Blood cell analyzer and bubble discharge method

Abstract

The application discloses a blood cell analyzer and a bubble discharging method. The blood cell analyzer comprises a flow chamber, a pressure source, a first control valve, a second control valve and a third control valve, the flow chamber comprises a liquid containing cavity and a first liquid inlet, a second liquid inlet and a liquid outlet communicated with the liquid containing cavity, the first control valve is connected with the first liquid inlet through a pipeline, the second control valve is connected with the liquid outlet through a pipeline, the third control valve is connected with the second liquid inlet through a pipeline, and the pressure source is connected with at least one of the first liquid inlet and the second liquid inlet through a pipeline; when the first liquid exists in the liquid containing cavity, the pressure source cooperates with the first control valve, the second control valve and the third control valve to provide positive pressure and negative pressure to the liquid containing cavity, so that the liquid is filled in the liquid containing cavity to obtain the second liquid, wherein the bubbles in the second liquid are less than the bubbles in the first liquid. Therefore, the bubbles in the liquid in the flow chamber can be discharged through a simple structure.

Description

Technical Field

[0001] This application relates to the field of medical testing and analysis technology, and in particular to a blood cell analyzer and a method for removing air bubbles. Background Technology

[0002] A hematology analyzer, a commonly used instrument in medical testing, is a type of sample analyzer that detects the number and proportion of blood cells (red blood cells, white blood cells, and platelets) in the blood. Through blood analysis, hematology analyzers can determine the type of microbial infection in the tested sample, diagnose and treat anemia, and diagnose hematological diseases. With technological advancements and scientific development, the functions of hematology analyzers have been continuously expanded, their performance improved, and their level of automation increased, leading to their widespread clinical application.

[0003] A blood cell analyzer may include devices such as a flow chamber assembly. A blood cell analyzer can be a device that classifies and counts particles based on flow cytometry detection technology. The basic measurement principle is that after the processed sample particles (such as blood cells) are wrapped in sheath fluid, they are pushed through the flow chamber one by one under pressure, thereby detecting the sample particles.

[0004] To improve the accuracy of sample testing, the flow chamber needs to be kept as free of air bubbles as possible. However, in existing flow chamber structures used in hematology analyzers, a significant number of air bubbles still adhere to the inner wall of the flow chamber or block the flow channels. The presence of numerous air bubbles in the flow chamber can cause them to be identified as sample particles during testing, affecting the test results; furthermore, a large number of air bubbles can disrupt the pressure balance of the flow channels, preventing the formation of sample flow, and other issues. Summary of the Invention

[0005] The main objective of this application is to provide a blood cell analyzer and a bubble removal method, which aims to solve the aforementioned technical problems existing in the prior art.

[0006] To address the aforementioned problems, this application provides a blood cell analyzer, comprising: a flow chamber, a pressure source, a first control valve, a second control valve, and a third control valve. The flow chamber includes a liquid-containing cavity and a first inlet, a second inlet, and an outlet communicating with the liquid-containing cavity. The first control valve is connected to the first inlet via a pipeline, the second control valve is connected to the outlet via a pipeline, and the third control valve is connected to the second inlet via a pipeline. The pressure source is connected to at least one of the first inlet and the second inlet via a pipeline. When a first liquid is present in the liquid-containing cavity, the pressure source, in conjunction with the first control valve, the second control valve, and the third control valve, provides positive and negative pressure to the liquid-containing cavity to fill it with liquid, resulting in a second liquid, wherein the second liquid contains fewer air bubbles than the first liquid.

[0007] In some embodiments, the pressure source is connected to at least the second inlet via a pipeline, and the liquid-containing cavity, the pipeline connecting the flow chamber and the first control valve, the pipeline connecting the flow chamber and the second control valve, and the pipeline connecting the pressure source and the second inlet are all filled with the first liquid. When the first and second control valves are in a closed state and the third control valve is in a closed state, the pressure source provides negative pressure to the liquid-containing cavity to cause at least some of the bubbles in the liquid-containing cavity to enlarge. When the first and second control valves are in a closed state and the third control valve is in a closed state, the pressure source provides positive pressure to the liquid-containing cavity and injects liquid into the liquid-containing cavity at least through the second inlet to cause at least some of the enlarged bubbles to break and be discharged from the liquid-containing cavity, thereby filling the liquid-containing cavity with the second liquid.

[0008] In some embodiments, the blood cell analyzer further includes: a controller, the controller being configured to: control the repeated execution of the following steps according to a preset number of times: when the first control valve and the second control valve are set to a closed state and the third control valve is set to a conducting state, the pressure source provides negative pressure to the liquid-containing cavity to cause at least some of the bubbles in the liquid-containing cavity to enlarge; when the first control valve and the second control valve are set to a conducting state and the third control valve is set to a closed state, the pressure source provides positive pressure to the liquid-containing cavity and injects liquid into the liquid-containing cavity at least through the second liquid inlet to cause at least some of the enlarged bubbles to break and be discharged from the liquid-containing cavity.

[0009] In some embodiments, the pressure source is connected to the first inlet and the second inlet via a pipeline. When the liquid in the liquid-containing cavity contains the first liquid, with the third control valve and the first control valve in a conducting state and the second control valve in a closed state, the pressure source provides negative pressure to the liquid-containing cavity, so that the liquid in the liquid-containing cavity flows out of the liquid-containing cavity from the first inlet at a first flow rate less than a preset flow rate threshold. With the first control valve and the second control valve in a conducting state and the third control valve in a closed state, the pressure source provides positive pressure to the liquid-containing cavity, so that the liquid flows into the liquid-containing cavity from the first inlet at a second flow rate less than the preset flow rate threshold, thereby filling the liquid-containing cavity with liquid.

[0010] In some embodiments, the blood cell analyzer further includes a sample needle, a flow restrictor, a first conduit, and a reaction chamber connected to atmospheric pressure. The sample needle is located within the liquid-containing cavity and connected to the second inlet. The reaction chamber is connected between the pressure source and the flow chamber. The pressure source is at least connected to the first inlet, and the pressure source and the first inlet are connected via the flow restrictor and the first conduit. When the third control valve and the flow restrictor are in a conducting state, and the second control valve and the first conduit are in a closed state, the pressure source provides negative pressure to the liquid-containing cavity through the flow restrictor, so that the liquid in the liquid-containing cavity flows out of the liquid-containing cavity from the first inlet through the flow restrictor at a first flow rate less than a preset flow rate threshold.

