embodiments of the present application, as shown in FIGS. 17-19, the maintenance kit 40 of the present embodiment includes a plurality of cleaning liquid pools 21 for storing cleaning liquids with different cleaning strengths. At least one of the plurality of cleaning liquid pools 21 is used as the backflush liquid pool described above. For example, the plurality of cleaning liquid pools 21 are sequentially and adjacently arranged from high to low in cleaning strength, or the plurality of cleaning liquid pools 21 are randomly arranged. One of the plurality of cleaning liquid pools 21 is used as the backflush liquid pool described above, or two of the plurality of cleaning liquid pools 21 are used as the backflush liquid pool described above.

[0288] When the clogging of the liquid suction passage exists, the cytometric component 10 is configured to suck the washing liquid from at least one of the plurality of washing liquid pools 21 by the liquid discharging member 120 and to impact the liquid suction passage by the washing liquid.

[0289] For example, the cytometric component 10 sucks the washing liquid with low washing strength from one of the washing liquid pools 21 of the maintenance kit 40 by the liquid discharging member 120 and impacts the liquid suction passage by the washing liquid with low washing strength. Alternatively, when the clogging of the liquid suction passage exists, the cytometric component 10 sucks the washing liquid with high washing strength from another of the washing liquid pools 21 of the maintenance kit 40 by the liquid discharging member 120 and impacts the liquid suction passage by the washing liquid with high washing strength.

[0290] The present embodiment is configured such that, when the clogging of the liquid suction passage exists, the cytometric component 10 sucks the washing liquid from one of the plurality of washing liquid pools 21 by the liquid discharging member 120 and impacts the liquid suction passage by the washing liquid. This allows the POCT blood cell analyzer 1 to have the ability to deal with the clogging of the liquid suction passage and to solve the clogging of the liquid suction passage with a high probability, thereby improving the accuracy of the detection result of the POCT blood cell analyzer 1.

[0291] According to some embodiments of the present application, the plurality of washing liquid pools 21 of the present embodiment includes a first washing liquid pool 211, a second washing liquid pool 212, and a third washing liquid pool 213, which are sequentially arranged along the extension direction of the maintenance kit 40.

[0292] The washing strength of the washing liquid of the first washing liquid pool 211 is greater than the washing strength of the washing liquid of the second washing liquid pool 212, and the washing strength of the washing liquid of the second washing liquid pool 212 is greater than or equal to the washing strength of the washing liquid of the third washing liquid pool 213.

[0293] For example, the washing liquid of the first washing liquid pool 211 is an alkaline strong washing liquid, the washing liquid of the second washing liquid pool 212 is a weakly acidic washing liquid, and the washing liquid of the third washing liquid pool 213 is pure water; or the washing liquid of the first washing liquid pool 211 is an alkaline strong washing liquid, the washing liquid of the second washing liquid pool 212 is pure water, and the washing liquid of the third washing liquid pool 213 is pure water.

[0294] The cytometric component 10 is configured to suck the washing liquid from the third washing liquid pool 213, the second washing liquid pool 212, or the first washing liquid pool 211 by the liquid discharging member 120.

[0295] When the suction passage is blocked, the cytometric component 10 sucks the washing liquid from the third washing liquid pool 213 through the liquid discharging member 120, and the washing liquid in the third washing liquid pool 213 is used to impact the suction passage. Alternatively, when the suction passage is blocked, the cytometric component 10 sucks the washing liquid from the second washing liquid pool 212 through the liquid discharging member 120, and the washing liquid in the second washing liquid pool 212 is used to impact the suction passage. Alternatively, when the suction passage is blocked, the cytometric component 10 sucks the washing liquid from the first washing liquid pool 211 through the liquid discharging member 120, and the washing liquid in the first washing liquid pool 211 is used to impact the suction passage.

[0296] The cytometric component 10 of the embodiment is configured to suck the washing liquid from the third washing liquid pool 213, the second washing liquid pool 212 or the first washing liquid pool 211 through the liquid discharging member 120. In this way, the POCT blood cell analyzer 1 has the ability to deal with the blockage of the suction passage, can solve the blockage of the suction passage with a high probability, and improves the accuracy of the detection result of the POCT blood cell analyzer 1.

[0297] According to some embodiments of the present application, the cytometric component 10 of the embodiment is configured to discharge the washing liquid in the main body 11 through the liquid discharging member 120.

[0298] Specifically, the cytometric component 10 sucks the washing liquid from the washing liquid pool 21 through the liquid discharging member 120 to impact the suction passage with the washing liquid, and then discharges the washing liquid in the main body 11 into the washing liquid pool 21 through the liquid discharging member 120 when the suction passage is not blocked after the impact.

[0299] For example, the cytometric component 10 can be moved relative to the maintenance kit 40 to insert the liquid discharging member 120 into the third washing liquid pool 213, and then suck the washing liquid from the third washing liquid pool 213 through the liquid discharging member 120 to impact the suction passage when the suction passage is blocked. When the suction passage is not blocked after the impact, the cytometric component 10 can be moved relative to the maintenance kit 40 to insert the liquid discharging member 120 into the second washing liquid pool 212 and the liquid discharging member 110 into the third washing liquid pool 213, and then discharge the washing liquid in the main body 11 into the third washing liquid pool 213 through the liquid discharging member 110.

[0300] Alternatively, when the occlusion exists in the liquid suction channel, the cytometry assembly 10 sucks the cleaning liquid from the second cleaning liquid pool 212 through the liquid discharge member 120 to impact the liquid suction channel. When the occlusion does not exist in the liquid suction channel after the impact, the cytometry assembly 10 can be moved relative to the maintenance kit 40 so that the liquid discharge member 120 is inserted into the first cleaning liquid pool 211 and the liquid suction member 110 is inserted into the second cleaning liquid pool 212, and the cytometry assembly 10 discharges the cleaning liquid in the main body 11 to the second cleaning liquid pool 212 through the liquid suction member 110.

[0301] Optionally, when the liquid discharge member 120 of the cytometry assembly 10 is inserted into the third cleaning liquid pool 213, the liquid suction member 110 of the cytometry assembly 10 is located outside the third cleaning liquid pool 213, for example, the liquid suction member 110 is located on the side of the third cleaning liquid pool 213 away from the second cleaning liquid pool 212.

[0302] In other embodiments, the liquid discharge member 120 and the liquid suction member 110 of the cytometry assembly 10 are inserted into the same cleaning liquid pool 21. For example, the liquid discharge member 120 and the liquid suction member 110 of the cytometry assembly 10 are inserted into the third cleaning liquid pool 213, and when the occlusion exists in the liquid suction channel, the cleaning liquid is sucked from the third cleaning liquid pool 213 through the liquid suction member 110 to impact the liquid suction channel. When the occlusion does not exist in the liquid suction channel after the impact, the cytometry assembly 10 discharges the cleaning liquid in the main body 11 to the third cleaning liquid pool 213 through the liquid suction member 110.

[0303] The cytometry assembly 10 of the present embodiment is configured to discharge the cleaning liquid in the main body 11 through the liquid suction member 110, which is simple to operate and improves the detection efficiency of the POCT blood cell analyzer 1.

[0304] According to some embodiments of the present application, when the occlusion does not exist in the liquid suction channel after the impact, the cytometry assembly 10 is configured to suck the cleaning liquid from different cleaning liquid pools 21 through the liquid suction member 110 in descending order of cleaning intensity, and discharge the cleaning liquid in the main body 11 to the maintenance kit 40 through the liquid discharge member 120.

[0305] After the impact on the liquid suction channel is completed, the liquid suction channel after the impact does not exist blockage, and the cell counting assembly 10 needs to be cleaned. For example, the cell counting assembly 10 can be moved relative to the maintenance kit 40 to insert the liquid suction member 110 into the first cleaning liquid pool 211, and the cleaning liquid is sucked from the first cleaning liquid pool 211 through the liquid suction member 110; when the liquid suction member 110 completes the suction of the cleaning liquid from the first cleaning liquid pool 211, the cell counting assembly 10 can be moved relative to the maintenance kit 40 to insert the liquid suction member 110 into the second cleaning liquid pool 212, and the liquid discharge member 120 is inserted into the first cleaning liquid pool 211. The cell counting assembly 10 discharges the cleaning liquid in the main body 11 to the first cleaning liquid pool 211 through the liquid discharge member 120, thereby completing the first cleaning of the cell counting assembly 10. The cell counting assembly 10 sucks the cleaning liquid from the second cleaning liquid pool 212 through the liquid suction member 110; when the liquid suction member 110 completes the suction of the cleaning liquid from the second cleaning liquid pool 212, the cell counting assembly 10 can be moved relative to the maintenance kit 40 to insert the liquid suction member 110 into the third cleaning liquid pool 213, and the liquid discharge member 120 is inserted into the second cleaning liquid pool 212. The cell counting assembly 10 discharges the cleaning liquid in the main body 11 to the second cleaning liquid pool 212 through the liquid discharge member 120, thereby completing the second cleaning of the cell counting assembly 10. The cell counting assembly 10 sucks the cleaning liquid from the third cleaning liquid pool 213 through the liquid suction member 110, and discharges the cleaning liquid in the main body 11 to the second cleaning liquid pool 212 through the liquid discharge member 120, or the cell counting assembly 10 can be moved relative to the maintenance kit 40 to insert the liquid discharge member 120 into the third cleaning liquid pool 213. The cleaning liquid in the main body 11 is discharged to the third cleaning liquid pool 213 through the liquid discharge member 120, thereby completing the third cleaning of the cell counting assembly 10.

[0306] Optionally, when the liquid suction member 110 of the cell counting assembly 10 is inserted into the first cleaning liquid pool 211, the liquid discharge member 120 of the cell counting assembly 10 is located outside the first cleaning liquid pool 211, for example, the liquid discharge member 120 is located on the side of the first cleaning liquid pool 211 away from the second cleaning liquid pool 212.

[0307] Optionally, the cytometry component 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 and the liquid discharge member 120 are inserted into the first cleaning liquid pool 211, the cleaning liquid is sucked from the first cleaning liquid pool 211 by the liquid suction member 110, and the cleaning liquid in the main body 11 is discharged to the first cleaning liquid pool 211 by the liquid discharge member 120, thereby completing the first cleaning of the cytometry component 10. The cytometry component 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 and the liquid discharge member 120 are inserted into the second cleaning liquid pool 212, the cleaning liquid is sucked from the second cleaning liquid pool 212 by the liquid suction member 110, and the cleaning liquid in the main body 11 is discharged to the second cleaning liquid pool 212 by the liquid discharge member 120, thereby completing the second cleaning of the cytometry component 10. The cytometry component 10 can be moved relative to the maintenance kit 40 so that the liquid suction member 110 and the liquid discharge member 120 are inserted into the third cleaning liquid pool 213, the cleaning liquid is sucked from the third cleaning liquid pool 213 by the liquid suction member 110, and the cleaning liquid in the main body 11 is discharged to the third cleaning liquid pool 213 by the liquid discharge member 120, thereby completing the third cleaning of the cytometry component 10.

