A microfluidic cartridge for rapid detection of biomolecules

Abstract

This invention relates to the field of biodetection technology, specifically disclosing a microfluidic cartridge for rapid detection of biomolecules. The microfluidic cartridge includes a housing, a fluid channel, a porous membrane, a flow-driving structure, a mixing and guiding structure, and a detection chamber. The fluid channel communicates with an inlet, and the porous membrane is placed within the channel for sample lysis and target analyte capture. The flow-driving structure includes a reservoir and a driving component, capable of pre-storing and sequentially releasing multiple reagents, and generating negative and positive pressures to drive the fluid through manual operation. The mixing and guiding structure features a spiral guide section for efficient passive mixing of reagents. The detection chamber is equipped with an optical window and a probe array for signal generation and reading. This invention highly integrates the entire process of sample processing, reagent release, fluid driving, mixing, and detection within the cartridge, achieving integrated rapid detection from sample entry to result exit. It offers advantages such as ease of operation, high portability, good anti-contamination properties, and accurate and reliable detection results.

Description

Technical Field

[0001] This invention relates to the field of biodetection technology, specifically a microfluidic cartridge for rapid detection of biomolecules. Background Technology

[0002] Traditional biomolecular detection methods typically involve multiple independent steps, such as sample pretreatment, reagent addition, mixing reaction, and result reading. These methods are cumbersome and highly dependent on professional personnel and laboratory environment, making it difficult to meet the needs of rapid on-site testing.

[0003] Currently, Chinese patent application number CN202310305686.4 discloses a microfluidic biological sample detection chip that integrates pumping and micromixing functions. This invention aims to solve the problem of long mixing time required for fluids in microfluidic chips. It uses a piezoelectric drive to achieve the integration of liquid pumping and micromixing functions in the same pump chamber or the same structural unit, so that biological reagents can be quantitatively pumped from the inlet to the sample detection channel, while the reagents can be fully mixed with fluorescent microspheres or magnetic beads to achieve efficient integration of structure and function.

[0004] However, existing technologies rely on external precision electronic components such as piezoelectric actuators for the detection of biomolecules. This not only increases the manufacturing cost of the chip and the complexity of the system, but also makes it difficult for the entire detection device to completely eliminate the need for external power supply and control circuits, affecting its applicability and portability in environments without stable power supply or with limited resources. Secondly, this type of active driving method has high requirements for the precision and reliability of components, which can easily increase the failure rate. Summary of the Invention

[0005] The purpose of this invention is to provide a microfluidic cartridge for rapid detection of biomolecules, in order to solve the problems mentioned in the background art.

[0006] To achieve the above objectives, the present invention adopts the following technical solution: a microfluidic box for rapid detection of biomolecules, comprising a box body, a sheath, a liquid inlet, a sealing plug, a fluid channel, a porous membrane, a flow-driving structure, a mixing and guiding structure, a detection chamber, and an exhaust channel. The outer surface of the box body is covered with a sheath, and a liquid inlet is provided on the upper front side of the box body. A sealing plug is provided inside the liquid inlet. A fluid channel is provided in the upper middle part of the box body, and the top side of the fluid channel is connected to the liquid inlet. A porous membrane is provided in the lower middle part of the fluid channel, and a flow-driving structure is connected to the right side below the porous membrane. A mixing and guiding structure is connected to the bottom of the flow-driving structure, and the bottom of the mixing and guiding structure is inserted into the detection chamber. The detection chamber is located in the lower middle part of the box body, and an exhaust channel is provided in the upper rear part of the detection chamber.

[0007] The flow-driving structure includes an inlet pipe connected to a fluid channel on the left side. A liquid storage chamber is locked and fixed on the top side of the inlet pipe away from the fluid channel. At least one partition is embedded inside the liquid storage chamber to form multiple storage chambers. A liquid storage bubble is provided in each storage chamber. The two outlets at the bottom of the inlet pipe are connected to a driving component. The two outlets at the bottom of the driving component are connected to an outlet pipe. The bottom of the outlet pipe has three flow outlets, and the bottoms of the three flow outlets are connected to a mixing and guiding structure.

[0008] Preferably, the porous membrane divides the fluid channel into upper and lower parts, and the surface or interior of the porous membrane is pre-embedded with lysis reagents or nucleic acid binding solid materials. When the sample liquid flows through the porous membrane, it can be lysed and the target molecules can be captured and purified.