[0011] In some embodiments, the hematology analyzer further includes a sample needle located within the liquid-containing chamber and connected to the second inlet. The sample needle extends along the flow direction of the liquid within the liquid-containing chamber. The flow chamber further includes a rectifier disposed within the liquid-containing chamber. The rectifier divides the area within the liquid-containing chamber, excluding the sample needle, into a first chamber and a second chamber along the flow direction of the liquid. The first inlet communicates with the first chamber, and the rectifier has a rectifier orifice communicating with the first chamber and the second chamber. When the third control valve and the flow-limiting tube are in a conducting state, and the second control valve and the first pipeline are in a closed state, the pressure source passes through the flow-limiting tube. A negative pressure is provided to the liquid-containing cavity so that the first liquid in the first cavity, the second cavity, and the rectifier orifice flows out of the liquid-containing cavity from the first inlet through the flow-limiting tube at a first flow rate less than a preset flow rate threshold, thereby at least expelling air bubbles from the first cavity and the rectifier orifice; when the pressure source flows the liquid into the liquid-containing cavity from the first inlet at the second flow rate, if liquid is detected entering the second cavity through the rectifier orifice, the second control valve is set to the open state, and the pressure source flows the liquid into the first cavity from the first inlet at a fourth flow rate, so that the liquid fills the first cavity and the second cavity; wherein, the fourth flow rate is greater than the second flow rate.

[0012] In some embodiments, the hematology analyzer further includes a sample needle located within the fluid-containing cavity and connected to the second inlet. The sample needle extends along the flow direction of the liquid within the fluid-containing cavity. The fluid-containing cavity includes a sheath fluid chamber surrounding the sample needle. When the sheath fluid chamber is filled with liquid, a pressure source provides positive pressure to the fluid-containing cavity to force liquid into the fluid-containing cavity from the first inlet at a third flow rate, wherein the third flow rate is greater than the second flow rate, and / or, the third flow rate is greater than the fourth flow rate. While the liquid is at the third flow rate, the pressure source injects liquid into the sample needle to fill the sample needle with liquid.

[0013] In some embodiments, the hematology analyzer further includes a flow-limiting tube and a first conduit, with the pressure source and the first inlet connected via the flow-limiting tube and the first conduit; when the sheath fluid chamber is filled with liquid, the second control valve, the flow-limiting tube, and the first conduit are all configured to be open, and the pressure source provides positive pressure to the fluid-containing chamber through the flow-limiting tube, the first conduit, and the second control valve to allow liquid to flow into the fluid-containing chamber from the first inlet at the third flow rate; and while the liquid is at the third flow rate, the third control valve is configured to be open, and the pressure source injects liquid into the sample needle to fill the sample needle with liquid.

[0014] In some embodiments, the pressure source includes a first metering pump connected to a second inlet via a conduit, the first metering pump being used to provide positive and negative pressure to the liquid-containing cavity; and / or the pressure source includes a syringe connected to the second inlet via a conduit, the syringe being used to provide positive and negative pressure to the liquid-containing cavity; and / or, the pressure source includes a first storage tank, a second storage tank, a second metering pump, and a positive pressure source, the second metering pump being connected to the second storage tank and the first storage tank via a conduit, the positive pressure source being connected to the second storage tank via a conduit; the second metering pump is used to provide positive pressure to allow liquid in the second metering pump to flow into the first storage tank, and the second metering pump is used to provide negative pressure to draw liquid from the second storage tank to establish a negative pressure in the second storage tank, the positive pressure source is used to provide positive pressure to the second storage tank to establish a positive pressure in the second storage tank, the second storage tank being used to provide both positive and negative pressure to the liquid-containing cavity.

[0015] To address the aforementioned issues, this application provides a bubble removal method for use in the aforementioned blood cell analyzer. The bubble removal method includes: when a first liquid is present in the liquid-containing chamber, a pressure source, in conjunction with the first control valve, the second control valve, and the third control valve, provides positive and negative pressure to the liquid-containing chamber to fill it with liquid, thereby obtaining a second liquid, wherein the number of bubbles in the second liquid is less than the number of bubbles in the first liquid.

[0016] Compared with the prior art, the blood cell analyzer of this application includes: a flow chamber, a pressure source, a first control valve, a second control valve, and a third control valve. The flow chamber includes a liquid-containing cavity and a first inlet, a second inlet, and an outlet communicating with the liquid-containing cavity. The first control valve is connected to the first inlet via a pipeline, the second control valve is connected to the outlet via a pipeline, and the third control valve is connected to the second inlet via a pipeline. The pressure source is connected to at least one of the first inlet and the second inlet via a pipeline. When a first liquid is present in the liquid-containing cavity, the pressure source, in conjunction with the first, second, and third control valves, provides positive and negative pressure to the liquid-containing cavity to fill it with liquid, thereby obtaining a second liquid. The second liquid contains fewer air bubbles than the first liquid. Through the above implementation method, the pressure source, together with the first control valve, the second control valve and the third control valve, provides positive pressure and negative pressure to the liquid-containing chamber, which can form a second liquid with fewer bubbles than the first liquid. Thus, the bubbles in the liquid in the flow chamber can be discharged through a simple structure, reducing the accumulation of bubbles inside the flow chamber and enhancing the accuracy and reliability of the blood cell analyzer. Attached Figure Description

[0017] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0018] Figure 1 This is a schematic diagram of the structure of the first embodiment of the blood cell analyzer provided in this application;

[0019] Figure 2 This is a schematic diagram of the structure of the second embodiment of the blood cell analyzer provided in this application;

[0020] Figure 3 This is a schematic diagram of the third embodiment of the blood cell analyzer provided in this application;

[0021] Figure 4 This is a schematic diagram of an embodiment of the flow chamber provided in this application.

[0022] Reference numerals: Hematology analyzer 10; Flow chamber 100; First inlet 110; Outlet 120; Second inlet 130; Liquid-containing chamber 140; First chamber 141; Second chamber 142; Rectifying component 150; Rectifying orifice 151; Sheath fluid chamber 160; First control valve 210; Second control valve 220; Third control valve 230; Sample needle 300; Pressure source 400; First metering pump 410; Syringe 420; First reservoir 430; Second reservoir 440; Second metering pump 450; Controller 500; First pipeline 610; Flow limiting tube 620; Reaction cell 630; Flow direction X. Detailed Implementation

[0023] The embodiments of the technical solution of this application will now be described in detail with reference to the accompanying drawings. These embodiments are only used to more clearly illustrate the technical solution of this application and are therefore merely examples, and should not be used to limit the scope of protection of this application.

[0024] 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 this application pertains; the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the application; the terms “comprising” and “having”, and any variations thereof, in the specification, claims, and foregoing description of the drawings are intended to cover non-exclusive inclusion.

[0025] In the description of the embodiments of this application, technical terms such as "first" and "second" are used only to distinguish different objects and should not be construed as indicating or implying relative importance or implicitly specifying the number, specific order, or primary and secondary relationship of the indicated technical features. In the description of the embodiments of this application, "multiple" means two or more, unless otherwise explicitly defined.

[0026] In this document, the term "embodiment" means that a particular feature, structure, or characteristic described in connection with an embodiment may be included in at least one embodiment of this application. The appearance of this phrase in various places throughout the specification does not necessarily refer to the same embodiment, nor is it a separate or alternative embodiment mutually exclusive with other embodiments. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described herein can be combined with other embodiments.

[0027] In the description of the embodiments in this application, the term "and / or" is merely a description of the relationship between related objects, indicating that three relationships can exist. For example, A and / or B can represent: A existing alone, A and B existing simultaneously, or B existing alone. Additionally, the character " / " in this document generally indicates that the preceding and following related objects have an "or" relationship.