[0308] In other embodiments, when there is no blockage in the liquid suction channel after the impact, the cytometry component 10 is configured to suck the cleaning liquid from different cleaning liquid pools 21 by the liquid discharge member 120 from high to low according to the cleaning strength, and discharge the cleaning liquid in the main body 11 to the maintenance kit 40 by the liquid suction member 110.

[0309] In this embodiment, when there is no blockage in the liquid suction channel after the impact, the cytometry component 10 is configured to suck the cleaning liquid from different cleaning liquid pools 21 by the liquid suction member 110 from high to low according to the cleaning strength, and discharge the cleaning liquid in the main body 11 to the maintenance kit 40 by the liquid discharge member 120. This achieves cleaning of the post-impact cytometry component 10, reduces waste liquid residue of the cytometry component 10, and improves the accuracy of the detection results of the POCT blood cell analyzer 1.

[0310] According to some embodiments of the present application, please refer to FIG. 17, FIG. 18 and FIG. 23, FIG. 23 is a structural schematic diagram of a third embodiment of the maintenance kit in FIG. 17. The maintenance kit 40 of this embodiment further comprises a second waste liquid pool 23 adjacent to the backflush liquid pool.

[0311] Specifically, the plurality of cleaning liquid pools 21 include a first cleaning liquid pool 211, a second cleaning liquid pool 212, and a third cleaning liquid pool 213, which are sequentially arranged along the extension direction of the maintenance kit 40. Among them, the cleaning strength of the cleaning liquid in the first cleaning liquid pool 211 is greater than that of the cleaning liquid in the second cleaning liquid pool 212, and the cleaning strength of the cleaning liquid in the second cleaning liquid pool 212 is greater than or equal to that of the cleaning liquid in the third cleaning liquid pool 213. Among them, the third cleaning liquid pool 213 is used as a backflushing liquid pool, and the second waste liquid pool 23 is arranged on the side of the third cleaning liquid pool 213 away from the second cleaning liquid pool 212.

[0312] When there is a blockage in the liquid suction channel, the cytometric component 10 is arranged to draw liquid from the backflushing liquid pool through the liquid discharge member 120, and to impact the liquid suction channel with the liquid, and the second waste liquid pool 23 is used to contain the liquid suction member 110 and the liquid discharged by the impact.

[0313] When there is a blockage in the liquid suction channel, the liquid discharge member 120 is inserted into the third cleaning liquid pool 213, and the liquid suction member 110 is inserted into the second waste liquid pool 23, i.e. the cleaning liquid in the third cleaning liquid pool 213 is used as the liquid in the backflushing liquid pool, the third cleaning liquid pool 213 is used to contain the liquid discharge member 120, and the second waste liquid pool 23 is used to contain the liquid suction member 110; the cytometric component 10 draws the cleaning liquid in the third cleaning liquid pool 213 through the liquid discharge member 120 to impact the liquid suction channel with the cleaning liquid in the third cleaning liquid pool 213, and the cleaning liquid in the third cleaning liquid pool 213 is discharged to the second waste liquid pool 23 through the liquid suction member 110, i.e. the second waste liquid pool 23 is used to contain the liquid discharged by the impact.

[0314] When the cytometric component 10 after the impact is cleaned, the cytometric component 10 draws the cleaning liquid in the third cleaning liquid pool 213 through the liquid discharge member 120 to clean the liquid suction channel with the cleaning liquid in the third cleaning liquid pool 213, and discharges the cleaning liquid in the main body 11 to the second waste liquid pool 23 through the liquid suction member 110.

[0315] Optionally, the spacing distance between the liquid suction member 110 and the liquid discharge member 120 is equal to the distance between the center axis of the second waste liquid pool 23 and the center axis of the third cleaning liquid pool 213, or the distance between the center axis of the third cleaning liquid pool 213 and the center axis of the second cleaning liquid pool 212, or the distance between the center axis of the second cleaning liquid pool 212 and the center axis of the first cleaning liquid pool 211.

[0316] When the liquid suction channel is blocked, the cytometric component 10 is configured to draw liquid from the backflush liquid pool through the liquid discharge member 120, and to impact the liquid suction channel with the liquid, and the second waste liquid pool 23 is configured to contain the liquid discharged by the impact, thereby improving the detection efficiency of the POCT blood cell analyzer 1. In addition, the second waste liquid pool 23 is configured to contain the liquid discharged by the impact, thereby avoiding contamination of the cleaning liquid pool 21 (i.e., the third cleaning liquid pool 213) with the weakest cleaning strength, and allowing the cleaning liquid in the third cleaning liquid pool 213 to clean the cytometric component 10 after the impact, thereby reducing the waste liquid residue of the cytometric component 10 and improving the accuracy of the detection results of the POCT blood cell analyzer 1.

[0317] Optionally, please refer to FIG. 24, which is a structural schematic diagram of a fourth embodiment of the maintenance kit in FIG. 17. The maintenance kit 40 in this embodiment includes a second waste liquid pool 23 adjacent to the backflush liquid pool, and a first waste liquid pool 22 adjacent to the cleaning liquid pool 21 with the strongest cleaning strength.

[0318] The plurality of cleaning liquid pools 21 includes a first cleaning liquid pool 211, a second cleaning liquid pool 212, and a third cleaning liquid pool 213, which are sequentially arranged along the extension direction of the maintenance kit 40. The cleaning strength of the cleaning liquid in the first cleaning liquid pool 211 is greater than that of the cleaning liquid in the second cleaning liquid pool 212, and the cleaning strength of the cleaning liquid in the second cleaning liquid pool 212 is greater than or equal to that of the cleaning liquid in the third cleaning liquid pool 213. The third cleaning liquid pool 213 is used as the backflush liquid pool, the second waste liquid pool 23 is arranged on the side of the third cleaning liquid pool 213 away from the second cleaning liquid pool 212, and the first waste liquid pool 22 is arranged on the side of the first cleaning liquid pool 211 away from the second cleaning liquid pool 212.

[0319] The cytometric component 10 is configured to insert the liquid suction member 110 into the cleaning liquid pool 21 with the strongest cleaning strength while inserting the liquid discharge member 120 into the first waste liquid pool 22. For example, in the maintenance mode, the cytometric component 10 is configured to insert the liquid suction member 110 into the first cleaning liquid pool 211 while inserting the liquid discharge member 120 into the first waste liquid pool 22.

[0320] In other embodiments, the cytometric component 10 can be configured to insert the liquid discharge member 120 into the first cleaning liquid pool 211 while inserting the liquid suction member 110 into the first waste liquid pool 22.

[0321] The maintenance kit 40 of the embodiment includes a second waste liquid pool 23 adjacent to the cleaning liquid pool 21 with the weakest cleaning intensity, and a first waste liquid pool 22 adjacent to the cleaning liquid pool 21 with the strongest cleaning intensity; the cell counting assembly 10 can suck the cleaning liquid from the maintenance kit 40 through the liquid discharging member 120 when the liquid suction channel is blocked, and can suck the cleaning liquid from the maintenance kit 40 through the liquid suction member 110 or the liquid discharging member 120 in the maintenance mode, that is, the maintenance kit 40 can be applied to the maintenance mode and the scene where the liquid suction channel is blocked, thereby reducing the cost.

[0322] Optionally, before the cell counting assembly 10 sucks the liquid from the maintenance kit 40 through the liquid discharging member 120, the cell counting assembly 10 performs the suction and exhaust cleaning on the liquid discharging member 120.

[0323] For example, when the liquid suction channel is blocked, the cell counting assembly 10 performs the suction and exhaust cleaning on the liquid discharging member 120, and sucks the liquid from the maintenance kit 40 through the liquid discharging member 120.

[0324] The cell counting assembly 10 of the embodiment performs the suction and exhaust cleaning on the liquid discharging member 120, which can prevent the pollution attached to the liquid discharging member 120 from entering the inner cavity 130 of the main body 11, reduce the pollution carried by the liquid discharging member 120, and improve the accuracy of the detection result of the POCT blood cell analyzer 1.

[0325] Optionally, along the extension direction of the liquid suction member 110, the spacing between the free end of the liquid suction member 110 and the free end of the liquid discharging member 120 is greater than or equal to one half of the depth of the cleaning liquid pool 21 of the maintenance kit 40, and less than or equal to two thirds of the depth of the cleaning liquid pool 21 of the maintenance kit 40.

[0326] The spacing between the free end of the liquid suction member 110 and the free end of the liquid discharging member 120 of the embodiment is greater than or equal to one half of the depth of the cleaning liquid pool 21 of the maintenance kit 40, and less than or equal to two thirds of the depth of the cleaning liquid pool 21 of the maintenance kit 40; so that the free end of the liquid discharging member 120 is located in the cleaning liquid pool 21 of the maintenance kit 40 to suck the cleaning liquid, and the liquid can be placed to prevent splashing to the maintenance kit 40 when the liquid discharging member 120 discharges the liquid.

[0327] According to some embodiments of the present application, the cell counting assembly 10 is provided with a maintenance mode, in which the cell counting assembly 10 is set to suck the cleaning liquid from different cleaning liquid pools 21 through the liquid suction member 110 from high to low in cleaning intensity, and discharge the cleaning liquid in the main body 11 to the maintenance kit 40 through the liquid discharging member 120. The cell counting assembly 10 of the embodiment in the maintenance mode is the same as the maintenance mode of the above-mentioned embodiments, which will not be described here again.

[0328] According to some embodiments of the present application, referring to FIG. 18 and FIG. 21, the cytometry component 10 is provided with a detection mode, and the loading seat is further used for receiving a detection kit 30 loaded therein. In the detection mode, the cytometry component 10 sucks the detection liquid from the detection kit 30 through the liquid suction member 110, and discharges the detection liquid in the main body 11 to the detection kit 30 through the liquid discharge member 120. The cytometry component 10 in the detection mode of the present embodiment is the same as the detection mode of the above-mentioned embodiments, and will not be described here again.

[0329] Optionally, the liquid discharge hole 117 is communicated with the liquid discharge member 120 through a switch valve 119 to form a liquid discharge channel. When the liquid discharge member 120 sucks liquid from the maintenance kit 40 or discharges liquid in the inner cavity 130, the switch valve 119 is controlled to be turned on, and at this time, the inner cavity 130 is communicated with the liquid discharge hole 117, the switch valve 119 and the liquid discharge member 120. When the liquid suction channel is impacted by gas or liquid, or the liquid suction member 110 sucks liquid, or the liquid suction member 110 discharges liquid in the inner cavity 130, the switch valve 119 is controlled to be turned off, and at this time, the inner cavity 130 is not communicated with the liquid discharge member 120.

