Whole blood cell concentration control method and chip

Abstract

The invention discloses a whole blood cell concentration control method and a chip, and belongs to the field of cell analysis. Whole blood stock solution is injected into a flow channel of the whole blood cell concentration control chip; the first transducer continuously works in the flow channel to generate a standing wave, and cells in the whole blood stock solution move to a standing wave node and are focused to form a cell flow; the second energy converter intermittently works in the flow channel to generate at least two standing waves, cells in the cell flow move towards nodes of the at least two standing waves, the input pulse duty ratio of the second energy converter is # imgabs0 #, the cells at the node of one standing wave move to the first outflow groove, the remaining cells move to the second outflow groove, the width of the second outflow groove is larger than that of the first outflow groove, and the first outflow groove is communicated with the second outflow groove. Through the steps, the concentration of cells entering the detection area from the first outflow groove is reduced, no extra reagent or sheath fluid needs to be added, the cell suspension with the required concentration is provided under the condition that the original physiological environment where blood cells are located is maintained, and high-quality detection or analysis of follow-up in-vivo flow cytometry is facilitated.

Description

Technical Field

[0001] The present invention relates to the field of cell analysis, and particularly to a method for controlling the concentration of whole blood cells and a chip. Background Art

[0002] Flow cytometry is a fundamental and versatile tool for cell quantification, biochemical analysis, and cell sorting. Traditionally known as in vitro flow cytometry, it has been widely used in basic biomedical research and clinical practice. In this technique, target cells are obtained from patients or experimental animals, labeled with fluorescent tracers, and then introduced into a sheath fluid flow. Under the excitation of a laser beam in the flow, the emitted fluorescence is detected and analyzed to provide key physical and biochemical information. However, traditional flow cytometry is limited to in vitro analysis and requires blood extraction and processing, which alters the natural biological environment of blood cells. In addition, the limited blood sample volume in small animal models such as rats and rabbits can significantly affect their physiological state through multiple long-term blood draws. To address these limitations, in vivo flow cytometry has been proposed in recent years.

[0003] The basic principle of in vivo flow cytometry involves using plasma as the sheath fluid flow, eliminating the need for additional reagents. When cells flow through capillaries or drainage tubes and pass through a laser slit, exogenous or endogenous chemical contrast agents are excited to generate fluorescence signals that provide cell information. Compared with in vitro flow cytometry, in vivo flow cytometers can perform real-time, non-invasive, and dynamic monitoring of cells in their natural environment. Currently, due to technical limitations, in vivo flow cytometry is mainly used to detect blood in the capillaries of organs such as the ear and retina. However, the blood flow velocity in the capillaries of these organs is slow, and the cycle of completing systemic blood circulation is very long, making it difficult to complete a sufficient amount of blood detection in a short time. Directly drawing blood out of blood vessels through a drainage tube from a vein or artery and then forming a "single-cell" flow through methods such as ultrasonic focusing and inertial focusing for subsequent flow cytometry detection can achieve blood flow cytometry detection with statistical significance. However, this method also has some problems. For example, the number of cells per unit volume in whole blood is huge. During the cell focusing process, a "non-single-cell" flow with numerous cell aggregations will be formed. When flowing through the laser excitation beam, it is difficult to perform flow cytometry detection or analysis with single-cell resolution. In addition, whole blood contains a huge number of red blood cells, and these red blood cells will be completely mixed in the "single-cell" flow of white blood cells, which will also bring very large background noise to the flow cytometry detection and analysis of white blood cell subsets. Therefore, in order to drain whole blood cells in veins or arteries and perform high-throughput in vivo flow cytometry detection, it is urgent to solve the problem of numerous cell aggregations passing through the laser detection area during the process of forming a "single-cell" flow for in vivo detection of whole blood. Summary of the Invention

[0004] To overcome the deficiencies of the prior art, one of the objectives of the present invention is to provide a whole blood cell concentration control method that can reduce the concentration of non-detected cells in the detection area.

[0005] To overcome the deficiencies of the prior art, another objective of the present invention is to provide a whole blood cell concentration control chip that can reduce the concentration of non-detected cells in the detection area.

