Liquid inlet control device and liquid inlet control method for microfluidic chip

Abstract

The present invention provides a liquid inlet control device for a microfluidic chip, comprising a microfluidic chip and a detection device; the detection device controls the liquid inlet of the microfluidic chip; the microfluidic chip comprises a plurality of measurement chambers of an array, a buffer chamber, a first gas circuit interface, a second gas circuit interface, and a sampling needle; the plurality of measurement chambers are connected to the bottom of the buffer chamber, and the plurality of measurement chambers are connected to the second gas circuit interface; the top of the buffer chamber is connected to the sampling needle, and the top of the buffer chamber is connected to the first gas circuit interface; the detection device comprises at least an air pressure drive interface and a one-way valve interface, the air pressure drive interface is connected to the first gas circuit interface, and the air pressure drive interface is configured to: vacuumize or pressurize the first gas circuit interface; the one-way valve interface is connected to the second gas circuit interface, and when the air pressure drive interface presses the first gas circuit interface, the one-way valve interface is turned on. The present invention completes the injection of sample liquid into the microfluidic chip for turbidimetric detection by pumping air and pressing air, and the interface and the detection device are simple.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a liquid inlet control device and a liquid inlet control method for a microfluidic chip. Background Art

[0002] Microfluidics refers to the science and technology involved in systems that use microchannels to process or manipulate tiny fluids. It is an emerging interdisciplinary subject involving chemistry, fluid physics, microelectronics, new materials, biology and biomedical engineering. Microfluidics can concentrate the detection process on a chip ranging from centimeters to micrometers, making the entire detection miniaturized and automated. It is a very promising technical direction in the field of in vitro diagnosis.

[0003] Turbidimetry is one of the main detection methods for in vitro diagnosis. Its detection principle is that the analyte in the sample reacts specifically with the reagent to form a complex, and the complex aggregates within a certain period of time to produce turbidity. When light passes through the solution, it can be absorbed by the complex. The more complex there is, the more light is absorbed. Within a certain range, it is positively correlated with the amount of the complex. Therefore, by optically comparing the depth of the solution color, the concentration of the analyte that specifically binds to the reagent in the sample can be determined. Turbidimetry is often used in biochemical testing, immunoassays, coagulation tests and other projects.

[0004] For example, a biochip box and its operation method disclosed in Chinese invention patent application CN106970026A, and a detection device of a biochemical analyzer disclosed in Chinese utility model patent CN207198028U, use diagnostic equipment and consumables of turbidimetry, and the consumables are cuvettes with a single cup or multiple cups. The sample to be tested is mixed with the reagent manually or automatically by the device and then added to the cuvette, and the cuvette performs turbidimetric detection between the light source and the detector. The cuvette only serves to contain the reaction solution and transmit turbidimetry. Usually, the pretreatment and preparation process of the reaction solution is complicated. If it is prepared manually, the labor intensity is high and it is easy to introduce human interference; if the device is automatically realized, the design of the device is difficult, and the size and floor space of the device are generally large.

[0005] Another example is a method for coagulation analysis based on a biochemical reagent disk disclosed in Chinese invention patent application CN108169499A. The biochemical detection scheme is implemented through a disk-type microfluidic chip. After the sample to be tested is added to the microfluidic chip, it is diluted by a preset liquid, and then the microfluidic chip is driven to rotate by the device. The diluted sample to be tested is thrown into the reaction chamber at the outer edge of the chip by centrifugal force, and reacts after mixing with the preset freeze-dried reagent in the chamber. During the rotation of the disk, each reaction chamber is detected by the light source and detector inside the device in turn. The disk chamber and flow channel design of this scheme are complex, and the high-speed rotation has high requirements on the dynamic balance of the disk; the detection equipment needs to drive the disk to rotate at high speed through a motor, and the volume is large. Summary of the invention

[0006] The present invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip, so as to solve the technical problems that the microfluidic chip for in vitro diagnosis by turbidimetry is complex in structure, and the liquid inlet control device is difficult to design and has a large volume.