[0009] Preferably, the bottom of the detection cavity is an optically transparent detection window, and a pre-embedded detection probe array is fixed on the top inner wall of the detection cavity. The detection probe array is directly opposite the detection window, which facilitates the reading of detection signals from the bottom of the box by optical equipment (such as a fluorescence scanner).

[0010] Preferably, pads are provided on both the left and right sides of the bottom of the storage chamber to support the liquid storage blister packs. The multiple liquid storage blister packs contain different liquid reagents, such as elution buffer, amplification reaction solution, detection substrate, etc.

[0011] Preferably, the top side of the inlet pipe is provided with the same number of openings as the storage chamber, and a hollow piece is embedded in the lower middle side of the opening to connect the storage chamber and the inlet pipe. A pointed tip is integrally formed on the top of the hollow piece, and the tip of the pointed tip is inserted into the bottom side of the storage chamber.

[0012] Preferably, the drive assembly includes a silo fixed inside the housing. Two hollow columns are provided on both the upper and lower sides of the silo, and the hollow columns on the upper and lower sides are arranged in pairs. An annular plate is fixed above the two hollow columns on the upper side and below the two hollow columns on the lower side. An opening and closing plate is hinged to the bottom right side of the annular plate. When the opening and closing plate rotates to the top side, it contacts the annular plate to form a seal. A sliding rod slides through the right side of the silo, and a sliding plug is connected to the left end of the sliding rod. The sliding plug is slidably connected to the inside of the silo. A spring is abutted against the sliding plug. The end of the spring away from the sliding plug is connected to the silo. The two hollow columns on the upper side are connected to the inlet pipe above, and the two hollow columns on the lower side are connected to the outlet pipe below.

[0013] Preferably, the right side of the silo is embedded in the right side wall of the box body, and an annular internal thread groove is opened on the inner side of the right part of the silo. The end of the slide rod away from the sliding block is rotatably connected to a turntable. An external thread protrusion ring is provided on the outer periphery of the side of the turntable near the silo. When the slide rod moves to the leftmost position, the external thread protrusion ring is used to spirally lock into the annular internal thread groove to lock the position of the slide rod.

[0014] Preferably, the mixing and guiding structure includes three microchannels, the bottom of which is connected to the liquid collection seat. A spiral guide section is longitudinally arranged on the left side inside the liquid collection seat, and the upper rear part of the spiral guide section is connected to the guide microtube. The other end of the guide microtube is inserted into the detection chamber, which is beneficial for liquids from different flow paths to be fully mixed in the spiral guide section before being smoothly introduced into the detection chamber.

[0015] Compared with the prior art, the beneficial effects of the present invention are:

[0016] This invention highly integrates the entire process of sample lysis and purification, multi-reagent pre-storage and sequential release, fluid-driven mixing, and final detection into a single device. Users only need to perform extremely simple operations such as adding sample, pressing, and pulling to automatically complete the entire process from sample processing to result output. This integrated design of sample in and result out greatly reduces the professional requirements for operators, shortens the detection time, and can minimize sample cross-contamination, reagent contamination, and aerosol contamination that may be caused by manual operation, thus significantly improving the reliability and safety of detection.

[0017] This invention optimizes the flow-driving and mixing structures, enabling fluid control without the need for complex external pump and valve systems. The manually operated drive component integrates a one-way valve and a mechanical locking mechanism, reliably generating negative and positive pressures to precisely control liquid intake, pumping, and process pauses. The power source is simple and reliable. Simultaneously, the spiral guide section utilizes the passive microfluidic principle to achieve rapid and thorough mixing of multiple reagents during transport, ensuring reaction efficiency and uniformity. This makes the entire detection system independent of large peripheral equipment, compact in structure, and suitable for rapid on-site testing and resource-constrained environments, enhancing the product's portability and adaptability to various scenarios.

