A microfluidic chip and a detection device

Abstract

The present application provides a microfluidic chip and a detection device, which relate to the field of molecular detection. The microfluidic chip includes a body and a heat receiving body, the heat receiving body is connected to the body, and the heat receiving body protrudes relative to one side surface of the body, and the reaction area is located in the heat receiving body. The microfluidic chip detection device includes the aforementioned microfluidic chip. The microfluidic chip and the detection device can improve the heating efficiency of the reagent in the reaction area, shorten the detection time, and improve the detection efficiency.

Description

Technical Field

[0001] The present application relates to the field of molecular detection, and in particular to a microfluidic chip and a detection device. Background Art

[0002] PCR nucleic acid detection technology is a method that uses a segment of DNA as a template and, with the participation of DNA polymerase and nucleotide substrate, amplifies the segment of DNA to a sufficient amount for structural and functional analysis.

[0003] During the PCR amplification nucleic acid detection process, the reagents in the amplification reaction area need to be heated. In the prior art, the heating efficiency of the reagents in the amplification reaction area is low, which increases the time to obtain the test results and reduces the detection efficiency. Summary of the invention

[0004] In view of this, the embodiments of the present application are directed to providing a microfluidic chip, the microfluidic chip detection device of which can improve the heating efficiency of reagents in the reaction area, shorten the detection time, and improve the detection efficiency.

[0005] According to one aspect of the present application, a microfluidic chip provided in one embodiment of the present application includes: a microfluidic chip, including a main body and a heat receiving body, the heat receiving body is connected to the main body, and the heat receiving body protrudes relative to one side surface of the main body, and a reaction zone is arranged in the heat receiving body.

[0006] According to another aspect of the present application, the heat receiving body protrudes relative to the bottom side surface of the main body.

[0007] According to another aspect of the present application, the heated body includes: a first heated wall; and a second heated wall, which is opposite to the first heated arm and is inclined relative to the first heated wall to form the V-shaped structure.

[0008] According to another aspect of the present application, the first heated wall is arranged parallel to the body, and the second heated wall is arranged inclined relative to the body.

[0009] According to another aspect of the present application, the main body is provided with a sample addition port, a nucleic acid release area and a mixing area, and the sample addition port, the nucleic acid release area, the mixing area and the reaction area are connected in sequence.

[0010] According to another aspect of the present application, a first air channel is also provided in the main body, and the two ends of the first air channel are respectively connected to the sample addition port and the nucleic acid release area. A microfluidic valve is provided in the first air channel, and the microfluidic valve is used to control the connection or disconnection of the first air channel.

[0011] According to another aspect of the present application, a second air channel is also provided in the main body, and the two ends of the second air channel are respectively connected to the sample addition port and the mixing area. A microfluidic valve is provided in the second air channel, and the microfluidic valve is used to control the connection or disconnection of the second air channel.

[0012] According to another aspect of the present application, a first control valve is arranged on the second air channel, the first control valve includes a first main channel arranged on the second air channel and a first branch connected to the first main channel, a meltable solid material is arranged in the first branch, the meltable solid material is used to flow into the first main channel after melting, so as to close the first main channel, thereby closing the second air channel; and / or, a second control valve is arranged on the channel between the mixing zone and the reaction zone, the second control valve includes a second main channel arranged on the channel between the mixing zone and the reaction zone and a second branch connected to the second main channel, the second branch is provided with a meltable solid material, the meltable solid material is used to flow into the second main channel after melting, so as to close the second main channel, thereby closing the channel between the mixing zone and the reaction zone.

[0013] According to another aspect of the present application, the microfluidic valve includes: a connecting channel; a meltable solid material, which is arranged in the connecting channel, and the meltable solid material is used to control the connection of the connecting channel after melting; a first accommodating chamber, which is connected to the connecting channel; and a second accommodating chamber, which is connected to the connecting channel, and the second accommodating chamber and the first accommodating chamber are respectively located on both sides of the connecting channel; wherein the first accommodating chamber and the second accommodating chamber are used to receive the melted solid material.