[0007] The technical solution provided by the present invention is as follows:

[0008] An object of the present invention is to provide a liquid inlet control device for a microfluidic chip, the liquid inlet control device comprising a microfluidic chip and a detection device; the detection device controls the liquid inlet of the microfluidic chip;

[0009] Wherein, the microfluidic chip includes a plurality of measurement chambers of the array, a buffer chamber, a first gas path interface, a second gas path interface, and a sampling needle;

[0010] The plurality of measuring chambers are connected to the bottom of the buffer chamber, and the plurality of measuring chambers are connected to the second gas path interface; the top of the buffer chamber is connected to the sampling needle, and the top of the buffer chamber is connected to the first gas path interface;

[0011] Wherein, the detection device at least comprises a pneumatic drive interface and a one-way valve interface, the pneumatic drive interface is connected to the first gas circuit interface, and the pneumatic drive interface is configured to: evacuate or pressurize the first gas circuit interface;

[0012] The one-way valve interface is connected to the second air circuit interface. When the air pressure driving interface applies air pressure to the first air circuit interface, the one-way valve interface is opened.

[0013] In a preferred embodiment, magnetic beads are preset in the cache chamber and the multiple measuring chambers, and different reagent balls are preset in the cache chamber and the multiple measuring chambers, respectively.

[0014] In a preferred embodiment, a liquid level sensor is provided in the buffer chamber.

[0015] In a preferred embodiment, the microfluidic chip further includes an exhaust main flow channel and a plurality of exhaust branch flow channels;

[0016] A plurality of exhaust manifolds are connected to the exhaust main flow channel, and one exhaust manifold is connected to one measurement chamber, and a breather filter is provided in each exhaust manifold.

[0017] In a preferred embodiment, the detection device further comprises an air pump, a first solenoid valve and a second solenoid valve;

[0018] The first solenoid valve is connected to the air pump via a first air pipe, and the second solenoid valve is connected to the air pump via a second air pipe;

[0019] Furthermore, the first solenoid valve is connected to the air pressure drive interface via a third air pipe, and the second solenoid valve is connected to the air pressure drive interface via a fourth air pipe.

[0020] In a preferred embodiment, the third air pipe is connected to the fourth air pipe via a fifth air pipe, the fifth air pipe is connected to the air pressure drive interface, and the fifth air pipe is provided with an air pressure sensor.

[0021] In a preferred embodiment, the detection device further comprises a one-way valve, and the one-way valve is connected to the one-way valve interface.

[0022] Another object of the present invention is to provide a liquid inlet control method for a microfluidic chip, the control method comprising the following steps:

[0023] S1, the sampling needle of the vacuum blood collection tube is inserted into the microfluidic chip;

[0024] S2, eliminating the negative pressure in the vacuum blood collection tube, including: the air pressure driving interface applies air pressure to the first air path interface, and the gas is injected into the vacuum blood collection tube through the buffer chamber;

[0025] S3, liquid is introduced into the buffer chamber, including: the air pressure driving interface draws a vacuum toward the first air path interface to draw the sample liquid in the vacuum blood collection tube into the buffer chamber;

[0026] S4, liquid is introduced into the multiple measuring chambers, including: the air pressure driving interface applies air pressure to the first air path interface to inject the sample liquid in the buffer chamber into the multiple measuring chambers.

[0027] In a preferred embodiment, in step S2, when the air pressure driving interface pressurizes the first air circuit interface, a portion of the gas is pumped into the vacuum blood collection tube through the buffer chamber, and the other portion of the gas is discharged into the outside atmosphere.

[0028] In a preferred embodiment, in step S4, when the air pressure driving interface applies air pressure to the first air circuit interface, a portion of the gas is pumped into the vacuum blood collection tube through the buffer chamber, and another portion of the gas squeezes the sample liquid in the buffer chamber, pumping the sample liquid in the buffer chamber into multiple measuring chambers.

[0029] The above technical solution of the present invention has at least the following beneficial effects compared with the prior art:

[0030] The present invention provides a liquid inlet control device and liquid inlet control method for a microfluidic chip. A freeze-dried reagent is preset inside the microfluidic chip, and a vacuum blood collection tube is inserted into the microfluidic chip to automatically complete the entire process of sample liquid driving, reaction liquid quantification, reagent mixing, and detection. The microfluidic chip is a card-type design, and the liquid inside is driven by air pressure. The sample liquid is injected into the microfluidic chip by pumping and pumping air pressure for turbidimetric detection, and the interface and detection device are simple.