[0006] One of the objectives of the present invention is achieved by the following technical solution: A whole blood cell concentration control method, comprising the following steps: Injecting whole blood stock solution: passing the whole blood stock solution through the flow channel of the whole blood cell concentration control chip; Central focusing: a first transducer generates a standing wave in the flow channel, the first transducer works continuously, and the cells to be detected and non-detected cells in the whole blood stock solution move towards the standing wave nodes, focusing to form a cell stream; Cell offset: a second transducer works to generate at least two standing waves in the flow channel, the cells to be detected and non-detected cells in the cell stream move towards at least two standing wave nodes, the second transducer works intermittently, and the input pulse duty cycle of the second transducer , t w is greater than or equal to the time required for the cells to be detected to move to the node line position, T is the driving period of the second transducer; Proportional cell output: the cells to be detected and non-detected cells at at least one standing wave node move to the first outflow groove, and the cells to be detected and non-detected cells at the remaining standing wave nodes move to the second outflow groove, and the width of the second outflow groove is greater than the width of the first outflow groove.

[0007] Further, in the step of injecting the whole blood stock solution, the cross-section of the flow channel is rectangular, and the ratio of the width W to the depth D of the flow channel is greater than 1.

[0008] Further, W is 10 - 1000 microns, D is 5 - 500 microns, and the ratio of W to D is 2 - 4.

[0009] Further, in the step of proportional cell output, the ratio of the width of the first outflow groove to the width of the second outflow groove is 0.2 - 0.6.

[0010] Another objective of the present invention is achieved by the following technical solution: A whole blood cell concentration control chip is used to implement the above-mentioned whole blood cell concentration control method. The whole blood cell concentration control chip includes a main body, and a flow channel, a first outflow groove, and a second outflow groove are arranged in the main body. The first outflow groove and the second outflow groove are both communicated with the end of the flow channel. The width of the second outflow groove is greater than the width of the first outflow groove. The whole blood cell concentration control chip further includes a first transducer and a second transducer. The second transducer is located between the first transducer and the first outflow groove. The first transducer generates a standing wave in the flow channel to form a cell flow, and the second transducer generates at least two standing waves in the flow channel to offset the cells in the cell flow. The first outflow groove outputs some offset cells to reduce the cell concentration.

[0011] Further, the flow channel, the first outflow groove, and the second outflow groove form a Y structure.

[0012] Further, the ratio of the width of the first outflow groove to the width of the second outflow groove is 0.2 - 0.6.

[0013] Further, a bifurcation part is formed between the first outflow groove and the second outflow groove, and the end of the bifurcation part is arc-shaped.

[0014] Further, the cross-section of the flow channel is rectangular. The width W of the flow channel is 10 - 1000 microns, the depth D of the flow channel is 5 - 500 microns, and the ratio value of W to D is 2 - 4.

[0015] Further, the whole blood cell concentration control chip further includes a first interface, a second interface, and a third interface. The first interface, the second interface, and the third interface are all fixed on the main body. The first interface is communicated with one end of the flow channel far from the first outflow groove, the second interface is communicated with one end of the first outflow groove far from the flow channel, and the third interface is communicated with one end of the second outflow groove far from the flow channel.

[0016] Compared with the prior art, in the whole blood cell concentration control method of the present invention, the whole blood stock solution is injected into the flow channel of the whole blood cell concentration control chip; the first transducer generates a standing wave in the flow channel, and the first transducer works continuously. The cells to be detected and the non-detected cells in the whole blood stock solution move towards the standing wave nodes and are focused to form a cell flow; the second transducer works to generate at least two standing waves in the flow channel, and the cells to be detected and the non-detected cells in the cell flow move towards at least two standing wave nodes. The second transducer works intermittently, and the input pulse duty cycle of the second transducer , t w is greater than or equal to the time required for the cells to be detected to move to the node line position, Tis the driving period of the second transducer; the cells to be detected and the non-detected cells at at least one standing wave node move to the first outflow groove, and the cells to be detected and the non-detected cells at the remaining standing wave nodes move to the second outflow groove. The width of the second outflow groove is greater than that of the first outflow groove. Through the above steps, the cell concentration entering the detection area from the first outflow groove is reduced, without the need to add additional reagents or sheath fluid, and a cell suspension with the required concentration is provided while maintaining the original physiological environment of the blood cells, which is beneficial to the high-quality detection or analysis of subsequent in vivo flow cytometry. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] Figure 1 is a flowchart of the method for controlling the concentration of whole blood cells of the present invention; Figure 2 is a perspective view of the whole blood cell concentration control chip of the present invention; Figure 3 is Figure 2 a perspective view of the internal structure of the whole blood cell concentration control chip of Figure 4 is Figure 3 an enlarged view of part A of Figure 5 is Figure 2 a schematic diagram of the use state of the whole blood cell concentration control chip of Figure 6 is Figure 5 a partial schematic diagram of the use state of the whole blood cell concentration control chip of Figure 7 is a schematic diagram of the driving pulse of the second transducer.

