Blood cell joint detection analyzer

Abstract

According to the blood cell joint detection analyzer, the length of a guide shaft is larger than 400 mm, the moving distance of a linear sliding sleeve in the horizontal direction is larger than 360 mm, the number of assemblies, participating in detection, of a sample suction needle can be increased, and the practicability of the blood cell joint detection analyzer is improved. Meanwhile, the extension direction of the sample suction needle and the extension direction of the erythrocyte sedimentation rate detection module are both parallel to the vertical direction, and the vertical distance between the sample suction needle and the erythrocyte sedimentation rate detection module is less than 60mm, so that the distance between the sample suction needle and the erythrocyte sedimentation rate detection module is reduced; the shaking of a pipeline between a sample suction needle and an erythrocyte sedimentation rate detection module caused by the movement of the sample suction needle relative to the erythrocyte sedimentation rate detection module is reduced, the disturbance of a sample in the pipeline is reduced, and the detection accuracy and the detection efficiency of the erythrocyte sedimentation rate detection module on the sample are improved.

Description

Technical Field

[0001] The present application relates to the technical field of cell detection, and in particular to a blood cell combined detection analyzer. Background Art

[0002] Erythrocyte Sedimentation Rate (ESR), referred to as ESR, refers to the sedimentation rate of red blood cells under certain conditions. When anticoagulated blood is placed in a small vertical glass tube, red blood cells naturally sink under the action of gravity due to their large specific gravity. Under normal circumstances, the sinking is very slow. The sedimentation rate of red blood cells is often expressed by the distance that red blood cells sink at the end of the first hour, which is called ESR.

[0003] In the existing combined detection analyzer, the erythrocyte sedimentation rate detection module for cells is generally integrated into the sample suction pipeline, and the erythrocyte sedimentation rate detection is performed on the sample suction pipeline, which places strict requirements on the state of the sample in the pipeline. Summary of the invention

[0004] In order to solve the above technical problems, the present application provides a blood cell combined detection analyzer, which includes a partition, a bottom plate, a guide shaft, a linear sleeve, a stepper motor, a belt, a sample suction needle and an erythrocyte sedimentation rate detection module; The partition is vertically fixed in the blood cell combined detection analyzer, the bottom plate is fixed on the partition, the guide shaft is fixed on the bottom plate, and the guide shaft extends in the horizontal direction; The linear sleeve is sleeved on the guide shaft, and the stepping motor is connected to the linear sleeve through the belt to drive the linear sleeve to slide horizontally along the guide shaft; The sample aspirating needle and the erythrocyte sedimentation rate detection module are arranged on the linear sleeve, and the linear sleeve drives the sample aspirating needle and the erythrocyte sedimentation rate detection module to move horizontally; Wherein, the length of the guide shaft is greater than 400 mm, and the sliding distance of the linear sleeve in the horizontal direction is greater than 360 mm; The extending direction of the sample aspirating needle and the extending direction of the erythrocyte sedimentation rate detection module are both parallel to the vertical direction, and the vertical distance between the sample aspirating needle and the erythrocyte sedimentation rate detection module is less than 60 mm.

[0005] Wherein, the two horizontal edges of the bottom plate are provided with curling edges; and / or, at least one vertical edge of the bottom plate is provided with a rolled edge; and / or, the maximum horizontal length of the base plate is greater than or equal to 5 times the maximum vertical length of the base plate; The horizontal side of the bottom plate is the side of the bottom plate parallel to the horizontal direction, and the vertical side of the bottom plate is the side of the bottom plate parallel to the vertical direction.

[0006] Wherein, the blood cell combined detection analyzer also includes an in-place optical coupling component, the in-place optical coupling component is fixed on the linear sleeve, and the in-place optical coupling component includes a light emitting module and a photoelectric conversion module; Wherein, a plurality of positioning grooves are arranged on the bottom plate.

[0007] Wherein, the blood cell combined detection analyzer comprises a plurality of sample holding pools, and the plurality of sample holding pools are arranged inside the blood cell combined detection analyzer along a horizontal direction; After the sample aspirating needle absorbs the sample, the linear sleeve moves on the guide shaft to drive the sample aspirating needle to move to the sample holding pool to distribute the sample; Wherein, in the vertical direction, the plurality of sample holding pools are located below the bottom plate; And / or, each of the sample holding pools has a pool opening opening upward; And / or, the sample holding pool is disposed below at least two of the plurality of positioning grooves; And / or, the number of the positioning grooves is greater than or equal to the number of the sample holding pools.

[0008] Wherein, part of the edge of the positioning groove is perpendicular to the bottom plate; And / or, in the vertical direction, the central axis of the positioning groove is aligned with the central axis of the corresponding pool opening of the sample holding pool; And / or, the width of the positioning groove is smaller than the maximum pool opening width of the sample holding pool; and / or, the minimum distance between the plurality of positioning grooves is greater than 10 mm; And / or, the minimum groove width of the plurality of positioning grooves is greater than 6 mm.

[0009] Wherein, the blood cell combined detection analyzer also includes a driving plunger pump and a hose; The sample suction needle is a double-ended open cylinder, the upper end of which is connected to the first end of the hose, and the driving plunger pump is connected to the second end of the hose; The inner diameter of the hose is less than or equal to 2 mm; And / or, the length of the hose is greater than 800 mm; And / or, the radial cross-sectional area of ​​the upper end of the double-ended open cylinder is greater than the radial cross-sectional area of ​​the lower end of the double-ended open cylinder.

[0010] There are at least two fixing points on the hose, and the at least two fixing points fix the first sub-pipeline of the hose on the linear sleeve, and the extension direction of the first sub-pipeline is parallel to the vertical direction, and the erythrocyte sedimentation rate detection module is used to detect the cell sedimentation parameters of the sample in the first sub-pipeline; The sub-pipeline of the hose between one end of the first sub-pipeline close to the sample aspirating needle and the connection between the sample aspirating needle and the hose is the second sub-pipeline; The length of the second sub-pipeline is greater than or equal to 70 mm; And / or, a sleeve is provided on the outer side of the second sub-pipeline.

[0011] Wherein, the length of the second sub-pipeline is less than or equal to 400 mm; And / or, the sample undergoes at least one 180-degree turn when passing through the second sub-pipeline.

[0012] Wherein, the sub-pipeline of the hose between the end of the first sub-pipeline away from the sample aspirating needle and the connection between the driving plunger pump and the hose is the third sub-pipeline; Wherein, the blood cell combined detection analyzer further comprises a tank chain, and the tank chain is sleeved on the outside of the third sub-pipeline; The length of the third sub-pipeline is greater than or equal to 500 mm; And / or, a casing is provided outside the pipe section of the third sub-pipeline wrapped by the tank chain; And / or, the vertical width of the tank chain is less than or equal to 50 mm.

[0013] The blood cell combined detection analyzer further comprises a control module, which is connected to the sample suction needle, the erythrocyte sedimentation rate detection module and the linear sleeve. When the erythrocyte sedimentation rate detection module detects the sample in the first sub-pipeline, the control module is used to control the sample aspiration needle and the linear sleeve to stop moving; And / or, the control module is further used to control the time point when the erythrocyte sedimentation rate detection module starts to detect the sample in the first sub-pipeline, and the time point when the sample aspiration needle and the linear sleeve stop moving is greater than 0.1 seconds.

[0014] Beneficial effects of the present application: Different from the prior art, the blood cell combined detection analyzer provided by the present application includes a partition, a base plate, a guide shaft, a linear sleeve, a stepper motor, a belt, a sample suction needle and an erythrocyte sedimentation rate detection module. The partition is vertically fixed in the analyzer, the base plate is fixed on the partition, the guide shaft is fixed on the base plate, and the extension direction of the guide shaft is parallel to the horizontal direction; the linear sleeve is sleeved on the guide shaft, and the stepper motor is connected to the linear sleeve through a belt to drive the linear sleeve to slide horizontally along the guide shaft; the sample suction needle and the erythrocyte sedimentation rate detection module move along the guide shaft. Among them, the length of the guide shaft is greater than 400mm, and the horizontal movement distance of the linear sleeve is greater than 360mm, which can expand the number of components involved in the detection of the sample suction needle and improve the practicality of the blood cell combined detection analyzer. At the same time, the extension direction of the sample aspiration needle and the extension direction of the erythrocyte sedimentation rate detection module are parallel to the vertical direction, and the vertical distance between the sample aspiration needle and the erythrocyte sedimentation rate detection module is less than 60mm, thereby reducing the distance between the sample aspiration needle and the erythrocyte sedimentation rate detection module, thereby reducing the shaking of the pipeline between the sample aspiration needle and the erythrocyte sedimentation rate detection module caused by the movement of the sample aspiration needle relative to the erythrocyte sedimentation rate detection module, reducing the disturbance of the sample in the pipeline, and improving the detection accuracy and efficiency of the sample by the erythrocyte sedimentation rate detection module. BRIEF DESCRIPTION OF THE DRAWINGS

[0015] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the following briefly introduces the drawings required for use in the description of the embodiments. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work. Among them: Figure 1 It is a structural schematic diagram of an embodiment of the blood cell combined detection analyzer of the present application; Figure 2 yes Figure 1 Schematic diagram of the structure of the local area A; Figure 3 yes Figure 1 Schematic diagram of the structure of local area A from another perspective.