[0330] According to some embodiments of the present application, referring to FIG. 18, FIG. 25, FIG. 26 and FIG. 27, FIG. 26 is a structural schematic diagram of a first embodiment of the pressure mechanism of the present application; and FIG. 27 is a structural schematic diagram of a second embodiment of the pressure mechanism of the present application. The POCT blood cell analyzer 1 of the present embodiment further comprises a pressure mechanism 310, which is communicated with the pressure interface 116 and is used for building pressure in the inner cavity 130. The pressure mechanism 310 can be the pressure building component 101 of the above-mentioned embodiments.

[0331] The pressure mechanism 310 comprises a pressure pump 311, a first switch valve 312, a second switch valve 313 and a three-way joint 314. The first end of the pressure pump 311 is connected with the first end of the three-way joint 314 through the first switch valve 312, the second end of the pressure pump 311 is connected with the second end of the three-way joint 314 through the second switch valve 313, and the third end of the three-way joint 314 is connected with the pressure interface 116.

[0332] As shown in FIG. 26, the first switch valve 312 is controlled to be turned on, and the second switch valve 313 is controlled to be turned off, and at this time, the pressure pump 311 is communicated with the cytometry component 10 through the first switch valve 312 to build negative pressure in the cytometry component 10.

[0333] As shown in FIG. 27, the second switch valve 313 is controlled to be turned on, and the first switch valve 312 is controlled to be turned off, and at this time, the pressure pump 311 is communicated with the cytometry component 10 through the second switch valve 313 to build positive pressure in the cytometry component 10.

[0334] The pressure mechanism 310 of the embodiment includes a pressure pump 311, a first switch valve 312, a second switch valve 313, and a three-way joint 314, and by controlling the first switch valve 312 and the second switch valve 313, negative pressure or positive pressure is established for the cytometric assembly 10, which is simple in structure, easy to implement, and reduces cost.

[0335] According to some embodiments of the present application, as shown in FIG. 18 and FIG. 25, the cytometric assembly 10 further includes a quick release 100, which is detachably connected with the main body 11, and cooperates with the main body 11 to confine the microporous sheet 12 and the second electrode 14 in the front cavity 111. The quick release 100 and the main body 11 can be fixed by screws or buckles, etc.

[0336] When the microporous sheet 12 needs to be replaced, the quick release 100 is directly detached from the main body 11, and the liquid suction member 110, the second electrode 14, and the microporous sheet 12 are detached from the front cavity 111 to replace the microporous sheet 12. The updated microporous sheet 12, the second electrode 14, and the microporous sheet 12 are sequentially loaded into the front cavity 111, and the quick release 100 is installed on the main body 11 to confine the microporous sheet 12 and the second electrode 14 in the front cavity 111.

[0337] The case where the microporous sheet 12 needs to be replaced includes, but is not limited to, the case where the liquid suction channel is still blocked after impact, or the case where the cytometric assembly 10 fails in self-checking, or the case where the POCT blood cell analyzer 1 generates an alarm to remind replacement of the microporous sheet 12.

[0338] The cytometric assembly 10 of the embodiment further includes a quick release 100, which is detachably connected with the main body 11, and can be directly detached from the main body 11 when the microporous sheet 12 needs to be replaced, so as to replace the microporous sheet 12 without the need for professional operation, which is easy to operate and reduces cost.

[0339] According to some embodiments of the present application, as shown in FIG. 18 and FIG. 25, the cytometric assembly 10 further includes a connecting member 18, a first sealing ring 15, a second sealing ring 19, and a third sealing ring 16.

[0340] The first sealing ring 15 is arranged between the main body 11 and the microporous sheet 12, and is used to seal the gap between the microporous sheet 12 and the main body 11. The third sealing ring 16 is arranged between the second electrode 14 and the microporous sheet 12 to seal the second electrode 14 and the microporous sheet 12.

[0341] The second electrode 14 is provided with a first through hole 141 along the axial direction of the micropore 121. The first through hole 141 includes a first hole segment 142, a second hole segment 143, and a third hole segment 145. The first hole segment 142 is located closer to the microporous sheet 12 than the second hole segment 143. The inner diameter of the first hole segment 142 is smaller than that of the second hole segment 143, thereby forming an annular table 144 at the connection between the second hole segment 143 and the first hole segment 142. The third hole segment 145 is located closer to the microporous sheet 12 than the first hole segment 142. The inner diameter of the first hole segment 142 is smaller than that of the third hole segment 145. The microporous sheet 12, the third sealing ring 16, and the third hole segment 145 of the second electrode 14 form the front chamber 111.

[0342] The second sealing ring 19 is clamped between the end surface of the liquid-absorbing member 110 and the annular platform 144 , and abuts against the side wall of the second hole section 143 .

[0343] The main body 11 is provided with a through hole 118 , and the connector 18 is passed through the through hole 118 . The connector 18 is used to be electrically connected to the second electrode 14 so that the impedance detection circuit supplies power to the second electrode 14 through the connector 18 .

[0344] Please refer to Figure 28, which is a schematic diagram of the structure of the fifth embodiment of the POCT blood cell analyzer of the present application. The POCT blood cell analyzer 1 provided in this embodiment includes a housing, a loading base, and a cell counting assembly 10. The loading base is used to receive the reagent kit 20. The cell counting assembly 10 is disposed within the housing and can move relative to the reagent kit 20, for example, horizontally or vertically, to approach the reagent kit 20, aspirate the test sample from the reagent kit 20, and perform a count test on the test sample.

[0345] Please refer to Figures 29 and 30. Figure 29 is a schematic diagram of the structure of the first embodiment of the cell counting assembly of the present application; Figure 30 is a partially enlarged schematic diagram of the structure of area B in Figure 29. The cell counting assembly 10 provided in this embodiment of the application includes a main body 11, a microporous sheet 12, a first electrode 13, a second electrode 14, and a quick-release member 100. The microporous sheet 12 includes a jewel sheet.

[0346] The main body 11 is provided with a front cavity 111 and a rear cavity 112 that are connected; the microporous sheet 12 is used to separate the front cavity 111 and the rear cavity 112, and the microporous sheet 12 is provided with micropores 121, and the front cavity 111 and the rear cavity 112 are connected through the micropores 121. The first electrode 13 is provided in the rear cavity 112 and is used to electrically connect to the test sample in the rear cavity 112; the second electrode 14 is provided in the front cavity 111 and is used to electrically connect to the test sample in the front cavity 111. The quick-release part 100 is detachably connected to the main body 11, and the quick-release part 100 is configured to cooperate with the main body 11 to confine the microporous sheet 12 and / or the second electrode 14 in the front cavity 111.

[0347] In an embodiment, the side wall of the front cavity 111 has a mounting hole, and the quick release part 100 can be mounted on the main body 11 through the mounting hole and define the micropore sheet 12 in the front cavity 111. When the micropore sheet 12 needs to be replaced, the quick release part 100 can be detached from the mounting hole, and then the quick release part 100 is detached from the main body 11. The user can pull the micropore sheet 12 out of the front cavity 111 through the mounting hole to replace the micropore sheet 12. Or, the quick release part 100 is connected with the micropore sheet 12. When the quick release part 100 is detached from the mounting hole, the micropore sheet 12 can be pulled out of the front cavity 111 with the quick release part 100. The user can replace the micropore sheet 12.

[0348] In another embodiment, as shown in FIG. 29, the quick release part 100 is arranged on the side of the main body 11 where the opening of the front cavity 111 faces. Then, the quick release part 100 is partially arranged at the opening of the front cavity 111 to define the second electrode 14 and the micropore sheet 12 in the front cavity 111. When the micropore sheet 12 needs to be replaced, the user can detach the quick release part 100 from the main body 11. Then, the second electrode 14 and the micropore sheet 12 can fall off from the front cavity 111. The user can replace the micropore sheet 12 and put the replaced micropore sheet 12 and the second electrode 14 back into the front cavity 111. Then, the user connects the quick release part 100 with the main body 11. The quick release part 100 defines the second electrode 14 and the micropore sheet 12 in the front cavity 111 to ensure the detection function of the cytometry assembly 10.

[0349] The quick release part 100 can be connected with the main body 11 through screws, buckle structures or other detachable structures.

[0350] The quick release part 100 defines the micropore sheet 12 and / or the second electrode 14 in the front cavity 111, and the quick release part 100 is detachably connected with the main body 11. Therefore, when the micropore sheet 12 needs to be replaced, the user can directly detach the quick release part 100 from the main body 11. Then, the micropore sheet 12 and / or the second electrode 14 can fall off from the front cavity 111. This facilitates the user to replace the micropore sheet 12, reduces the difficulty of replacing the micropore sheet 12 in the cytometry assembly 10, reduces the difficulty of maintaining the POCT blood cell analyzer 1, and improves the user experience of using the POCT blood cell analyzer 1.

[0351] In an embodiment, the side wall of the front cavity 111 can have an electrode interface. Then, an external power source can be connected with the second electrode 14 through the electrode interface to realize the electrical connection between the second electrode 14 and the detection sample in the front cavity 111. The external power source can also be connected with the first electrode 13 to realize the electrical connection between the first electrode 13 and the detection sample in the rear cavity 112.

[0352] Optionally, as shown in FIG. 29, the quick release member 100 is provided with a boss 151 on the side close to the main body 11, the boss 151 is arranged in the front cavity 111, and the boss 151 cooperates with the main body 11 to limit the second electrode 14 and / or the microporous sheet 12 in the front cavity 111.

[0353] Specifically, when the quick release member 100 is connected with the main body 11, the boss 151 is located in the front cavity 111 and abuts against the second electrode 14, thereby extruding the second electrode 14 and the microporous sheet 12 to fix the second electrode 14 and the microporous sheet 12 in the front cavity 111, so as to avoid the displacement of the second electrode 14 and the microporous sheet 12 and affect the counting detection accuracy of the cell counting assembly 10.

[0354] It can be understood that the setting height of the boss 151 can be determined by the depth of the front cavity 111, the length of the second electrode 14, and the thickness of the microporous sheet 12, so as to avoid the following situations: the setting height of the boss 151 is too high, the second electrode 14 and the microporous sheet 12 are excessively extruded, or the quick release member 100 cannot be connected with the main body 11 due to the length relationship between the boss 151 and the second electrode 14 and the microporous sheet 12; or the setting height of the boss 151 is too low, and the boss 151 cannot fix the second electrode 14 and the microporous sheet 12.

[0355] In an embodiment, when the cell counting assembly 10 needs to replace the microporous sheet 12, the user can detach the quick release member 100 from the main body 11, and without the action force of the boss 151 on the second electrode 14 and the microporous sheet 12, the second electrode 14 and the microporous sheet 12 can be separated from the front cavity 111, so as to facilitate the user to replace the microporous sheet 12.

[0356] After the user puts the new microporous sheet 12 and the second electrode 14 into the front cavity 111 again, the user can connect the quick release member 100 with the main body 11, and then the quick release member 100 sets the replaced microporous sheet 12 and the second electrode 14 in the front cavity 111, thereby completing the replacement of the microporous sheet 12.