[0031] The present invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip, which pump gas into a vacuum blood collection tube by pumping air pressure, thereby avoiding the situation where the sample liquid in the vacuum blood collection tube cannot be pumped into the microfluidic chip by only pumping air, and ensures that the sample liquid in the vacuum blood collection tube can be pumped into the microfluidic chip according to the amount.

[0032] The present invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip. Turbidimetric detection can be performed by simply inserting a vacuum blood collection tube filled with sample liquid into a sampling needle, without the need for pretreatment of the sample liquid and reagents, which is convenient and quick.

[0033] The present invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip. The microfluidic chip has multiple measuring chambers, which can be designed as sample reaction chambers, negative control chambers, positive control chambers, baseline control chambers, blank control chambers, etc. according to needs.

[0034] The invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip. A freeze-dried reagent can be pre-installed in the microfluidic chip, thereby avoiding the preparation of the reagent and enabling storage and transportation at room temperature.

[0035] The invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip. Magnetic beads are preset in the microfluidic chip, and can cooperate with the reciprocating permanent magnet of the device to realize rapid mixing of reagents.

[0036] The present invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip. The volumes of a plurality of measuring chambers of the microfluidic chip can be determined as fixed volumes according to requirements, thereby achieving quantification of a reaction system.

[0037] The present invention provides a liquid inlet control device and a liquid inlet control method for a microfluidic chip. The microfluidic chip supports the mixing and incubation of two-component reagents respectively and can be adapted to a variety of reaction types. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the drawings required for use in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0039] Figure 1 It is a topological diagram of the cooperation between a microfluidic chip and a detection device of a liquid inlet control device of a microfluidic chip of the present invention.

[0040] Figure 2 It is a topological diagram for eliminating negative pressure in a vacuum blood collection tube in a liquid inlet control method of a microfluidic chip of the present invention.

[0041] Figure 3 It is a topological diagram of liquid inflow into a buffer chamber in a liquid inflow control method of a microfluidic chip of the present invention.

[0042] Figure 4 It is a topological diagram of liquid inflow into multiple measuring chambers in a liquid inflow control method of a microfluidic chip of the present invention.

[0043] Figure 5 It is a schematic diagram of turbidimetric detection of the sample solution of the present invention. DETAILED DESCRIPTION

[0044] In order to make the purpose, technical solution and advantages of the embodiment of the present invention clearer, the technical solution of the embodiment of the present invention will be clearly and completely described below in conjunction with the drawings of the embodiment of the present invention. Obviously, the described embodiment is a part of the embodiment of the present invention, not all of the embodiments. Based on the described embodiment of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0045] Unless otherwise defined, the technical terms or scientific terms used in the present invention should be understood by people with ordinary skills in the field to which the present invention belongs. The words "first", "second" and similar words used in the present invention do not indicate any order, quantity or importance, but are only used to distinguish different components. Similarly, words such as "one", "one" or "the" do not indicate a quantitative limitation, but indicate the existence of at least one. Words such as "include" or "comprise" mean that the elements or objects appearing before the word include the elements or objects listed after the word and their equivalents, without excluding other elements or objects. Words such as "connect" or "connected" are not limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect.

[0046] It should be noted that the terms "up", "down", "left", "right", "front", "back", etc. used in the present invention are only used to indicate relative position relationships. When the absolute position of the object being described changes, the relative position relationship may also change accordingly.

[0047] like Figure 1 As shown, according to an embodiment of the present invention, a liquid inlet control device for a microfluidic chip is provided, comprising a microfluidic chip A and a detection device B, wherein the detection device B controls the liquid inlet of the microfluidic chip A.

[0048] The microfluidic chip A includes a plurality of measurement chambers in an array, a buffer chamber 2 , a first gas path interface 41 , a second gas path interface 42 , and a sampling needle 1 .