[0016] Figure numbers: blood cell combined detection analyzer 1; partition 11; bottom plate 12; curling edge 121; positioning groove 122; auxiliary strip 123; guide shaft 13; linear sleeve 14; belt 15; stepping motor 16; sample suction needle 17; erythrocyte sedimentation rate detection module 18; hose 19; first sub-pipeline 191; second sub-pipeline 192; third sub-pipeline 193; driving plunger pump 20; tank chain 21. DETAILED DESCRIPTION

[0017] The scheme of the embodiment of the present application is described in detail below in conjunction with the drawings of the specification.

[0018] In the following description, for the purpose of explanation rather than limitation, specific details such as specific system structures, interfaces, and technologies are provided to facilitate a thorough understanding of the present application.

[0019] Reference to "embodiments" in this application means that a particular feature, structure, or characteristic described in conjunction with the embodiments may be included in at least one embodiment of the present application. The appearance of the phrase in various locations in the specification does not necessarily refer to the same embodiment, nor is it an independent or alternative embodiment that is mutually exclusive with other embodiments. It is explicitly and implicitly understood by those skilled in the art that the embodiments described herein may be combined with other embodiments.

[0020] The term "and / or" in this application is only a description of the association relationship of associated objects, indicating that there may be three relationships. For example, A and / or B can represent: A exists alone, A and B exist at the same time, and B exists alone. In addition, the character " / " in this article generally indicates that the objects associated before and after are in an "or" relationship. In addition, "many" in this article means two or more than two. In addition, the term "at least one" in this article means any combination of at least two of any one or more of a plurality of, for example, including at least one of A, B, and C, and can mean including any one or more elements selected from the set consisting of A, B, and C. In addition, the terms "first", "second", and "third" in this application are used for descriptive purposes only and cannot be understood as indicating or implying relative importance or implicitly indicating the number of indicated technical features.

[0021] See also Figure 1~Figure 3 , Figure 1 This is a schematic diagram of the structure of an embodiment of the blood cell combined detection analyzer of the present application. Figure 2 yes Figure 1 Schematic diagram of the structure of the local area A in the middle. Figure 3 yes Figure 1 A structural diagram of another perspective of the local area A in the middle. The blood cell combined detection analyzer 1 provided in the embodiment of the present application includes a partition 11, a bottom plate 12, a guide shaft 13, a linear sleeve 14, a belt 15, a stepper motor 16, a sample suction needle 17 and an erythrocyte sedimentation rate detection module 18. Among them, the detectable items of the blood cell combined detection analyzer 1 include but are not limited to blood routine detection items, specific protein (such as CRP, SAA) detection items, biochemical detection items, immune detection items, blood type detection, erythrocyte sedimentation rate detection, etc.

[0022] The partition 11 is vertically fixed in the blood cell combined detection analyzer 1, the bottom plate 12 is fixed on the partition 11, the guide shaft 13 is fixed on the bottom plate 12, and the guide shaft 13 extends in the horizontal direction. The linear sleeve 14 is sleeved on the guide shaft 13, and the stepper motor is connected to the linear sleeve 14 through the belt 15 to drive the linear sleeve 14 to slide horizontally along the guide shaft 13.

[0023] In one embodiment, the guide shaft 13 may also be a guide rail, and the linear sleeve 14 may be a slide seat matched with the guide rail, etc. The present application does not limit the specific structure of the guide shaft 13 and the linear sleeve 14.

[0024] The sample suction needle 17 and the erythrocyte sedimentation rate detection module 18 are arranged on the linear sleeve 14, and the linear sleeve 14 drives the sample suction needle 17 and the erythrocyte sedimentation rate detection module 18 to move horizontally, wherein the sample suction needle 17 can be used to suck the sample in the sample tube and distribute the sample on the moving path under the drive of the linear sleeve 14, and the erythrocyte sedimentation rate detection module 18 is used to perform erythrocyte sedimentation rate detection on the sample sucked by the sample suction needle 17.

[0025] In this embodiment, a partition 11 and a bottom plate 12 are provided, and the guide shaft 13, the linear sleeve 14, etc. are provided on the bottom plate 12, which can reduce the user's maintenance of the guide shaft 13 and other structures. Since the guide shaft 13 and other structures are provided on the bottom plate 12, the user can move the bottom plate 12 out of the blood cell combined detection analyzer 1 and repair the structure on the bottom plate 12. If the guide shaft 13 and other structures are provided on the partition 11, since the partition 11 also plays a supporting role in the blood cell combined detection analyzer 1, that is, the blood cell combined detection analyzer 1 cannot be removed, the user needs to repair the structure in the blood cell combined detection analyzer 1, and the maintenance difficulty is relatively large. Therefore, by providing the partition 11 and the bottom plate 12, the maintenance difficulty of the blood cell combined detection analyzer 1 can be reduced.

[0026] Furthermore, since the area of ​​the partition 11 is larger than the area of ​​the bottom plate 12, that is, the deformation probability of the partition 11 is greater than that of the bottom plate 12. If the guide shaft 13 and other structures are arranged on the partition 11, the partition 11 is easy to deform, which will affect the movement of the linear sleeve 14, the operating efficiency of the blood cell combined detection analyzer 1, and the accuracy of the erythrocyte sedimentation rate and other tests. If the deformation probability of the partition 11 is reduced by increasing the thickness of the partition 11, the manufacturing cost of the partition 11 will be increased, and the installation difficulty of the partition 11 will be increased. Therefore, this embodiment proposes to improve the operating efficiency and detection accuracy of the blood cell combined detection analyzer 1 by setting the bottom plate 12, and the guide shaft 13 and other structures are arranged on the bottom plate 12.

[0027] Among them, when the sample flows through the pipeline, if the pipeline moves, the disturbance of the sample in the pipeline will be increased, and the erythrocyte sedimentation rate detection module 18 detects the erythrocyte sedimentation rate of the sample, and the disturbance of the sample will affect the erythrocyte sedimentation rate of the sample, thereby affecting the detection accuracy and detection efficiency of the erythrocyte sedimentation rate detection module 18. In this embodiment, by fixing the sample suction needle 17 and the erythrocyte sedimentation rate detection module 18 on the linear sleeve 14, the relative movement between the sample suction needle 17 and the erythrocyte sedimentation rate detection module 18 can be reduced, that is, the movement of the pipeline between the sample suction needle 17 and the erythrocyte sedimentation rate detection module 18 is reduced, and the disturbance of the sample in the pipeline is reduced, so as to improve the detection accuracy and detection efficiency of the sample by the erythrocyte sedimentation rate detection module 18.

[0028] Optionally, the length of the guide shaft 13 is greater than 400 mm, and the sliding distance of the linear sleeve 14 in the horizontal direction is greater than 360 mm. As described above, the sample suction needle 17, driven by the linear sleeve 14, will perform sample separation on the moving path, and by increasing the length of the guide shaft 13 and the sliding distance of the linear sleeve 14 in the horizontal direction, the moving distance of the sample suction needle 17 can be increased, that is, the setting distance and setting number of the sample pool (used to receive the sample distributed by the sample suction needle 17) in the blood cell combined detection analyzer 1 are increased, allowing the sample suction needle 17 to perform sample separation on more sample pools, thereby increasing the number of items of sample detection by the blood cell combined detection analyzer 1.

[0029] Optionally, the extension direction of the sample aspirating needle 17 and the extension direction of the erythrocyte sedimentation rate detection module 18 are both parallel to the vertical direction, and the vertical distance between the sample aspirating needle 17 and the erythrocyte sedimentation rate detection module 18 is less than 60 mm.

[0030] Specifically, when the linear sleeve 14 drives the sample aspiration needle 17 to move horizontally to above any sample holding pool, or when the sample aspiration needle 17 is located above the sample tube, the sample aspiration needle 17 can move downward in the vertical direction to separate the sample or absorb the sample, that is, the sample aspiration needle 17 can move in the vertical direction relative to the linear sleeve 14, and by limiting the extension direction of the sample aspiration needle 17 to be parallel to the vertical direction, the sample aspiration needle 17 can be effectively controlled to move to the corresponding sample tube or sample holding pool for operation, thereby improving the operating efficiency of the sample aspiration needle 17.

[0031] The pipeline connected to one end of the sample suction needle 17 may have a part of the sub-pipeline arranged in the vertical direction, and the ESR detection module 18 also extends in the vertical direction and is sleeved on the part of the sub-pipeline to perform ESR detection on the sample in the part of the sub-pipeline.

[0032] The vertical distance between the sample aspirating needle 17 and the erythrocyte sedimentation rate detection module 18 is the horizontal distance between the sample aspirating needle 17 and the erythrocyte sedimentation rate detection module 18 when both are arranged on the linear sleeve 14. By setting the vertical distance between the sample aspirating needle 17 and the erythrocyte sedimentation rate detection module 18 to be less than 60 mm, Figure 3 As shown, the pipeline connected to one end of the sample suction needle 17 will be bent and then passed through the erythrocyte sedimentation rate detection module 18. The greater the curvature of the pipeline, the more curved the pipeline through which the sample flows, the greater the energy consumption due to the change in flow direction during the flow, and the smaller the energy used for axial impact, that is, the flow rate becomes smaller, which can reduce the disturbance of the sample in the pipeline, so as to improve the detection accuracy and efficiency of the erythrocyte sedimentation rate detection module 18 on the sample.