[0028] In the description of the embodiments of this application, the term "multiple" refers to two or more (including two), similarly, "multiple sets" refers to two or more (including two sets), and "multiple pieces" refers to two or more (including two pieces).

[0029] In the description of the embodiments of this application, the technical terms "center," "longitudinal," "lateral," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counterclockwise," "axial," "radial," and "circumferential" indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing the embodiments of this application and simplifying the description, and are not intended to indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the embodiments of this application.

[0030] In the description of the embodiments of this application, unless otherwise expressly specified and limited, technical terms such as "installation," "connection," "joining," and "fixing" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. For those skilled in the art, the specific meaning of the above terms in the embodiments of this application can be understood according to the specific circumstances.

[0031] This application provides a blood cell analyzer.

[0032] The hematology analyzer includes a sampling module, a sample preparation module, and a flow chamber assembly. The sampling module acquires the sample, while the sample preparation module receives the sample and mixes it with reagents to obtain the test sample. The sample preparation module may further include a transport module, a reagent dispensing module, a reagent module, and a reaction module. The flow chamber assembly includes a flow chamber and optical detection equipment. In use, the raw sample is transferred to the sampling module via the transport module, where it is quantitatively sampled and then transferred to the reaction module to await reaction. The reagent module contains and prepares the reagents needed for sample testing, and the transport module and reagent dispensing module quantitatively add the reagents currently needed to the sample to the reaction module.

[0033] The added reagents and the original sample are mixed in the reaction module to form the test sample. The test sample enters the flow chamber assembly, and as the sample particles of the test sample pass through the detection channel of the flow chamber assembly, the optical detection device detects the test sample and converts photoelectric data to obtain detection data.

[0034] However, the flow chamber is a key component in a hematology analyzer, primarily used to form a stable sample flow for detection. During use, the flow chamber should be kept as free of air bubbles as possible, as accumulated bubbles can cause the following problems: (1) Insufficient sample flow stability: the presence of bubbles affects the pressure balance of the flow channel, causing sample flow jitter, or even preventing the formation of a sample flow, thus impacting instrument performance. (2) Bubbles themselves are identified as particles, leading to inaccurate detection results. (3) Bubble signals overwhelm cell signals, resulting in lower detection results. To improve the accuracy of sample detection, the flow chamber should be kept as free of air bubbles as possible. Common methods for removing air bubbles involve increasing the flow rate to flush them away.

[0035] However, the flow channel in the top detection area of ​​the flow chamber is narrow, while the bottom steady flow area is large. Due to the limitation of the flow channel in the detection area, it is difficult to increase the flow rate of the liquid through the flow chamber. In addition, the flow in the steady flow area inside the flow chamber is usually relatively stable with a low flow velocity. The effect of increasing the flow rate to remove bubbles is not obvious. As a result, small bubbles are easy to adhere to the inner wall of the flow chamber, and large bubbles are easy to be blocked in a certain flow channel and cannot be removed.

[0036] Based on the above-mentioned technical problems, this application provides a blood cell analyzer, see [link to relevant documentation]. Figure 1 , Figure 1 This is a schematic diagram of the structure of the first embodiment of the blood cell analyzer provided in this application.

[0037] The hematology analyzer 10 includes a flow chamber 100. The flow chamber 100 includes a liquid-containing cavity 140 and a first inlet 110, a second inlet 130, and an outlet 120 connected to the liquid-containing cavity 140. The first inlet 110 can be a sheath fluid inlet, used to connect to a sheath fluid pool via a pipeline. The sheath fluid can enter the liquid-containing cavity 140 from the first inlet 110 to form a sheath flow within the liquid-containing cavity 140. The sample to be tested can enter the liquid-containing cavity 140 from the second inlet 130. After the sample particles (e.g., blood cells) of the sample entering the liquid-containing cavity 140 are encapsulated by the sheath fluid, they are pushed one by one through the detection channel of the flow chamber 100 under pressure, thereby enabling the detection of sample particles.

[0038] The blood cell analyzer 10 includes a pressure source 400, a first control valve 210, a second control valve 220, and a third control valve 230. The first control valve 210 is connected to a first liquid inlet 110 via a pipeline, the second control valve 220 is connected to a liquid outlet 120 via a pipeline, and the third control valve 230 is connected to a second liquid inlet 130 via a pipeline. The pressure source 400 is connected to at least one of the first liquid inlet 110 and the second liquid inlet 130 via a pipeline. When there is a first liquid in the liquid-containing chamber 140, the pressure source 400, in conjunction with the first control valve 210, the second control valve 220, and the third control valve 230, provides positive and negative pressure to the liquid-containing chamber 140 to fill the liquid-containing chamber 140 with liquid, thereby obtaining a second liquid, wherein the number of air bubbles in the second liquid is less than the number of air bubbles in the first liquid.

[0039] The first control valve 210, the second control valve 220, and the third control valve 230 are all controllable valves, capable of switching between on and off states by receiving control signals. The pressure source 400 can provide positive and negative pressure. In some embodiments, the first control valve 210, the second control valve 220, and the third control valve 230 can be controlled to open or close, and then the pressure source 400 can supply positive and negative pressure to the liquid chamber 140, thereby forming a second liquid with fewer bubbles than the first liquid.

[0040] The first liquid in the liquid-containing cavity 140 can be considered as liquid that has not undergone bubble removal treatment. For example, when the liquid-containing cavity 140 is empty, liquid enters the liquid-containing cavity 140 through the first inlet 110, thereby forming the first liquid in the liquid-containing cavity 140. The second liquid can be considered as liquid that has undergone bubble removal treatment; therefore, the number of bubbles remaining in the second liquid should be less than the number of bubbles remaining in the first liquid. It should be noted that "the number of bubbles in the second liquid is less than the number of bubbles in the first liquid" can be understood as: comparing the two liquids in the same volume, such as comparing the first and second liquids when both liquids fill the liquid-containing cavity 140, the second liquid has fewer bubbles than the first liquid. Alternatively, "the number of bubbles in the second liquid is less than the number of bubbles in the first liquid" can also be understood as: the ratio of the number of bubbles per unit volume, the second liquid has fewer bubbles than the first liquid. Or, "the number of bubbles in the second liquid is less than the number of bubbles in the first liquid" can also be understood as: in the same volume of the first and second liquids, the total volume and / or number of bubbles in the second liquid is less than the total volume and / or number of bubbles in the first liquid.

[0041] Through the above implementation method, the pressure source 400, together with the first control valve 210, the second control valve 220 and the third control valve 230, provides positive and negative pressure to the liquid-containing chamber 140, which can form a second liquid with fewer bubbles than the first liquid. Thus, the bubbles in the liquid in the flow chamber 100 can be discharged through a simple structure, reducing the accumulation of bubbles inside the flow chamber 100 and enhancing the accuracy and reliability of the blood cell analyzer 10.

[0042] See Figure 2 , Figure 2 This is a schematic diagram of the second embodiment of the blood cell analyzer 10 provided in this application.

[0043] The pressure source 400 is connected to at least the second liquid inlet 130 through a pipeline. The liquid-containing cavity 140, the pipeline connecting the flow chamber 100 and the first control valve 210, the pipeline connecting the flow chamber 100 and the second control valve 220, and the pipeline connecting the pressure source 400 and the second liquid inlet 130 are all filled with the first liquid.