[0018] The porous membrane module of this invention enables real-time online lysis and purification of samples, providing high-quality targets for subsequent reactions; the independent reservoir blister and the pointed puncture structure ensure the stability of reagents during long-term storage and the precise and controllable release; the detection chamber, combined with the exhaust channel and optical window, eliminates bubble interference and optimizes the signal acquisition path; all modules constitute a stable and efficient microfluidic working system within the housing, thereby ensuring high sensitivity and reliable results in the detection process as a whole. Attached Figure Description

[0019] Figure 1 This is a schematic diagram of the structure of the present invention;

[0020] Figure 2 This is a schematic diagram of the internal structure of the box body of the present invention;

[0021] Figure 3 This is a schematic diagram of the flow-driving structure of the present invention;

[0022] Figure 4 This is a schematic diagram of the connection between the liquid inlet pipe and the drive assembly of the present invention;

[0023] Figure 5 For the present invention Figure 4 Enlarged view of the local structure at point A;

[0024] Figure 6 This is a schematic diagram of the connection between the silo and the slide bar in this invention;

[0025] Figure 7 This is a schematic diagram of the hybrid conductive structure of the present invention.

[0026] In the diagram: Box-1, Sheath-2, Liquid Inlet-3, Sealing Plug-4, Fluid Channel-5, Porous Membrane-6, Flow Driving Structure-7, Mixing and Conveying Structure-8, Detection Chamber-9, Exhaust Channel-10, Liquid Inlet Pipe-71, Liquid Storage Tank-72, Partition-73, Liquid Storage Bubble Cap-74, Drive Assembly-75, Liquid Outlet Pipe-76, Through-port-711, Hollow Plate-712, Point-713, Silo-751, Annular Plate-752, Opening and Closing Plate-753, Slide Rod-754, Sliding Plug-755, Spring-756, Annular Internal Threaded Groove-7511, Turntable-7541, External Threaded Convex Ring-7542, Microchannel-81, Liquid Collector-82, Spiral Guide Section-83, Guide Microtube-84. Detailed Implementation

[0027] To further explain the technical solution of the present invention, a detailed description is provided below through specific embodiments.

[0028] Please see Figure 1 and Figure 2 The present invention provides a microfluidic box for rapid detection of biomolecules, comprising an overall flat box body 1, a sheath 2, a liquid inlet 3, a sealing plug 4, a fluid channel 5, a porous membrane 6, a flow-driving structure 7, a mixing and conducting structure 8, a detection chamber 9, and an exhaust channel 10.

[0029] The box body 1 is injection molded from a transparent polymer material, which facilitates observation of the internal liquid flow and reaction state. The outer surface of the box body 1 is covered with a protective sleeve 2, which provides a non-slip grip and serves as physical protection and aesthetics for the internal structure. A liquid inlet 3 is provided on the upper front side of the box body 1. A sealing plug 4 is provided inside the liquid inlet 3 to ensure that the liquid inlet 3 is reliably sealed after the sample is added, preventing evaporation, contamination or leakage of biohazardous substances.

[0030] A fluid channel 5 is provided in the upper middle part of the box 1, and the top side of the fluid channel 5 is connected to the liquid inlet 3, providing the initial flow path for the sample. A porous membrane 6 is provided in the lower middle part of the fluid channel 5, which divides the fluid channel 5 into upper and lower parts, forming a physical filtration and reaction interface. Lysis reagents or nucleic acid binding solid phase materials are pre-embedded on the surface or inside of the porous membrane 6. When the sample liquid flows through the porous membrane 6, cells / viruses can be lysed immediately, and the released target nucleic acid can be specifically captured, realizing rapid on-site purification of the sample and eliminating the cumbersome centrifugation step.

[0031] A flow-driving structure 7 is connected to the right side of the fluid channel 5, located below the porous membrane 6. The flow-driving structure 7 provides fluid power and reagent source for subsequent processes. A mixing and guiding structure 8 is connected to the bottom of the flow-driving structure 7, and the bottom of the mixing and guiding structure 8 is inserted into the detection chamber 9 to form a continuous flow path from driving, mixing to detection. The detection chamber 9 is located in the lower middle part of the housing 1. Its bottom is an optically transparent detection window, which allows external optical detection equipment to read signals from below without interference. The top inner wall of the detection chamber 9 is fixed with a pre-embedded detection probe array (such as a microarray of fixed specific oligonucleotide probes or antigens / antibodies), and the detection probe array is directly opposite the detection window to ensure that the signal generated by the reaction can be efficiently collected and improve the detection sensitivity. An exhaust channel 10 is provided at the upper rear part of the detection chamber 9 to exhaust the internal air when liquid is injected into the detection chamber 9, ensuring that the chamber is completely and bubble-free, and guaranteeing reaction uniformity and detection accuracy.