[0033] In one embodiment, the optical axis direction of the light beam emitted by the ESR detection module 18 can be horizontal. Since the extension direction of the detected sub-pipeline is also vertical, the optical axis direction of the light beam emitted by the ESR detection module 18 is perpendicular to the extension direction of the sub-pipeline, so that the light beam can vertically enter the sub-pipeline, and the mesoscopic scale sample will only settle in the vertical direction, and the cells will not be subjected to additional resistance on the inner wall of the tube due to the tilt, thereby avoiding the influence of gravity on the measurement accuracy and efficiency of the sample by the ESR detection module 18.

[0034] In another embodiment, the ESR detection module 18 itself or its shell can be made of light-shielding material to prevent stray light in the environment from entering the detection sub-pipeline through the ESR detection module 18 itself or its shell, thereby preventing the measurement accuracy of the ESR detection module 18 from being affected, thereby further improving the measurement efficiency of the ESR detection module 18 on the sample.

[0035] Alternatively, if Figure 1 As shown, the two horizontal edges of the bottom plate 12 are provided with curling edges 121, wherein the horizontal edges of the bottom plate 12 are also the two opposite side edges of the bottom plate 12 parallel to the horizontal direction. By providing the curling edges 121 on the two horizontal edges of the bottom plate 12, the two horizontal edges of the bottom plate 12 are rolled up, thereby improving the strength of the bottom plate 12, avoiding deformation of the bottom plate 12, affecting the smooth movement of the linear sleeve 14, and further disturbing the sample in the hose 19, especially the measurement accuracy of the erythrocyte sedimentation rate detection module 18 is easily affected by the shaking or swinging of the pipeline. The rigidity of the bottom plate 12 is improved, which can greatly reduce such interference.

[0036] Optionally, at least one vertical edge of the bottom plate 12 is provided with a curling edge 121, wherein the vertical edge of the bottom plate 12 is also the side edge of the bottom plate 12 parallel to the vertical direction. By providing the curling edge 121 on at least one vertical edge of the bottom plate 12, the strength of the bottom plate 12 is further improved, the smoothness of the movement of the linear sleeve 14 is improved, and the disturbance to the sample is reduced. In particular, the measurement accuracy of the erythrocyte sedimentation rate detection module 18 is easily affected by the shaking or swinging of the pipeline. The rigidity of the bottom plate 12 is improved, which can greatly reduce such interference.

[0037] In one embodiment, the maximum horizontal length of the bottom plate 12 is greater than or equal to 5 times the maximum vertical length of the bottom plate 12. As can be seen from the foregoing, the guide shaft 13 needs to be set to a larger length to increase the moving distance of the linear sleeve 14 and increase the sample separation position of the sample suction needle 17. Therefore, the horizontal length of the bottom plate 12 should be relatively large. Therefore, this embodiment proposes that the maximum horizontal length of the bottom plate 12 is greater than or equal to 5 times the maximum vertical length of the bottom plate 12, so as to appropriately reduce the vertical length of the bottom plate 12, reduce the manufacturing cost of the bottom plate 12, and increase the setting distance and setting number of the sample pools in the blood cell combined detection analyzer 1 in the horizontal direction, allowing the sample suction needle 17 to perform sample separation on more sample pools, increase the number of items for sample detection by the blood cell combined detection analyzer 1, and increase the number of combined detection items of the blood cell combined detection analyzer 1.

[0038] Among them, Figure 1 It can be seen that the guide shaft 13, belt 15, etc. on the bottom plate 12 are all extended in the horizontal direction, so the vertical length of the bottom plate 12 does not need to be set too large; if the vertical length of the bottom plate 12 is large, the maximum horizontal length of the bottom plate 12 is less than 5 times the maximum vertical length of the bottom plate 12, that is, there will be more empty areas on the bottom plate 12, wasting space, increasing manufacturing costs, and due to the expansion of the area, the strength of the bottom plate 12 may be reduced, which is not worth the loss. Therefore, this embodiment proposes that the maximum horizontal length of the bottom plate 12 is greater than or equal to 5 times the maximum vertical length of the bottom plate 12.

[0039] In one embodiment, the side edge of the partition 11 may also be provided with a curling edge to increase the strength of the partition 11 .

[0040] Optionally, the blood cell combined detection analyzer 1 also includes an in-place optical coupling component (not shown), which is fixed on the linear sleeve 14. By setting the in-place optical coupling component on the moving part and the optical coupling trigger component on the fixed part, since there may be multiple optical coupling trigger positions, the in-place optical coupling component is set on the moving part and the optical coupling trigger component is set on the fixed part, which can reduce the number of in-place optical coupling components, reduce equipment cost and equipment complexity, and because the optical coupling has a feedback signal, the smoothness and accuracy of the movement are guaranteed, thereby reducing the adverse effects of pipeline shaking caused by the movement on the erythrocyte sedimentation rate detection.

[0041] The in-place optical coupler assembly includes a light emitting module and a photoelectric conversion module, and a plurality of positioning grooves 122 are provided on the bottom plate 12. The positioning grooves 122 are a simple optical coupler trigger assembly, which is easy to process and further reduces the equipment cost and equipment complexity.

[0042] Specifically, an auxiliary bar 123 may be provided on the bottom plate 12, and the auxiliary bar 123 may be spaced apart from the guide shaft 13 and extended in the horizontal direction, and a plurality of positioning grooves 122 may be spaced apart on the auxiliary bar 123. Further, the in-place optical coupling component may be partially provided above the auxiliary bar 123 and partially provided below the auxiliary bar 123, for example, the light emitting module is provided above the auxiliary bar 123, and the photoelectric conversion module is provided below the auxiliary bar 123. Then, in the process of the linear sleeve 14 sliding horizontally along the guide shaft 13, the auxiliary bar 123 will block the light beam emitted by the light emitting module until it moves to one side of the positioning groove 122 on the auxiliary bar 123, and the light beam emitted by the light emitting module is not blocked and enters the photoelectric conversion module, and then the in-place optical coupling component may respond to the linear sleeve 14 moving into position. Alternatively, during the horizontal sliding process of the linear sleeve 14 along the guide shaft 13, at the beginning, the light-emitting module and the photoelectric conversion module are both in the positioning groove, and the light beam emitted by the light-emitting module is not blocked and enters the photoelectric conversion module until it moves to the other side of the positioning groove 122 on the auxiliary strip 123. The auxiliary strip 123 will block the light beam emitted by the light-emitting module, and then the optical coupler component can respond to the linear sleeve 14 moving into position.

[0043] In another embodiment, the positioning groove 122 may also be disposed on one of the horizontal curling edges 121 of the bottom plate 12 without additionally disposing an auxiliary strip 123 . Disposing the positioning groove 122 on the curling edge 121 can reduce material cost and installation cost.

[0044] The positions of the plurality of positioning grooves 122 can be respectively set to correspond to the positions of the sample holding pools, and the cooperation between the in-place optical coupling assembly and the positioning grooves 122 can improve the movement accuracy of the linear sleeve 14 and the sample separation efficiency of the sample aspiration needle 17.

[0045] It is understandable that the positions of the plurality of positioning slots 122 are arranged corresponding to the positions of the sample pool, and the distance between the sample suction needle 17 and the optical coupling assembly in place is fixed, so the positions of the sample pool and the sample suction needle 17, especially the position of the sample pool opening, can still be located by the positions of the positioning slots 122. This ensures that the sample suction needle 17 can inject the sample into the sample pool, ensures the stability and accuracy of the movement, and further reduces the adverse effects of the pipeline shaking caused by the movement on the erythrocyte sedimentation rate detection.

[0046] Optionally, the blood cell combined detection analyzer 1 includes multiple sample holding pools, which are horizontally arranged inside the blood cell combined detection analyzer 1. After the sample aspiration needle 17 absorbs the sample, the linear sleeve 14 moves on the guide shaft 13 to drive the sample aspiration needle 17 to move to the sample holding pool to distribute the sample.

[0047] Specifically, since the position of the positioning groove 122 corresponds to the position of the sample pool, when the linear sleeve 14 slides to the positioning groove 122, the optical coupling assembly responds to the linear sleeve 14 moving into position. At this time, the sample suction needle 17 can be located at the corresponding position of the sample pool, thereby separating the samples in the sample pool.

[0048] Among them, multiple sample pools are not fixed on the bottom plate 12. Specifically, there are the following reasons for the setting: First, since the bottom plate 12 is provided with moving parts such as the guide shaft 13 and the linear sleeve 14, when the linear sleeve 14 and a large number of related devices carried thereon move, the movement inertia is large, which may cause the bottom plate 12 to shake. If the sample pool is fixed on the bottom plate 12, the shaking of the bottom plate 12 will be transmitted to the sample pool, the erythrocyte sedimentation detection module 18 and its related pipelines, and may even cause resonance, thereby increasing the disturbance to the sample in the pipeline. The sample pool itself is not a moving part and may not be fixed on the bottom plate 12, and a vibration isolation device (such as a spring pad, etc.) is set between the bottom plate 12 and the partition 11, and between the partition 11 and the sample pool to prevent the moving parts from affecting the fixed parts. Second, when the sample holding pool is not fixed on the base plate 12, although the base plate 12 is provided with moving parts such as the guide shaft 13, the linear sleeve 14, the sample suction needle 17, the erythrocyte sedimentation rate detection module 18, the stepper motor 16, etc., the moving parts and the fixed parts (such as the sample holding pool, etc.) are arranged in a separated manner. Although there are many pipelines connected to the fixed parts such as the sample holding pool, when the moving module (that is, the entire base plate and the guide shaft 13, the linear sleeve 14, the sample suction needle 17, the erythrocyte sedimentation rate detection module 18, the stepper motor 16, etc.) arranged thereon fails due to a lot of movement and wear, it is only necessary to replace the entire moving module, and there is no need to plug and unplug a large number of related pipelines on the fixed parts, thereby greatly reducing the maintenance cost.