[0044] With the first control valve 210 and the second control valve 220 set to the off state and the third control valve 230 set to the on state, the pressure source 400 provides negative pressure to the liquid-containing chamber 140, causing at least some of the bubbles in the liquid-containing chamber 140 to enlarge. Since the liquid-containing chamber 140, the pipeline connecting the flow chamber 100 and the first control valve 210, the pipeline connecting the flow chamber 100 and the second control valve 220, and the pipeline connecting the pressure source 400 and the second inlet 130 are all filled with the first liquid, when the first control valve 210 and the second control valve 220 are set to the off state and the third control valve 230 is set to the on state, making the flow chamber 100 completely sealed, when the pressure source 400 provides negative pressure to the liquid-containing chamber 140 through the second inlet 130, the liquid in the liquid-containing chamber 140 will not move significantly. In one embodiment, with the first control valve 210 and the second control valve 220 in a closed state and the third control valve 230 in a forward state, negative pressure can be provided by a pressure source 400 connected to the third control valve 230. In another embodiment, the pressure source includes a syringe connected to the second inlet 130, and a reaction tank is also connected to the connecting pipe between the syringe and the second inlet 130. With the first control valve 210 and the second control valve 220 in a closed state and the third control valve 230 in a forward state, negative pressure can be provided by the syringe. In other embodiments, the pressure source includes a pressure source (such as a metering pump) connected to the third control valve 230 and a syringe connected to the second inlet 130. A reaction tank is also connected to the connecting pipe between the syringe and the second inlet 130. With the first control valve 210 and the second control valve 220 in a closed state and the third control valve 230 in a forward state, negative pressure can be provided by the pressure source connected to the third control valve 230 and the syringe together.

[0045] In some specific scenarios, when air bubbles are present inside the liquid-containing cavity 140, small bubbles may adhere to the wall surface of the cavity 140. Due to the buoyancy, fluid drag, and shear force acting on the bubbles, it is difficult to break this equilibrium and dislodge or break the bubbles. Large bubbles, however, may block narrow flow channels, making it difficult to remove them even with flushing. In this embodiment, when the liquid-containing cavity 140 is in a closed state, a negative pressure is provided to it. This negative pressure is transmitted through the fluid to the surface of the bubbles inside the flow chamber 100, causing the bubbles to expand and even break. For small bubbles, as the external pressure decreases, the bubble diameter increases. The buoyancy, fluid drag, and fluid shear force acting on them increase with the increase in bubble diameter, making it easier for the bubbles to detach from the wall. Due to the increased bubble diameter, external forces make it easier for the bubbles to deform or even break, transforming large bubbles into smaller ones that can more easily pass through narrow channels.

[0046] After the pressure source 400 provides negative pressure to the liquid-containing cavity 140, the first control valve 210 and the second control valve 220 can be set to the open state, and the third control valve 230 can be set to the closed state. The pressure source 400 then provides positive pressure to the liquid-containing cavity 140 and injects liquid into the cavity at least through the second inlet 130. This causes at least some of the enlarged bubbles to break and exit the liquid-containing cavity 140, thereby filling the cavity 140 with the second liquid. Due to the rapid pressure change inside the liquid-containing cavity 140, the enlarged bubbles break, and the positive pressure provided by the pressure source 400 allows the broken bubbles to exit from the outlet 120, thus filling the cavity 140 with the second liquid and reducing the accumulation of bubbles inside the cavity. In this embodiment, the first liquid discharged from the liquid discharge chamber 140 can be discharged into a solution pool. After the first liquid is left to stand in the solution pool for a period of time, bubbles in the first liquid will rise to the surface of the liquid, or the bubbles will separate from the first liquid. Alternatively, the first liquid discharged from the liquid discharge chamber 140 can be discharged into the solution pool first, and then the first liquid in the solution pool can be discharged into a waste liquid pool to replace the liquid in the solution pool. Or, the first liquid discharged from the liquid discharge chamber 140 can be directly discharged into the waste liquid pool. In one embodiment, the pressure source 400 includes a positive pressure source connected to the second liquid inlet 130, which can provide positive pressure to the liquid discharge chamber 140. In another embodiment, the pressure source 400 includes a positive pressure source connected to the second liquid inlet 130. The positive pressure source and the second liquid inlet 130 are connected by a flow restrictor A and a pipe B in parallel. The liquid flow rate in the flow restrictor A is slower than the liquid flow rate in the pipe B. Preferably, positive pressure can be provided to the liquid discharge chamber 140 through the positive pressure source and the pipe B. By using a larger positive pressure, that is, a positive pressure with a greater pressure difference compared to the previous negative pressure, the negative pressure can be effectively enhanced to quickly switch to positive pressure. The pressure inside the flow chamber changes drastically, from negative pressure to a larger positive pressure (relative to turning on the positive pressure source and flow restrictor A), causing the bubbles in the flow chamber to break up and carry away the bubbles in the flow chamber.

[0047] Furthermore, the blood cell analyzer 10 also includes a controller 500, which is used to control the repeated execution of the following steps according to a preset number of times: When the first control valve 210 and the second control valve 220 are in the off state and the third control valve 230 is in the on state, the pressure source 400 provides negative pressure to the liquid chamber 140 to cause at least some of the bubbles in the liquid chamber 140 to enlarge; when the first control valve 210 and the second control valve 220 are in the on state and the third control valve 230 is in the off state, the pressure source 400 provides positive pressure to the liquid chamber 140 and injects liquid into the liquid chamber 140 at least through the second inlet 130 to cause at least some of the enlarged bubbles to break and be discharged from the liquid chamber 140. The controller 500 can be the overall control system of the blood cell analyzer 10, and the preset number of executions can be two, three, four, or other numbers. To obtain a second liquid with the lowest possible gas content, this can be achieved by repeatedly executing alternating positive and negative pressure.

[0048] See Figure 3 , Figure 3 This is a schematic diagram of the third embodiment of the blood cell analyzer 10 provided in this application.

[0049] The pressure source 400 is connected to the first liquid inlet 110 and the second liquid inlet 130 through a pipeline.

[0050] When the liquid chamber 140 contains a first liquid, with the third control valve 230 and the first control valve 210 in the open state and the second control valve 220 in the closed state, the pressure source 400 provides negative pressure to the liquid chamber 140, so that the liquid in the liquid chamber 140 flows out of the liquid chamber 140 from the first inlet 110 at a first flow rate less than a preset flow rate threshold. When the liquid chamber 140 contains a first liquid, since the gas content of the first liquid does not meet the requirements, it is necessary to remove air bubbles from the liquid in the liquid chamber 140. In this embodiment, this is achieved by first emptying the first liquid in the liquid chamber 140 and then filling it with a second liquid. Specifically, a predetermined negative pressure is provided to the liquid cavity 140 by the pressure source 400 so that the first liquid flows out of the liquid cavity 140 at a lower flow rate, thereby achieving the effect of evacuating the liquid cavity 140. Since the first liquid flows out of the liquid cavity 140 at a lower flow rate, the problem of air bubbles remaining inside the liquid cavity 140 can also be reduced.