[0357] It can be understood that since the boss 151 is arranged in the front cavity 111, the boss 151 also has a positioning effect on the installation of the quick release member 100 on the main body 11, and when the user wants to connect the quick release member 100 with the main body 11, the user can determine that the quick release member 100 is installed in place when the boss 151 is located in the front cavity 111, thereby improving the installation accuracy of the quick release member 100.

[0358] In summary, by arranging the quick release member 100 detachable from the main body 11, when the quick release member 100 is connected to the main body 11, the quick release member 100 can limit the microporous sheet 12 and / or the second electrode 14 in the front cavity 111, fix the second electrode 14 and the microporous sheet 12, and improve the detection accuracy of the cytometric assembly 10. When the microporous sheet 12 needs to be replaced, the user can directly detach the quick release member 100 from the main body 11 to replace the microporous sheet 12, thereby reducing the difficulty of replacing the microporous sheet 12 in the cytometric assembly 10.

[0359] Optionally, the cytometric assembly 10 further comprises a fixing member (not shown in the figure). The main body 11 is provided with at least one first connecting hole 140 on the side close to the quick release member 100. The quick release member 100 is provided with at least one second connecting hole 152 corresponding to the first connecting hole 140. The fixing member is arranged to pass through the first connecting hole 140 and the second connecting hole 152.

[0360] In an embodiment, the fixing member can be the screw structure described above. Then, the screw passes through the first connecting hole 140 and the second connecting hole 152 and is fixed by a nut, thereby achieving detachable connection of the quick release member 100 and the main body 11. When the microporous sheet 12 needs to be replaced, the user can directly detach the quick release member 100 from the main body 11 by unscrewing the screw structure, thereby replacing the microporous sheet 12. In other embodiments, the fixing member can also be other detachable structures, or the quick release member 100 and the main body 11 are connected by other detachable structures, which are not limited in the present application.

[0361] Optionally, the second electrode 14 comprises an axially through first cavity 150 (i.e. the first through hole 141 in the above embodiment). The cytometric assembly 10 further comprises a liquid suction member 110. The liquid suction member 110 abuts against the annular plane at the end of the second electrode 14 away from the microporous sheet 12. The liquid suction member 110 and the second electrode 14 form a liquid suction channel. The liquid suction member 110 can be a liquid suction pipe.

[0362] In the kit, the detection sample can be sucked into the front cavity 111 by the liquid suction member 110 and fully contacts and electrically connects with the second electrode 14 through the first cavity 150 of the second electrode 14.

[0363] It can be understood that, since the second electrode 14 in the present embodiment is a sleeve structure, the detection sample flows through the cavity of the second electrode 14, and the residual detection sample can coagulate in the first cavity 150 of the second electrode 14 to block the liquid suction channel. Therefore, the user can also replace the second electrode 14 by detaching the quick release member 100 from the main body 11, thereby avoiding the situation that the liquid suction channel is blocked to affect the detection function of the cytometric assembly 10.

[0364] In the second electrode 14 of one embodiment, the tube diameter of the first cavity 150 near the end of the microporous sheet 12 is larger than the tube diameter of the first cavity 150 near the end of the wick 110. By slowing down the flow rate of the detection sample, the liquid flow of the detection sample through the micropores 121 of the microporous sheet 12 is more stable, further ensuring that the detection sample is in sufficient contact with the second electrode 14, and also avoiding the situation that bubbles are generated due to the narrow space between the second electrode 14 and the microporous sheet 12 during the flow of the detection sample, affecting the efficiency of the detection sample passing through the microporous sheet 12 into the rear cavity 112, and improving the technical detection accuracy of the cytometric assembly 10 on the detection sample.

[0365] In one embodiment, the second electrode 14 and the wick 110 can also be an integrated structure. When the quick-release assembly 100 is arranged on the main body 11 with the opening of the front cavity 111 facing one side, the user can disassemble the quick-release assembly 100 from the main body 11 when replacing the microporous sheet 12. Since the wick 110 is arranged on the boss 151, the wick 110 and the second electrode 14 can be separated from the main body 11 along with the quick-release assembly 100 to expose the microporous sheet 12 in the front cavity 111, facilitating the user to replace the microporous sheet 12. When the second electrode 14 and the wick 110 are an integrated structure, the end of the integrated structure near the microporous sheet 12 can be made of conductive material to realize the electrical connection function with the detection sample, and the end of the integrated structure away from the microporous sheet 12 can be made of ordinary material to realize the function of allowing the detection sample to pass through.

[0366] In another embodiment, the cytometric assembly 10 can further include a plurality of sealing members 160, which can be respectively arranged as a first sealing ring between the microporous sheet 12 and the bottom of the front cavity 111, a third sealing ring between the microporous sheet 12 and the second electrode 14, and a second sealing ring between the second electrode 14 and the wick 110, to seal the gap between the two parts and ensure the sealing of the wicking channel.

[0367] In other embodiments, as shown in FIG. 29, the first cavity 150 includes a third hole section 145, a first hole section 142 and a second hole section 143, which are sequentially arranged in a direction away from the microporous sheet 12, the inner diameter of the first hole section 142 is smaller than that of the second hole section 143, thereby forming an annular plane at the joint of the first hole section 142 and the second hole section 143, one end of the liquid suction member 110 can abut on the annular plane, and the second hole section 143 positions the liquid suction member 110. The inner diameter of the third hole section 145 is larger than that of the first hole section 142, so as to slow down the flow rate of the detection sample, avoid the formation of bubbles of the detection sample at the second electrode 14 and the microporous sheet 12, make the liquid flow of the detection sample passing through the micropores 121 of the microporous sheet 12 more stable, and further ensure that the detection sample fully contacts with the second electrode 14, thereby improving the technical detection efficiency of the cytometric assembly 10 on the detection sample.

[0368] Optionally, the cytometric assembly 10 further includes a liquid discharge member 120 and a switch valve 119, the liquid discharge member 120 is connected with the rear cavity 112 through the switch valve 119, so as to form a liquid discharge channel.

[0369] In an embodiment, please refer to FIG. 31, which is a structural schematic diagram of a first embodiment of the switch valve of the present application. The switch valve 119 includes a valve seat 181, a valve core 182 and a driving block 183.

[0370] The valve seat 181 includes a liquid flow pipeline 1811, the liquid inlet of the liquid flow pipeline 1811 is connected with the rear cavity 112, the liquid outlet of the liquid flow pipeline 1811 is connected with the liquid discharge member 120, and the driving block 183 is arranged spaced apart from the valve seat 181, so as to drive the valve core 182 to move close to or away from the liquid flow pipeline 1811.

[0371] Specifically, the driving block 183 can drive the valve core 182 to move close to the liquid flow pipeline 1811, when the valve core 182 moves into the liquid flow pipeline 1811 and abuts against the wall of the liquid flow pipeline 1811, the valve core 182 blocks the liquid flow pipeline 1811, and the liquid flow pipeline 1811 is cut off, at this time, the switch valve 119 is closed. When the driving block 183 drives the valve core 182 to move away from the liquid flow pipeline 1811, the valve core 182 moves out of the liquid flow pipeline 1811, the liquid flow pipeline 1811 is conducted, at this time, the switch valve 119 is opened.

[0372] In an embodiment, the valve core 182 can be an iron core, and the driving block 183 can be an electromagnetic member, when the driving block 183 is electrified, it can attract or repel the valve core 182, so as to realize the driving of the driving block 183 to move the valve core 182 close to or away from the liquid flow pipeline 1811. In other embodiments, the driving block 183 and the valve core 182 can also have other structures, which are not limited in the present application.

[0373] In the cell counting component 10, referring to FIG. 28, the main body 11 can include an inlet hole 114 and an outlet hole 117, the inlet hole 114 is arranged at the bottom of the front cavity 111 to communicate the front cavity 111 with the rear cavity 112, and the micropore sheet 12 can be arranged at the side of the inlet hole 114 close to the front cavity 111. The outlet hole 117 is arranged at the bottom of the rear cavity 112, and the outlet member 120 is connected with the outlet hole 117 through the on-off valve 119.

[0374] When the detection sample enters the front cavity 111 from the suction member 110 and contacts the second electrode 14, the detection sample can further enter the rear cavity 112 through the micropore 121 on the micropore sheet 12 and the inlet hole 114, and contact the first electrode 13. At this time, the first electrode 13 is electrically connected with the detection sample in the rear cavity 112, the second electrode 14 is electrically connected with the detection sample in the front cavity 111, the external power supply, the first electrode 13, the second electrode 14 and the detection sample form a complete current loop, and the cell counting component 10 can perform counting detection on the detection sample.

[0375] Among them, since the first electrode 13 is arranged on the side wall of the rear cavity 112 and has a certain height difference with the inlet of the micropore sheet 12, during the process that the detection sample enters the rear cavity 112 from the front cavity 111, the first electrode 13 can contact the accumulated detection sample to realize electrical connection only after a certain amount of detection sample is accumulated in the rear cavity 112. Therefore, at this time, the on-off valve 119 at the outlet channel is in a closed state to avoid the detection sample entering the rear cavity 112 from the front cavity 111 directly discharged through the outlet channel, so that the detection sample cannot be stored in the rear cavity 112 and cannot be electrically connected with the first electrode 13, which affects the counting detection function of the cell counting component 10.

[0376] After the cell counting component 10 completes the counting detection of the detection sample, the on-off valve 119 can be opened, and the detection sample in the rear cavity 112 can be discharged through the outlet member 120. Since the outlet hole 117 is arranged at the bottom of the rear cavity 112, it can ensure that the detection sample in the rear cavity 112 is completely discharged.

[0377] In an embodiment, the on-off valve 119 and the outlet member 120 can be arranged on the main body 11 and connected with the outlet hole 117, and located on the same side of the inlet channel of the main body 11. Then the quick release member 100 has a through hole corresponding to the outlet member 120. When the quick release member 100 is connected with the main body 11, one end of the outlet member 120 passes through the through hole on the quick release member 100 and is exposed outside the quick release member 100, so as to ensure the outlet function of the outlet member 120.

[0378] Further, when the user needs to replace the microwell sheet 12 of the cytometry assembly 10, after the user detaches the quick-release assembly 100 from the main body 11, the on-off valve 119 and the liquid discharge assembly 120 will not be separated from the main body 11 along with the quick-release assembly 100, reducing the user's installation steps for other components except the microwell sheet 12, further reducing the user's difficulty in replacing the microwell sheet 12 in the cytometry assembly 10, reducing the maintenance difficulty and maintenance cost of the POCT blood cell analyzer 1, and improving the user's experience of using the POCT blood cell analyzer 1.