[0049] In this embodiment, n measuring chambers are exemplarily provided, namely, the first measuring chamber 4, the second measuring chamber 5, ..., the nth measuring chamber 6. The multiple measuring chambers are designed as sample reaction chambers, negative control chambers, positive control chambers, baseline control chambers, blank control chambers, etc. according to the requirements. For example, the first measuring chamber 4 is a sample reaction chamber, the second measuring chamber 5 is a negative control chamber, ..., and the nth measuring chamber is a blank control chamber.

[0050] According to an embodiment of the present invention, a plurality of measuring chambers are connected to the bottom of the buffer chamber 2 , and a plurality of measuring chambers are connected to the second gas path interface 42 .

[0051] Specifically, the microfluidic chip A further comprises a transfer channel 23, a liquid separation main channel 24, and a plurality of liquid separation branch channels. The transfer channel 23 is connected to the liquid separation main channel 24, a plurality of liquid separation branch channels are connected to the liquid separation main channel 24, and one liquid separation branch channel is connected to one measuring chamber.

[0052] In this embodiment, the bottom of the buffer chamber 2 is connected to the transfer channel 23, and the transfer channel 23 is connected to the first measuring chamber 4, the second measuring chamber 5, ..., the nth measuring chamber 6 through the liquid separation main channel 24.

[0053] Furthermore, the liquid separation main flow channel 24 is connected to the first liquid separation branch flow channel 25 , the second liquid separation branch flow channel 26 , . . . , the nth liquid separation branch flow channel 27 .

[0054] The first liquid-separating manifold 25 is connected to the first measuring chamber 4 , the second liquid-separating manifold 26 is connected to the second measuring chamber 5 , ... , and the nth liquid-separating manifold 27 is connected to the nth measuring chamber 6 .

[0055] According to an embodiment of the present invention, the microfluidic chip A further comprises an exhaust main flow channel 31 and a plurality of exhaust manifolds. The plurality of exhaust manifolds are connected to the exhaust main flow channel 31, and one exhaust manifold is connected to one measuring chamber, and each exhaust manifold is provided with a ventilation filter.

[0056] In this embodiment, the exhaust main flow channel 31 is connected to the first exhaust manifold 28, the second exhaust manifold 29, ..., and the nth exhaust manifold 30. The first exhaust manifold 28 is connected to the first measurement chamber 4, the second exhaust manifold 29 is connected to the second measurement chamber 5, ..., and the nth exhaust manifold 30 is connected to the nth measurement chamber 6.

[0057] The exhaust main flow channel 31 is connected to the second gas path interface 42 , so that the second gas path interface 42 is connected to the first measuring chamber 4 , the second measuring chamber 5 , . . . , the nth measuring chamber 6 .

[0058] The first exhaust manifold 28 is provided with a first breather filter 7 , the second exhaust manifold 29 is provided with a second breather filter 8 , . . . , and the nth exhaust manifold 30 is provided with an nth breather filter 9 .

[0059] According to an embodiment of the present invention, the top of the buffer chamber 2 is connected to the sampling needle 1 , and the top of the buffer chamber 2 is connected to the first gas path interface 41 .

[0060] In this embodiment, the top of the buffer chamber 2 is connected to the sampling needle 1 through the liquid inlet channel 21 , and the top of the buffer chamber 2 is connected to the first gas path interface 41 through the driving channel 22 .

[0061] According to an embodiment of the present invention, magnetic beads are preset in the cache chamber 2 and the multiple measuring chambers, and different reagent balls are preset in the cache chamber 2 and the multiple measuring chambers, respectively.

[0062] In this embodiment, the first magnetic beads 71 ​​are preset in the buffer chamber 2, the second magnetic beads 72 are preset in the first measuring chamber 4, the third magnetic beads 73 are preset in the second measuring chamber 5, ..., and the nth magnetic beads 74 are preset in the nth measuring chamber 6. The first reagent ball 81 is preset in the buffer chamber 2, the second reagent ball 82 is preset in the first measuring chamber 4, the third reagent ball 83 is preset in the second measuring chamber 5, ..., and the nth reagent ball 84 is preset in the nth measuring chamber 6. The liquid level sensor 3 is provided in the buffer chamber 2.