[0049] Optionally, in the vertical direction, multiple sample pools are located below the bottom plate 12, that is, the sample pools are not set on the bottom plate 12, which can prevent other devices inside the blood cell combined detection analyzer 1 from operating the samples in the sample pools, causing the bottom plate 12 to shake, thereby shaking the pipeline, increasing the disturbance of the samples in the pipeline, improving the stability of the blood cell combined detection analyzer 1, and improving the detection accuracy and efficiency of the erythrocyte sedimentation rate detection module 18 on the samples.

[0050] Optionally, each sample pool has a pool opening that opens upward. Specifically, since multiple sample pools are arranged below the bottom plate 12, that is, the sample suction needle 17 is located above the sample pool, each sample pool has a pool opening that opens upward. After the linear sleeve 14 drives the sample suction needle 17 to move into place, the sample suction needle 17 can move downward in the vertical direction to sample the sample pool through the pool opening that opens upward, thereby improving the sampling efficiency of the sample suction needle 17.

[0051] Optionally, a sample pool is disposed below at least two of the multiple positioning grooves 122. As described above, the position of the positioning groove 122 can be set corresponding to the position of the sample pool, and the sample pool is disposed below at least two of the multiple positioning grooves 122, thereby improving the movement accuracy of the linear sleeve 14 and improving the efficiency of the sample aspiration needle 17 in dividing the sample into the sample pool through the cooperation between the positioning groove 122 and the in-place optical coupling assembly.

[0052] Optionally, the number of positioning grooves 122 is greater than or equal to the number of sample pools. Inside the blood cell combined detection analyzer 1, there may be other devices that require the devices on the linear sleeve to participate in the operation, and corresponding positioning grooves 122 can also be set to ensure the accuracy of the linear sleeve 14 in this position. Therefore, this embodiment proposes that the number of positioning grooves 122 is greater than or equal to the number of sample pools to improve the accuracy of the linear sleeve 14 moving inside the blood cell combined detection analyzer 1.

[0053] Optionally, part of the edge of the positioning groove 122 is perpendicular to the bottom plate 12. As described above, after the linear sleeve 14 moves to the corresponding position, the light beam generated by the light emitting module will enter the photoelectric conversion module through the positioning groove 122, and respond to the linear sleeve 14 moving into position. This embodiment further proposes that part of the edge of the positioning groove 122 is perpendicular to the bottom plate 12, so that after the linear sleeve 14 moves into position, the light beam emitted by the light emitting module can be completely received by the photoelectric conversion module, responding to the linear sleeve 14 moving into position, thereby improving the accuracy of the optical coupling component's response to the linear sleeve 14 being in position.

[0054] In another embodiment, if part of the edge of the positioning groove 122 is not perpendicular to the base plate 12, for example, part of the edge of the positioning groove 122 is arc-shaped, then when the light beam generated by the light-emitting module passes through the positioning groove 122 and enters the photoelectric conversion module, part of the light beam may be blocked, and the photoelectric conversion module receives an incomplete light beam and may not be able to respond accurately, thereby reducing the movement accuracy of the linear sleeve 14.

[0055] Optionally, in the vertical direction, the central axis of the positioning groove 122 is aligned with the central axis of the corresponding sample pool mouth, and then after the linear sleeve 14 moves into place, the sample suction needle 17 can be basically located directly above the sample pool to ensure that the sample suction needle 17 is close to the sample pool and accurately injects the sample into the sample pool, thereby improving the sample separation efficiency of the sample suction needle 17.

[0056] Optionally, the width of the positioning groove 122 is smaller than the maximum pool opening width of the sample pool, where the pool opening width is the width of the pool opening of the sample pool in the moving direction of the linear sleeve 14. As described above, when the light-emitting module is not at the positioning groove, the emitted light beam is blocked (such as by an auxiliary strip or a curling edge that opens the positioning groove); when the light-emitting module is at the positioning groove, the emitted light beam is no longer blocked, and after the light beam emitted by the light-emitting module enters the photoelectric conversion module through the positioning groove 122, the linear sleeve 14 moves into position in response, and at this time, the linear sleeve 14 stops moving, and at the same time, the sample suction needle 17 can move in the vertical direction and perform sample separation on the sample pool. If the width of the positioning groove 122 is larger than the maximum width of the pool mouth of the sample pool, it may happen that when the linear sleeve 14 stops moving in response to moving into position, the projection of the sample suction needle 17 in the vertical direction cannot overlap with the projection of the pool mouth of the sample pool. In other words, the sample suction needle 17 is located outside the sample pool when moving in the vertical direction. Firstly, the sample cannot be injected into the sample pool, and there may be a risk of sample leakage. Secondly, it is impossible to avoid the sample suction needle 17 hitting the pool mouth and other positions due to the stepping motor losing steps when the sample suction needle 17 is lowered, resulting in damage to the sample suction needle 17.

[0057] Therefore, the present embodiment proposes that the width of the positioning groove 122 is smaller than the maximum pool opening width of the sample pool, and when the light beam emitted by the light emitting module enters the photoelectric conversion module, the sample suction needle 17 is located above the sample pool, thereby improving the efficiency of sample separation for the sample pool. During the alignment of the sample suction needle 17, if the groove width of the positioning groove 122 is small, smaller than the pool opening width of the sample pool, the sample suction needle 17 is more easily aligned with the central axis of the sample pool, and the sample can be more smoothly injected into the sample pool, thereby avoiding the possibility that the sample suction needle 17 will collide with the pool wall of the sample pool, thereby damaging the sample suction needle 17 or the sample pool.

[0058] Optionally, after the light beam emitted by the light-emitting module enters the photoelectric conversion module through the positioning groove 122, the linear sleeve 14 moves into place in response, and the sample suction needle 17 needs to move a specific number of steps to ensure that the lowering position of the sample suction needle 17 is not at the edge of the pool mouth, but near the center axis of the sample pool mouth. In this way, even if the sample suction needle 17 stirs below the liquid surface in the sample pool, it will not collide with the sample pool mouth, causing unexpected damage.

[0059] Optionally, when the sample suction needle 17 is lowered, the vertical projection point of the sample suction needle 17 does not need to be located on the same straight line perpendicular to the movement direction of the linear sleeve 14 as the vertical projection point of the central axis of the sample pool mouth. It is sufficient to ensure that the sample suction needle 17 and the in-place optical coupling assembly are both fixed on the linear sleeve 14 and their projection distance remains unchanged. Such a setting provides more design flexibility, and the layout of each module is more convenient and flexible.

[0060] Specifically, as described above, the positions of the plurality of positioning slots 122 are arranged to correspond to the positions of the sample pool, and the distance between the sample suction needle 17 and the in-place optical coupling assembly is fixed, so the positions of the sample pool and the sample suction needle 17, especially the position of the sample pool mouth, can still be located by the positions of the positioning slots 122, to ensure that the sample suction needle 17 can inject the sample into the sample pool. Optionally, the minimum distance between the plurality of positioning slots 122 is greater than 10 mm. By setting the distance between the positioning slots 122, time is reserved for starting and stopping the stepper motor that drives the linear sleeve 14 to move. If the distance between the positioning slots 122 is too small, the speed of the stepper motor may not reach the maximum speed or the steady movement speed during the process of the stepper motor driving the linear sleeve 14 to move through the belt 15, and the linear sleeve 14 immediately moves to the next positioning slot 122, so that the stepper motor needs to stop immediately, which will affect the operation of the stepper motor. At the same time, since the stepper motor starts and stops quickly in a short period of time, it is easy to cause the stepper motor to lose steps and other similar faults. In order to ensure the accuracy of the movement of the linear sleeve 14, the stepper motor needs to be corrected for lost steps, which will cause unexpected sharp and large shaking of the pipeline, increase the disturbance to the sample, and affect the accuracy of the sample detection by the erythrocyte sedimentation rate detection module 18.

[0061] Therefore, this embodiment proposes that the minimum distance between the plurality of positioning grooves 122 is greater than 10 mm to improve the movement accuracy of the linear sleeve 14 , while ensuring the stability of the movement of the linear sleeve 14 and improving the practicality of the blood cell combined detection analyzer 1 .

[0062] Optionally, the minimum groove width of the positioning groove 122 is greater than 6 mm, wherein the groove width of the positioning groove 122 may be the width of the positioning groove 122 in the moving direction of the linear sleeve 14 .

[0063] Similarly, the minimum slot width of the positioning slot 122 cannot be too small, and time is reserved for the start and stop of the stepper motor that drives the linear sleeve 14 to move. If the minimum slot width of the positioning slot 122 is too small, the speed of the stepper motor may not reach the maximum speed or the stable movement speed during the process of the stepper motor driving the linear sleeve 14 to move through the belt 15, and the linear sleeve 14 will then move to the next positioning slot 122, so that the stepper motor needs to stop immediately, which will affect the operation of the stepper motor. After the sample suction needle 17 injects the sample into the sample pool, it may be necessary to stir the reagent in the sample pool. Therefore, some space for stirring and moving needs to be reserved for the sample suction needle 17. Therefore, this embodiment proposes that the minimum slot width of the positioning slot 122 is greater than 6 mm, which not only ensures the smooth movement of the motor and avoids accidental loss of steps or even collisions, but also reserves space for stirring the sample suction needle 17, improves the safety of the sample suction needle 17, and improves the safety of the blood cell combined detection analyzer 1.