[0379] Optionally, as shown in FIG. 32, FIG. 32 is a structural schematic diagram of the sixth embodiment of the POCT blood cell analyzer provided in the present application. The POCT blood cell analyzer 1 provided in the embodiment of the present application further comprises a pressure mechanism 310 connected with the rear cavity 112 of the cytometry assembly 10.

[0380] Specifically, the pressure mechanism 310 is configured to provide negative pressure to the rear cavity 112, and the liquid suction assembly 110 is configured to suck the detection sample from the reagent box 20 to flow into the rear cavity 112; the pressure mechanism 310 is further configured to provide positive pressure to the rear cavity 112, and the liquid discharge channel is configured to discharge the detection sample in the rear cavity 112.

[0381] Specifically, when the cytometry assembly 10 in the POCT blood cell analyzer 1 moves close to the reagent box 20 to make the liquid suction assembly 110 contact with the detection sample in the reagent box 20, the on-off valve 119 is closed, and the pressure mechanism 310 provides negative pressure to the rear cavity 112. Due to the action of the negative pressure, the detection sample in the reagent box 20 enters the front cavity 111 through the liquid suction assembly 110, is electrically connected with the second electrode 14, and enters the rear cavity 112 through the microwell 121 of the microwell sheet 12 and the liquid inlet hole 114, and is electrically connected with the first electrode 13, and then the cytometry assembly 10 performs counting detection on the detection sample through the current parameter between the first electrode 13 and the second electrode 14.

[0382] When the counting detection of the detection sample by the cytometry assembly 10 is completed, the on-off valve 119 is opened, and the pressure mechanism 310 provides positive pressure to the rear cavity 112. Under the action of the positive pressure, the detection sample in the rear cavity 112 can be discharged from the rear cavity 112 through the liquid discharge hole 117, the on-off valve 119 and the liquid discharge assembly 120 in turn. In an embodiment, when the liquid suction assembly 110 of the cytometry assembly 10 sucks the reagent in the reagent box 20, the end of the liquid discharge assembly 120 away from the rear cavity 112 can also be located in the reagent box 20, and then the detection sample after the counting detection can return to the reagent box 20 through the liquid discharge assembly 120, without the need to additionally set a sample waste liquid collection device, thereby reducing the manufacturing cost of the POCT blood cell analyzer 1.

[0383] It can be understood that, due to the absence of valve or other structure in the liquid suction channel, when the pressure mechanism 310 provides positive pressure to the rear cavity 112, part of the detection sample in the rear cavity 112 will also be discharged from the liquid suction channel, but the amount of the detection sample discharged from the liquid suction channel can be ignored due to the blockage of the micropores 121 of the micropore sheet 12. Therefore, the valve structure is not added in the liquid suction channel in the present embodiment, so as to avoid increasing the volume and cost of the cytometer assembly 10.

[0384] Optionally, the pressure mechanism 310 comprises a pressure pump 311, a first switch valve 312, a second switch valve 313 and a three-way joint 314. The first end of the pressure pump 311 is connected with the first end of the three-way joint 314 through the first switch valve 312, the second end of the pressure pump 311 is connected with the second end of the three-way joint 314 through the second switch valve 313, and the third end of the three-way joint 314 is connected with the rear cavity 112 of the cytometer assembly 10.

[0385] In an embodiment, when the pressure mechanism 310 needs to provide negative pressure to the rear cavity 112, the first switch valve 312 connected with the negative pressure passage of the pressure pump 311 is opened, and the second switch valve 313 connected with the positive pressure passage of the pressure pump 311 is closed, so that the pressure pump 311 provides negative pressure to the rear cavity 112 through the first switch valve 312 and the first end of the three-way joint 314; when the pressure mechanism 310 needs to provide positive pressure to the rear cavity 112, the second switch valve 313 connected with the positive pressure passage of the pressure pump 311 is opened, and the first switch valve 312 connected with the negative pressure passage of the pressure pump 311 is closed, so that the pressure pump 311 provides positive pressure to the rear cavity 112 through the second switch valve 313 and the second end of the three-way joint 314.

[0386] In another embodiment, the first switch valve 312 and the second switch valve 313 can also be combined into a two-position three-way valve to switch the positive pressure or negative pressure provided by the pressure pump 311 to the rear cavity 112. In the case of switching the positive pressure or negative pressure provided by the pressure pump 311 to the rear cavity 112, the present embodiment does not limit the number and types of valves included in the pressure mechanism 310.

[0387] In summary, in the cell counting component 10 of the POCT blood cell analyzer 1 provided in the embodiments of the present application, the microwell sheet 12 and the second electrode 14 are located in the front cavity 111 of the main body 11, the quick-release member 100 is detachably connected with the main body 11, and when the quick-release member 100 is connected with the main body 11, the quick-release member 100 fixes the second electrode 14 and / or the microwell sheet 12 in the front cavity 111. When the microwell sheet 12 needs to be replaced in the cell counting component 10, the user can directly detach and separate the quick-release member 100 from the main body 11, so that the second electrode 14 and / or the microwell sheet 12 are separated from the front cavity 111. The user can directly replace the microwell sheet 12 and / or the second electrode 14, and after the replacement of the microwell sheet 12 or the second electrode 14 is completed, the user reconnects the quick-release member 100 with the main body 11, so that the counting detection function of the cell counting component 10 is restored. The replacement difficulty of the microwell sheet 12 or the second electrode 14 in the cell counting component 10 is reduced, and the replacement does not need professional personnel, but can be performed by the user. The maintenance difficulty and cost of the POCT blood cell analyzer 1 are reduced, and the user experience of the POCT blood cell analyzer 1 is improved.

[0388] Referring to FIGS. 33-35, FIG. 33 is a structural schematic diagram of a seventh embodiment of the POCT blood cell analyzer provided in the present application, FIG. 34 is a structural schematic diagram of a first embodiment of a cell counting component in FIG. 33, and FIG. 35 is a structural schematic diagram of a second embodiment of the cell counting component in FIG. 33. As shown in FIGS. 33-35, in the embodiments of the present application, the POCT blood cell analyzer 1 includes a shell 5, a transfer mechanism 3, a first driving member 190, and a cell counting component 10.

[0389] Specifically, the shell 5 is used to shield the transfer mechanism 3, the first driving member 190, and the cell counting component 10, so that various work processes of the POCT blood cell analyzer 1 can be performed in a closed environment, reducing the risk of external interference and sample leakage. The transfer mechanism 3 is arranged in the shell 5, and the transfer mechanism 3 is used to receive and transport a reagent box 20, which is used to store samples and / or reagents. The cell counting component 10 is arranged in the shell 5, and the cell counting component 10 includes a main body 11 and a suction and discharge assembly 161. The main body 11 is fixedly installed in the shell 5, and the suction and discharge assembly 161 is connected with the main body 11 through a pipeline. The first driving member 190 is arranged in the shell 5, and the first driving member 190 is used to drive the suction and discharge assembly 161 to move, so that the suction and discharge assembly 161 can move relative to the reagent box 20. The suction and discharge assembly 161 is used to perform liquid suction and / or liquid discharge operations on the reagent box 20. The samples and / or reagents in the reagent box 20 can be mixed and reacted under external operations, so that the reagent box 20 stores detection samples that can be used for testing by the cell counting component 10.

[0390] The suction and discharge assembly 161 can include a liquid suction assembly 162 and a liquid discharge assembly 163. The liquid suction assembly 162 cooperates with the main body 11 to form a liquid suction channel for conveying the detection sample; the liquid discharge assembly 163 cooperates with the main body 11 to form a liquid discharge channel for conveying the detection sample; the liquid suction assembly 162 is used to suck the detection sample from the reagent box 20, so that the main body 11 is used to count the impedance of the detection sample and obtain the detection result; when the impedance counting of the cytometric assembly 10 is completed, the liquid discharge assembly 163 is used to discharge the detection sample that has completed the detection to the reagent box 20. It can be understood that the main body 11 of the cytometric assembly 10 is used as a detection area, the main body 11 is connected with the liquid suction assembly 162 through the liquid suction channel, and the main body 11 is connected with the liquid discharge assembly 163 through the liquid discharge channel. When the liquid suction assembly 162 sucks the detection sample from the first liquid pool, the detection sample sucked by the liquid suction assembly 162 enters the main body 11 through the liquid suction channel, so that the main body 11 counts the impedance of the detection sample and obtains the detection result. After the impedance counting of the cytometric assembly 10 is completed, the liquid discharge assembly 163 is used to discharge the detection sample that has completed the detection in the main body 11 to the rear cavity of the reagent box 20.

[0391] The reagent box 20 can include a plurality of liquid pools for respectively storing samples, reagents and / or mixed liquids. For example, the reagent box 20 can include a first liquid pool and a second liquid pool, the first liquid pool is used to store the mixed liquid of the reagent and the sample, i.e. the detection sample; the liquid suction assembly 162 and the liquid discharge assembly 163 can perform liquid suction and discharge operations in the first liquid pool of the reagent box 20, the liquid suction assembly 162 can also perform liquid suction operation in the first liquid pool of the reagent box 20, and perform liquid discharge operation on the second liquid pool of the reagent box 20 through the liquid discharge assembly 163, which is not limited here.

[0392] In the embodiment of the present application, the POCT blood cell analyzer 1 receives and transmits the reagent box 20 through the pipetting mechanism 4, the reagent box 20 is used to store samples and / or reagents; the cytometric assembly 10 of the POCT blood cell analyzer 1 is arranged in the shell 5, the main body 11 of the cytometric assembly 10 is fixedly installed in the shell 5, the suction and discharge assembly 161 is connected with the main body 11 through the pipeline, and the first driving member 190 is used to drive the suction and discharge assembly 161 to move relative to the reagent box 20 to complete the liquid suction and / or discharge operation. In the above manner, the first driving member 190 only drives the suction and discharge assembly 161 to move relative to the reagent box 20 to complete the liquid suction and / or discharge operation, and the main body 11 fixedly installed in the shell 5 can count the impedance of the sample in the reagent box 20 through the liquid suction and / or discharge operation of the suction and discharge assembly 161, so that the reagent box 20 can realize rapid detection without separately arranging a counting mechanism, which is beneficial to reduce the manufacturing cost of the reagent box 20.

[0393] In an embodiment, the suction and discharge assembly 161 comprises a suction assembly 162, a discharge assembly 163 and a seat body 1000, the suction assembly 162 and the discharge assembly 163 are arranged on the seat body 1000, the seat body 1000 is connected with the first driving member 190, the first driving member 190 is used to drive the seat body 1000 to move, so that the suction assembly 162 and the discharge assembly 163 can move to a preset position relative to the cartridge 20, and then the suction assembly 162 and the discharge assembly 163 can perform suction and discharge operations on the liquid in the cartridge 20. The main body 11 further comprises a suction pipe 17 and a discharge pipe 115, the suction assembly 162 is connected with the suction pipe 17 through a pipeline, and the discharge assembly 163 is connected with the discharge pipe 115 through a pipeline.