[0063] The first reagent ball 81, the second reagent ball 82, the third reagent ball 83, ..., and the nth reagent ball 84 are different reagent balls.

[0064] According to the embodiment of the present invention, the detection device includes an air pump 53 , a first solenoid valve 54 and a second solenoid valve 55 , as well as an air pressure drive interface 51 and a one-way valve interface 52 .

[0065] The air pressure driving interface 51 is in communication with the first air circuit interface 41 , and the air pressure driving interface 51 is configured to: evacuate or pressurize the first air circuit interface 41 .

[0066] The one-way valve interface 52 is connected to the second air circuit interface 42 . When the air pressure driving interface 51 applies air pressure to the first air circuit interface 41 , the one-way valve interface 52 is opened.

[0067] Specifically, the detection device further includes a one-way valve 56, which is connected to the one-way valve interface 52, and the one-way valve 56 is connected to the external atmosphere 57. When the air pressure driving interface 51 presses air pressure to the first air circuit interface 41, the one-way valve 56 is turned on, so that the one-way valve interface 52 is turned on, and the second air circuit interface 42 is turned on with the external atmosphere 57.

[0068] According to an embodiment of the present invention, the first solenoid valve 54 is connected to the air pump 53 through the first air pipe 64, and the second solenoid valve 55 is connected to the air pump 53 through the second air pipe 63. The first solenoid valve 54 is connected to the air pressure drive interface 51 through the third air pipe 65, and the second solenoid valve 55 is connected to the air pressure drive interface 51 through the fourth air pipe 62.

[0069] Furthermore, the third air pipe 65 is connected to the fourth air pipe 62 via the fifth air pipe 61 , the fifth air pipe 61 is connected to the air pressure drive interface 51 , and the fifth air pipe 51 is provided with an air pressure sensor 58 .

[0070] The third air pipe 65 is connected to the fourth air pipe 62 via the fifth air pipe 61 , and the fifth air pipe 61 is connected to the air pressure driving interface 51 , so that the air pressure driving interface 51 is connected to the first solenoid valve 54 and the second solenoid valve 55 .

[0071] When the air pump 53 applies air pressure (applies positive pressure), the first solenoid valve 54 is connected, and the second solenoid valve 55 is cut off, so that the first air pipe 64 and the third air pipe 65 are connected, and the second air pipe 63 and the fourth air pipe 62 are cut off, and the air pump 53 pressurizes the buffer chamber 2 through the first air pipe 64, the first solenoid valve 54, the third air pipe 65, the fifth air pipe 61, the air pressure drive interface 51, and the first air circuit interface 41. Figure 2 and Figure 4 shown.

[0072] When the air pump 53 is evacuated (negative pressure is applied), the first solenoid valve 54 is cut off and the second solenoid valve 55 is connected, so that the first air pipe 64 and the third air pipe 65 are cut off, and the second air pipe 63 and the fourth air pipe 62 are connected. The air pump 53 evacuates the buffer chamber 2 through the second air pipe 63, the second solenoid valve 55, the fourth air pipe 62, the fifth air pipe 61, the air pressure drive interface 51, and the first air circuit interface 41. Figure 3 shown.

[0073] When the air pump 53 inflates the air (applies positive pressure) or draws a vacuum (applies negative pressure), the air pressure sensor 58 measures the gas pressure in the fifth air pipeline 61. The air pump 53 adjusts the rotation speed of the air pump 53 according to the gas pressure feedback in the fifth air pipeline 61 measured by the air pressure sensor 58, thereby realizing feedback control of the positive pressure or negative pressure at the air circuit interface 51 and outputting precise pressure.

[0074] Combination Figures 2 to 4 According to an embodiment of the present invention, a liquid inlet control method for a microfluidic chip is provided, comprising the following method steps:

[0075] Step S1, inserting the vacuum blood collection tube Z into the sampling needle 1 of the microfluidic chip A.