[0064] Alternatively, if Figure 3 As shown, the blood cell combined detection analyzer 1 also includes a hose 19 and a driving plunger pump 20. The driving plunger pump 20 can be a syringe or the like.

[0065] The sample suction needle 17 is a double-ended open cylinder, the upper end of which is connected to the first end of the hose 19, and the driving plunger pump 20 is connected to the second end of the hose 19. The driving plunger pump 20 can then apply force to the sample suction needle 17 through the hose 19, so that the sample suction needle 17 can suck the sample in the sample tube and / or distribute the sample in the hose 19 to multiple sample pools.

[0066] The inner diameter of the hose 19 is less than or equal to 2 mm.

[0067] Specifically, in actual applications, under the same circumstances, the shaking of a pipeline with a larger inner diameter will cause greater disturbance to the sample flowing through the pipeline than the shaking of a pipeline with a smaller inner diameter, and the disturbance caused to the sample flowing through the pipeline will be greater. Therefore, this embodiment limits the inner diameter of the hose 19, and limits the inner diameter of the hose 19 to be less than or equal to 2 mm, so as to reduce the shaking caused to the sample in the hose 19 when the hose 19 moves, reduce the disturbance to the sample, and improve the detection accuracy and efficiency of the sample by the erythrocyte sedimentation rate detection module 18.

[0068] The energy inside the pipe is mainly composed of three parts: basic energy, that is, the energy in the laminar state; disturbance energy, that is, the energy increased or decreased in the disturbance state relative to the laminar state; dissipated energy, that is, the energy lost due to the viscosity effect. We also found that the basic energy is mainly provided by the end pressure difference, the disturbance energy is mainly converted from the basic energy, and the dissipated energy is mainly converted from the disturbance energy. For the convenience of description, a dimensionless number "Reynolds number" is introduced in fluid mechanics to describe the flow of the pipeline.

[0069] For flow in a pipe, the Reynolds number Defined as: (1) Among them, ρ is the density of the fluid in the pipeline. U is the average flow velocity of the fluid in the pipeline, D is the inner diameter of the pipeline, μ is the viscosity of the fluid in the pipeline, ν is the dynamic viscosity of the fluid in the pipeline, Q is the flow rate of the fluid in the pipeline, and A is the cross-sectional area of ​​the pipeline.

[0070] It can be obtained from the above formula that, when other parameters remain unchanged, the size of the Reynolds number is positively correlated with the inner diameter of the pipeline. Therefore, in order to reduce the disturbance of the fluid in the pipeline and reduce the size of the Reynolds number, it is necessary to limit the inner diameter of the pipeline.

[0071] The Reynolds number can be expressed as the ratio of inertial force to viscous force in the fluid. When the Reynolds number is small, the influence of viscous force is greater than that of inertial force. The disturbance of the fluid in the pipeline will be attenuated by the viscous force. The fluid flow is stable and laminar. The fluid flows along the pipeline in a direction parallel to the extension of the pipeline. Because the fluid is very stable, it can be regarded as stacked layers without mutual interference between the layers. The velocity distribution of the fluid in the pipe is in the shape of a parabola, and the velocity distribution facing the section is a parabola, and the flow friction loss is small.

[0072] When the Reynolds number increases, both the basic energy and the disturbance energy will increase, while the dissipated energy will first increase and then decrease. When the Reynolds number reaches a critical value, the disturbance energy exceeds the dissipated energy, resulting in laminar instability. Because there is a transitional flow state between laminar flow and turbulent flow, in this interval, the flow velocity gradually increases, and the streamlines of the fluid begin to swing in a wave-like manner. The frequency and amplitude of the swing increase with the increase in flow velocity. Some small pressure disturbances will produce long-term and long-distance oscillations. Depending on the external conditions, the flow may be laminar or turbulent.

[0073] When the Reynolds number continues to increase, the disturbance energy is much greater than the dissipated energy, the influence of inertial force is greater than the viscous force, the fluid flow is relatively unstable, and a small change in flow velocity is easy to develop and enhance, forming a disordered and irregular turbulent flow field. At this time, the flow state of the fluid in the pipe is that the molecules collide violently with each other, the flow is not linear but vortex-shaped, the flow friction loss is large, the fluid disturbance in the pipeline is large, and turbulence is formed.

[0074] Generally, when the Reynolds number of a pipe flow is less than 2100, it is a laminar flow (also known as viscous flow or linear flow), when it is greater than 4000, it is a turbulent flow (also known as turbulent flow or disturbed flow), and when it is between 2100 and 4000, it is a transitional flow. Transitional flow mainly manifests itself in three forms: laminar flow; intermittent turbulence, that is, the flow presents local and short-term turbulent areas, but still maintains a laminar structure; and complete turbulence. The transition of transitional flow from laminar flow to intermittent turbulence and then to complete turbulence is a continuous and smooth process, and is closely related to the two unstable modes obtained from linear stability analysis.

[0075] Optionally, the length of the hose 19 is greater than 800 mm. Specifically, considering the horizontal movement distance of the sample aspirating needle 17 driven by the linear sleeve 14, and the vertical movement distance of the sample aspirating needle 17 close to the sample reservoir, the present embodiment limits the length of the hose 19 to be greater than 800 mm, so as to avoid pulling the hose 19 during the horizontal movement of the linear sleeve 14 or the vertical movement of the sample aspirating needle 17, thereby damaging the hose 19, or shaking the hose 19 during the pulling process, thereby increasing the disturbance of the sample in the hose 19, and improving the operating efficiency of the blood cell combined detection analyzer 1.

[0076] Optionally, the radial cross-sectional area of ​​the upper end of the double-ended open cylinder is larger than the radial cross-sectional area of ​​the lower end of the double-ended open cylinder, that is, the inner diameter of the upper end of the double-ended open cylinder is smaller than the inner diameter of the lower end of the double-ended open cylinder, wherein the lower end of the double-ended open cylinder is the end away from the hose 19. In addition, the smaller the inner diameter of the needle port (i.e., the lower end) of the double-ended open cylinder, the smaller the amount of liquid hanging at the needle port, and the better the consistency between machines.

[0077] When the Reynolds number increases, two unstable modes will appear in the laminar flow, one is the axial mode, that is, the disturbance propagates along the axial direction of the pipeline; the other is the circumferential mode, that is, the disturbance propagates along the circumferential direction of the pipeline. The critical Reynolds numbers, corresponding wavelengths and frequencies of the above two modes are different, and the end effect has different effects on the two modes: the axial mode is mainly affected by the ratio of the length to the diameter of the pipeline, so increasing the inner diameter of the tube is conducive to reducing the axial impact. Specifically, the lower end of the double-ended open cylinder can enter the sample tube to absorb the sample, and then transport the sample to the hose 19. Since the radial cross-sectional area of ​​the upper end of the double-ended open cylinder is larger than the radial cross-sectional area of ​​the lower end of the double-ended open cylinder, in the process of the sample flowing from the lower end of the double-ended open cylinder through the upper end of the double-ended open cylinder, due to the increase in the cross-sectional area of ​​the flow, the flow velocity of the sample in the double-ended open cylinder becomes smaller accordingly, and then the smaller the energy of the axial impact, the more effectively the disturbance of the sample transported in the sample suction needle 17 can be reduced.

[0078] Optionally, there are at least two fixed points on the hose 19, which fix the first sub-pipeline 191 of the hose 19 to the linear sleeve 14, and the extension direction of the first sub-pipeline 191 is parallel to the vertical direction. The erythrocyte sedimentation rate detection module 18 is used to detect the cell sedimentation parameters of the sample in the first sub-pipeline 191.

[0079] Specifically, the ESR detection module 18 can be mounted on the first sub-pipeline 191 to detect the sample in the first sub-pipeline 191, thereby preventing ambient light from entering the first sub-pipeline 191 and affecting the detection result of the ESR detection module 18, thereby improving the detection accuracy and efficiency of the ESR detection module 18.

[0080] Optionally, the sub-pipeline of the hose 19 from one end of the first sub-pipeline 191 close to the sample aspirating needle 17 to the connection between the sample aspirating needle 17 and the hose 19 is the second sub-pipeline 192. The length of the second sub-pipeline 192 is greater than or equal to 70 mm.

[0081] By limiting the length of the second sub-pipeline 192, it is convenient to replace the sample aspirating needle 17 multiple times. In the process of aspirating the sample in the sample tube, the sample aspirating needle 17 needs to penetrate the tube cap of the sample tube, so it is subject to greater impact and wear, and is a vulnerable part that needs to be replaced frequently. The sample aspirating needle 17 is often bonded to the second sub-pipeline 192 by glue, so the pipe end of the second sub-pipeline 192 must be destroyed when replacing it (generally, a section of the interface pipe that has been bonded at the end can be cut off).

[0082] In a practical application, when the blood cell combined detection analyzer 1 needs to replace the sample suction needle 17, the part of the second sub-pipeline 192 connected to the sample suction needle 17 is cut off, and then the end of the new end of the second sub-pipeline 192 is connected to the new sample suction needle 17. That is, in the process of multiple replacements of the sample suction needle 17 by the blood cell combined detection analyzer 1, the length of the second sub-pipeline 192 will gradually decrease. Therefore, this embodiment proposes that the length of the second sub-pipeline 192 is greater than or equal to 70 mm, ensuring that the length of the second sub-pipeline 192 is sufficient during the process of replacing the sample suction needle 17. The user does not need to replace the entire second sub-pipeline 192, that is, replace the entire hose 19 and the sample suction needle 17. The replacement cost is too high and the replacement is difficult. It is only necessary to cut off a section of the pipeline, which simplifies the operation of replacing the sample suction needle 17 and improves the user experience.