[0394] Specifically, the first driving member 190 is used to drive the seat body 1000 to move, so that the suction assembly 162 moves to the suction position of the cartridge 20, and the suction assembly 162 is used to suck the detection sample in the cartridge 20, so that the liquid sucked by the suction assembly 162 can enter a certain cavity of the main body 11 through the pipeline and the suction pipe 17 to perform impedance counting. After the impedance counting is completed, the detection sample of the main body 11 can be discharged through the pipeline and the discharge pipe 115, and the detection sample is discharged to the cartridge 20 through the discharge assembly 163. Therefore, the POCT blood cell analyzer 1 of the embodiment can suck the detection sample of the cartridge 20 through the suction assembly 162, and make the detection sample enter the main body 11 through the pipeline and perform impedance counting, after the impedance counting is completed, the detection sample after the detection is discharged to the cartridge 20 through the discharge assembly 163, so that the rapid detection of the cartridge 20 is realized; the detection sample after the detection is discharged to the cartridge 20, without the need to additionally arrange a sample waste liquid collecting device in the shell 5, so as to reduce the structural space of the POCT blood cell analyzer 1, and further reduce the manufacturing cost of the POCT blood cell analyzer 1.

[0395] For example, in an embodiment, the suction assembly 162 is used to suck the detection sample from the first liquid pool, and the discharge assembly 163 is used to discharge the detection sample after the detection to the first liquid pool. In another embodiment, the suction assembly 162 is used to suck the detection sample from the first liquid pool, and the discharge assembly 163 is used to discharge the detection sample after the detection to other liquid pools of the cartridge 20 except the first liquid pool. For example, the cartridge 20 can further comprise a dilution pool for performing dilution operation, a sample pool for storing samples, a reagent pool for storing reagents, etc., and the discharge assembly 163 can be used to discharge the detection sample after the detection to any of the dilution pool, the sample pool, the reagent pool and the first liquid pool, which is not limited here.

[0396] In an embodiment, as shown in FIG. 34, the main body 11 is provided with a front cavity 111 and a rear cavity 112, and the cell counting assembly 10 further comprises a first electrode 13, a second electrode 14, and a microporous sheet 12 provided with micropores, the front cavity 111 and the rear cavity 112 are communicated through the micropores, the first electrode 13 is arranged in the rear cavity 112, the second electrode 14 is configured to electrically connect with the detection sample in the front cavity 111, a liquid suction assembly 162 is connected with the front cavity 111 through a liquid suction channel, and a liquid discharge assembly 163 is connected with the rear cavity 112 through a liquid discharge channel, the liquid suction assembly 162 is configured to suck the detection sample in the first liquid pool so as to make the detection sample enter the front cavity 111, the detection sample in the front cavity 111 enters the rear cavity 112 through the micropores, and the liquid discharge assembly 163 is configured to discharge the detection sample in the rear cavity 112.

[0397] Specifically, the front cavity 111 of the main body 11 can also be referred to as a front pool, the rear cavity 112 can also be referred to as a rear pool or a waste liquid cavity, etc., the microporous sheet 12 is configured to isolate the front cavity 111 and the rear cavity 112, the microporous sheet 12 is provided with micropores, and the front cavity 111 and the rear cavity 112 are communicated through the micropores. The liquid suction tube 17 can be arranged on one side of the front cavity 111, the liquid discharge tube 115 can be arranged on one side of the rear cavity 112, and the liquid suction tube 17 and the liquid discharge tube 115 can be arranged on the same side wall of the main body 11, so as to facilitate the regular distribution of the liquid suction assembly 162, the liquid discharge assembly 163 and the pipelines, and improve the layout aesthetics of the cell counting assembly 10. The microporous sheet 12 can also be referred to as a gemstone hole sheet, a gemstone sheet or a detection sheet, and the micropores can also be referred to as gemstone holes or detection holes. For example, the detection sample in the front cavity 111 flows through the micropores into the rear cavity 112, so as to allow the cells of the detection sample to flow through the micropores one by one. The first electrode 13 is arranged in the rear cavity 112, and one end of the first electrode 13 can be arranged in the rear cavity 112, and the other end of the first electrode 13 is located outside the rear cavity 112. The first electrode 13 can be referred to as a rear pool electrode, and the second electrode 14 can be referred to as a front pool electrode.

[0398] The liquid suction assembly 162 is connected with the liquid suction tube 17 through a pipeline, and the liquid discharge assembly 163 is connected with the liquid discharge tube 115 through a pipeline. The liquid suction assembly 162 is configured to suck the detection sample from the reagent box 20, and make the detection sample enter the front cavity 111 through the pipeline and the liquid suction tube 17, and the detection sample in the front cavity 111 enters the rear cavity 112 through the micropores. In this process, the first electrode 13, the second electrode 14 and the detection sample between the first electrode 13 and the second electrode 14 form a detection circuit. Since the blood cells are poor conductors, when the blood cells flow through the micropores, the resistance is formed and the electric pulse signal between the first electrode 13 and the second electrode 14 is changed. The cell counting assembly 10 can characterize the blood cell characteristics of the detection sample by collecting the change of the electric pulse signal between the first electrode 13 and the second electrode 14, and obtain a detection result.

[0399] In possible implementation manners, the cytometric component 10 can move relative to the kit 20; specifically, the cytometric component 10 moves, the kit 20 does not move; or the cytometric component 10 moves, the kit 20 moves; or the cytometric component 10 does not move, the kit 20 moves. For example, the kit 20 is placed on the transfer mechanism 3, and the cytometric component 10 can move relative to the position of the kit 20 so that the liquid suction component 162 can be opposite to the front cavity 111 and suck the detection sample in the front cavity 111.

[0400] In the embodiment of the present application, the POCT blood cell analyzer 1 sucks the detection sample in the first liquid pool by the liquid suction component 162, so that the detection sample enters the front cavity 111 through the suction tube 17, the detection sample in the front cavity 111 enters the rear cavity 112 through the micropore and obtains a detection result, the liquid discharge component 163 is used for discharging the detection sample in the rear cavity 112 to the rear cavity 112 of the kit 20, so that the cytometric component 10 can perform impedance counting on the detection sample of the kit 20, the kit 20 does not need to be provided with the micropore sheet 12 to achieve rapid detection, and the micropore sheet 12 of the cytometric component 10 can be reused, which is beneficial to reduce the manufacturing cost of the kit 20, reduce the detection cost of the sample, and improve the practicability of the POCT blood cell analyzer 1.

[0401] Optionally, the main body 11 further comprises a quick release 100, and the micropore sheet 12 is detachably connected with the front cavity 111 through the quick release 100; or the main body 11 is detachably installed in the shell 5 as a whole.

[0402] Specifically, in an embodiment, the main body 11 is detachably installed in the shell 5 as a whole, for example, the main body 11 can be detachably installed in the shell 5 by means of fasteners such as buckles, screws, bolts, etc., so that the user can replace or maintain the microwell sheet 12 in the main body 11 by detaching the main body 11. In another embodiment, the sidewall of the front cavity 111 is provided with a mounting hole, the quick-release component 100 is mounted on the main body 11 through the mounting hole, and the microwell sheet 12 in the front cavity 111 is defined. When the microwell sheet 12 needs to be replaced, the quick-release component 100 is detached from the mounting hole to separate the quick-release component 100 from the main body 11, so that the user can pull the microwell sheet 12 out of the front cavity 111 through the mounting hole to replace the microwell sheet 12; or the quick-release component 100 is connected with the microwell sheet 12, and when the quick-release component 100 is detached from the mounting hole, the microwell sheet 12 can be pulled out of the front cavity 111 along with the quick-release component 100, and the user can replace the microwell sheet 12; or the quick-release component 100 is arranged on the side of the front cavity 111 facing the opening, so as to define the second electrode 14 and the microwell sheet 12 in the front cavity 111. When the microwell sheet 12 needs to be replaced, the user can separate the quick-release component 100 from the main body 11, so that the second electrode 14 and the microwell sheet 12 can be separated from the front cavity 111. The user can replace the microwell sheet 12, and after replacement, the replaced microwell sheet 12 and the second electrode 14 are put back into the front cavity 111, so that the quick-release component 100 is reconnected with the main body 11, and the detection function of the cytometry assembly 10 is ensured to work normally.

[0403] Since the cytometry assembly 10 can be used for multiple impedance counting, the microwells of the microwell sheet 12 may be blocked after multiple counting, and accidents such as microwell blockage may occur due to the influence of liquid, reagent crystallization, etc., resulting in a high maintenance frequency of the cytometry assembly 10. Therefore, the cytometry assembly 10 of the present embodiment can detachably connect the microwell sheet 12 with the front cavity 111 through the quick-release component 100, or the main body 11 of the cytometry assembly 10 is detachably installed in the shell 5 as a whole, so that the user can detach and replace the microwell sheet 12 of the cytometry assembly 10, which is beneficial to the regular maintenance of the microwell sheet 12 and reduces the adverse effects of accidents such as blockage on the detection function of the cytometry assembly 10.

[0404] Optionally, please refer to FIG. 36, which is a structural schematic diagram of an embodiment of the pressure building mechanism provided in the present application. As shown in FIG. 36, the POCT blood cell analyzer 1 of the present embodiment further comprises a pressure mechanism 310 connected with the rear cavity 112. The pressure mechanism 310 is used to provide negative pressure for the rear cavity 112, so that the detection sample in the front cavity 111 enters the rear cavity 112 under the action of negative pressure. The pressure mechanism 310 is also used to provide positive pressure for the rear cavity 112, so that the detection sample in the rear cavity 112 is discharged under the action of positive pressure through the liquid discharge assembly 163.

[0405] Specifically, the pressure mechanism 310 is connected with the rear cavity 112 and is used to build pressure on the rear cavity 112. For example, the pressure mechanism 310 can build pressure through a syringe, a pressure pump 311 or the like, so that the rear cavity 112 is in a positive pressure environment or a negative pressure environment. The positive pressure generally refers to a pressure environment with a pressure higher than the atmospheric pressure, and the negative pressure generally refers to a pressure environment with a pressure lower than the atmospheric pressure. The front cavity 111 is generally in a normal pressure or an atmospheric pressure environment. When the pressure mechanism 310 provides the negative pressure for the rear cavity 112, a pressure difference is formed between the front cavity 111 and the rear cavity 112, and the detection sample in the front cavity 111 enters the rear cavity 112 through the micropore under the action of the negative pressure of the rear cavity 112, so that the detection sample flows through the micropore to be counted by impedance and obtain a corresponding detection result. After the detection is completed, the pressure mechanism 310 provides the positive pressure for the rear cavity 112, one end of the drainage assembly 163 is connected with the rear cavity 112 through a pipeline and a drainage connector, the other end of the drainage assembly 163 is exposed to the atmospheric environment, and a pressure difference is formed between the detection sample in the rear cavity 112 and the drainage assembly 163, so that the detection sample in the rear cavity 112 is drained to the rear cavity 112 through the drainage assembly 163 under the action of the pressure difference.