[0014] According to another aspect of the present application, along the airflow direction, the second accommodating chamber located upstream and the first accommodating chamber located downstream are arranged in sequence.

[0015] According to another aspect of the present application, a bottom surface of the first accommodating cavity is lower than a bottom surface of the second accommodating cavity.

[0016] According to another aspect of the present application, the connection point between the connecting channel and the first accommodating cavity is located in the middle position of the first accommodating cavity in the height direction.

[0017] According to another aspect of the present application, the side surface where the bottom surface of the first accommodating cavity is connected to the connecting channel is a first inclined surface, and the angle between the axis of the connecting channel and the first inclined surface along the direction of the airflow is an acute angle.

[0018] According to another aspect of the present application, a plurality of branch channels are arranged on the upper portion of the first accommodating chamber.

[0019] According to another aspect of the present application, the connection point between the connecting channel and the second accommodating cavity is located in the middle position of the second accommodating cavity in the height direction.

[0020] According to another aspect of the present application, the side surface where the bottom surface of the second accommodating cavity is connected to the connecting channel is a second inclined surface, and the angle between the axis of the connecting channel and the second inclined surface along the opposite direction of the airflow is an acute angle.

[0021] The present invention also provides a microfluidic chip detection device, comprising the above-mentioned microfluidic chip and a heating seat, wherein the seat is provided with a heating cavity, the inner wall of the heating cavity is in contact with the outer wall of the heated body to heat the nucleic acid reagent in the reaction area.

[0022] According to another aspect of the present application, the heating cavity is a V-shaped cavity adapted to the heated body.

[0023] According to another aspect of the present application, the heating seat includes: a bottom plate; a first protrusion connected to the bottom plate, the first protrusion is provided with a first heating wall, and the first heating wall is in contact with the first heated wall; a second protrusion connected to the bottom plate, the second protrusion is provided with a second heating wall, the second heating wall is in contact with the second heated wall, and the second heating wall is inclined relative to the first heating wall so that the area between the first heating wall and the second heating wall forms the V-shaped cavity.

[0024] According to another aspect of the present application, the first heating wall is disposed perpendicularly to the bottom plate, and the second heating wall is disposed obliquely relative to the bottom plate.

[0025] The microfluidic chip provided in the embodiment of the present application includes a reaction zone heating body protruding relative to one side surface of the main body, so as to improve the heating efficiency of the reagent in the reaction zone, shorten the detection time, and improve the detection efficiency. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1 A schematic structural diagram of a microfluidic chip detection device provided as an exemplary embodiment of the present application.

[0027] Figure 2 for Figure 1 A magnified schematic diagram of center A.

[0028] Figure 3 A schematic diagram of the structure of a microfluidic chip provided as an exemplary embodiment of the present application.

[0029] Figure 4 A schematic structural diagram of a microfluidic chip provided in another exemplary embodiment of the present application.

[0030] Figure 5A schematic structural diagram of a microfluidic chip provided in another exemplary embodiment of the present application.

[0031] Figure 6 A schematic structural diagram of a microfluidic chip provided in another exemplary embodiment of the present application.

[0032] Description of the drawings: 2-microfluidic chip detection device; 1-microfluidic chip; 11-body; 111-first airway; 112-second airway; 113-nucleic acid release area; 114-mixing area; 115-reaction area; 116-branch channel; 120-first branch; 121-second branch; 124-sample addition port; 125-first control valve; 126-first main channel; 127-second control valve; 128-second main channel; 13-microfluidic valve; 131 -connecting channel; 133-first accommodating chamber; 1331-first inclined surface; 134-second accommodating chamber; 1341-second inclined surface; 137-first microfluidic valve; 138-second microfluidic valve; 213-heated body; 2132-first heated wall; 2133-second heated wall; 22-heating seat; 221-heating chamber; 222-bottom plate; 223-first protrusion; 2231-first heating wall; 224-second protrusion; 2241-second heating wall. DETAILED DESCRIPTION

[0033] The following will be combined with the drawings in the embodiments of the present application to clearly and completely describe the technical solutions in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of this application.

