A finger-driven microfluidic chip

Abstract

This invention discloses a finger-driven microfluidic chip, belonging to the field of microfluidic chips. The volume of the first air bladder is different from that of the second air bladder. A check valve is disposed between the sample chamber and the second air bladder and / or the first air bladder. When one of the first air bladder and the second air bladder is pressed, the sample in the sample chamber flows between the sample chamber and the mixer, causing the sample to fuse with the pre-filled solid or liquid reagent in the first reagent chamber and enter the mixer for preliminary mixing. When the other of the first air bladder and the second air bladder is pressed, the sample in the sample chamber flows between the sample chamber and the second reagent chamber, causing the pre-mixed liquid to fuse with the pre-filled solid or liquid reagent in the second reagent chamber and be mixed in the mixer. Through the design of the first and second air bladders, the deformation volume can be precisely controlled individually each time, thereby controlling the flow of liquid. It adopts a finger-pressing method, eliminating the need for pump drive and simplifying operation. The check valve prevents liquid backflow.

Description

Technical Field

[0001] This invention relates to the field of microfluidic chips, and in particular to finger-driven microfluidic chips. Background Technology

[0002] Coagulation function testing plays a crucial role in clinical diagnosis, serving to screen for and monitor thrombotic diseases, hemorrhagic diseases, and the effectiveness of anticoagulant therapy. Traditional coagulation testing methods typically rely on large automated instruments and specialized operators, which have limitations such as large blood volumes, complex procedures, and long processing times, making them unsuitable for scenarios like primary healthcare institutions, emergency rooms, or home health monitoring. In recent years, microfluidic technology, with its advantages of high automation, easy integration, and rapid response, has demonstrated broad application potential in the field of coagulation testing.

[0003] However, existing microfluidic coagulation detection systems still have significant shortcomings: on the one hand, they typically rely on external pumps, valves, and tubing to drive and control the fluid, resulting in complex system structures, high costs, and poor portability; on the other hand, the fluids in microfluidic chips are mostly in a laminar flow state, leading to low mixing efficiency and often requiring external power devices to improve mixing performance, further increasing the complexity and operational difficulty of the equipment. Furthermore, the numerous external connection interfaces and tubing also result in a large dead volume, increasing sample requirements. These shortcomings limit their use in resource-constrained scenarios. Therefore, how to achieve pump-free, simple-to-operate, low-blood-volume, and low-cost blood sample pretreatment is an urgent problem to be solved.

[0004] Currently, press-type microfluidic chips have appeared on the market, but the flow of liquid in different cavities is not easy to control when pressed, and backflow of liquid is prone to occur. Summary of the Invention

[0005] In order to overcome the shortcomings of the prior art, one of the objectives of this invention is to provide a finger-driven microfluidic chip that does not require pump drive, has controllable liquid flow, does not backflow, and is easy to operate.

[0006] One of the objectives of this invention is achieved through the following technical solution:

[0007] A finger-driven microfluidic chip includes a main body. The main body has a sample chamber, a first reagent chamber, and a second reagent chamber. The finger-driven microfluidic chip also includes a first air bladder, a second air bladder, a check valve, and a mixer. The first air bladder and the second air bladder are in communication, and the volumes of the first air bladder and the second air bladder are different. The surface of the main body has a first pressing part and a second pressing part. The position of the first pressing part corresponds to the position of the first air bladder, and the position of the second pressing part corresponds to the position of the second air bladder. The check valve is disposed between the sample chamber and the second air bladder and / or the first air bladder. The sample chamber, the first reagent chamber, the mixer, and the second reagent chamber are all connected. The reagent chambers are connected in sequence. When one of the first airbags is pressed by the first pressing part and the other of the second airbags is pressed by the second pressing part, the sample in the sample chamber flows between the sample chamber and the mixer, causing the sample to fuse with the pre-filled solid or liquid reagent in the first reagent chamber and enter the mixer for preliminary mixing. When the other of the second airbags is pressed by the first pressing part and the other of the second pressing part is pressed by the second pressing part, the sample in the sample chamber flows between the sample chamber and the second reagent chamber, causing the pre-mixed liquid to fuse with the pre-filled solid or liquid reagent in the second reagent chamber and be mixed in the mixer.