[0032] Please see Figures 1-6This invention provides a microfluidic cartridge for rapid biomolecular detection. The flow-driving structure 7 includes an inlet pipe 71 connected to a fluid channel 5 on the left side. A storage chamber 72 is locked and fixed to the top of the inlet pipe 71 away from the fluid channel 5. At least one partition 73 is embedded inside the storage chamber 72 to form multiple independent storage compartments, achieving physical separation and storage of various reagents to avoid cross-contamination or premature reaction. Each storage compartment is provided with a storage blister 74. Pads are provided on both the left and right sides of the bottom of the storage compartment to support the storage blister 74, protecting it from accidental crushing during transportation and storage, and ensuring reagent stability. The multiple storage blister 74s contain different liquid reagents, such as elution buffer, nucleic acid amplification reaction premix (such as LAMP, RPA reagents), fluorescent detection substrates, etc. All the key reagents required for the detection process are integrated into the cartridge, realizing reagent pre-storage. Users do not need to prepare or add reagents manually, simplifying operation and reducing the risk of contamination.

[0033] The liquid inlet pipe 71 has an opening 711 on its top side corresponding to the storage chamber. A perforated piece 712 is embedded in the lower middle side of the opening 711. Under normal conditions, it is isolated from the storage chamber, but it becomes a liquid channel when needed. A pointed tip 713 is integrally formed on the top of the perforated piece 712. The top tip of the pointed tip 713 is inserted into the bottom side of the storage chamber, forming a reliable puncture structure. When the user presses the area above the corresponding storage chamber from the outside of the box 1, the liquid blister 74 is pushed downward and punctured by the pointed tip 713, forming a simple, reliable, and user-controlled reagent release mechanism. Different reagents can be activated in sequence according to the detection process. The released liquid reagent then flows into the liquid inlet pipe 71 through the perforated piece 712.

[0034] The two outlets at the bottom of the inlet pipe 71 are connected to the drive assembly 75. The drive assembly 75 includes a silo 751 fixed inside the box 1. Two hollow columns are provided on the upper and lower sides of the silo 751, and the hollow columns on the upper and lower sides are arranged in pairs. An annular plate 752 is fixed above the two hollow columns on the upper side and below the two hollow columns on the lower side. An opening and closing plate 753 is hinged to the bottom right side of the annular plate 752, which together form a one-way valve structure. When the opening and closing plate 753 rotates to the top side, it contacts the annular plate 752 to form a seal, ensuring that the fluid can only pass through in one direction and preventing backflow.

[0035] A sliding rod 754 slides through the right side of the silo 751, and a sliding plug 755 is connected to the left end of the sliding rod 754. The sliding plug 755 is slidably connected inside the silo 751, and a spring 756 abuts against the sliding plug 755. The end of the spring 756 away from the sliding plug 755 is connected to the silo 751. The spring 756 provides a reset force for the sliding plug 755 and converts the user's pulling and pushing operations into suction and pushing forces on the liquid. The two hollow columns on the upper side are connected to the liquid inlet pipe 71, and the two hollow columns on the lower side are connected to the liquid outlet pipe 76, forming a complete manual pumping circuit.

[0036] The silo 751 is embedded in the right side wall of the box 1, and an annular internal thread groove 7511 is provided on the inner side of the right part of the silo 751. The end of the slide rod 754 away from the sliding plug 755 is rotatably connected to the turntable 7541. The outer periphery of the turntable 7541 near the silo 751 is provided with an external thread protrusion ring 7542, forming a separable locking mechanism. After the user pulls the turntable 7541 outward to move the slide rod 754 and the sliding plug 755 to the right (inhalation stage), the turntable 7541 is pushed back to the left and rotated, so that the external thread protrusion ring 7542 can be screwed into the annular internal thread groove 7511, locking the sliding plug 755 in the compressed position, allowing the user to perform other operations in the locked state (such as pressing a liquid storage blister).

[0037] The two outlets at the bottom of the drive assembly 75 are connected to the liquid outlet pipe 76. The liquid outlet pipe 76 has three flow outlets at the bottom, and the bottoms of the three flow outlets are connected to the mixing and guiding structure 8 to reasonably distribute the pumped liquid into the mixing and guiding structure 8.