[0083] Since the second sub-pipeline 192 has a certain curvature and one end thereof needs to move with the vertical movement of the sample suction needle 17, it must have a certain basic tube length. Adding the additional tube length, the tube length of the second sub-pipeline 192 should be greater than or equal to 70 mm. The additional tube length is obtained by multiplying the number of possible replacements of the sample suction needle 17 within the maintenance period by the tube length of the end cut off each time, plus a certain margin.

[0084] Optionally, a sleeve is provided on the outer side of the second sub-pipeline 192 , wherein the sleeve may be a rubber sleeve or the like.

[0085] The sleeve protects the second sub-pipeline 192. When the sample aspiration needle 17 drives one end of the second sub-pipeline 192 to move in the vertical direction, the sleeve can isolate the second sub-pipeline 192 from other components in the blood cell combined detection analyzer 1 close to the second sub-pipeline 192, thereby preventing the second sub-pipeline 192 from being worn by other components, causing pipeline damage and leakage, and improving the safety of the second sub-pipeline 192. It can also reduce the vibration of the second sub-pipeline 192 during movement, reduce the disturbance of the sample in the second sub-pipeline 192, and ensure the accuracy of the erythrocyte sedimentation rate test.

[0086] Optionally, the length of the second sub-pipeline 192 is less than or equal to 400 mm. By setting the length of the second sub-pipeline 192, the movement of the end of the second sub-pipeline 192 connected to the first sub-pipeline 191 is appropriately reduced, thereby reducing the disturbance of the samples in the first sub-pipeline 191 and the second sub-pipeline 192 caused by the movement of the second sub-pipeline 192, reducing the movement of the movable end of the second sub-pipeline 192, and appropriately reducing the impact of sample suction due to the pipe resistance caused by the pipe length, thereby reducing the fluctuation of the sample and ensuring the accuracy of the erythrocyte sedimentation rate detection.

[0087] Among them, the first sub-pipeline 191 can be defined as a pipeline section that fixes part of the sub-pipeline of the hose 19 between the upper and lower fixed structures (such as a cable tie) on the linear sleeve 14, or a pipeline section on the hose 19 wrapped by the erythrocyte sedimentation rate detection module 18, that is, the length of the first sub-pipeline 191 here is the pipeline length of the first sub-pipeline 191 itself, or the length of the first sub-pipeline 191 can be understood as the distance between the upper and lower fixed structures (such as a cable tie) used to fix the first sub-pipeline 191 (the length of the pipeline section fixed by the upper and lower fixed structures), or the pipeline length of the first sub-pipeline 191 wrapped by the erythrocyte sedimentation rate detection module 18 to prevent stray light from entering, or the pipeline length of the first sub-pipeline 191 wrapped by the erythrocyte sedimentation rate detection module 18 to heat the wrapped pipeline.

[0088] Optionally, the sample undergoes at least one 180-degree turn when passing through the second sub-pipeline 192. The greater the curvature of the second sub-pipeline 192, the more curved the pipeline through which the sample flows, the greater the energy consumption due to the change in flow direction during the flow, and the smaller the energy used for axial impact, that is, the flow rate decreases, reducing the disturbance of the sample in the second sub-pipeline 192. Therefore, by setting the sample to undergo at least one 180-degree turn in the second sub-pipeline 192, the flow rate of the sample is reduced during the sample transmission process, thereby reducing the disturbance to the sample and ensuring the accuracy of the erythrocyte sedimentation rate test.

[0089] Optionally, the second sub-pipeline 192 has two types: an inverted U-shape and an S-shape (ie, two U-shapes combined together): The inverted U-shape means that the second sub-pipeline 192 is connected to the first sub-pipeline 191 from the upper end of the sample suction needle 17 in an inverted U shape, and in the vertical direction, the end of the first sub-pipeline 191 connected to the second sub-pipeline 192 is fixed above the end of the first sub-pipeline 191 away from the second sub-pipeline 192.

[0090] In the S-type, one end of the first sub-pipeline 191 connected to the second sub-pipeline 192 is fixed below the end of the first sub-pipeline 191 away from the second sub-pipeline 192. The second sub-pipeline 192 is connected to the first sub-pipeline 191 from the bottom in an S shape. Generally, the length of the S-shaped second sub-pipeline 192 is greater than the length of the inverted U-shaped second sub-pipeline 192.

[0091] Optionally, the sub-pipeline of the first sub-pipeline 191 away from one end of the sample suction needle 17 to the connection between the driving plunger pump 20 and the hose 19 is the third sub-pipeline 193, wherein the blood cell combined detection analyzer 1 also includes a tank chain 21, and the tank chain 21 is arranged on the outside of the third sub-pipeline 193.

[0092] When the linear sleeve 14 moves in the horizontal direction, the third sub-pipeline 193 will bend or straighten accordingly, and the tank chain 21 can wrap the third sub-pipeline 193 to protect the third sub-pipeline 193 when it bends, thereby avoiding wear between the third sub-pipeline 193 and other components, damaging the safety of the hose 19, and affecting the operating efficiency of other components, thereby improving the safety of the blood cell combined detection analyzer 1; at the same time, it can reduce the shaking of the third sub-pipeline 193 during bending or straightening, reduce the disturbance of the sample in the third sub-pipeline 193, and improve the detection accuracy and efficiency of the erythrocyte sedimentation rate detection module 18.

[0093] Optionally, the length of the third sub-pipeline 193 is greater than or equal to 500 mm. By limiting the length of the third sub-pipeline 193, the end effect at the third sub-pipeline 193 is reduced, the disturbance of the sample in the third sub-pipeline 193 is reduced, and the detection accuracy and efficiency of the sample by the erythrocyte sedimentation rate detection module 18 are improved.

[0094] Among them, because the universal laws of fluid mechanics fail at the mesoscopic scale: the mesoscopic scale is larger than the microscopic scale of a single molecule, but smaller than the macroscopic scale, where the universal laws apply. A typical example of a mesoscopic fluid is the blood flowing through blood vessels; the blood cells that make up this fluid are so large that they cannot be simply regarded as a collection of microscopic molecules, but should be considered as mesoscopic entities with complex behaviors. Establishing accurate mathematical models for such materials remains an ongoing challenge.

[0095] However, when the tube length and diameter are not set reasonably, the above-mentioned technical solution is very likely to fall into the transition flow state of Reynolds number Re=2100~4000. Combined with the complex behavior of blood cells in the mesoscopic state, this poses a great challenge to the accurate measurement in IVD equipment.

[0096] In order to obtain reasonable parameters for our above-mentioned technical solution, we borrowed the fluid mechanics model constructed in the paper Pomerenka O, Carrillo Segura S, Cao F, Wu J, Ristroph L. Hydrodynamics of finite-length pipes at intermediate Reynolds numbers[J]. Journal of Fluid Mechanics, 2023,959: A28. The organizational framework of the proposed model is obtained by dimensional analysis of the smooth circular pipe flow problem. The relevant physical parameters include pipe length L and inner diameter D, fluid density ρ and viscosity μ, average flow velocity U, and pressure difference Δp. These six quantities can be regarded as one dependent variable and five independent variables, such as .

[0097] By using the Buckingham Pi theorem and noting that there are three dimensions involved: mass, length, and time, the five independent dimensional quantities can be reduced to two dimensionless groups. The dependent variable can also be dimensionless, resulting in a total of three dimensionless groups, any of which can be viewed as a function of the others. Following common convention, the flow Reynolds number is chosen to be and pipe aspect ratio As independent variables, these variables determine the Darcy friction factor: (2) The latter is a dimensionless form of the pressure drop, where the applied gradient is affected by the inertial term associated with fully developed turbulence. Therefore, all pipe flow conditions can be represented by the function To express.

[0098] Corresponds to The classical limit of the domain can be explained by scaling the terms in the Navier–Stokes equations. The balance between the pressure drop gradient, inertial and viscous effects, each of which scales with the dimensional variables. The studied limit of pipe flow corresponds to this balance where the gradient dominates over one effect, with the other effects playing a negligible role.

[0099] For example, like a mosquito sucking blood through its proboscis, the first case is suitable for well-developed laminar flow, with a gradient To balance the viscous resistance , which yields the Hagen–Poiseuille law applicable to sufficiently slow flows through long, thin pipes, i.e., low Re and high α. In dimensionless form, it is , and does not depend on α. ​​In the second case, just as an elephant sucking water with its trunk may satisfy this turbulent attraction, the classical pipe flow turbulence corresponds to the applied gradient Transverse inertia gradient to the pipe axis This is suitable for fast flow and slender pipes, that is, high Re and high α. The dimensionless form is , and is independent of Re and α. The third case is like pursed lips for drinking water, and is related to Torricelli's law for flow through an orifice or a very short pipe, i.e. low α, in which case, Used to overcome the inertial gradient along the pipe axis The dimensionless form is , and is independent of Re. This can be roughly viewed as forming a very short pipe.