[0076] The vacuum blood collection tube Z contains sample liquid Y (such as a blood sample). The vacuum blood collection tube Z is inserted upside down into the microfluidic chip A. The sampling needle 1 pierces the sealing film of the vacuum blood collection tube Z and is inserted into the vacuum blood collection tube Z.

[0077] Step S2, eliminating the negative pressure in the vacuum blood collection tube Z.

[0078] like Figure 2As shown, the air pressure driving interface 51 applies air pressure (positive pressure) to the first air circuit interface 41 , and injects the gas into the vacuum blood collection tube Z through the buffer chamber 2 .

[0079] Since there is vacuum and sample liquid Y inside the vacuum blood collection tube Z, excessive vacuum will result in the sample liquid Y not being completely extracted or only being partially extracted. Therefore, after the vacuum blood collection tube Z is inverted and inserted into the microfluidic chip A, positive pressure needs to be applied to the inside of the microfluidic chip A first to eliminate the negative pressure inside the vacuum blood collection tube Z.

[0080] Specifically, Figure 2 As shown, the air pump 53 pumps air pressure (applies positive pressure), the first solenoid valve 54 is turned on, and the second solenoid valve 55 is turned off, so that the first air pipe 64 and the third air pipe 65 are turned on, and the second air pipe 63 and the fourth air pipe 62 are turned off, and the air pump 53 pumps air pressure into the cache chamber 2 through the first air pipe 64, the first solenoid valve 54, the third air pipe 65, the fifth air pipe 61, the air pressure drive interface 51, and the first air path interface 41.

[0081] The gas enters the buffer chamber 2, and a part of the gas is pumped into the vacuum blood collection tube Z through the buffer chamber 2 to eliminate the negative pressure in the vacuum blood collection tube Z. The other part of the gas (excess gas) enters the transfer channel 23 through the bottom of the buffer chamber 2, and is discharged to the outside atmosphere 57 through the liquid separation main channel 24, multiple measuring chambers (the first measuring chamber 4, the second measuring chamber 5, ..., the nth measuring chamber 6), the exhaust main channel 31, the second gas path interface 42, the one-way valve interface 52, and the one-way valve 56.

[0082] Step S3, liquid is added to the buffer chamber 2.

[0083] like Figure 3 As shown, the air pressure driving interface 51 evacuates the first air path interface 41 (applies negative pressure) to draw the sample liquid Y in the vacuum blood collection tube Z into the buffer chamber 2 .

[0084] When the air pump 53 is evacuated (applies negative pressure), the air pressure in the microfluidic chip A is lower than the external atmospheric pressure, the one-way valve 56 is closed, and the external atmosphere 57 cannot enter the microfluidic chip A through the one-way valve 56.

[0085] Specifically, Figure 3 As shown, the air pump 53 draws a vacuum (applies negative pressure), the first solenoid valve 54 is cut off, and the second solenoid valve 55 is connected, so that the first air pipe 64 and the third air pipe 65 are cut off, and the second air pipe 63 and the fourth air pipe 62 are connected. The air pump 53 draws a vacuum from the cache chamber 2 through the second air pipe 63, the second solenoid valve 55, the fourth air pipe 62, the fifth air pipe 61, the air pressure drive interface 51, and the first air path interface 41.

[0086] Since in step S1, positive pressure has been established in the vacuum blood collection tube Z, while the buffer chamber 2 is now at negative pressure, the pressure difference between the two will cause the sample liquid Y to enter the buffer chamber 2 from the vacuum blood collection tube Z. In this process, the positive pressure in the vacuum blood collection tube Z gradually disappears and turns into negative pressure. As long as the negative pressure generated by the air pump 53 is greater than the negative pressure generated by the outflow of the sample liquid Y in the vacuum blood collection tube Z, the sample liquid Y can be pumped into the buffer chamber 2.

[0087] The sample liquid Y is drawn into the buffer chamber 2, and the air pump 53 stops vacuuming (stops applying negative pressure) when it reaches the height of the liquid level sensor 3. The height of the liquid level sensor 3 should make the volume of the sample liquid Y flowing into the buffer chamber 2 greater than the sum of the volumes of the n measuring chambers.