[0038] Please see Figure 2 , Figure 3 and Figure 7 This invention provides a microfluidic cartridge for rapid detection of biomolecules. The mixing and guiding structure 8 includes three microchannels 81, the bottom of which are all connected to a liquid collection seat 82 to initially converge liquid flows from different outlets of the liquid outlet pipe 76. A spiral guide section 83 is longitudinally arranged on the left side inside the liquid collection seat 82. The spiral channel extends the mixing path and generates micro-vortices, so that multi-component liquids (such as eluent, amplification reagent, and detection reagent) pumped in sequentially or from different flow paths can be rapidly and fully passively mixed here without the need for an external stirring device.

[0039] The upper rear part of the spiral guide section 83 is connected to the guide microtube 84. The other end of the guide microtube 84 is inserted into the detection cavity 9, so that the fully mixed reaction liquid is smoothly and controllably introduced into a specific position of the detection cavity 9, avoiding direct impact of the liquid on the detection probe array and ensuring a uniform and stable reaction interface.

[0040] The present invention provides a microfluidic cell for rapid detection of biomolecules, the working principle of which is as follows:

[0041] First, the user opens the sealing plug 4 and adds the liquid sample to be tested through the inlet 3. Under the action of gravity or the subsequent negative pressure, the sample enters the fluid channel 5 and flows through the porous membrane 6, which is pre-embedded with lysis reagent and nucleic acid binding solid material. This causes the cells or viruses in the sample to be lysed immediately and the impurities to be separated. Thus, the rapid lysis and purification of the sample is automatically completed in the box, providing clean target material for subsequent detection.

[0042] Second, according to the detection process sequence, press the corresponding storage chamber area on the liquid storage tank 72 from the outside of the box 1. This pressing action causes the liquid storage blister 74 in the storage chamber to move downward and be pierced by the tip 713 pre-placed at the opening 711 on the lower liquid inlet pipe 71. The liquid reagents (such as elution buffer, amplification reaction solution, detection substrate, etc.) sealed in different liquid storage blister 74 are thus released as needed and in sequence, and flow into the lower liquid inlet pipe 71 through the perforated piece 712.

[0043] Third, the liquid is driven to flow along a preset path by operating the drive component 75. Specifically, the user pulls the turntable 7541 outward, causing the slide bar 754 and the sliding plug 755 to move to the right, generating a negative pressure in the left chamber of the silo 751. This negative pressure draws the liquid in the inlet pipe 71 into the silo 751 through the one-way valve composed of the annular plate 752 and the opening and closing plate 753. Subsequently, the user pushes the turntable 7541 back and rotates it, causing the external threaded protrusion ring 7542 to lock into the annular internal threaded groove 7511. At this time, the sliding plug 755 moves to the left to generate positive pressure, pumping the liquid in the chamber out through the one-way valve below to the outlet pipe 76 and delivering it to the mixing and guiding structure 8. After the liquid is initially distributed in the three microchannels 81 of the mixing and guiding structure 8, it flows into the spiral guide section 83 of the liquid collecting seat 82. The micro vortex generated by the spiral channel achieves rapid and sufficient passive mixing of different liquid components. Finally, the mixed liquid is smoothly introduced into the detection chamber 9 through the guide microtube 84.

[0044] Fourth, after the mixed reaction solution enters the detection chamber 9, the air inside the chamber is discharged through the exhaust channel 10, ensuring that the liquid completely fills the chamber. The target molecules in the liquid react specifically with the detection probe array pre-embedded in the top wall of the detection chamber 9 (such as hybridization or immune binding) and generate a detectable signal (such as fluorescence). At this time, through the optically transparent detection window at the bottom of the box 1, the external optical detection equipment can collect and read the reaction signal without interference, thereby completing the entire rapid detection process of sample entry and result exit.