[0034] Furthermore, in the exemplary embodiments, since the same reference numerals denote the same components having the same structure or the same steps of the same method, if one embodiment is exemplarily described, only structures or methods different from the described embodiment are described in other exemplary embodiments.

[0035] Throughout the specification and claims, when a component is described as being “connected” to another component, the component may be “directly connected” to the other component, or “electrically connected” to the other component through a third component. In addition, unless explicitly described to the contrary, the term “include” and its corresponding terms should be understood to include only the components described, and should not be understood to exclude any other components.

[0036] Figure 1 This is a schematic diagram of the structure of a microfluidic chip detection device 2 provided by an exemplary embodiment of the present application. Figure 1As shown, the microfluidic chip detection device 2 provided in the embodiment of the present application may include a microfluidic chip 1, which can perform nucleic acid reagent lysis, mixing, amplification and other detection procedures to quickly obtain the detection results of the nucleic acid reagent.

[0037] like Figure 1 As shown, the microfluidic chip 1 may include a body 11 and a heat receiving body 213, wherein the heat receiving body 213 is connected to the body 11, and the heat receiving body 213 protrudes relative to one side surface of the body 11, so that the heat receiving body 213 can be easily heated separately. In addition, a reaction area 115 is provided inside the heat receiving body 213, and after the heat receiving body 213 is heated, the heat is transferred to the nucleic acid reagent in the reaction area 115, so that the nucleic acid reagent can quickly perform an amplification reaction, thereby increasing the reaction rate.

[0038] like Figure 1 As shown, the microfluidic chip 1 may further include a heating seat 22, the heating seat 22 is provided with a heating cavity 221, the heated body 213 is inserted into the heating cavity 221, and the heat in the heating cavity 221 can heat the heated body 213, thereby heating the reaction area 115 in the heated body 213. Moreover, the inner wall of the heating cavity 221 is fitted with the outer wall of the heated body 213, which can increase the heat exchange efficiency between the heating seat 22 and the heated body 213, improve the heating efficiency of the reagent in the reaction area 115, shorten the detection time, and improve the detection efficiency.

[0039] In one embodiment, the heating seat 22 is disposed below the microfluidic chip 1 , and correspondingly, the heating body 213 protrudes relative to the bottom surface of the body 11 , so as to facilitate the cooperation between the heating body 213 and the heating cavity 221 .

[0040] The microfluidic chip detection device 2 provided in the embodiment of the present application can increase the heat exchange efficiency between the heating seat 22 and the heated body 213 by fitting the inner wall of the heating chamber 221 with the outer wall of the heated body 213, improve the heating efficiency of the reagent in the reaction area 115, shorten the detection time, and improve the detection efficiency.

[0041] Figure 2 for Figure 1 The enlarged schematic diagram of A in the figure. Figure 1 and Figure 2As shown, the heated body 213 is a V-shaped structure, and the heating chamber 221 is a V-shaped chamber adapted to the shape of the heated body 213. In this way, both opposite sides of the heated body 213 can be heated, which increases the heat transfer efficiency and improves the amplification reaction efficiency of the reagents in the reaction area 115. In addition, after the heated body 213 with a V-shaped structure is inserted into the V-shaped heating chamber 221, the inner wall of the heating chamber 221 can also limit the microfluidic chip 1, preventing the microfluidic chip 1 from tipping over during the heating process, and the inner wall of the heating chamber 221 and the outer wall of the heated body 213 will fit more closely, so that the heating temperature can be more accurately controlled and the heating time can be reduced.