[0008] Furthermore, the deformable volume of the first airbag is the sum of the volume of the first reagent chamber, the volume of the mixer, and the volume of the flow channel connecting the sample chamber, the first reagent chamber, and the mixer.

[0009] Furthermore, the main body is provided with a first groove and a first blocking post, the first blocking post is located in the first groove, the first pressing part is the outer wall of the first groove, and the first groove and the first blocking post together form the first airbag.

[0010] Furthermore, the deformable volume of the second airbag is the sum of the volume of the first reagent chamber, the volume of the mixer, the volume of the second reagent chamber, and the volume of the flow channel connecting the sample chamber, the first reagent chamber, the mixer, and the second reagent chamber.

[0011] Furthermore, the main body is also provided with an outflow channel, which is connected to the second reagent chamber. The end of the outflow channel forms an outlet. The sum of the deformation volume of the first airbag and the deformation volume of the second airbag is greater than the volume from the end of the first reagent chamber to the end of the outflow channel, so that when the first airbag and the second airbag are pressed at the same time, the mixture flows out from the outlet.

[0012] Furthermore, the mixer includes multiple expansion channels and multiple contraction channels, wherein the width of the expansion channels is greater than the width of the contraction channels, and the expansion channels and contraction channels are arranged at an angle and connected to each other.

[0013] Furthermore, the width of the expansion channel is 0.6-0.8 mm, and the width of the contraction channel is 0.2-0.4 mm.

[0014] Furthermore, the multiple expansion channels and the multiple contraction channels are alternately arranged in a zigzag shape.

[0015] Furthermore, the mixer has an S-shaped structure.

[0016] Furthermore, the main body includes a cover plate and a base plate fixedly connected to the cover plate, and the sample chamber, the first reagent chamber, the second reagent chamber, the first airbag, the second airbag, the check valve, and the mixer are disposed between the cover plate and the base plate.

[0017] Compared to existing technologies, the finger-driven microfluidic chip of this invention comprises a first airbag, a second airbag, a check valve, and a mixer. The first and second airbags are connected, and their volumes differ. The main body surface is provided with a first pressing part and a second pressing part, the position of which corresponds to the first airbag and the position of which corresponds to the second airbag. The check valve is located between the sample chamber and the second airbag and / or the first airbag. The sample chamber, the first reagent chamber, the mixer, and the second reagent chamber are sequentially connected. When the first airbag is pressed by the first pressing part and the second airbag is pressed by the second pressing part, the sample in the sample chamber... The sample flows between the sample chamber and the mixer, allowing the sample to mix with the pre-filled solid or liquid reagent in the first reagent chamber and enter the mixer for initial mixing. When the first airbag is pressed by the first pressing part and the other airbag is pressed by the second pressing part, the sample in the sample chamber flows between the sample chamber and the second reagent chamber, allowing the initially mixed liquid to mix with the pre-filled solid or liquid reagent in the second reagent chamber and be mixed in the mixer. Through the design of the first and second airbags, the deformation volume of each time can be precisely controlled, thereby controlling the flow of liquid. It adopts a finger pressing method, which does not require pump drive and is simple to operate. A check valve is set to prevent liquid backflow. Attached Figure Description

[0018] Figure 1 This is a perspective view of the finger-driven microfluidic chip of the present invention;

[0019] Figure 2 for Figure 1 An exploded view of a finger-driven microfluidic chip;

[0020] Figure 3 for Figure 1 A three-dimensional view of the cover plate of the finger-driven microfluidic chip;

[0021] Figure 4 for Figure 1 A three-dimensional cross-sectional view of a finger-driven microfluidic chip;

[0022] Figure 5 for Figure 4 A schematic diagram of the pressing state of the first air bladder of the finger-driven microfluidic chip;

[0023] Figure 6 for Figure 4 A schematic diagram of the structure of the mixer of the finger-driven microfluidic chip;

[0024] Figure 7 for Figure 6 A diagram showing the mixing process of the mixer;

[0025] Figure 8 for Figure 7 A schematic diagram illustrating the mixing efficiency of the mixer;

[0026] Figure 9 To compare the results of coagulation tests on blood processed and unprocessed by a finger-driven microfluidic chip.