[0045] The above description is merely a preferred embodiment of the present invention and is not intended to limit the present invention. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art can still modify the technical solutions described in the foregoing embodiments or make equivalent substitutions for some of the technical features. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A microfluidic cartridge for rapid detection of biomolecules, comprising a cartridge body (1), wherein a sheath (2) is provided on the outer surface of the cartridge body (1), and a liquid inlet (3) is provided on the upper front side of the cartridge body (1), wherein a sealing plug (4) is provided inside the liquid inlet (3), and a fluid channel (5) is provided in the upper middle part of the cartridge body (1), wherein the top side of the fluid channel (5) is connected to the liquid inlet (3), characterized in that, A porous membrane (6) is disposed on the lower side of the fluid channel (5), and a flow-driving structure (7) is disposed on the right side below the porous membrane (6). The porous membrane (6) divides the fluid channel (5) into upper and lower parts, and a lysis reagent and a nucleic acid binding solid phase material are pre-embedded on the surface or inside of the porous membrane (6). A mixing and conducting structure (8) is connected to the bottom of the flow-driving structure (7), and the bottom of the mixing and conducting structure (8) is inserted into the detection chamber (9). The detection chamber (9) is disposed in the lower middle part of the box body (1), and an exhaust channel (10) is disposed at the upper rear part of the detection chamber (9). The flow-driving structure (7) includes a left side connected to the fluid channel. (5) A liquid inlet pipe (71) is connected to the liquid inlet pipe (71). A liquid storage chamber (72) is locked and fixed on the side of the liquid inlet pipe (71) away from the fluid channel (5). At least one partition (73) is embedded in the liquid storage chamber (72) to form multiple storage chambers inside the liquid storage chamber (72). A liquid storage bubble (74) is provided in the storage chamber. The two outlets at the bottom of the liquid inlet pipe (71) are connected to the drive assembly (75). The two outlets at the bottom of the drive assembly (75) are connected to the liquid outlet pipe (76). The bottom of the liquid outlet pipe (76) is provided with three flow outlets, and the bottom of the three flow outlets is connected to the mixing and guiding structure (8).

2. The microfluidic cartridge for rapid detection of biomolecules according to claim 1, characterized in that: The bottom of the detection cavity (9) is an optically transparent detection window, and a pre-embedded detection probe array is fixed on the top inner wall of the detection cavity (9), with the detection probe array facing the detection window.

3. The microfluidic cartridge for rapid detection of biomolecules according to claim 1, characterized in that: The storage chamber has pads on both the left and right sides at the bottom to support the liquid storage blister (74), and different liquid reagents are sealed inside the multiple liquid storage blister (74).

4. The microfluidic cartridge for rapid detection of biomolecules according to claim 1, characterized in that: The top side of the inlet pipe (71) is provided with the same number of openings (711) as the storage chamber, and a hollow piece (712) is embedded in the lower middle side of the opening (711) to connect the storage chamber and the inlet pipe (71).

5. A microfluidic cartridge for rapid detection of biomolecules according to claim 4, characterized in that: The hollow piece (712) has a pointed tip (713) integrally formed on its upper part, and the top tip of the pointed tip (713) is inserted into the bottom side of the storage chamber.

6. The microfluidic cartridge for rapid detection of biomolecules according to claim 1, characterized in that: The drive assembly (75) includes a silo (751) fixed inside the housing (1). Two hollow columns are provided on both the upper and lower sides of the silo (751), and the hollow columns on the upper and lower sides are arranged in pairs. Annular plates (752) are fixed above the two upper hollow columns and below the two lower hollow columns. An opening / closing plate (753) is hinged to the bottom right side of the annular plate (752). When the opening / closing plate (753) rotates to its highest position, it contacts the annular plate (752) to form a seal. A sliding rod (754) slides through the right side of the interior, and a sliding plug (755) is connected to the left end of the sliding rod (754). The sliding plug (755) is slidably connected to the inside of the silo (751). The sliding plug (755) abuts against a spring (756). The end of the spring (756) away from the sliding plug (755) is connected to the silo (751). The two hollow columns on the upper side are connected to the inlet pipe (71) above, and the two hollow columns on the lower side are connected to the outlet pipe (76) below.

7. A microfluidic cartridge for rapid detection of biomolecules according to claim 6, characterized in that: The silo (751) is embedded in the right side wall of the box body (1), and an annular internal thread groove (7511) is provided on the inner side of the right side of the silo (751).

8. A microfluidic cartridge for rapid detection of biomolecules according to claim 7, characterized in that: The end of the slide rod (754) away from the sliding block (755) is rotatably connected to a turntable (7541). The turntable (7541) has an external threaded protrusion ring (7542) on its outer periphery near the silo (751). When the slide rod (754) moves to the leftmost position, the external threaded protrusion ring (7542) is used to spirally lock into the annular internal thread groove (7511).

9. A microfluidic cartridge for rapid detection of biomolecules according to claim 1, characterized in that: The mixed-conducting structure (8) includes three microchannels (81), the bottom of which is connected to the liquid collection seat (82). The liquid collection seat (82) has a spiral guide section (83) arranged longitudinally on the left side, and the upper rear part of the spiral guide section (83) is connected to the guide microtube (84). The other end of the guide microtube (84) is inserted into the detection cavity (9).

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