[0051] With the first control valve 210 and the second control valve 220 in the open state and the third control valve 230 in the closed state, the pressure source 400 provides positive pressure to the liquid-containing chamber 140, so that liquid flows from the first inlet 110 into the liquid-containing chamber 140 at a second flow rate less than a preset flow rate threshold, thereby filling the liquid-containing chamber 140 with liquid. After the liquid-containing chamber 140 is evacuated, it needs to be refilled with liquid. However, under normal use or during sheath fluid filling (flow chamber 100 from empty to full), air bubbles may enter the flow chamber 100 from the sheath fluid inlet and get stuck in dead zones or other locations in the liquid-containing chamber 140. Excessive accumulation of air bubbles may affect the width and stability of the sample flow, ultimately leading to abnormal results. In this embodiment, a predetermined positive pressure is provided to the liquid-containing cavity 140 by the pressure source 400, so that the liquid flows out of the liquid-containing cavity 140 at a lower flow rate, which can alleviate the problem of air bubbles being generated in the liquid-containing cavity 140 during the filling of the sheath fluid. As a result, the liquid-containing cavity 140 is filled with a second liquid with a lower air bubble content than the first liquid.

[0052] Further, see Figure 3 and Figure 4 , Figure 4 This is a schematic diagram of an embodiment of the flow chamber 100 provided in this application.

[0053] The hematology analyzer 10 also includes a sample needle 300, a flow restrictor 620, a first conduit 610, and a reaction chamber 630 connected to atmospheric pressure. The sample needle 300 is located within the liquid-containing chamber 140 and connected to the second inlet 130. The reaction chamber 630 is connected between the pressure source 400 and the flow chamber 100. The pressure source 400 is at least connected to the first inlet 110, and the pressure source 400 and the first inlet 110 are connected via the flow restrictor 620 and the first conduit 610. The first conduit 610 and the flow restrictor 620 can be connected to the first inlet 110 in parallel, and both the branch containing the first conduit 610 and the branch containing the flow restrictor 620 can be connected to control valves. By opening or closing the control valves, the pressure source 400 can be connected to the first inlet 110 through the first conduit 610 and / or the flow restrictor 620. The reaction chamber 630 is used to react the original sample with reagents to obtain the sample to be tested. The reaction chamber 630 is connected to atmospheric pressure and is also connected between the pressure source 400 and the flow chamber 100, so that the liquid-containing chamber 140 can be connected to atmospheric pressure through the reaction chamber 630. The sample to be tested can enter the sample needle 300 through the second inlet 130, so that the sample to be tested can be delivered to the predetermined position through the sample needle 300.

[0054] With the third control valve 230 and the flow-limiting pipe 620 in the open state, and the second control valve 220 and the first pipeline 610 in the closed state, the pressure source 400 provides negative pressure to the liquid-containing cavity 140 through the flow-limiting pipe 620, so that the liquid in the liquid-containing cavity 140 flows out of the liquid-containing cavity 140 from the first inlet 110 through the flow-limiting pipe 620 at a flow rate less than a preset flow rate threshold. The reaction tank 630 can be connected to the second inlet 130 through the third control valve 230. When there is a first liquid in the liquid-containing cavity 140, since the gas content of the first liquid does not meet the requirements, it is necessary to remove air bubbles from the liquid in the liquid-containing cavity 140. In this embodiment, by opening the third control valve 230, the flow chamber 100 is connected to atmospheric pressure, which facilitates the application of negative pressure to the liquid-containing cavity 140 to extract the first liquid in the liquid-containing cavity 140. Simultaneously, to control the flow rate of the first liquid, the flow-limiting tube 620 is connected, allowing the pressure source 400 to communicate with the liquid-containing chamber 140 via the flow-limiting tube 620. This facilitates the flow of liquid from the first inlet 110 through the flow-limiting tube 620 at a flow rate less than a preset flow rate threshold, thereby reducing the problem of air bubbles remaining inside the liquid-containing chamber 140. Furthermore, because the internal channel of the sample needle is a long and narrow channel, the sample needle acts as a flow-limiting device for the liquid flowing through it. Through the coordinated design of the liquid circuit and control valve, as well as the structural design of the internal channel of the sample needle, negative pressure can slowly evacuate the liquid in the flow chamber, allowing air bubbles in dead zones and other locations within the flow chamber to be discharged along with the liquid.

[0055] Furthermore, the sample needle 300 extends along the flow direction X of the liquid in the liquid-containing cavity 140. The flow chamber 100 also includes a rectifier 150 disposed within the liquid-containing cavity 140. The rectifier 150 divides the area within the liquid-containing cavity 140, excluding the sample needle 300, into a first cavity 141 and a second cavity 142 along the liquid flow direction X. The first inlet 110 connects to the first cavity 141, and the rectifier 150 is provided with rectifier holes 151 connecting the first cavity 141 and the second cavity 142. The number of rectifier holes 151 can be set according to actual conditions, such as 2-8. For example, the number of rectifier holes 151 can include 4, 5, 6, or other numbers. The length of the rectifier holes 151 can be set according to actual conditions. By limiting the length and number of rectifier holes 151, the liquid can enter the second cavity 142 through the rectifier holes 151 while reducing the possible adhesion area of ​​air bubbles. The sample needle 300 can be partially inserted into the rectifying component 150, such that one end of the sample needle 300 is connected to the second liquid inlet 130, and the other end extends into a predetermined position in the liquid-containing cavity 140. In one embodiment, when the third control valve and the flow-limiting tube are in a conducting state, and the second control valve and the first pipeline are in a closed state, the pressure source provides negative pressure to the liquid-containing cavity through the flow-limiting tube, so that the first liquid in the first cavity, the second cavity, and the rectifying orifice flows out of the liquid-containing cavity from the first liquid inlet through the flow-limiting tube at a first flow rate less than a preset flow rate threshold, thereby at least expelling air bubbles in the first cavity and the rectifying orifice; wherein, the rectifying orifice 151 is provided with The rectifying orifice 151 is a strip-shaped channel, with its axial direction parallel to the length of the sample needle 300, meaning the axial direction of the rectifying orifice 151 is parallel to the extension direction of the sample needle 300. The diameter of the cross-section of the rectifying orifice 151 is smaller than the distance between the first and second points on the reference cross-section. The reference cross-section is a plane parallel to the cross-section of the rectifying orifice 151. The first point is a point on the outer wall of the reference cross-section where the rectifying component 150 contacts the flow chamber 100, and the second point is a point on the inner wall of the reference cross-section where the rectifying component 150 contacts the sample needle 300. The rectifying orifice 151 is a narrow and elongated flow channel, which also allows turbulent liquid flow to gradually become orderly as it enters the second cavity 142.To control the flow rate of the first liquid, the flow-limiting pipe 620 is connected, allowing the pressure source 400 to communicate with the liquid-containing cavity 140 via the flow-limiting pipe 620. This facilitates the flow of liquid from the first inlet 110 through the flow-limiting pipe 620 at a flow rate less than a preset flow rate threshold. Furthermore, due to the large air bubbles located in the second cavity and completely blocking the rectifier orifice, under negative pressure, the liquid in the second cavity compresses these large air bubbles. This causes the surface tension of the large air bubbles to be unable to maintain their original shape due to the direct negative pressure and the pressure of the liquid in the second cavity, resulting in the bubbles expanding, deforming, and even breaking. Instead of clogging the rectifier orifice; or for bubbles located in the second cavity that partially clog the rectifier orifice, under the action of negative pressure, the surface tension of the partially clogged bubble cannot maintain the original shape of the bubble, causing the bubble to expand, deform, or even break; or for bubbles located in the channel of the rectifier orifice, especially for bubbles that clog the channel of the rectifier orifice, under the action of negative pressure, the bubbles in the narrow channel expand under the action of external pressure, and due to the restriction of the inner wall of the channel, the surface tension inside the bubble cannot maintain the original shape of the bubble, making the bubble more likely to deform, and then break into smaller bubbles that are not easy to clog the rectifier orifice, thus expelling the bubbles that are easy to clog the rectifier orifice. In addition, the dead zone in the first cavity is located in the area of ​​the second cavity near the rectifier. The dead zone is prone to large liquid disturbance when filling the first cavity, which causes unstable liquid flow in the first cavity. As a result, some dead zones in the first cavity cannot be filled, and bubbles are formed in some dead zones. Through the action of negative pressure, the large bubbles in the dead zone are deformed or even broken, and the small bubbles are increased in diameter due to external force and then detach from the wall or break, so as to expel the bubbles in the dead zone.