[0027] In the diagram: 10. Main body; 11. Cover plate; 110. First pressing part; 111. Second pressing part; 112. Sample dispensing hole; 113. First groove; 114. Gas groove; 115. Second groove; 116. Valve chamber; 117. Sample tank; 118. Liquid tank; 119. First reagent tank; 120. Mixing tank; 121. Second reagent tank; 122. Outflow tank; 12. Base plate; 1200. Plate body ; 1201, First blocking column; 1202, Second blocking column; 1203, Valve column; 20, Plug; 30, First airbag; 40, Second airbag; 50, Airway; 60, Check valve; 70, Sample chamber; 80, Flow channel; 90, First reagent chamber; 100, Mixer; 101, Expansion channel; 102, Contraction channel; 210, Second reagent chamber; 220, Outflow channel; 230, Outlet. Detailed Implementation

[0028] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0029] It should be noted that when a component is said to be "fixed to" another component, it can be directly on the other component or it can be fixed through another intermediate component. When a component is said to be "connected to" another component, it can be directly connected to the other component or it may be fixed through another intermediate component. When a component is said to be "set on" another component, it can be set directly on the other component or it may be set through another intermediate component. The terms "vertical," "horizontal," "left," "right," and similar expressions used in this document are for illustrative purposes only.

[0030] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used herein in the description of the invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0031] Please see Figures 1 to 4 This application discloses a finger-driven microfluidic chip, which includes a main body 10 and a plug 20 installed on the main body 10. The main body 10 is provided with a first airbag 30, a second airbag 40, an airway 50, a check valve 60, a sample chamber 70, a flow channel 80, a first reagent chamber 90, a mixer 100, a second reagent chamber 210, and an outflow channel 220.

[0032] The main body 10 has a double-layer structure. Specifically, the main body 10 includes a cover plate 11 and a base plate 12 fixedly connected to the cover plate 11. The cover plate 11 and the base plate 12 are made of any one of PDMS (polydimethylsiloxane), ABS (acrylonitrile butadiene styrene), silicone rubber, PE (polyethylene), PU (polyurethane), PS (polystyrene), PP (polypropylene), and PC (polycarbonate). They are manufactured by demolding on a negative mold and are fixed together by a bonding process.

[0033] Grooves are provided on the cover plate 11 and / or the base plate 12. After the cover plate 11 and the base plate 12 are mated, a first airbag 30, a second airbag 40, an air passage 50, a check valve 60, a sample chamber 70, a flow channel 80, a first reagent chamber 90, a mixer 100, a second reagent chamber 210, and an outflow channel 220 are formed. In this embodiment, the grooves are provided on the cover plate 11. Specifically, the upper surface of the cover plate 11 is provided with a first pressing part 110, a second pressing part 111, and a sample dispensing hole 112. The first pressing part 110 and the second pressing part 111 are elastic bodies that can deform after being pressed. The sample dispensing hole 112 communicates with the sample groove 117 and is used for sample dispensing.

[0034] The lower surface of the cover plate 11 is provided with a first groove 113, an air groove 114, a second groove 115, a valve chamber 116, a sample chamber 117, a liquid chamber 118, a first reagent chamber 119, a mixing chamber 120, a second reagent chamber 121, and an outflow groove 122 that are connected in sequence. The first groove 113 is used to form a first airbag 30, the air groove 114 is used to form an air passage 50, the second groove 115 is used to form a second airbag 40, the valve chamber 116 is used to form a check valve 60, the sample chamber 117 is used to form a sample chamber 70, the liquid chamber 118 is used to form a flow channel 80, the first reagent chamber 119 is used to form a first reagent chamber 90, the mixing chamber 120 is used to form a mixer 100, the second reagent chamber 121 is used to form a second reagent chamber 210, and the outflow groove 122 is used to form an outflow channel 220.