[0042] like Figure 2 As shown, the heat receiving body 213 may include a first heat receiving wall 2132, which may be connected to the bottom wall of the main body 11. The first heat receiving wall 2132 is arranged parallel to the side wall of the main body 11, that is, the first heat receiving wall 2132 is perpendicular to the bottom wall surface of the main body 11, which can make the process of inserting the heat receiving body 213 into the heating cavity 221 smoother and facilitate the insertion of the heat receiving body 213 into the heating cavity 221.

[0043] like Figure 2 As shown, the heated body 213 may further include a second heated wall 2133, the second heated wall 2133 is inclined relative to the side wall of the body 11, and the first heated wall 2132 and the second heated wall 2133 form a V-shaped heated body 213. The inclined second heated wall 2133 can increase the heated area and the heat transfer efficiency of the heated body 213, thereby improving the heating efficiency of the reagent in the reaction area 115, shortening the detection time, and improving the detection efficiency.

[0044] Correspondingly, if Figure 2 As shown, the heating seat 22 may include a bottom plate 222 , which may play a supporting and bearing role. After the heated body 213 is inserted into the heating cavity 221 , the bottom plate 222 may support the microfluidic chip 1 .

[0045] like Figure 2 As shown, the heating seat 22 may further include a first protrusion 223, which is connected to the bottom plate 222, and the first protrusion 223 is provided with a first heating wall 2231, which is in contact with the first heated wall 2132, so that the heat generated by the first heating wall 2231 can be transferred to the first heated wall 2132, thereby heating the nucleic acid reagent in the reaction area 115.

[0046] like Figure 2As shown, the heating seat 22 may further include a second protrusion 224, which is connected to the bottom plate 222, and the second protrusion 224 is provided with a second heating wall 2241, which is in contact with the second heated wall 2133, so that the heat generated by the second heating wall 2241 can be transferred to the second heated wall 2133, thereby heating the nucleic acid reagent in the reaction area 115.

[0047] It should be understood that the first heating wall 2231 and the second heating wall 2241 can heat the nucleic acid reagent in the reaction area 115 at the same time, which can effectively improve the heating efficiency of the nucleic acid reagent.

[0048] like Figure 2 As shown, the second heating wall 2241 is tilted relative to the first heating wall 2231, which is conducive to the second heating wall 2241 and the second heated wall 2133 being completely fitted together, and the heat transfer effect is better. In addition, the area between the first heating wall 2231 and the tilted second heating wall 2241 forms a V-shaped heating cavity 221, which is also convenient for inserting the heated body 213.

[0049] like Figure 2 As shown, the first heating wall 2231 is vertically arranged with respect to the bottom plate 222, and the second heating wall 2241 is inclined relative to the bottom plate 222. In this way, the V-shaped heating cavity 221 formed between the first heating wall 2231 and the second heating wall 2241 is better adapted to the V-shaped heated body 213, the first heating wall 2231 and the first heated wall 2132 can be more closely fitted, the second heating wall 2241 and the second heated wall 2133 can be more closely fitted, and the heat transfer effect is better.

[0050] like Figure 2 As shown, both the first protrusion 223 and the second protrusion 224 are V-shaped structures, so that the first protrusion 223 and the second protrusion 224 have better stability, which is conducive to more stably supporting the microfluidic chip 1.

[0051] In one embodiment, the number of the first protrusion 223 and the second protrusion 224 can be multiple, and correspondingly, the number of the heating chamber 221 formed between the first protrusion 223 and the second protrusion 224 can also be multiple. Therefore, the heating seat 22 can heat multiple microfluidic chips 1 at the same time, and can assist the nucleic acid reagents in the multiple microfluidic chips 1 to perform amplification reactions, thereby effectively improving the overall detection efficiency.

[0052] Figure 3 The schematic diagram of the structure of the microfluidic chip 1 provided by an exemplary embodiment of the present application is shown in FIG. Figure 3 As shown, a first air channel 111 and a second air channel 112 are provided in the body 11 , and the first air channel 111 and the second air channel 112 can provide gas flow so as to allow the nucleic acid reagent to flow to different locations.