[0018] In the figure: 10, main body; 11, upper cover; 12, bottom plate; 13, flow channel; 14, first outflow groove; 15, second outflow groove; 16, bifurcation part; 20, first interface; 30, second interface; 40, third interface; 50, first transducer; 60, second transducer. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0019] Next, the technical solutions in the embodiments of the present invention will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present invention.

[0020] It should be noted that when a component is referred to as "fixed to" another component, it can be directly on the other component or there may also be another intermediate component through which it is fixed. When a component is considered to be "connected to" another component, it can be directly connected to the other component or there may be another intermediate component at the same time. When a component is considered to be "disposed on" another component, it can be directly disposed on the other component or there may be another intermediate component at the same time. The terms "vertical", "horizontal", "left", "right" and similar expressions used in this article are only for the purpose of illustration.

[0021] Unless otherwise defined, all technical and scientific terms used in this article have the same meaning as commonly understood by those skilled in the technical field to which this invention belongs. The terms used in the description of this invention in this article are only for the purpose of describing specific embodiments and are not intended to limit this invention. The term "and / or" used in this article includes any and all combinations of one or more of the related listed items.

[0022] The method for controlling the concentration of whole blood cells in this invention is used to solve the problem that when performing in-vivo flow cytometry on whole blood stock solution, that is, using plasma as the sheath fluid flow and without adding other reagents additionally, numerous cells aggregate and pass through the laser detection area. The method for controlling the concentration of whole blood cells in this application can reduce the cell concentration in the laser detection area and can control the cell concentration in the laser detection area by controlling the input pulse duty ratio of the second transducer 60.

[0023] Please refer to Figure 1 , the method for controlling the concentration of whole blood cells in this invention includes the following steps: Inject whole blood stock solution: Inject the whole blood stock solution through the flow channel 13 of the whole blood cell concentration control chip; Central focusing: The first transducer 50 generates a standing wave in the flow channel 13. The first transducer 50 works continuously, and the cells to be detected and non-detected cells in the whole blood stock solution move towards the standing wave nodes, and a cell stream is formed by focusing. Cell offset: The second transducer 60 works to generate at least two standing waves in the flow channel 13. The cells to be detected and non-detected cells in the cell stream move towards at least two standing wave nodes. The second transducer 60 works intermittently, and the input pulse duty ratio of the second transducer 60 , is greater than or equal to the time required for the cells to be detected to move to the node position. T is the driving period of the second transducer 60; Proportionate output of cells: The cells to be detected and non-detected cells at at least one standing wave node move to the first outflow groove 14, and the cells to be detected and non-detected cells at the remaining standing wave nodes move to the second outflow groove 15. The width of the second outflow groove 15 is greater than the width of the first outflow groove 14.

[0024] In the step of injecting the whole blood stock solution, plasma is used as the sheath fluid flow in the whole blood stock solution, and no additional reagents need to be added, which is convenient for re-injecting back into the body after subsequent blood tests. The flow channel 13 is linear, the cross-section of the flow channel 13 is rectangular, and the ratio of the width W to the depth D of the flow channel 13 is greater than 1. Preferably, W is 10 - 1000 microns, D is 5 - 500 microns, and the ratio of W to D is 2 - 4.

[0025] Please continue to refer to Figure 5 、 Figure 6 , in the central focusing step, the standing wave nodes generated by the first transducer 50 in the flow channel 13 are located on the center line of the flow channel 13, and the cells in the whole blood stock solution aggregate on the center line of the flow channel 13. The first transducer 50 continuously works, so that when the whole blood stock solution moves along the flow channel 13, both the cells to be detected and the non-detected cells are focused on the nodes.