[0088] After the sample liquid Y is drawn into the buffer chamber 2, the first magnetic bead 71 is driven to reciprocate by the permanent magnet outside the microfluidic chip A, so that the first reagent ball 81 is dissolved and mixed with the sample liquid Y. The mixed sample liquid Y is incubated at room temperature or at a fixed temperature for a preset time in conjunction with the heating module of the sample analyzer.

[0089] Step S4: liquid is introduced into multiple measuring chambers.

[0090] like Figure 4 As shown, the air pressure driving interface 51 applies air pressure (positive pressure) to the first air circuit interface 41 to pump the sample liquid Y in the buffer chamber 2 into multiple measuring chambers (the first measuring chamber 4, the second measuring chamber 5, ..., the nth measuring chamber 6).

[0091] Specifically, Figure 4 As shown, the air pump 53 pumps air pressure (applies positive pressure), the first solenoid valve 54 is turned on, and the second solenoid valve 55 is turned off, so that the first air pipe 64 and the third air pipe 65 are turned on, and the second air pipe 63 and the fourth air pipe 62 are turned off, and the air pump 53 pumps air pressure into the cache chamber 2 through the first air pipe 64, the first solenoid valve 54, the third air pipe 65, the fifth air pipe 61, the air pressure drive interface 51, and the first air path interface 41.

[0092] When the air pressure driving interface 51 applies air pressure to the first air path interface 41, a part of the gas is injected into the vacuum blood collection tube through the buffer chamber, and the other part of the gas squeezes the sample liquid Y in the buffer chamber 2, and injects the sample liquid Y in the buffer chamber 2 into multiple measuring chambers (the first measuring chamber 4, the second measuring chamber 5, ..., the nth measuring chamber 6).

[0093] Since the interior of the vacuum blood collection tube Z has been evacuated to a negative pressure in step S2 , excess gas will enter the vacuum blood collection tube Z, so that the air pressure inside the vacuum blood collection tube Z is balanced with the positive pressure applied by the air pump 53 .

[0094] Then, the air pump 53 continues to pump air (apply positive pressure). When the difference between the pressure in the microfluidic chip A and the atmospheric pressure is greater than the opening pressure of the one-way valve 56, the sample liquid Y in the buffer chamber 2 is pressed into a plurality of measuring chambers (the first measuring chamber 4, the second measuring chamber 5, ..., the nth measuring chamber 6).

[0095] The ventilation filters (first ventilation filter 7, second ventilation filter 78, ..., nth ventilation filter 9) are air-permeable and water-stopping filters, through which the gas in the multiple measurement chambers can pass, but the sample liquid Y cannot pass, and the multiple measurement chambers are all filled with sample liquid Y.

[0096] After the sample liquid Y is injected into multiple measuring chambers (first measuring chamber 4, second measuring chamber 5, ..., nth measuring chamber 6), the corresponding permanent magnets in the sample analyzer drive the magnetic beads (second magnetic beads 72, third magnetic beads 73, ..., nth magnetic beads 74) to reciprocate, so that the reagent balls (second reagent balls 82, third reagent balls 83, ..., nth reagent balls 84) in the multiple measuring chambers are dissolved and mixed with the sample liquid Y. The mixed sample liquid Y is incubated for a preset time at room temperature or at a fixed temperature in conjunction with the heating module of the sample analyzer.

[0097] Finally, light sources and detectors are arranged on both sides of multiple measuring chambers (the first measuring chamber 4, the second measuring chamber 5, ..., the nth measuring chamber 6), and turbidimetry is used for detection. Figure 5 shown.

[0098] There are a few points to note:

[0099] (1) The drawings of the embodiments of the present invention only relate to the structures related to the embodiments of the present invention, and other structures may refer to the general design.

[0100] (2) For the sake of clarity, in the drawings used to describe the embodiments of the present invention, the thickness of the layers or regions is exaggerated or reduced, that is, these drawings are not drawn according to the actual scale. It is understood that when an element such as a layer, film, region or substrate is referred to as being "on" or "under" another element, the element may be "directly" "on" or "under" the other element or there may be intermediate elements.

[0101] (3) In the absence of conflict, the embodiments of the present invention and the features therein may be combined with each other to obtain new embodiments.