[0053] like Figure 3 As shown, the body 11 may also be provided with a sample addition port 124, a nucleic acid release area 113, a mixing area 114 and a reaction area 115 which are connected in sequence. Figure 3 In the placement state shown, among the sample adding port 124, the nucleic acid release area 113, the mixing area 114 and the reaction area 115, the sample adding port 124 is located at the top, the reaction area 115 is located at the bottom, the nucleic acid release area 113 and the mixing area 114 are both located between the sample adding port 124 and the reaction area 115, wherein the nucleic acid release area 113 is located above the mixing area 114. It should be understood that, under the action of gravity, the sample can enter the nucleic acid release area 113 from the sample adding port 124, then enter the mixing area 114 from the nucleic acid release area 113, and then enter the reaction area 115 from the mixing area 114.

[0054] In one embodiment, the nucleic acid release area 113 contains a nucleic acid release freeze-dried reagent, and the sample enters the nucleic acid release area 113 through the sample injection port 124 to complete the lysis and release the nucleic acid.

[0055] In one embodiment, the mixing zone 114 is pre-stored with PCR freeze-dried reagents, and the liquid in the nucleic acid release zone 113 enters the mixing zone 114 to complete the mixing of the sample and the PCR reagents in the mixing zone 114 .

[0056] In one embodiment, after the liquid in the mixing area 114 enters the reaction area 115, the corresponding position of the reaction area 115 is heated, and after the amplification reaction is completed, the detection result is obtained through optical detection.

[0057] like Figure 3 As shown, the microfluidic chip 1 may further include a microfluidic valve 13, and the microfluidic valve 13 is disposed in both the first air channel 111 and the second air channel 112, wherein the microfluidic valve 13 disposed on the first air channel 111 is a first microfluidic valve 137, and the microfluidic valve 13 disposed on the second air channel 112 is a second microfluidic valve 138, the first microfluidic valve 137 can control the on-off of the first air channel 111, and the second microfluidic valve 138 can control the on-off of the second air channel 112.

[0058] Specifically, Figure 3As shown, the microfluidic valve 13 may include a connecting channel 131. For the first microfluidic valve 137, the connecting channel 131 of the first microfluidic valve 137 may be used as a part of the first airway 111. When the connecting channel 131 is connected, the first airway 111 is in a connected state. When the connecting channel 131 is disconnected, the first airway 111 is also disconnected. For the second microfluidic valve 138, the connecting channel 131 of the second microfluidic valve 138 may be used as a part of the second airway 112. When the connecting channel 131 is connected, the second airway 112 is in a connected state. When the connecting channel 131 is disconnected, the second airway 112 is also disconnected.

[0059] In one embodiment, the connecting channel 131 of the first microfluidic valve 137 may also be connected to the first airway 111 as an independent channel.

[0060] In one embodiment, the connecting channel 131 of the second microfluidic valve 138 may also be connected to the second airway 112 as an independent channel.

[0061] like Figure 3 As shown, the microfluidic valve 13 may also include a fusible solid material, which is a material that can be molten when heated and solidified after cooling, such as paraffin, etc. The fusible solid material is arranged in the connecting channel 131. When the fusible solid material is not heated, it is a solid structure, and the connecting channel 131 can be disconnected. After the fusible solid material is heated, the fusible solid material becomes a molten state, and the connecting channel 131 can be connected.

[0062] like Figure 3 As shown, the microfluidic valve 13 may also include a first accommodating cavity 133 and a second accommodating cavity 134, and the first accommodating cavity 133 and the second accommodating cavity 134 are respectively connected to the two ends of the connecting channel 131, so that after the meltable solid material is melted, it can flow into the first accommodating cavity 133 or the second accommodating cavity 134, so that the connecting channel 131 is connected. The microfluidic valve 13 receives the melted solid material through the first accommodating cavity 133 and the second accommodating cavity 134, which can not only control the connection of the connecting channel 131, but also prevent the melted solid material from flowing back, thereby avoiding the melted solid material from affecting the detection result of the nucleic acid reagent.