[0026] Please continue to refer to 6 and Figure 7 , in the cell offset step, the two standing wave nodes generated by the second transducer 60 are parallel to each other and symmetric about the center line of the flow channel 13. In this embodiment, the cells to be detected are white blood cells, and the non-detected cells are red blood cells. When the second transducer 60 works, since the particle size of red blood cells is smaller than that of white blood cells, the moving speed of red blood cells is lower than that of white blood cells. Therefore, when the input pulse duty ratio of the second transducer 60 is, the white blood cells have moved from the center line to the two standing wave nodes generated by the second transducer 60, but the red blood cells are still in the moving process. Therefore, on the premise that the second outflow groove 15 diverts part of the red blood cells and white blood cells, the proportion of red blood cells entering the first outflow groove 14 can also be reduced, and the proportion of white blood cells is increased. Therefore, by controlling , the number of cells flowing into the first outflow groove 14 can be quantitatively allocated.

[0027] In the step of outputting cells in a fixed proportion, the ratio of the width of the first outflow groove 14 to the width of the second outflow groove 15 is 0.2 - 0.6. A bifurcation part 16 is formed between the first outflow groove 14 and the second outflow groove 15, and the end of the bifurcation part 16 is arc-shaped to avoid interfering with the cell flow direction. By controlling the ratio of the width of the first outflow groove 14 to the width of the second outflow groove 15, the number of cells flowing into the first outflow groove 14 can be further controlled. The cells flowing out of the first outflow groove 14 include the cells to be detected and the non-detected cells, that is, white blood cells and red blood cells in this embodiment, but the number of cells to be detected and non-detected cells in the first outflow groove 14 is reduced, which is equivalent to reducing the cell concentration in the plasma and increasing the proportion of cells to be detected.

[0028] Please continue to refer to Figures 2 to 4 , this application also discloses a whole blood cell concentration control chip for implementing the above whole blood cell concentration control method.

[0029] The whole blood cell concentration control chip includes a main body 10, a first interface 20, a second interface 30, a third interface 40, a first transducer 50, and a second transducer 60.

[0030] The main body 10 includes an upper cover 11 and a bottom plate 12. The upper cover 11 is fixedly connected to the bottom plate 12, and a flow channel 13, a first outflow groove 14, and a second outflow groove 15 are formed between the upper cover 11 and the bottom plate 12. Specifically, the upper cover 11 and the bottom plate 12 are connected by curing glue or molecular bonding. The upper cover 11 and the bottom plate 12 are made of acoustic matching materials such as glass or silicon-based materials. The upper cover 11 is provided with an input hole, a first output hole, and a second output hole. The input hole is communicated with one end of the flow channel 13. The input hole is used for inputting the whole blood stock solution and for installing the first interface 20. The first output hole is communicated with the end of the first outflow groove 14. The first output hole is used for outputting the proportionally quantified cell count and for installing the second interface 30. The second output hole is communicated with the end of the second outflow groove 15. The second output hole is used for outputting non-controlled cell counts and for installing the third interface 40.

[0031] The bottom plate 12 is provided with grooves for forming the flow channel 13, the first outflow groove 14, and the second outflow groove 15. The flow channel 13, the first outflow groove 14, and the second outflow groove 15 are all linear, and the flow channel 13, the first outflow groove 14, and the second outflow groove 15 form a Y-shaped structure. The cross-section of the flow channel 13 is rectangular, the groove width W of the flow channel 13 is 10 - 1000 microns, the groove depth D is 5 - 500 microns, and the ratio value of the groove width W to the groove depth D is greater than 1, preferably 2 - 4.

[0032] Both the first outflow groove 14 and the second outflow groove 15 are communicated with the end of the flow channel 13, and the width of the first outflow groove 14 is smaller than the width of the second outflow groove 15. Specifically, the first outflow groove 14 and the second outflow groove 15 are of an asymmetric structure, and the ratio value of the width W1 of the first outflow groove 14 to the width W2 of the second outflow groove 15 is less than 1, preferably 0.2 - 0.6. A bifurcation part 16 is formed between the first outflow groove 14 and the second outflow groove 15, and the end of the bifurcation part 16 is in an arc shape to avoid interfering with the cell flow direction.