[0406] In the embodiment of the present application, the POCT blood cell analyzer 1 adjusts the pressure environment of the rear cavity 112 through the pressure mechanism 310, so that the detection sample in the front cavity 111 enters the rear cavity 112 through the micropore when the rear cavity 112 is in the positive pressure environment, and the detection sample in the rear cavity 112 is drained under the action of the positive pressure through the drainage assembly 163 when the rear cavity 112 is in the negative pressure environment, so that the cell counting assembly 10 can quickly count the detection sample of the reagent box 20. The reagent box 20 does not need to be provided with the micropore sheet 12 and can also realize rapid detection, and the micropore sheet 12 of the cell counting assembly 10 can be repeatedly used, which is beneficial to reduce the manufacturing cost of the reagent box 20, reduce the detection cost of the sample, and improve the practicability of the POCT blood cell analyzer 1.

[0407] Further, the cell counting assembly 10 further includes a switch valve 119, and the drainage pipe 115 is connected with the rear cavity 112 through the switch valve 119. When the cell counting assembly 10 completes the counting and detection of the detection sample, the switch valve 119 is opened, and the pressure mechanism 310 provides the positive pressure for the rear cavity 112. Under the action of the positive pressure, the detection sample in the rear cavity 112 can be sequentially drained to the reagent box 20 through the switch valve 119, the drainage pipe 115, the pipeline and the drainage assembly 163.

[0408] Wherein, since the first electrode 13 is arranged on the sidewall of the rear cavity 112 and has a certain height difference with the microporous sheet 12, in the counting process of detecting the sample from the front cavity 111 into the rear cavity 112, the first electrode 13 can contact and realize electrical connection with the accumulated detection sample in the rear cavity 112 after a certain amount of detection sample is accumulated in the rear cavity 112. At this time, the switch valve 119 is in a closed state to avoid the detection sample from the front cavity 111 entering the rear cavity 112 and being directly discharged without being stored in the rear cavity 112, thereby causing the detection sample to fail to realize electrical connection with the first electrode 13 and affecting the counting detection function of the cell counting assembly 10. After the cell counting assembly 10 completes the counting detection of the detection sample, the switch valve 119 can be opened, and the detection sample in the rear cavity 112 can be discharged through the liquid discharge pipe 115. Since the liquid discharge pipe 115 is arranged at the bottom of the rear cavity 112, it can ensure that the detection sample in the rear cavity 112 is completely discharged.

[0409] It can be understood that, since the channel where the liquid suction pipe 17 is located does not have a valve or the like structure, in the case that the pressure mechanism 310 provides positive pressure to the rear cavity 112, part of the detection sample in the rear cavity 112 will also be discharged from the liquid suction pipe 17, but the amount of the detection sample discharged from the liquid suction pipe 17 is not much and can be ignored due to the obstruction of the micropores of the microporous sheet 12. Therefore, in the present embodiment, a valve structure is not added in the channel where the liquid suction pipe 17 is located, so as to avoid increasing the volume and cost of the cell counting assembly 10.

[0410] Optionally, the pressure mechanism 310 includes a pressure pump 311, a first switch valve 312, a second switch valve 313, and a three-way joint 314. Wherein, the first end of the pressure pump 311 is connected with the first end of the three-way joint 314 through the first switch valve 312, the second end of the pressure pump 311 is connected with the second end of the three-way joint 314 through the second switch valve 313, and the third end of the three-way joint 314 is connected with the rear cavity 112 of the cell counting assembly 10.

[0411] At this time, when the pressure mechanism 310 needs to provide negative pressure to the rear cavity 112, the first switch valve 312 connected with the negative pressure passage of the pressure pump 311 is opened, and the second switch valve 313 connected with the positive pressure passage of the pressure pump 311 is closed, so that the pressure pump 311 provides negative pressure to the rear cavity 112 through the first switch valve 312 and the first end of the three-way joint 314; when the pressure mechanism 310 needs to provide positive pressure to the rear cavity 112, the second switch valve 313 connected with the positive pressure passage of the pressure pump 311 is opened, and the first switch valve 312 connected with the negative pressure passage of the pressure pump 311 is closed, so that the pressure pump 311 provides positive pressure to the rear cavity 112 through the second switch valve 313 and the second end of the three-way joint 314.

[0412] In an embodiment, as shown in FIG. 35, the cell counting assembly 10 of the embodiment further comprises a first driving member 190, a seat body 1000, a first shielding member 191 and / or a fourth shielding member 192, the liquid suction assembly 162 and the liquid discharge assembly 163 are arranged on the seat body 1000, the first driving member 190 is configured to drive the seat body 1000 to move in the vertical direction, so that the liquid suction assembly 162 and the liquid discharge assembly 163 move relative to the cartridge 20. The first shielding member 191 is arranged outside the main body 11 for electromagnetic shielding, the first shielding member 191 is provided with a through hole, and the pipeline connected between the main body 11 and the suction and discharge assembly 161 passes through the through hole of the first shielding member 191 for wiring, so as to ensure the electromagnetic shielding performance of the first shielding member 191. And / or, the fourth shielding member 192 is arranged outside the first driving member 190, and the fourth shielding member 192 is configured to shield the first driving member 190 from electromagnetic signals.

[0413] Specifically, the first driving member 190 can be, but is not limited to, a driving motor, a cylinder or other driving member capable of driving the seat body 1000 to move. The seat body 1000 is provided with the liquid suction assembly 162 and the liquid discharge assembly 163 on one side, the main body 11 can be arranged on the side of the cell counting assembly 10 away from the liquid suction assembly 162 and the liquid discharge assembly 163, and the main body 11 can be fixedly arranged at a certain position of the cell counting assembly 10, or the main body 11 can move with the seat body 1000, which is not limited here. The first driving member 190 is configured to drive the seat body 1000 to move in the vertical direction, for example, the first driving member 190 can drive the seat body 1000 to move up and down in the vertical direction, so that the liquid suction assembly 162 and the liquid discharge assembly 163 can be located at different heights.

[0414] In the embodiment, the main body 11 of the cell counting assembly 10 obtains the detection result by collecting the electric pulse signal between the first electrode 13 and the second electrode 14, and the electric pulse signal is usually weak and easy to be disturbed by electromagnetic signals and other factors, which can cause large errors in impedance counting. Therefore, the cell counting assembly 10 of the embodiment is arranged with the first shielding member 191 arranged outside the main body 11, and / or the fourth shielding member 192 arranged outside the first driving member 190, so as to reduce the interference of electromagnetic signals received by the main body 11, improve the accuracy of impedance counting, and improve the anti-interference performance of the POCT blood cell analyzer 1.

[0415] Optionally, please refer to FIG. 37, which is a structural schematic diagram of an eighth embodiment of the POCT blood cell analyzer provided in the present application. As shown in FIG. 37, the shell 5 can include a bottom plate and a side plate 51, the bottom plate is used as a bearing seat for the structures such as the transfer assembly, the cytometer assembly 10, the first driving member 190, etc., and the side plate 51 is arranged around the side of the bottom plate. In this embodiment, the first shielding member 191 forms a receiving space when shielding the main body 11, and the main body 11 is located in the receiving space of the first shielding member 191, so that the first shielding member 191 can be used to block the electromagnetic signals outside the receiving space. The side plate 51 is used as a component part of the first shielding member 191, for example, the first shielding member 191 can include a plurality of shielding surfaces, and the side plate 51 is used as one of the shielding surfaces of the first shielding member 191 to perform electromagnetic shielding around the main body 11.

[0416] The side plate 51 further includes an opening and closing door 52, which is used to shield or expose the receiving space formed by the first shielding member 191 in different states, so as to disassemble the main body 11 as a whole and / or the quick-release member 100. Specifically, the opening and closing door 52 can be rotationally connected with the side plate 51 through a rotating shaft, or the opening and closing door 52 is detachably connected with the side plate 51 through a fastener, a screw, a bolt or the like assembly, so that the user can shield or expose the receiving space formed by the first shielding member 191 by switching the state of the opening and closing door 52. When the user exposes the receiving space by rotating or disassembling the opening and closing door 52, the user can disassemble the main body 11 as a whole in the first shielding member 191 or disassemble the quick-release member 100 in the main body 11 through the exposed position of the opening and closing door 52, thereby improving the disassembly efficiency of the user, facilitating the user to disassemble and replace the micropore sheet 12, and further improving the user experience.

[0417] In an embodiment, the POCT blood cell analyzer 1 further includes a pipetting mechanism 4 arranged in the shell 5, and the pipetting mechanism 4 is used to mix the reagent and the sample in the first liquid pool of the reagent box 20, so that the first liquid pool is loaded with the detection sample.

[0418] Specifically, the reagent and / or the sample are stored in the reagent box 20. For example, the reagent box 20 can include a first liquid pool, a sample pool and a reagent pool, the sample pool is used to store the sample, the reagent pool is used to store the reagent, and the pipetting mechanism 4 can be used to perform pipetting operation between the first liquid pool, the sample pool and the reagent pool, so as to mix the reagent and the sample and make the first liquid pool store the detection sample; or the reagent box 20 can include a first liquid pool and a sample pool, and the POCT blood cell analyzer 1 further includes a reagent mechanism storing the reagent, and the pipetting mechanism 4 can be used to perform pipetting operation on the reagent of the reagent mechanism and the sample of the sample pool, so as to mix the reagent and the sample and make the first liquid pool store the detection sample.

[0419] In the embodiment of the present application, the POCT blood cell analyzer 1 mixes the reagent and the sample in the first liquid pool of the reagent box 20 through the pipetting mechanism 4, so that the first liquid pool is loaded with the detection sample, reduces the manual participation of the user, improves the automatic detection level of the POCT blood cell analyzer 1, and further improves the detection efficiency of the POCT blood cell analyzer 1.

[0420] Optionally, as shown in FIG. 33, the transfer mechanism 3 includes a moving guide rail 301, a tray 302, and a second driving member 303. The tray 302 is in sliding connection with the moving guide rail 301, and the second driving member 303 is connected with the tray 302. The second driving member 303 is used to drive the tray 302 to slide along the moving guide rail 301. The reagent box 20 includes a plurality of linearly arranged liquid pools. The tray 302 is used to carry the reagent box 20, and the second driving member 303 is used to drive the reagent box 20 to move along the extension direction of the moving guide rail 301. The pipetting mechanism 4 is used to perform pipetting operation on the plurality of liquid pools to mix the reagent and the sample and obtain the detection sample.