[0100] These laws provide a good fit to the data in the appropriate limits of Re and α, and the model is able to provide accurate predictions over the entire range of parameter values. and , all existing laws fail to apply, and the model is able to accurately calculate the fluid friction. Given the data presented in the paper and our practical implementation, the model can be considered to successfully provide a high level of accuracy in predicting the fluid dynamic losses in finite-length pipes at the critical Re number.

[0101] One of the main results of this work in this paper is that the three cases are structurally interesting on the unified model they constructed, with their boundary line adjacent in a triple point-like region. Moreover, the typical Re and α values ​​of our test results are also shown to be close to this adjacent region, and although the actual fluid state is different from the idealized pipe flow problem studied here, this practical situation can serve as an aid to the boundary between the studied hydraulic region and the "inapplicability region" where the traditional relations therefore do not apply. This background also inspired the authors to construct a general hydraulic model that is supported and verified by experimental measurement information and spans these adjacent regions, providing approximate pressure-flow relations for the critical cases.

[0102] This paper proposes such a model that aims to explain the fluid dynamics of pipes with different aspect ratios at different flow rates, especially pipes that are between classical flow regimes. The ultimate goal is to obtain a general function This paper adopts a mixed theoretical and empirical approach to unify and integrate many previous descriptions of smooth pipe hydraulics, especially the features of flow through orifices, flow in the inlet region, developing and fully developed laminar and turbulent regimes, and the transition from laminar to turbulent flow. In the model structure and parameter selection, the paper cites theory and observations as much as possible. In other aspects, for reasons of mathematical simplicity or convenience, the model takes the following general form: (3) in , and is a function that captures the individual contributions of inlet effect, laminar flow, and turbulence to the friction factor. This construction is motivated by the fact that inlet effect contributes in all conditions in all pipes and therefore space, while the laminar and turbulent effects are relatively independent and only apply within different ranges of Re.

[0103] here, and are selection functions that take the value 1 when Re goes deep into the laminar and turbulent regimes, respectively, and zero elsewhere. We use logistic functions for this purpose, which behave like smoothed Heaviside or step functions: (4) as well as (5) Here, Re∗ is the critical Reynolds number for the laminar to turbulent transition and δ can be interpreted as the width or range over which the Re transition occurs. The parameter value Re∗ = 2000 is consistent with literature on the transition in the presence of sufficiently strong perturbations. The choice of δ = 200 has been shown to match experimental data well.

[0104] This paper then defines the contributing friction terms starting from the entrance effect. The impact of the entrance effect on the transition flow is significant and complex: on the one hand, the entrance effect promotes the occurrence and development of the transition flow, making the transition flow more likely to appear and reach full turbulence faster; on the other hand, the entrance effect changes the spatial distribution and temporal evolution of the transition flow, making the transition flow present different shapes and frequencies. We also use energy analysis to explore the mechanism of transition flow in finite-length pipes, that is, the reason for the transition from laminar flow to turbulent flow. In the short pipe or orifice limit α→0, the acceleration effect dominates, and the applied pressure gradient is invested in the axial inertia gradient, that is, As described by Bernoulli's principle and Torricelli's law, water is generally an ideal inviscid fluid in the form of , or equivalently, The actual outflow velocity is slightly lower due to streamline contraction and viscous effects. These complexities determine the discharge coefficient CD ≤ 1 or the ratio of the actual to the ideal outflow velocity, whose value depends on Re and the geometric details of the orifice. We assume a constant CD = 0.85, so This parameter value is within the wide range of 0.6–1.0 reported in previous studies and was chosen to satisfactorily explain the low α fraction in the experimental dataset.

[0105] Contribution to laminar flow The consideration must include the developing flow far out in the pipe as well as the developing flow in the inlet region. For sufficiently low Re and high α, the developing laminar flow involves the applied pressure balancing the viscous stresses, The developing flow profile is parabolic and the hydraulics are described by the Hagen-Poiseuille law, namely: (6) This is equivalent to The cumulative pressure drop factor in the inlet region due to viscous and inertial effects is With the flow coordinate increases with the increase of Much longer than the hydrodynamic inlet length When , its value tends to a value of an order of magnitude. Associated with L and reconstructed in units of α, we obtain: (7) in ,for ,but .

[0106] We assume the exponential form of b and use the empirical formula , as the inlet length at which the flow profile approaches a developed parabolic profile within 99%, with k = 0.05. Therefore, the friction contribution due to developing and fully developed laminar flow is given by: (8) in is a simple choice that will be shown to be in good agreement with experimental data. Previous theoretical studies have suggested values ​​in the range 1.2–1.4, while experiments agree with slightly lower values ​​of 1–1.2.

[0107] Finally, consider the turbulence contribution applicable for sufficiently high Re. Fully developed turbulence for a long pipe or high α involves the applied pressure gradient being balanced with the inertial gradient across the pipe, corresponding to , which produces a uniform and constant Extensive characterization showed ,and It is more sensitive to changes in Re. or In the critical case, the influence of turbulent flow development has been shown to no longer be confined to a relatively short inlet region, whose length is relatively sensitive to Re. Since the increased pressure drop due to development and inlet effects occurs in the same region of the pipe and cannot be clearly distinguished, a simplifying assumption is made that the former does not lead to an additional contribution. Therefore, our turbulent state model only considers fully developed flows, which is consistent with the constant Related, for In the case of , the previously measured values ​​of 0.03~0.05 are representative. In summary, the complete model form is: (9) Especially for the critical value or , many existing laws do not apply, and the influence of turbulent flow development has been shown to no longer be limited to a relatively short inlet region, whose length It is relatively sensitive to Re, and the above model can accurately calculate fluid friction. Among them, the six parameters and their values ​​are = 0.85, Re∗ = 2000, δ = 200, b∞ = 1, k = 0.05 and =0.04. The upper limit of the inner diameter of the third sub-pipeline 193 is 2 mm. At present, the detection speed of the whole machine of the cell parameter joint analyzer is getting faster and faster, resulting in the flow velocity in the pipeline, especially the local flow velocity, which may exceed 20 m / s. Therefore, the Reynolds number of the fluid flow state in the pipeline has a high probability of falling into the critical interval. or , and then substitute other empirical parameters into the above formula, and multiply the calculated length of the third sub-pipeline 193 by a certain redundancy coefficient (selected as 3 based on experience), then the length of the third sub-pipeline 193 is 0.4931m. After rounding, the length of the third sub-pipeline 193 should be greater than or equal to 500mm.

[0108] Optionally, a sleeve is provided on the outer shell of the pipe section of the third sub-pipeline 193 wrapped by the tank chain 21, and the sleeve is used to isolate the tank chain 21 from the third sub-pipeline 193 to avoid wear between the third sub-pipeline 193 and the tank chain 21, further improving the safety of the third sub-pipeline 193, and reducing the disturbance of the liquid in the pipeline caused by the movement of the tank chain, thereby improving the detection accuracy and efficiency of the erythrocyte sedimentation rate detection module 18 on the sample.

[0109] Optionally, the vertical width of the tank chain 21 is less than or equal to 50 mm. The specific setting value can be set by the user according to the outer diameter of the third sub-pipeline 193, so that the tank chain 21 can better protect the third sub-pipeline 193 without affecting the movement of the pipeline or the tank chain 21. In the process of bending or straightening of the third sub-pipeline 193, the tank chain 21 moves with the third sub-pipeline 193 to provide protection for the third sub-pipeline 193, thereby improving the detection accuracy and efficiency of the erythrocyte sedimentation rate detection module 18 on the sample.

[0110] Optionally, the cross-sectional shape of the upper horizontal edge of the bottom plate 12 is L-shaped, so as to form a receiving groove at the upper horizontal edge of the bottom plate 12 to receive debris dropped during the movement of the tank chain 21, thereby preventing the debris generated by the tank chain 21 from falling into the sample pool and contaminating the sample pool, thereby improving the safety of the operation of the blood cell combined detection analyzer 1.

[0111] Similarly, optionally, the cross-sectional shape of the lower horizontal edge of the bottom plate 12 is U-shaped, wherein, as described above, both horizontal edges of the bottom plate 12 are provided with curled edges, and the curled edges of the lower horizontal edge of the bottom plate 12 can be U-shaped, so as to form a receiving groove at the lower horizontal edge of the bottom plate 12 to receive debris dropped during the movement of the tank chain 21, thereby preventing the debris generated by the tank chain 21 from falling into the sample pool and contaminating the sample pool, thereby improving the safety of the operation of the blood cell combined detection analyzer 1.

[0112] The cross-sectional shape of the lower horizontal edge of the base plate 12 is U-shaped. When the base plate and related moving components are removed, the sample pool below the base plate is generally not disassembled. Debris that falls into the U-shaped receiving groove generally will not easily fall into the sample pool. However, this is not the case with the L-shaped receiving groove. Debris near the edge of the lower horizontal edge is not blocked on one side, so the debris that falls in is still likely to fall into the sample pool during maintenance and disassembly, increasing the difficulty and cost of maintenance.

[0113] Optionally, the blood cell combined detection analyzer 1 also includes a control module (not shown), which is connected to the sample suction needle 17, the erythrocyte sedimentation rate detection module 18 and the linear sleeve 14. When the erythrocyte sedimentation rate detection module 18 detects the sample in the first sub-pipeline 191, the control module is used to control the sample suction needle 17 and the linear sleeve 14 to stop moving; and / or, the control module is used to control the time point when the erythrocyte sedimentation rate detection module 18 starts to detect the sample in the first sub-pipeline 191, and the difference between the time point when the sample suction needle 17 and the linear sleeve 14 stop moving is greater than 0.1 second.