[0033] The joints of the first interface 20, the second interface 30, and the third interface 40 are all made of stainless steel, titanium alloy, or other engineering plastic materials with good biocompatibility.

[0034] The first transducer 50 is disposed on the flow channel 13 near the first interface 20. The first transducer 50 forms a standing wave, and the nodes of the standing wave form a straight line located in the flow channel 13, which is used to aggregate the cells in whole blood. Under the action of the ultrasonic wave of the first transducer 50, the blood cells in the whole blood will move towards the nodes of the standing wave, that is, an effect of aggregating towards the center of the flow channel 13 is formed. The first transducer 50 continuously operates, resulting in the continuous aggregation of cells towards the standing wave node line.

[0035] The second transducer 60 is disposed on the flow channel 13 near the outflow groove. The second transducer 60 forms at least two standing waves, and the nodes of the at least two standing waves form at least two parallel lines. The multiple parallel lines are symmetric about the center line of the flow channel 13 and are used for cell offset. The second transducer 60 is under the action of a pulse driven by a control signal. By controlling the duty cycle of the input pulse of the second transducer 60 , that is , to quantitatively allocate the number of cells flowing into the first outflow groove 14. Among them, T is the driving period acting on the second transducer 60. t w is the pulse duration for generating acoustic wave action during the entire driving period, and t w is not less than the duration required for white blood cells to move to the node line position. In this embodiment, white blood cells are the targets to be detected, and red blood cells are non-detected cells. When the second transducer 60 operates, since the particle size of red blood cells is smaller than that of white blood cells, the moving speed of red blood cells is lower than that of white blood cells. Therefore, when the duty cycle of the input pulse of the second transducer 60 , the white blood cells have moved from the center line to the nodes of the two standing waves generated by the second transducer 60, but the red blood cells are still in the moving process. Therefore, on the premise that part of the red blood cells and white blood cells are shunted in the second outflow groove 15, the proportion of red blood cells entering the first outflow groove 14 can also be reduced, and the proportion of white blood cells can be increased. Therefore, by controlling , the number of cells flowing into the first outflow groove 14 can be quantitatively allocated.

[0036] When using the whole blood cell concentration control chip, the central controller is used for the focusing and allocation enabling control of the signal generator, and respectively sends the driving frequency and driving voltage setting values of the first transducer 50 and the second transducer 60 to the signal generator 1 and the signal generator 2; after receiving the focusing enabling, the signal generator 1 and the signal generator 2 respectively output continuous signals with corresponding frequencies and voltages to the power amplifier board 1 and pulse signals with corresponding frequencies and voltages to the power amplifier board 2 according to the input driving frequency and driving voltage setting values; the power amplifier board 1 and the power amplifier board 2 respectively amplify the input pulse signals and respectively drive the first transducer 50 and the second transducer 60. The first transducer 50 and the second transducer 60 generate ultrasonic standing waves under the driving voltage and respectively perform linear focusing on the whole blood cells and control a specific number of blood cells to flow to the first outflow groove 14 in a fixed proportion.

[0037] Compared with the prior art, the whole blood cell concentration control method of the present invention passes the whole blood stock solution through the flow channel 13 of the whole blood cell concentration control chip; the first transducer 50 generates a standing wave in the flow channel 13, and the first transducer 50 works continuously. The cells to be detected and the non-detected cells in the whole blood stock solution move towards the standing wave nodes, and a cell stream is formed by focusing; the second transducer 60 works in the flow channel 13 to generate at least two standing waves, and the cells to be detected and the non-detected cells in the cell stream move towards at least two standing wave nodes. The second transducer 60 works intermittently. The cells to be detected and the non-detected cells at at least one standing wave node move to the first outflow groove 14, and the cells to be detected and the non-detected cells at the remaining standing wave nodes move to the second outflow groove 15. The width of the second outflow groove 15 is greater than the width of the first outflow groove 14. Through the above steps, the cell concentration entering the detection area from the first outflow groove 14 is reduced, without the need to add additional reagents or sheath fluid, and a cell suspension with the required concentration is provided while maintaining the original physiological environment of the blood cells, which is beneficial to high-quality detection or analysis of subsequent in vivo flow cytometry.