[0056] When the pressure source 400 draws liquid from the first inlet 110 into the liquid-containing cavity 140 at a second flow rate, if liquid is detected entering the second cavity 142 through the rectifier orifice 151, the second control valve 220 is set to the open state, and the pressure source 400 draws liquid from the first inlet 110 into the first cavity 141 at a fourth flow rate, so that the liquid fills the first cavity 141 and the second cavity 142; wherein the fourth flow rate is greater than the second flow rate. When liquid needs to fill the liquid-containing cavity 140, it needs to enter the first cavity 141 from the first inlet 110. At this time, the liquid can enter the first cavity 141 at the second flow rate and in a direction perpendicular to the flow direction X. Since the liquid enters the first cavity 141 at the second flow rate, it can alleviate the situation where a large number of bubbles are generated due to the collision between the liquid and the inner wall of the liquid-containing cavity 140. Moreover, since the liquid enters the liquid-containing cavity 140 from the first inlet 110 at the second flow rate, the second control valve 140 is in the closed state at this time, and the liquid-containing cavity 140 is relatively in a pressurized state. At this time, the second flow rate is a relatively slow flow rate. After the first chamber 141 is filled, the liquid will gradually fill the rectifier hole 151 and then gradually enter the second chamber 142 along the rectifier hole 151. When it is detected that the liquid has entered the second chamber 142 through the rectifier hole 151, the second control valve 220 can be set to the conducting state, so that the liquid chamber 140 is released from the pressure-holding state. Under the same positive pressure output, the flow rate of the liquid in the liquid chamber 140 can be increased, that is, the second flow rate can be increased to the fourth flow rate, thereby speeding up the filling of the liquid chamber 140 with liquid and improving the overall working efficiency.

[0057] Further, the liquid-containing cavity 140 includes a sheath fluid cavity 160 surrounding the sample needle 300. The liquid-containing cavity 140 can be divided into a sheath fluid cavity 160 for sheath fluid flow and a receiving cavity for accommodating the sample needle 300. When the sheath fluid cavity 160 is filled with liquid, the pressure source 400 provides positive pressure to the liquid-containing cavity 140 to force liquid into the liquid-containing cavity 140 from the first inlet 110 at a third flow rate, wherein the third flow rate is greater than the second flow rate, and / or, the third flow rate is greater than the fourth flow rate; while the liquid is at the third flow rate, the pressure source 400 injects liquid into the sample needle 300 to fill the sample needle 300 with liquid. In one embodiment, the pressure source 400 injects a sample into the sample needle 300 at a fifth flow rate to deliver the sample through the sample needle, thereby forming a sample flow in the flow chamber by the sheath fluid flowing in the sheath fluid cavity surrounding the sample, and then performing sample detection in the flow chamber, wherein the third flow rate is greater than the fifth flow rate.

[0058] Since the sheath fluid chamber 160 is already filled with liquid, and in order to quickly put the flow chamber 100 into a ready-to-use state, liquid needs to be injected into the sample needle 300. In this embodiment, when the sheath fluid chamber 160 is filled with liquid, the liquid is rapidly flowed into the sheath fluid chamber 160 at a third flow rate to establish a high-velocity sheath flow in the sheath fluid chamber 160. During the process of injecting liquid into the sample needle 300 to fill the sample needle 300, even if some air bubbles enter the sheath fluid chamber 160 from the outlet of the sample needle 300 (the end of the sample needle 300 that is open away from the second inlet 130), the sample carrying air bubbles can be wrapped by the high-velocity sheath flow or the air bubbles can be carried out of the flow chamber from the outlet 120. In particular, the high-velocity sheath flow wraps the sample or air bubbles that may carry air bubbles through the detection area of ​​the flow chamber, reducing the possibility of contact between the sample or air bubbles that may carry air bubbles and the inner wall of the flow chamber, thereby completing the purpose of air bubble removal in the flow chamber 100 and reducing the problem of air bubbles remaining inside the liquid-containing cavity 140.

[0059] Furthermore, when the sheath fluid chamber 160 is filled with liquid, the second control valve 220, the flow restrictor 620, and the first pipeline 610 are all set to the open state. The pressure source 400 provides positive pressure to the liquid-containing chamber 140 through the flow restrictor 620, the first pipeline 610, and the second control valve 220, so that the liquid flows into the liquid-containing chamber 140 from the first inlet 110 at a third flow rate. During the process of the liquid being at the third flow rate, the third control valve 230 is set to the open state, and the pressure source 400 injects liquid into the sample needle 300 to fill the sample needle 300 with liquid.

[0060] The first pipeline 610 and the flow-limiting pipe 620 can be connected in parallel to the first inlet 110. Both the branch containing the first pipeline 610 and the branch containing the flow-limiting pipe 620 can be connected to control valves. By opening or closing the control valves, the pressure source 400 can be connected to the first inlet 110 through the first pipeline 610 and / or the flow-limiting pipe 620. To allow the liquid to enter the sheath fluid chamber 160 at a higher flow rate when the sheath fluid chamber is full, the second control valve 220, the flow-limiting pipe 620, and the first pipeline 610 can all be set to an open state, allowing the liquid to simultaneously enter the first inlet 110 through both the first pipeline 610 and the flow-limiting pipe 620. When the pressure source 400 provides positive pressure to the liquid-containing cavity 140, more liquid can flow into the liquid-containing cavity 140 per unit time, enabling the liquid to flow from the first inlet 110 into the liquid-containing cavity 140 at a third flow rate. During this process, the pressure source 400 injects liquid into the sample needle 300 to fill the sample needle 300 with liquid. The high-velocity sheath flow can carry air bubbles out of the flow chamber 100 from the outlet 120, thereby completing the purpose of degassing the flow chamber 100 and reducing the problem of air bubbles remaining inside the liquid-containing cavity 140.