[0035] The base plate 12 includes a plate body 1200, a first blocking post 1201, a second blocking post 1202, and a valve post 1203, which extend from the plate body 1200. The first blocking post 1201 is located in a first groove 113, the second blocking post 1202 is located in a second groove 115, and the valve post 1203 is located in a valve chamber 116. The first blocking post 1201 is used to control the volume of fluid driven by the first airbag 30. The second blocking post 1202 is used to control the volume of fluid driven by the second airbag 40.

[0036] The plug 20 is detachably installed in the sample application hole 112 and is used to seal the sample application hole 112 after sample application.

[0037] Please continue reading. Figure 5Both the first airbag 30 and the second airbag 40 are used to drive fluid flow. Specifically, the first airbag 30 and the second airbag 40 deform when pressed, thereby driving fluid flow. Through repeated pressing, the sample is fused and mixed with the pre-loaded solid or liquid reagent. In this embodiment, the first airbag 30 and the second airbag 40 deform to different volumes, thus driving the liquid flow to different positions and achieving different functions. In other embodiments, the first airbag 30 and the second airbag 40 can also be disposed outside the main body 10. In this embodiment, the first airbag 30 and the second airbag 40 are located inside the chip and are cylindrical. The first pressing part 110 and the second pressing part 111 at their top are thin elastic bodies with a thickness of 0.5-3 mm, which can be deformed by pressing with a finger. The blocking post is located at the bottom of the airbag and is cylindrical in shape. The deformed volume of the airbag determines the volume of gas that can be discharged, and thus the volume of liquid that can be driven. The height of the first airbag 30 and the second airbag 40 is 1-4 mm, and the radius is 10-20 mm. The dimensions of the blocking column are calculated based on the volume requirement of the driving fluid: where h is the height difference between the airbag and the blocking column, R is the radius of the airbag, and r is the radius of the blocking column. When a finger presses the airbag, the elastic body at the top of the airbag deforms. Under the premise that the modulus of the elastic body and the external pressing force remain unchanged, the degree of deformation of the elastic body is controlled by the blocking column.

[0038] The deformable volume of the first airbag 30 is the sum of the volume of the first reagent chamber 90, the volume of the mixer 100, and the volume of the flow channel 80 connecting the first reagent chamber 90 and the mixer 100. The deformable volume of the second airbag 40 is the sum of the volume of the first reagent chamber 90, the volume of the mixer 100, the volume of the second reagent chamber 210, and the volume of the flow channel 80 connecting the first reagent chamber 90, the mixer 100, and the second reagent chamber 210.

[0039] The airway 50 is used for gas flow and connects the first airbag 30 and the second airbag 40. The first airbag 30 is also connected to the sample chamber 70 via the airway 50. Specifically, the airway 50 has a rectangular cross-section with a length of 0.6 mm and a width of 0.5 mm.

[0040] The check valve 60 is a valve inside the air passage 50, used to prevent liquid from flowing back into the air passage 50, but does not affect the flow of gas. The check valve 60 is located between the first air bladder 30 and the sample chamber 70.

[0041] The sample chamber 70 is the chamber in which the sample is loaded inside the chip. One side of the sample chamber 70 is connected to the airway 50, and the other side is connected to the flow channel 80.

[0042] The sample cavity 70 has a movable stopper 20 at the top. The stopper 20 can be removed to add a sample, and the stopper 20 needs to be inserted after the sample is added. In this embodiment, the sample cavity 70 is cylindrical with a diameter of 4-6 mm, a height of 2-4 mm, and a total volume of approximately 25-100 μL. The stopper 20 and the aperture of the sample cavity 70 form an interference fit.