[0063] Along the air flow direction, the second accommodating chamber 134 located upstream and the first accommodating chamber 133 located downstream are arranged in sequence, and the second accommodating chamber 134 can be used to receive the solid material that flows back after melting.

[0064] Along the airflow direction, the first airway 111 and the second airway 112 are divided into an upstream section and a downstream section. Accordingly, the second accommodating chamber 134 of the first microfluidic valve 137 is connected to the nucleic acid release area 113 through the upstream section of the first airway 111, and the first accommodating chamber 133 of the first microfluidic valve 137 is connected to the sample injection port 124 through the downstream section of the first airway 111, wherein the branch channel 116 of the first microfluidic valve 137 is merged into the downstream section of the first airway 111.

[0065] The second accommodating chamber 134 of the second flow control valve 138 is connected to the reaction zone 115 through the upstream section of the second air channel 112, and the first accommodating chamber 133 of the second microfluidic valve 138 is connected to the sample addition port 124 through the downstream section of the second air channel 112, wherein the branch channel 116 of the second microfluidic valve 138 is merged into the downstream section of the second air channel 112.

[0066] In one embodiment, there may be multiple branch channels 116. When the main channel or part of the branch channels 116 is blocked, the gas may pass through another part of the branch channels 116, which is helpful to ensure the normal progress of the detection operation.

[0067] Figure 4 This is a schematic diagram of the structure of a microfluidic chip provided by another exemplary embodiment of the present application. Figure 3 and Figure 4 As shown, for the meltable solid material in the first air channel 111, the meltable solid material is a solid structure when not heated, and the first air channel 111 can be disconnected. After the meltable solid material is heated, the meltable solid material becomes a molten state, and the molten solid material flows from the connecting channel 131 to the first accommodating cavity 133 or the second accommodating cavity 134, so that the first air channel 111 is connected. At this time, the liquid in the nucleic acid release area 113 can fall into the mixing area 114 under the action of gravity.

[0068] In one embodiment, Figure 4 For example, in the first air channel 111, the second accommodating chamber 134 can prevent the melted solid material from flowing back into the mixing area 114, thereby preventing the melted solid material from affecting the detection result of the nucleic acid reagent.

[0069] Figure 5 This is a schematic diagram of the structure of a microfluidic chip provided by another exemplary embodiment of the present application. Figure 4 and Figure 5As shown, for the meltable solid material in the second gas channel 112, the meltable solid material is a solid structure when not heated, and the second gas channel 112 can be disconnected. After the meltable solid material is heated, the meltable solid material becomes a molten state, and the molten solid material flows from the connecting channel 131 to the first accommodating cavity 133 or the second accommodating cavity 134, so that the second gas channel 112 is connected. At this time, the liquid in the mixing zone 114 can fall into the reaction zone 115 under the action of gravity.

[0070] In one embodiment, Figure 5 For example, the second accommodating chamber 134 can prevent the melted solid material from flowing back into the reaction area 115, thereby preventing the melted solid material from affecting the detection result of the nucleic acid reagent.

[0071] The microfluidic valve 13 and the microfluidic chip 1 provided in the embodiment of the present application can receive the melted solid material through the first accommodating cavity 133 and the second accommodating cavity 134, which can not only control the connection of the connecting channel 131, but also prevent the melted solid material from flowing back, thereby avoiding the melted solid material from affecting the detection result of the nucleic acid reagent.

[0072] like Figure 3-Figure 5 As shown, the connection between the connecting channel 131 and the first accommodating chamber 133 is located in the middle position of the first accommodating chamber 133 in the height direction. In this way, after the melted solid material flows into the first accommodating chamber 133, the accumulated solid material is not easy to reach the height of the connection between the connecting channel 131 and the first accommodating chamber 133, so that the solid material in the first accommodating chamber 133 is not easy to block the connection between the connecting channel 131 and the first accommodating chamber 133, ensuring that the connecting channel 131 is in a through state.