[0061] In this application, during the evacuation of the liquid in the flow chamber at a first flow rate, the evacuation process proceeds slowly due to the flow restriction of the sample needle. When bubbles in the inner wall or dead zone of the flow chamber come into contact with air, they cannot maintain their shape due to surface tension and break down. During the subsequent liquid filling process at least at a second flow rate, the liquid flow velocity is relatively low (the second flow rate is relatively low) before the sheath fluid chamber of the flow chamber is filled with liquid, to avoid excessive liquid disturbance, which could cause unstable flow of the liquid inside the flow chamber and result in some dead zones not being filled, causing some gas to remain in the dead zones. During the final filling of the sample needle, under the protection of the sheath fluid, the air inside the sample needle is confined in the sample flow and cannot come into contact with the internal structure of the flow chamber. The bubbles can be smoothly discharged from the flow chamber under the protection of the sheath fluid, achieving the effect of degassing the flow chamber.

[0062] See Figure 2 and Figure 3 The pressure source 400 includes a first metering pump 410, which is connected to a second inlet 130 via a pipeline. The first metering pump 410 is used to provide positive and negative pressure to the liquid-containing chamber 140. One end of the first metering pump 410 can be connected to a positive pressure source and a negative pressure source via a pipeline, and the other end can be connected to the second inlet 130 via a pipeline. When it is necessary to provide positive pressure to the liquid-containing chamber 140, positive pressure can be output to the first metering pump 410 through the positive pressure source to provide positive pressure to the liquid-containing chamber 140; when it is necessary to provide negative pressure to the liquid-containing chamber 140, negative pressure can be output to the first metering pump 410 through the negative pressure source to provide negative pressure to the liquid-containing chamber 140.

[0063] The pressure source 400 includes a syringe 420, which is connected to a second inlet 130 via a tubing. The syringe 420 is used to provide positive and negative pressure to the liquid-containing chamber 140. In this embodiment, a first metering pump 410 and a syringe 420 can be connected to the second inlet 130 simultaneously. The syringe 420 or the first metering pump 410 can be controlled to provide positive or negative pressure to the liquid-containing chamber 140, or both can be controlled simultaneously.

[0064] In some embodiments, the pressure source 400 includes a first liquid storage tank 430, a second liquid storage tank 440, a second metering pump 450, and a positive pressure source. The second metering pump 450 is connected to the second liquid storage tank 440 and the first liquid storage tank 430 via pipelines, and the positive pressure source is connected to the second liquid storage tank 440 via pipelines. The second metering pump 450 is used to provide positive pressure so that liquid in the second metering pump 450 flows into the first liquid storage tank 430, and the second metering pump 450 is used to provide negative pressure to draw liquid from the second liquid storage tank 440 to establish a negative pressure in the second liquid storage tank 440. The positive pressure source is used to provide positive pressure to the second liquid storage tank 440 to establish a positive pressure in the second liquid storage tank 440. The second liquid storage tank 440 is used to provide both positive and negative pressure to the liquid-containing cavity 140.

[0065] Both the first storage tank 430 and the second storage tank 440 store liquid. Positive or negative pressure can be established in the second storage tank 440, and then supplied to the liquid-containing cavity 140 through the second storage tank 440. Specifically, when a negative pressure needs to be established in the second storage tank 440, the second storage tank 440 is first sealed. Then, liquid from the second metering pump 450 is transferred to the first storage tank 430 through a pipeline, and then the second metering pump 450 draws liquid from the second storage tank 440 to create a certain negative pressure in the second storage tank 440. When a larger negative pressure needs to be established in the second storage tank 440, the above process can be repeated. When a positive pressure needs to be established in the second storage tank 440, the second storage tank 440 is first sealed. Then, positive pressure is input into the second storage tank 440 through a positive pressure source, thereby creating a predetermined positive pressure in the second storage tank 440.

[0066] Combination Figure 3The second storage tank 440 can store a diluent, which can also be used as a sheath fluid during sample testing. The second storage tank 440 is connected to the first control valve 210 via a pipeline. The second storage tank 440 can be connected to atmospheric pressure via a control valve. In one embodiment, the control valve connected to atmospheric pressure can be opened to restore the pressure inside the second storage tank 440 to normal. After restoring normal pressure, the connection between the second storage tank 440 and atmospheric pressure is disconnected, at which point the second storage tank 440 is in a sealed state. The diluent in the second storage tank 440 is drawn into the second metering pump 450, which then pumps the drawn-in diluent into the first storage tank 430. This process is repeated multiple times. Because the second storage tank 440 is sealed, the diluent drawn into it by the second metering pump 450 gradually increases the pressure from atmospheric pressure to negative pressure. For example, the negative pressure in the second storage tank 440 can be set to -40 kPa. In another embodiment, positive pressure can be established in the second storage tank 440 through a positive pressure source connected to another control valve connected to the second storage tank 440. For example, another control valve connected to the second reservoir 440 is opened to establish a positive pressure in the second reservoir 440, for example, a positive pressure of about 70 kPa.

[0067] To address the technical problems existing in the prior art, this application also provides a bubble removal method. The bubble removal method can be applied to the blood cell analyzer 10 in any of the above embodiments. The bubble removal method may include: when there is a first liquid in the liquid chamber 140, the pressure source 400, in conjunction with the first control valve 210, the second control valve 220 and the third control valve 230, provides positive pressure and negative pressure to the liquid chamber 140 to fill the liquid chamber 140 with liquid to obtain a second liquid, wherein the number of bubbles in the second liquid is less than the number of bubbles in the first liquid.

[0068] The bubble removal method can be implemented based on the various components of the blood cell analyzer 10 in the above embodiments. The specific implementation method can be the same as or similar to the methods in the various embodiments of the blood cell analyzer 10, and will not be described in detail here.

[0069] Through the above implementation method, the pressure source 400, together with the first control valve 210, the second control valve 220 and the third control valve 230, provides positive and negative pressure to the liquid-containing chamber 140, which can form a second liquid with fewer bubbles than the first liquid. Thus, the bubbles in the liquid in the flow chamber 100 can be discharged through a simple structure, reducing the accumulation of bubbles inside the flow chamber 100 and enhancing the accuracy and reliability of the blood cell analyzer 10.

[0070] The above structure and method can be applied to remove air bubbles from the flow chamber during normal use of a hematology analyzer, and also to remove air bubbles from the flow chamber during the perfusion process of a hematology analyzer. The perfusion process includes initial perfusion and the air bubble removal process of the hematology analyzer described in this application. Before air bubble removal from the flow chamber, the first, second, and third control valves are all open, filling the flow chamber and the pipelines connected to the flow chamber's outlet, first inlet, and second inlet with liquid. This ensures that the liquid perfuses the flow chamber and the upstream and downstream pipelines connected to the flow chamber. The above structure and method help optimize the perfusion process and avoid introducing air bubbles during perfusion.