[0043] The flow channel 80 is a channel for fluid flow within the chip, which can connect the sample chamber 70 with the first reagent chamber 90, or the second reagent chamber 210 with the mixer 100. In this embodiment, the cross-sectional dimensions of the flow channel 80 are rectangular, with a length of 0.2-1 mm and a width of 0.3-0.6 mm.

[0044] The reagent chamber is a pre-loaded reagent compartment within the chip. The reagents inside need to be loaded before the cover plate 11 and the base plate 12 are aligned. In this application, a certain volume of liquid reagent is first loaded into the reagent chamber, and then it is converted into a solid state through freeze-drying or drying, making it easy to store and less prone to cross-contamination. The first reagent chamber 90 and the second reagent chamber 210 pre-load different types of reagents.

[0045] Please continue reading. Figure 4 as well as Figure 6 The mixer 100 is an in-chip microfluidic mixing structure that achieves rapid and uniform mixing of liquid samples and reagents under laminar flow conditions. In this application, the mixer 100 is a passive design that does not require external power input. The fluid can achieve rapid diffusion and flow of substances in laminar flow by means of the expansion and contraction of the channels inside the micromixer, thereby achieving uniform mixing.

[0046] The mixer 100 includes multiple expansion channels 101 and multiple contraction channels 102. The width of the expansion channels 101 is greater than the width of the contraction channels 102. The expansion channels 101 and contraction channels 102 are arranged at an angle and are connected. The width of the expansion channels 101 is 0.6-0.8 mm, and the width of the contraction channels 102 is 0.2-0.4 mm. The multiple expansion channels 101 and multiple contraction channels 102 are arranged alternately in a Z-shaped structure.

[0047] In this embodiment, the mixer 100 has an overall S-shaped structure. By repeatedly pressing and releasing the air bladder, the liquid reciprocates within the mixer 100, promoting the rapid diffusion of substances under laminar flow.

[0048] The following example uses coagulation detection to illustrate the use of the finger-driven microfluidic chip of this application:

[0049] Before coagulation testing begins, blood samples need to be properly processed to suit different subsequent testing purposes. In activated coagulation testing, the collected anticoagulated whole blood sample needs to be added to an activator to activate coagulation factors and incubated. After incubation, calcium ion reagent is added to the sample, and coagulation testing begins immediately. Therefore, as described above, the chip requires two reagent chambers. Kaolin activator is added to the first reagent chamber 90 according to the blood sample to reagent ratio, and calcium chloride solution is added to the second reagent chamber 210. After lyophilizing the reagents, chip assembly is completed. Specifically, 1.2 μL of kaolin activator is added to the first reagent chamber 90, and 2 μL of calcium chloride solution is added to the second reagent chamber 210. After lyophilizing the reagents, sample processing is prepared, as described below:

[0050] (1) Add 34 μL of anticoagulated blood into sample chamber 70 and seal the chamber with stopper 20;

[0051] (2) Pressing the first airbag 30 drives the sample into the first reagent chamber 90 and the mixer 100 in sequence. After pressing and releasing 5 times, the blood and kaolin activator are mixed.

[0052] (3) Wait 3-4 minutes to complete the incubation;

[0053] (4) Press the second airbag 40 to drive the incubated sample into the second reagent chamber 210, and press and release the airbag repeatedly 5-6 times to complete the mixing of blood and calcium chloride solution;

[0054] (5) Press the first airbag 30 and the second airbag 40 at the same time to pump the processed sample out from the outlet and use it for subsequent coagulation test.

[0055] In cases where anticoagulation is not feasible, finger-prick blood sampling can be used. Since the blood has not undergone anticoagulation, calcium ions are not required for coagulation testing; only an activator is needed. Add 1.2 μL of kaolin activator to the first reagent chamber (90), and do not add reagents to the second reagent chamber (210). After lyophilizing the reagents, prepare for sample processing as follows:

[0056] (1) Collect blood from the fingertip and drop it into the sample chamber 70 of the chip, and seal the sample chamber with the stopper 20;

[0057] (2) Press the first airbag 30 to drive the blood into the first reagent chamber 90 and the mixer 100 in sequence, and press and release the first airbag 30 repeatedly for a total of 5-6 times to complete the mixing of blood and kaolin activator;

[0058] (3) Wait 3-4 minutes to complete the incubation;

[0059] (4) Press the first airbag 30 and the second airbag 40 at the same time to pump the incubated sample out from the outlet and use it for subsequent coagulation tests.