[0073] Similarly, if Figure 3-Figure 5 As shown, the connection between the connecting channel 131 and the second accommodating chamber 134 is located in the middle position of the second accommodating chamber 134 in the height direction. In this way, after the melted solid material flows into the second accommodating chamber 134, the accumulated solid material is not easy to reach the height of the connection between the connecting channel 131 and the second accommodating chamber 134, so that the solid material in the second accommodating chamber 134 is not easy to block the connection between the connecting channel 131 and the second accommodating chamber 134, ensuring that the connecting channel 131 is in a through state.

[0074] like Figure 3-Figure 5As shown, the side surface where the bottom surface of the first accommodating cavity 133 is connected to the connecting channel 131 is a first inclined surface 1331, and the angle between the axis of the connecting channel 131 and the first inclined surface 1331 along the direction of the airflow is an acute angle. In this way, when the airflow enters the first accommodating cavity 133 from the connecting channel 131, the connection between the first inclined surface 1331 and the connecting channel 131 can play a role in drainage, so that the airflow can enter the first accommodating cavity 133 more stably, and avoid the formation of large bubbles at the bottom corner of the first accommodating cavity 133.

[0075] Figure 3-Figure 5 The angle α in the figure can be understood as the angle between the axis of the aforementioned connecting channel 131 and the first inclined surface 1331 along the direction of the airflow.

[0076] Similarly, the bottom surface of the second accommodating cavity 134 and the side surface connected to the connecting channel 131 are the second inclined surface 1341, and the angle between the axis of the connecting channel 131 and the second inclined surface 1341 in the opposite direction of the airflow is an acute angle. In this way, when the airflow enters the connecting channel 131 from the second accommodating cavity 134, the connection between the second inclined surface 1341 and the connecting channel 131 can play a role in guiding the airflow, so that the airflow can enter the connecting channel 131 more stably.

[0077] Figure 3-Figure 5 The angle β in φ can be understood as the angle between the axis of the aforementioned connecting channel 131 and the first inclined surface 1331 along the opposite direction of the airflow.

[0078] Specifically, Figure 3-Figure 5 As shown, in one embodiment, the outer contour of the first accommodating cavity 133 is a hexagon, and the melted solid material can smoothly enter the first accommodating cavity 133 without generating bubbles at the bottom corners. In addition, the solid material can be spread out on the bottom wall of the first accommodating cavity 133, and is not easy to be stacked too high, which will not hinder the flow of gas.

[0079] The outer contour of the second accommodating cavity 134 is also hexagonal, and the melted solid material can be accumulated on the bottom wall of the second accommodating cavity 134 without generating bubbles. In addition, the solid material can be spread out on the bottom wall of the second accommodating cavity 134, and it is not easy to stack too high, which will not hinder the flow of gas.

[0080] In one embodiment, the outer contour of the first accommodating cavity 133 and the outer contour of the second accommodating cavity 134 may be the same or different.

[0081] In one embodiment, the volume of the first accommodating cavity 133 and the volume of the second accommodating cavity 134 may be the same or different.

[0082] like Figure 3-Figure 5As shown, in one embodiment, since the volume of the molten solid material accumulated in the first accommodating cavity 133 is relatively large, the bottom surface of the first accommodating cavity 133 is lower than the bottom surface of the second accommodating cavity 134. In this way, more solid material can be accommodated in the first accommodating cavity 133, so that the solid material will not hinder the gas from passing through the first accommodating cavity 133.

[0083] Figure 6 This is a schematic diagram of the structure of a microfluidic chip provided by another exemplary embodiment of the present application. Figure 5 and Figure 6 As shown, a first control valve 125 is disposed on the second gas channel 112 , and the first control valve 125 includes a first main channel 126 disposed on the second gas channel 112 and a first branch 120 connected to the first main channel 126 , and a meltable solid material is disposed in the first branch 120 .