[0102] The above are only specific embodiments of the present invention, but the protection scope of the present invention is not limited thereto. The protection scope of the present invention shall be based on the protection scope of the claims.

Claims

1. A liquid inlet control device for a microfluidic chip, characterized in that: The liquid inlet control device comprises a microfluidic chip and a detection device; the detection device controls the liquid inlet of the microfluidic chip; Wherein, the microfluidic chip includes a plurality of measurement chambers of the array, a buffer chamber, a first gas path interface, a second gas path interface, and a sampling needle; Wherein, magnetic beads are preset in the cache chamber and the plurality of measuring chambers, and different reagent balls are preset in the cache chamber and the plurality of measuring chambers respectively; The plurality of measuring chambers are connected to the bottom of the buffer chamber, and the plurality of measuring chambers are connected to the second gas path interface; the top of the buffer chamber is connected to the sampling needle, and the top of the buffer chamber is connected to the first gas path interface; Wherein, the detection device at least comprises a pneumatic drive interface and a one-way valve interface, the pneumatic drive interface is connected to the first gas circuit interface, and the pneumatic drive interface is configured to: evacuate or pressurize the first gas circuit interface; The one-way valve interface is connected to the second air circuit interface, and when the air pressure driving interface applies air pressure to the first air circuit interface, the one-way valve interface is opened; Light sources and detectors are arranged on both sides of the multiple measurement chambers.

2. The liquid inlet control device according to claim 1, characterized in that: The buffer chamber is provided with a liquid level sensor.

3. The liquid inlet control device according to claim 1, characterized in that: The microfluidic chip also includes an exhaust main flow channel and a plurality of exhaust branch flow channels; A plurality of exhaust manifolds are connected to the exhaust main flow channel, and one exhaust manifold is connected to one measurement chamber, and a breather filter is provided in each exhaust manifold.

4. The liquid inlet control device according to claim 1, characterized in that: The detection device also includes an air pump, a first solenoid valve and a second solenoid valve; The first solenoid valve is connected to the air pump via a first air pipe, and the second solenoid valve is connected to the air pump via a second air pipe; Furthermore, the first solenoid valve is connected to the air pressure drive interface via a third air pipe, and the second solenoid valve is connected to the air pressure drive interface via a fourth air pipe.

5. The liquid inlet control device according to claim 4, characterized in that: The third air pipe is connected to the fourth air pipe through a fifth air pipe, the fifth air pipe is connected to the air pressure drive interface, and the fifth air pipe is provided with an air pressure sensor.

6. The liquid inlet control device according to claim 1, characterized in that: The detection device also includes a one-way valve, and the one-way valve is connected to the one-way valve interface.

7. A liquid inlet control method based on the liquid inlet control device according to any one of claims 1 to 6, characterized in that: The control method comprises the following steps: S1, the sampling needle of the vacuum blood collection tube is inserted into the microfluidic chip; S2, eliminating the negative pressure in the vacuum blood collection tube, including: the air pressure driving interface applies air pressure to the first air path interface, and the gas is injected into the vacuum blood collection tube through the buffer chamber; S3, liquid is introduced into the buffer chamber, including: the air pressure driving interface draws a vacuum toward the first air path interface to draw the sample liquid in the vacuum blood collection tube into the buffer chamber; S4, liquid is introduced into the multiple measuring chambers, including: the air pressure driving interface applies air pressure to the first air path interface to inject the sample liquid in the buffer chamber into the multiple measuring chambers.

8. The liquid inlet control method according to claim 7, characterized in that: In step S2, when the air pressure driving interface pressurizes the first air circuit interface, a part of the gas is injected into the vacuum blood collection tube through the buffer chamber, and the other part of the gas is discharged into the external atmosphere.

9. The liquid inlet control method according to claim 7, characterized in that: In step S4, when the air pressure driving interface applies air pressure to the first air circuit interface, a part of the gas is injected into the vacuum blood collection tube through the buffer chamber, and another part of the gas squeezes the sample liquid in the buffer chamber and injects the sample liquid in the buffer chamber into multiple measuring chambers.

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