[0071] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this application, and not to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some or all of the technical features therein. These modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of this application, and they should all be covered within the scope of the claims and specification of this application. In particular, as long as there is no structural conflict, the various technical features mentioned in the embodiments can be combined in any way. This application is not limited to the specific embodiments disclosed herein, but includes all technical solutions falling within the scope of the claims.

Claims

1. A blood cell analyzer, characterized in that, The blood cell analyzer includes: a flow chamber, a pressure source, a first control valve, a second control valve, and a third control valve. The flow chamber includes a liquid-containing cavity and a first inlet, a second inlet, and an outlet communicating with the liquid-containing cavity. The first control valve is connected to the first inlet via a pipeline, the second control valve is connected to the outlet via a pipeline, the third control valve is connected to the second inlet via a pipeline, and the pressure source is connected to at least one of the first inlet and the second inlet via a pipeline. When a first liquid is present in the liquid-containing cavity, the pressure source, in conjunction with the first control valve, the second control valve, and the third control valve, provides positive and negative pressure to the liquid-containing cavity to fill it with liquid, thereby obtaining a second liquid, wherein the number of air bubbles in the second liquid is less than the number of air bubbles in the first liquid; The pressure source is connected to the first liquid inlet and the second liquid inlet through a pipeline. When the liquid in the liquid-containing cavity contains the first liquid, the third control valve and the first control valve are set to the open state, and the second control valve is set to the closed state. The pressure source provides negative pressure to the liquid-containing cavity so that the liquid in the liquid-containing cavity flows out of the liquid-containing cavity from the first liquid inlet at a first flow rate less than a preset flow rate threshold. With the first control valve and the second control valve set to the open state and the third control valve set to the closed state, the pressure source provides positive pressure to the liquid-containing cavity so that liquid flows from the first inlet into the liquid-containing cavity at a second flow rate less than the preset flow rate threshold through the pressure source, so as to fill the liquid-containing cavity with liquid. The blood cell analyzer also includes a sample needle, which is located in the liquid-containing cavity and connected to the second liquid inlet. The sample needle extends along the flow direction of the liquid in the liquid-containing cavity, and the liquid-containing cavity includes a sheath fluid cavity that wraps around the outside of the sample needle. When the sheath fluid chamber is filled with liquid, the pressure source provides positive pressure to the fluid-containing cavity to force liquid into the fluid-containing cavity from the first inlet at a third flow rate, wherein the third flow rate is greater than the second flow rate.

2. The blood cell analyzer according to claim 1, characterized in that, The blood cell analyzer further includes a sample needle, a flow limiting tube, a first pipeline, and a reaction cell connected to atmospheric pressure. The sample needle is located in the liquid-containing chamber and connected to the second liquid inlet. The reaction cell is connected between the pressure source and the flow chamber. The pressure source is at least connected to the first liquid inlet, and the pressure source and the first liquid inlet are connected through the flow limiting tube and the first pipeline. With the third control valve and the flow limiting tube set to the open state, and the second control valve and the first pipeline set to the closed state, the pressure source provides negative pressure to the liquid-containing cavity through the flow limiting tube, so that the liquid in the liquid-containing cavity flows out of the liquid-containing cavity from the first inlet through the flow limiting tube at a first flow rate less than a preset flow rate threshold.

3. The blood cell analyzer according to claim 2, characterized in that, The blood cell analyzer also includes a sample needle, which is located in the liquid-containing cavity and connected to the second inlet. The sample needle extends along the flow direction of the liquid in the liquid-containing cavity. The flow chamber also includes a rectifier disposed in the liquid-containing cavity. The rectifier divides the area in the liquid-containing cavity, excluding the sample needle, into a first cavity and a second cavity in the flow direction of the liquid. The first inlet communicates with the first cavity, and the rectifier is provided with a rectifier hole that communicates with the first cavity and the second cavity. When the third control valve and the flow-limiting pipe are in the open state, and the second control valve and the first pipeline are in the closed state, the pressure source provides negative pressure to the liquid-containing cavity through the flow-limiting pipe, so that the first liquid in the first cavity, the second cavity, and the rectifier orifice flows out of the liquid-containing cavity from the first inlet through the flow-limiting pipe at a first flow rate less than a preset flow rate threshold, thereby at least expelling air bubbles in the first cavity and the rectifier orifice; when the pressure source flows the liquid into the liquid-containing cavity from the first inlet at the second flow rate, if liquid is detected entering the second cavity through the rectifier orifice, the second control valve is in the open state, and the pressure source flows the liquid into the first cavity from the first inlet at a fourth flow rate, so that the liquid fills the first cavity and the second cavity; wherein, the fourth flow rate is greater than the second flow rate.

4. The blood cell analyzer according to claim 3, characterized in that, The third flow velocity is greater than the fourth flow velocity; During the process of the liquid being at the third flow rate, the pressure source injects liquid into the sample needle to fill the sample needle with liquid.

5. The blood cell analyzer according to claim 4, characterized in that, The blood cell analyzer also includes a flow limiting tube and a first pipeline, and the pressure source and the first liquid inlet are connected through the flow limiting tube and the first pipeline; When the sheath fluid chamber is filled with liquid, the second control valve, the flow limiting tube, and the first pipeline are all set to the open state. The pressure source provides positive pressure to the liquid-containing cavity through the flow limiting tube, the first pipeline, and the second control valve so that the liquid flows into the liquid-containing cavity from the first inlet at the third flow rate. Furthermore, during the process of the liquid being at the third flow rate, the third control valve is set to the open state, and the pressure source injects liquid into the sample needle to fill the sample needle with liquid.

6. The blood cell analyzer according to claim 1, characterized in that, The pressure source includes a first metering pump, which is connected to the second inlet via a pipeline. The first metering pump is used to provide positive and negative pressure to the liquid-containing cavity. And / or the pressure source includes a syringe, which is connected to the second inlet via a pipeline. The syringe is used to provide positive and negative pressure to the liquid-containing cavity. And / or, the pressure source includes a first liquid storage tank, a second liquid storage tank, a second metering pump, and a positive pressure source. The second metering pump is connected to the second liquid storage tank and the first liquid storage tank via a pipeline. The positive pressure source is connected to the second liquid storage tank via a pipeline. The second metering pump is used to provide positive pressure so that liquid in the second metering pump flows into the first liquid storage tank, and the second metering pump is used to provide negative pressure to draw liquid from the second liquid storage tank to establish a negative pressure in the second liquid storage tank. The positive pressure source is used to provide positive pressure to the second liquid storage tank to establish a positive pressure in the second liquid storage tank. The second liquid storage tank is used to provide both positive and negative pressure to the liquid-containing cavity.

7. A method for removing air bubbles, characterized in that, The method for removing air bubbles, applicable to the blood cell analyzer according to any one of claims 1-6, comprises: When a first liquid is present in the liquid-containing cavity, the pressure source, in conjunction with the first control valve, the second control valve, and the third control valve, provides positive and negative pressure to the liquid-containing cavity to fill it with liquid and obtain a second liquid, wherein the number of air bubbles in the second liquid is less than the number of air bubbles in the first liquid.

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