[0084] Specifically, the meltable solid material in the first branch 120 is in a solid structure when not heated. After the solid material is heated, the solid material becomes a molten state and flows into the first main channel 126 , closing the first main channel 126 , thereby closing the second air channel 112 .

[0085] like Figure 5 and Figure 6 As shown, a second control valve 127 is arranged on the channel between the mixing zone 114 and the reaction zone 115. The second control valve 127 includes a second main channel 128 arranged on the channel between the mixing zone 114 and the reaction zone 115 and a second branch 121 connected to the second main channel 128. A meltable solid material is arranged in the second branch 121.

[0086] Specifically, the fusible solid material in the second branch 121 is in a solid structure when not heated. After the solid material is heated, the solid material becomes a molten state and flows into the second main channel 128, closing the second main channel 128, thereby closing the channel between the mixing zone 114 and the reaction zone 115.

[0087] After the second airway 112 is closed and the channel between the mixing area 114 and the reaction area 115 is closed, the reaction area 115 is in a closed state, which can prevent the nucleic acid reagent from flowing to other parts during the heating process, which is beneficial to ensure the accuracy of the nucleic acid detection results.

[0088] The fusible solid material mentioned in the above implementation refers to a material that can be molten when heated and solidify after cooling, such as paraffin.

[0089] The above description is only a specific embodiment of the present application and is not intended to limit the present application. Any modifications, equivalent substitutions, etc. made within the spirit and principles of the present application should be included in the protection scope of the present application.

Claims

1. A microfluidic chip, characterized in that: It comprises a body and a heat receiving body, wherein the heat receiving body is connected to the body, and the heat receiving body protrudes relative to a side surface of the body, and the reaction zone is located in the heat receiving body; The heat receiving body comprises: The first heated wall; A second heated wall, opposite to the first heated wall and inclined relative to the first heated wall to form a V-shaped structure; The body is provided with a sample addition port, a nucleic acid release area and a mixing area, and the sample addition port, the nucleic acid release area, the mixing area and the reaction area are connected in sequence; The body is also provided with a first airway, the two ends of which are respectively connected to the sample injection port and the nucleic acid release area, and the first airway is provided with a microfluidic valve, which is used to control the connection or disconnection of the first airway; A second air channel is also provided in the body, and two ends of the second air channel are respectively connected to the sample addition port and the mixing area, and a microfluidic valve is provided in the second air channel, and the microfluidic valve is used to control the connection or disconnection of the second air channel; The second air channel is provided with a first control valve, the first control valve comprises a first main channel provided on the second air channel and a first branch connected to the first main channel, a meltable solid material is provided in the first branch, the meltable solid material is used to flow into the first main channel after melting, so as to close the first main channel, thereby closing the second air channel; and / or, A second control valve is arranged on the channel between the mixing zone and the reaction zone, and the second control valve includes a second main channel arranged on the channel between the mixing zone and the reaction zone and a second branch connected to the second main channel, and a fusible solid material is arranged in the second branch, and the fusible solid material is used to flow into the second main channel after melting to close the second main channel, thereby closing the channel between the mixing zone and the reaction zone.

2. A microfluidic chip according to claim 1, characterized in that: The heat receiving body protrudes relative to the bottom side surface of the main body.

3. A microfluidic chip according to claim 1, characterized in that: The first heated wall is arranged parallel to the body, and the second heated wall is arranged inclined relative to the body.

4. A microfluidic chip detection device, characterized in that: A microfluidic chip comprising any one of claims 1 to 3, and The heating seat is provided with a heating cavity, the inner wall of the heating cavity is in contact with the outer wall of the heated body, so as to heat the nucleic acid reagent in the reaction area.

5. The microfluidic chip detection device according to claim 4, characterized in that: The heating cavity is a V-shaped cavity adapted to the heated body.

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