[0060] This blood sample processing method is particularly suitable for home monitoring of patients taking oral anticoagulants, as well as for situations requiring rapid coagulation testing, such as those in the operating room or ICU. Furthermore, for patients who have difficulty drawing blood, finger-prick blood sampling can greatly alleviate their discomfort.

[0061] To verify the mixing effect of the mixer 100 on the finger-driven microfluidic chip, the mixing process of indicator and water was characterized. Colored indicator and water were added to the sample chamber 70 and reagent chamber, respectively. The indicator was pumped into the first reagent chamber 90 by pressing the air bladder, and the water and indicator were pumped together into the mixer 100. The mixture was then mixed by repeatedly pressing and releasing the air bladder. The laminar flow state image within the reagent chamber after each press and release was recorded, such as... Figure 7 As shown. The grayscale values ​​of the acquired image are normalized to obtain the mixing efficiency of each pass through the micromixer, such as... Figure 8 As shown in the figure. The results show that the mixing efficiency can reach more than 85% after pressing and releasing the airbag 5 times, which is sufficient to prove that this mixer 100 can produce a good mixing effect on fluids under laminar flow conditions.

[0062] To further demonstrate the effectiveness of the finger-driven microfluidic chip and its application in coagulation detection, fingertip blood was collected from several volunteers, and coagulation detection was performed using a magnetoelastic sensing coagulation detection chip and system. The detection steps are as follows:

[0063] (1) Prepare a finger-driven microfluidic chip and a magnetoelastic coagulation detection chip and detection system pre-loaded with reagents;

[0064] (2) Collect blood from a volunteer's fingertip, immediately drip it into the sample chamber 70 of the finger-driven microfluidic chip, and seal it with a stopper 20;

[0065] (3) Press the first airbag 30 to drive the blood into the first reagent chamber 90 and the mixer 100 in sequence, and press and release the first airbag 30 repeatedly 5-6 times to complete the mixing of blood and kaolin activator;

[0066] (4) Wait 3-4 minutes to complete the incubation;

[0067] (5) Press the first airbag 30 and the second airbag 40 at the same time to pump the incubated sample out of the outlet and drip it onto the magnetoelastic sensing chip.

[0068] (6) Place the magnetoelastic coagulation detection chip into the detection system and begin measuring the blood coagulation process;

[0069] In this embodiment, the results of the blood coagulation process of the volunteer were obtained according to the above steps as follows: Figure 9 As shown by the solid line, blood that had not been processed by the finger-driven microfluidic chip was also compared and measured. Specifically, blood from one volunteer's fingertip was directly added to the magnetoelastic coagulation detection chip, and the results were as follows: Figure 9 As shown by the dashed line, this result demonstrates that blood treated with the finger-driven microfluidic chip (activated) has a faster coagulation process than untreated blood (unactivated), validating the effectiveness of the finger-driven microfluidic chip.

[0070] This application's microfluidic chip, through the design of a first airbag 30 and a second airbag 40, precisely controls the deformation volume each time, thereby controlling the flow of liquid. It operates via finger-pressing, eliminating the need for external pumps, valves, tubing, and other components and power devices, making it simple to use. A check valve 60 prevents backflow; a reagent chamber allows for pre-filled reagents for sample pretreatment; and a passive micromixer enables rapid and uniform mixing of substances under laminar flow. By encapsulating coagulation detection reagents within the chip, only tens of microliters of anticoagulated whole blood or fingertip blood need to be added. After pressing the chip's airbags several times, the blood sample and related reagents can be rapidly processed before coagulation testing, and then used for subsequent coagulation analysis. The adjustable number of airbags and reagent chambers allows for the sequential processing of multiple samples and reagents, meeting the micro-sample processing needs of various biochemical analyses.