[0038] The above embodiments only express several implementation manners of the present invention, and the description thereof is relatively specific and detailed, but it should not be construed as a limitation on the scope of the invention patent. It should be noted that for those of ordinary skill in the art, without departing from the concept of the present invention, several deformations and improvements can be made. These are all equivalent modifications and evolutions made to the above embodiments based on the substantial technology of the present invention, and all of these belong to the protection scope of the present invention.

Claims

1. A method for controlling whole blood cell concentration, characterized in that: The following steps are involved: Injecting whole blood stock solution: injecting the whole blood stock solution through the flow channel of the whole blood cell concentration control chip; Center focusing: The first transducer generates a standing wave in the flow channel. The first transducer works continuously, and the cells to be detected and the non-detected cells in the whole blood stock solution move to the standing wave node and focus to form a cell flow; Cell deviation: The second transducer generates at least two standing waves in the flow channel, and the cells to be detected and the non-detected cells in the cell flow move to at least two standing wave nodes. The second transducer works intermittently, and the input pulse duty cycle of the second transducer is , t w Greater than or equal to the time required for the cell to be detected to move to the node line position, T is the driving period of the second transducer. Since the particle sizes of the cells to be detected and the non-detected cells are different, the cells to be detected are moved to at least two standing wave nodes through the intermittent operation of the second transducer. The non-detected cells have not yet moved to the standing wave nodes during the movement process. Cell proportional output: the cells to be detected at at least one standing wave node and the non-detection cells near the standing wave node move to the first outflow slot, the concentration of the cells to be detected and the non-detection cells flowing out of the first outflow slot is lower than the cell concentration of the whole blood stock solution, the cells to be detected and the non-detection cells flowing out of the first outflow slot are used for subsequent detection, and the cells to be detected at the remaining standing wave nodes and the non-detection cells near the remaining standing wave nodes move to the second outflow slot, and the width of the second outflow slot is greater than the width of the first outflow slot.

2. The whole blood cell concentration control method according to claim 1, characterized in that: In the step of injecting the whole blood stock solution, the cross-section of the flow channel is rectangular, and the ratio of the flow channel width W to the flow channel depth D is greater than 1.

3. The whole blood cell concentration control method according to claim 2, characterized in that: W is 10 ~ 1000 microns, D is 5 ~ 500 microns, and the ratio of W to D is 2-4.

4. The whole blood cell concentration control method according to claim 2, characterized in that: In the cell proportional output step, the ratio of the width of the first outflow channel to the width of the second outflow channel is 0.2-0.

6.

5. A whole blood cell concentration control chip, used for implementing the whole blood cell concentration control method according to claim 1, the whole blood cell concentration control chip comprising a main body, a flow channel is provided in the main body, and is characterized in that: The main body is also provided with a first outflow groove and a second outflow groove, both of which are connected to the end of the flow channel, the width of the second outflow groove is greater than the width of the first outflow groove, the whole blood cell concentration control chip also includes a first transducer and a second transducer, the second transducer is located between the first transducer and the first outflow groove, the first transducer generates a standing wave in the flow channel to form a cell flow, the second transducer generates at least two standing waves in the flow channel to deviate the cells of the cell flow, and the first outflow groove outputs the partially deviated cells to reduce the cell concentration.

6. The whole blood cell concentration control chip according to claim 5, characterized in that: The flow channel, the first outflow groove, and the second outflow groove form a Y structure.

7. The whole blood cell concentration control chip according to claim 5, characterized in that: The ratio of the width of the first outflow groove to the width of the second outflow groove is 0.2-0.

6.

8. The whole blood cell concentration control chip according to claim 5, characterized in that: A fork portion is formed between the first outflow groove and the second outflow groove, and an end portion of the fork portion is in an arc shape.

9. The whole blood cell concentration control chip according to claim 5, characterized in that: The cross section of the flow channel is rectangular, the flow channel width W is 10 to 1000 microns, the flow channel depth D is 5 to 500 microns, and the ratio of W to D is 2-4.

10. The whole blood cell concentration control chip according to claim 5, characterized in that: The whole blood cell concentration control chip also includes a first interface, a second interface and a third interface, wherein the first interface, the second interface and the third interface are all fixed to the main body, the first interface is connected to an end of the flow channel away from the first outflow slot, the second interface is connected to an end of the first outflow slot away from the flow channel, and the third interface is connected to an end of the second outflow slot away from the flow channel.

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