[0114] Specifically, the control module can first control the sample suction needle 17 and the linear sleeve 14 to stop moving, and then control the erythrocyte sedimentation rate detection module 18 to detect the sample in the first sub-pipeline 191. Since the sample suction needle 17 and the linear sleeve 14 stop moving at this time, that is, the erythrocyte sedimentation rate detection module 18 and the first sub-pipeline 191 can remain still, thereby avoiding the movement of the sample suction needle 17 and the linear sleeve 14 from disturbing the sample in the first sub-pipeline 191, thereby improving the detection accuracy and efficiency of the erythrocyte sedimentation rate detection module 18 on the sample.

[0115] In another embodiment, the control module is also used to control the time point when the erythrocyte sedimentation rate detection module 18 starts to detect the sample in the first sub-pipeline 191, and the difference between the time point when the sample aspiration needle 17 and the linear sleeve 14 stop moving is greater than 0.1 second, wherein the above-mentioned time point is the time point when the sample aspiration needle 17, the linear sleeve 14 and the erythrocyte sedimentation rate detection module 18 receive the operation signal and start running.

[0116] Specifically, the above time point can be the time point when the control module sends an operation signal to the sample suction needle 17, the linear sleeve 14 and the erythrocyte sedimentation rate detection module 18, or the time point when the sample suction needle 17, the linear sleeve 14 and the erythrocyte sedimentation rate detection module 18 receive the operation signal.

[0117] It can be understood that in the blood cell combined detection analyzer 1, the distance between the control module and the sample suction needle 17, the linear sleeve 14 and the erythrocyte sedimentation rate detection module 18 is relatively close. Whether connected by wires or wirelessly, the time difference between the time point when the control module transmits a signal to the sample suction needle 17, the linear sleeve 14 and the erythrocyte sedimentation rate detection module 18 and the time point when the sample suction needle 17, the linear sleeve 14 and the erythrocyte sedimentation rate detection module 18 receive the signal can be ignored.

[0118] The control module first transmits a stop motion operation signal to the sample suction needle 17 and the linear sleeve 14 at a first moment. After the sample suction needle 17 and the linear sleeve 14 stop moving, the control module transmits a start detection operation signal to the erythrocyte sedimentation rate detection module 18 at a second moment, wherein the difference between the first moment and the second moment is greater than 0.1 seconds, to ensure that after the sample suction needle 17 and the linear sleeve 14 stop moving, the sample in the second sub-pipeline 192 has a certain amount of time to recover and stabilize, thereby improving the detection accuracy and efficiency of the sample by the erythrocyte sedimentation rate detection module 18.

[0119] In practical applications, different components have different response times to the signals sent by the control module, which are affected by factors such as the performance and service life of the components. Therefore, the embodiment of the present application proposes to determine the time point when the control module sends the signal to improve the accuracy of control.

[0120] In summary, the blood cell combined detection analyzer 1 provided by the present application includes a partition 11, a bottom plate 12, a guide shaft 13, a linear sleeve 14, a stepping motor, a belt 15, a sample suction needle 17, an erythrocyte sedimentation rate detection module 18 and a hose 19. By setting the structure of the bottom plate 12 and the structure of the hose 19, the disturbance of the sample during transportation is reduced, and the detection efficiency and accuracy of the erythrocyte sedimentation rate detection module 18 on the sample are improved.

[0121] The above description is only an implementation method of the present application, and does not limit the patent scope of the present application. Any equivalent structure or equivalent process transformation made using the contents of the present application specification and drawings, or directly or indirectly used in other related technical fields, are also included in the patent protection scope of the present application.

Claims

1. A blood cell combined detection analyzer, characterized in that: It includes a partition plate, a bottom plate, a guide shaft, a linear sleeve, a stepper motor, a belt, a sample suction needle and an erythrocyte sedimentation rate detection module; The partition is vertically fixed in the blood cell combined detection analyzer, the bottom plate is fixed on the partition, the guide shaft is fixed on the bottom plate, and the guide shaft extends in the horizontal direction; The linear sleeve is sleeved on the guide shaft, and the stepping motor is connected to the linear sleeve through the belt to drive the linear sleeve to slide horizontally along the guide shaft; The sample aspirating needle and the erythrocyte sedimentation rate detection module are arranged on the linear sleeve, and the linear sleeve drives the sample aspirating needle and the erythrocyte sedimentation rate detection module to move horizontally; Wherein, the length of the guide shaft is greater than 400 mm, and the sliding distance of the linear sleeve in the horizontal direction is greater than 360 mm; The extending direction of the sample aspirating needle and the extending direction of the erythrocyte sedimentation rate detection module are both parallel to the vertical direction, and the vertical distance between the sample aspirating needle and the erythrocyte sedimentation rate detection module is less than 60 mm.

2. The blood cell combined detection analyzer according to claim 1, characterized in that: The two horizontal edges of the bottom plate are provided with curling edges; and / or, at least one vertical edge of the bottom plate is provided with a rolled edge; and / or, the maximum horizontal length of the base plate is greater than or equal to 5 times the maximum vertical length of the base plate; The horizontal side of the bottom plate is the side of the bottom plate parallel to the horizontal direction, and the vertical side of the bottom plate is the side of the bottom plate parallel to the vertical direction.

3. The blood cell combined detection analyzer according to claim 1, characterized in that: The blood cell combined detection analyzer also includes an in-place optical coupling component, which is fixed on the linear sleeve, and includes a light emitting module and a photoelectric conversion module; Wherein, a plurality of positioning grooves are arranged on the bottom plate.

4. The blood cell combined detection analyzer according to claim 3, characterized in that: The blood cell combined detection analyzer comprises a plurality of sample holding pools, and the plurality of sample holding pools are arranged inside the blood cell combined detection analyzer along a horizontal direction; After the sample aspirating needle absorbs the sample, the linear sleeve moves on the guide shaft to drive the sample aspirating needle to move to the sample holding pool to distribute the sample; Wherein, the plurality of sample holding pools are not fixed on the bottom plate; And / or, in the vertical direction, the plurality of sample holding pools are located below the bottom plate; And / or, each of the sample holding pools has a pool opening opening upward; And / or, the sample holding pool is disposed below at least two of the plurality of positioning grooves; And / or, the number of the positioning grooves is greater than or equal to the number of the sample holding pools.

5. The blood cell combined detection analyzer according to claim 4, characterized in that: Part of the edge of the positioning groove is perpendicular to the bottom plate; And / or, in the vertical direction, the central axis of the positioning groove is aligned with the central axis of the corresponding pool opening of the sample holding pool; And / or, the width of the positioning groove is smaller than the maximum pool opening width of the sample holding pool; and / or, the minimum distance between the plurality of positioning grooves is greater than 10 mm; And / or, the minimum groove width of the plurality of positioning grooves is greater than 6 mm.

6. The blood cell combined detection analyzer according to claim 1, characterized in that: The blood cell combined detection analyzer also includes a driving plunger pump and a hose; The sample suction needle is a double-ended open cylinder, the upper end of which is connected to the first end of the hose, and the driving plunger pump is connected to the second end of the hose; The inner diameter of the hose is less than or equal to 2 mm; And / or, the length of the hose is greater than 800 mm; And / or, the radial cross-sectional area of ​​the upper end of the double-ended open cylinder is greater than the radial cross-sectional area of ​​the lower end of the double-ended open cylinder.

7. The blood cell combined detection analyzer according to claim 6, characterized in that: There are at least two fixing points on the hose, and the at least two fixing points fix the first sub-pipeline of the hose on the linear sleeve, and the extension direction of the first sub-pipeline is parallel to the vertical direction, and the erythrocyte sedimentation rate detection module is used to detect the cell sedimentation parameters of the sample in the first sub-pipeline; The sub-pipeline of the hose between one end of the first sub-pipeline close to the sample aspirating needle and the connection between the sample aspirating needle and the hose is the second sub-pipeline; The length of the second sub-pipeline is greater than or equal to 70 mm; And / or, a sleeve is provided on the outer side of the second sub-pipeline.

8. The blood cell combined detection analyzer according to claim 7, characterized in that: The length of the second sub-pipeline is less than or equal to 400 mm; And / or, the sample undergoes at least one 180-degree turn when passing through the second sub-pipeline.

9. The blood cell combined detection analyzer according to claim 7, characterized in that: The sub-pipeline of the hose between one end of the first sub-pipeline away from the sample aspirating needle and the connection between the driving plunger pump and the hose is the third sub-pipeline; Wherein, the blood cell combined detection analyzer further comprises a tank chain, and the tank chain is sleeved on the outside of the third sub-pipeline; The length of the third sub-pipeline is greater than or equal to 500 mm; And / or, a casing is provided outside the pipe section of the third sub-pipeline wrapped by the tank chain; And / or, the vertical width of the tank chain is less than or equal to 50 mm.

10. The blood cell combined detection analyzer according to claim 7, characterized in that: The blood cell combined detection analyzer also includes a control module, which is connected to the sample suction needle, the erythrocyte sedimentation rate detection module and the linear sleeve. When the erythrocyte sedimentation rate detection module detects the sample in the first sub-pipeline, the control module is used to control the sample aspiration needle and the linear sleeve to stop moving; And / or, the control module is further used to control the time point when the erythrocyte sedimentation rate detection module starts to detect the sample in the first sub-pipeline, and the time point when the sample aspiration needle and the linear sleeve stop moving is greater than 0.1 seconds.

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