[0421] Specifically, the linear arrangement direction of the reagent box 20 and the moving direction of the tray 302 are parallel. The transfer mechanism 3 drives the tray 302 to move in the horizontal direction through the second driving member 303, so as to transfer the reagent box 20 to the designated pipetting position, detection position, etc. through the tray 302. The reagent box 20 includes a plurality of linearly arranged liquid pools. When the pipetting mechanism 4 performs pipetting operation on the plurality of liquid pools, the second driving member 303 is used to drive the tray 302 to move in the horizontal direction and make the plurality of liquid pools respectively located below the pipetting mechanism 4, so that the pipetting mechanism 4 can directly suck the liquid of the corresponding liquid pool or discharge the liquid to the corresponding liquid pool. Therefore, the pipetting operation of the POCT blood cell analyzer 1 in the embodiment is simple. When the motor drives the tray 302, it only needs to move in one direction, and the driving space is small, which is conducive to the miniaturization application of the POCT blood cell analyzer 1.

[0422] Optionally, as shown in FIG. 33, the transfer mechanism 3 further includes a second shielding member 304. The second shielding member 304 covers the second driving member 303, and the second shielding member 304 is used to shield the electromagnetic signals of the second driving member 303.

[0423] Specifically, the second shielding member 304 covers the second driving member 303, and the second shielding member 304 is used to shield the electromagnetic signals of the second driving member 303. Therefore, the electromagnetic signals generated by the second driving member 303 during the driving process are not easy to interfere with the components outside the second shielding member 304, further reducing the electromagnetic interference during the impedance counting, and improving the accuracy of the blood cell counting.

[0424] In an embodiment, as shown in FIG. 33, the pipetting mechanism 4 comprises a third driving member 41, an adapter head 42, and a third shielding member 43, the third driving member 41 is connected with the adapter head 42, the third driving member 41 is used to drive the adapter head 42 to move in the vertical direction, the adapter head 42 is used to plug the pipette head and perform pipetting operation through the pipette head, and the third shielding member 43 covers the third driving member 41, and the third shielding member 43 is used to shield the third driving member 41 from electromagnetic signals.

[0425] Specifically, the third driving member 41 of the pipetting mechanism 4 is used to drive the adapter head 42 to move downward in the vertical direction, so that the pipette head plugged by the adapter head 42 can be located below the liquid surface of the liquid pool of the reagent box 20, so that the pipette head can be used to suck the sample and / or reagent in the liquid pool. The third driving member 41 is used to drive the adapter head 42 to move upward in the vertical direction, and the pipette head can be located above the moving path of the reagent box 20, the second driving member 303 is used to drive the tray 302 to move in the horizontal direction so that the plurality of liquid pools are located below the pipette head respectively, the pipette head can discharge the sucked liquid to the corresponding liquid pool, so as to realize the mixing of the reagent and the sample and make the first liquid pool store the detection sample. The third shielding member 43 covers the third driving member 41, and the third shielding member 43 is used to shield the third driving member 41 from electromagnetic signals, so that the electromagnetic signals generated by the third driving member 41 during pipetting do not easily interfere with components other than the third shielding member 43, further reducing the electromagnetic interference during impedance counting, and improving the accuracy of blood cell counting.

[0426] Finally, it should be noted that: the above embodiments are only used to illustrate the technical solutions of the present application, and not to limit them; although the present application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that they can still modify the technical solutions recorded in the foregoing embodiments, or make equivalent replacement for part or all of the technical features; and these modifications or replacements do not make the essence of the corresponding technical solutions deviate from the scope of the technical solutions of the embodiments of the present application, and they should be covered in the scope of the claims and the description of the present application. Especially, as long as there is no structural conflict, each technical feature mentioned in each embodiment can be combined in any way. The present application is not limited to the specific embodiments disclosed in the text, but includes all technical solutions falling within the scope of the claims.

Claims

1. A POCT blood cell analyzer, characterized in that: The invention comprises a cell counting component that can move relative to the reagent box; the cell counting component comprises: The main body is provided with a front cavity and a rear cavity; a microporous sheet, used to separate the front cavity and the rear cavity, wherein the microporous sheet is provided with micropores, and the front cavity and the rear cavity are connected through the micropores; A first electrode is provided in the rear cavity and is used for electrically connecting to the detection sample in the rear cavity. The shortest distance between the portion of the first electrode provided in the rear cavity and the micropore is in the range of 2-20 mm.

2. A POCT blood cell analyzer, characterized in that: The invention comprises a cell counting component that can move relative to the reagent box; the cell counting component comprises: The main body is provided with a front cavity and a rear cavity; a microporous sheet, used to separate the front cavity and the rear cavity, wherein the microporous sheet is provided with micropores, and the front cavity and the rear cavity are connected through the micropores; a first electrode, disposed through a side wall of the rear cavity, with the axial direction of the first electrode intersecting the axial direction of the micropore, and the first electrode being used to electrically connect to the test sample in the rear cavity; Along the axial direction of the micropore, there is a first distance between the first electrode and the micropore, and the range of the first distance is 2-20 mm.

3. The POCT blood cell analyzer according to claim 2, characterized in that: Along the radial direction of the microhole, the exposed portion of the first electrode in the back cavity has a first length, and the first length ranges from 2 to 10 mm.

4. The POCT blood cell analyzer according to claim 3, characterized in that: The first length ranges from 7 to 9 mm.

5. The POCT blood cell analyzer according to claim 2, characterized in that: The axial direction of the first electrode and the axial direction of the micropore have a first crossing angle, and the first crossing angle ranges from 80° to 100°.

6. The POCT blood cell analyzer according to claim 5, characterized in that: The axial direction of the first electrode is perpendicular to the axial direction of the micropore.

7. The POCT blood cell analyzer according to claim 6, characterized in that: Along the radial direction of the micropore, there is a second distance between the free end of the first electrode and the center of the micropore, and the second distance ranges from 0 to 1 mm.

8. The POCT blood cell analyzer according to any one of claims 2 to 7, characterized in that: The cell counting assembly further includes a second electrode, which is used to electrically connect to the detection sample in the front chamber. Along the axial direction of the micropore, there is a third distance between the second electrode and the micropore sheet, and the third distance ranges from 1 to 3 mm.

9. The POCT blood cell analyzer according to claim 8, characterized in that: There is a partition between the front cavity and the rear cavity, and the partition is provided with a liquid inlet hole. The microporous sheet is arranged on the side of the partition facing the front cavity. Along the axial direction of the micropore, the projection of the micropore falls into the liquid inlet hole. The diameter range of the liquid inlet hole is 1-5mm.

10. The POCT blood cell analyzer according to claim 9, characterized in that: The cell counting assembly further includes a first sealing ring disposed between the partition and the microporous sheet. The outer diameter of the first sealing ring ranges from 4 to 7 mm, and the thickness of the first sealing ring along the axial direction of the micropore ranges from 1 to 2 mm.

11. The POCT blood cell analyzer according to claim 9, characterized in that: Along the axial direction of the liquid inlet hole, the height range of the liquid inlet hole is 2-5 mm.

12. The POCT blood cell analyzer according to claim 8, characterized in that: The second electrode is provided with a first through hole along the axial direction of the micropore, the first through hole including a first hole segment and a second hole segment, the first hole segment being arranged closer to the microporous sheet relative to the second hole segment; the inner diameter of the first hole segment is smaller than the inner diameter of the second hole segment, thereby forming an annular table at the connection between the second hole segment and the first hole segment; The cell counting assembly further comprises a pipette, one end of which is disposed in the second hole section and abuts against the annular table, and the pipette is used for drawing the test sample from the reagent box.

13. The POCT blood cell analyzer according to claim 12, characterized in that: The ratio of the inner diameter of the pipette to the inner diameter of the first hole section is between 0.9 and 1.

1.

14. The POCT blood cell analyzer according to claim 12, characterized in that: The cell counting assembly further includes a second sealing ring, which is clamped between the end surface of the pipette and the annular table and abuts against the side wall of the second hole segment.

15. The POCT blood cell analyzer according to claim 8, characterized in that: The cell counting assembly further includes a pipette, and the pipette is integrally formed with the second electrode.

16. A POCT blood cell analyzer, characterized in that: include: case; A loading seat, used for receiving the reagent kit; A cell counting component is disposed in the housing and is movable relative to the reagent box; The cell counting component includes: main body; A liquid absorbing member, the liquid absorbing member cooperates with the main body to form a liquid absorbing channel for conveying liquid; a microporous sheet is provided in the liquid absorbing channel; a liquid discharge member, the liquid discharge member cooperates with the main body to form a liquid discharge channel for discharging liquid from the main body; When the aspiration channel is clogged, the cell counting component is configured to impact the aspiration channel through the gas in the main body, or to absorb liquid through the discharge member and impact the aspiration channel through the liquid.

17. The POCT blood cell analyzer according to claim 16, characterized in that: After the gas impacts the aspiration channel, and when the aspiration channel is blocked, the cell counting component is configured to absorb liquid through the liquid discharge member and impact the aspiration channel with the liquid.

18. A POCT blood cell analyzer, characterized in that: include: case; A loading seat, for receiving a maintenance reagent kit, wherein the maintenance reagent kit includes a plurality of cleaning liquid pools, and the plurality of cleaning liquid pools are used to store cleaning liquids of different cleaning strengths; a cell counting assembly, disposed in the housing, and movable relative to the maintenance reagent kit; The cell counting component includes: main body; a liquid absorbing member, the liquid absorbing member cooperates with the main body to form a liquid absorbing channel for conveying liquid; a liquid discharge member, the liquid discharge member cooperates with the main body to form a liquid discharge channel for discharging liquid from the main body; In which, the cell counting component is provided with a maintenance mode. In the maintenance mode, the cell counting component is configured to absorb the cleaning fluid from different cleaning fluid pools through the liquid aspirating component according to the cleaning intensity from high to low, and discharge the cleaning fluid in the main body into the maintenance reagent kit through the liquid discharge component.

19. A POCT blood cell analyzer, characterized in that: include: case; A loading seat, used for receiving the reagent kit; A cell counting component is disposed in the housing; the cell counting component is movable relative to the reagent box; The cell counting component includes: The main body is provided with a front cavity and a rear cavity in communication; a microporous sheet, used to separate the front cavity and the rear cavity, wherein the microporous sheet is provided with micropores, and the front cavity and the rear cavity are connected through the micropores; a first electrode, disposed in the rear cavity, and configured to be electrically connected to a test sample in the rear cavity; a second electrode disposed in the front cavity, the second electrode being used to electrically connect to the test sample in the front cavity; A quick-release piece is detachably connected to the main body, and the quick-release piece is configured to cooperate with the main body to confine the microporous sheet and / or the second electrode in the front cavity.

20. A POCT blood cell analyzer, characterized in that: include: case; a transfer mechanism disposed in the housing, the transfer mechanism being used to receive and transfer a reagent kit, the reagent kit being used to store samples and / or reagents; a first driving member; A cell counting assembly is disposed in the housing, and the cell counting assembly includes: A main body, fixedly installed in the shell; A suction and discharge assembly connected to the main body via a pipeline; The first driving member is used to drive the aspiration and discharge assembly to move relative to the reagent box to complete aspiration and / or discharge operations.

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