[0071] The above embodiments merely illustrate several implementation methods of the present invention, and their descriptions are relatively specific and detailed, but they should not be construed as limiting the scope of the invention patent. It should be noted that, for those skilled in the art, several modifications and improvements can be made without departing from the concept of the present invention. These are all equivalent modifications and improvements made to the above embodiments based on the essential technology of the present invention, and all of these fall within the protection scope of the present invention.

Claims

1. A finger-driven microfluidic chip, comprising a body, wherein the body is provided with a sample chamber, a first reagent chamber, and a second reagent chamber, characterized in that: The finger-driven microfluidic chip also includes a first airbag, a second airbag, a check valve, and a mixer. The first airbag and the second airbag are connected, and the volumes of the first airbag and the second airbag are different. The main body surface is provided with a first pressing part and a second pressing part. The position of the first pressing part corresponds to the position of the first airbag, and the position of the second pressing part corresponds to the position of the second airbag. The check valve is disposed between the sample chamber and the second airbag and / or the first airbag. The sample chamber, the first reagent chamber, the mixer, and the second reagent chamber are sequentially connected. When pressed by the first pressing part... When one of the first airbags and the second airbag is pressed by the second pressing part, the sample in the sample chamber flows between the sample chamber and the mixer, causing the sample to fuse with the pre-filled solid or liquid reagent in the first reagent chamber and enter the mixer for preliminary mixing; when the first airbag is pressed by the first pressing part and the other of the second airbags is pressed by the second pressing part, the sample in the sample chamber flows between the sample chamber and the second reagent chamber, causing the pre-mixed liquid to fuse with the pre-filled solid or liquid reagent in the second reagent chamber and be mixed in the mixer.

2. The finger-driven microfluidic chip according to claim 1, characterized in that: The deformable volume of the first airbag is the sum of the volume of the first reagent chamber, the volume of the mixer, and the volume of the flow channel connecting the sample chamber, the first reagent chamber, and the mixer.

3. The finger-driven microfluidic chip according to claim 1, characterized in that: The main body is provided with a first groove and a first blocking post. The first blocking post is located in the first groove, and the first pressing part is the outer wall of the first groove. The first groove and the first blocking post together form the first airbag.

4. The finger-driven microfluidic chip according to claim 1, characterized in that: The deformable volume of the second airbag is the sum of the volume of the first reagent chamber, the volume of the mixer, the volume of the second reagent chamber, and the volume of the flow channel connecting the sample chamber, the first reagent chamber, the mixer, and the second reagent chamber.

5. The finger-driven microfluidic chip according to claim 1, characterized in that: The main body is also provided with an outflow channel, which is connected to the second reagent chamber. The end of the outflow channel forms an outlet. The sum of the deformation volume of the first airbag and the deformation volume of the second airbag is greater than the volume from the end of the first reagent chamber to the end of the outflow channel, so that when the first airbag and the second airbag are pressed at the same time, the mixture flows out from the outlet.

6. The finger-driven microfluidic chip according to claim 1, characterized in that: The mixer includes multiple expansion channels and multiple contraction channels. The width of the expansion channels is greater than the width of the contraction channels. The expansion channels and contraction channels are arranged at an angle and are connected.

7. The finger-driven microfluidic chip according to claim 6, characterized in that: The width of the expansion channel is 0.6-0.8 mm, and the width of the contraction channel is 0.2-0.4 mm.

8. The finger-driven microfluidic chip according to claim 6, characterized in that: The multiple expansion channels and multiple contraction channels are alternately arranged in a zigzag shape.

9. The finger-driven microfluidic chip according to claim 1, characterized in that: The mixer has an S-shaped structure.

10. The finger-driven microfluidic chip according to claim 1, characterized in that: The main body includes a cover plate and a base plate fixedly connected to the cover plate. The sample chamber, the first reagent chamber, the second reagent chamber, the first airbag, the second airbag, the check valve, and the mixer are disposed between the cover plate and the base plate.

Images