Microfluidic chip and microfluidic detection device

Abstract

The application discloses a micro-fluidic chip and a micro-fluidic detection device. The micro-fluidic chip comprises a chip main body, a plurality of columnar chambers and a reverse L-shaped detection chamber, and the two are isolated from each other; a rotating plunger is rotatably assembled in the chip main body, and a plurality of micro-fluidic channels are etched on the surface of the rotating plunger, and the rotating plunger is used for selectively connecting different columnar chambers or connecting the columnar chamber and the detection chamber; a rubber sealing ring is nested between the chip main body and the rotating plunger, and the through hole of the rubber sealing ring is aligned with the columnar chamber; the detection device comprises a bottom plate, a liquid driving module, a rotating driving module, an optical detection module and a control module; the micro-fluidic chip is arranged on the bottom plate; the liquid driving module is used for injecting samples and reagents and discharging waste liquid; the rotating driving module is connected with the rotating plunger and is used for driving the rotating plunger to rotate; the optical detection module is used for detecting the detection chamber; and the control module is electrically connected with each module and is used for controlling the actions of each module. The application can realize the automation of nucleic acid extraction, amplification and detection, and reduces the dependence on professionals.

Description

Technical Field

[0001] This invention relates to the field of nucleic acid detection technology, and in particular to a microfluidic chip and a microfluidic detection device. Background Technology

[0002] Nucleic acid testing is a key technology for disease diagnosis, epidemic prevention and control, food safety, and environmental monitoring. Microfluidic technology, with its advantages of low reagent consumption, fast reaction speed, and high integration, has been widely applied in the development of integrated platforms for nucleic acid extraction, amplification, and detection.

[0003] Existing microfluidic nucleic acid testing platforms are mostly benchtop devices, generally characterized by their large size, complex structure, and cumbersome operation. They require highly skilled operators and are difficult to deploy rapidly in non-laboratory environments such as field sites, grassroots units, and outdoor locations. Furthermore, traditional nucleic acid testing processes rely on the coordinated operation of multiple pumps, valves, pipelines, and temperature control units, resulting in complex liquid path control and susceptibility to leaks, blockages, and uneven temperature control, leading to insufficient testing stability and repeatability. In addition, existing systems often employ a split design, making it difficult to highly integrate nucleic acid extraction, amplification, and detection modules within a limited space. This results in poor portability, high costs, and difficult maintenance, failing to meet the practical needs of on-site testing. Summary of the Invention

[0004] This invention aims to address at least one of the technical problems existing in the prior art. To this end, this invention proposes a microfluidic chip and a microfluidic detection device that can automate the entire process of nucleic acid extraction, amplification, and signal detection, reducing reliance on professional operators.

[0005] In a first aspect, a microfluidic chip according to embodiments of the present invention includes: The chip body has several cylindrical chambers of different volumes and an inverted L-shaped detection chamber, and the cylindrical chambers and the detection chamber are isolated from each other; A rotating plunger, with several microfluidic channels etched on its surface, is rotatably mounted within the chip body and seals against the cylindrical chamber and the detection chamber. The cylindrical chamber and the detection chamber are selectively fluidly connected via the rotating plunger. By rotating the rotating plunger, the several microfluidic channels selectively connect different cylindrical chambers or connect the cylindrical chamber and the detection chamber, thereby achieving the opening and closing of the liquid path and the mixing of the liquid. A rubber sealing ring is nested between the chip body and the rotating plunger to achieve liquid circuit sealing. The upper surface of the rubber sealing ring has several through holes, which are aligned with and connected to the cylindrical cavity.

[0006] The microfluidic chip according to embodiments of the present invention has at least the following beneficial effects: selective fluid communication between cylindrical chambers or between a cylindrical chamber and a detection chamber is achieved by rotating a rotary plunger; each microfluidic channel is a groove, and when the rotary plunger rotates to a specific angle, the two ends of the microfluidic channel are respectively aligned with two different chamber ports, thereby connecting the two chambers; a through hole is provided on the rubber sealing ring nested between the chip body and the rotary plunger, the through hole is aligned with and connected to the cylindrical chamber, and the liquid in the cylindrical chamber flows in through the through hole, ensuring the fluid path sealing; Compared with existing technologies, this invention achieves sequential connectivity between multiple chambers through the rotation of a single rotating plunger, replacing the complex external valve structure, simplifying the chip structure, and reducing costs; the cylindrical chambers are isolated from each other and selectively connected to the detection chamber through the rotating plunger, effectively avoiding cross-contamination; the inverted L-shaped detection chamber provides a continuous reaction space for nucleic acid amplification and CRISPR detection, realizing the integration of nucleic acid extraction and detection.

[0007] According to some embodiments of the present invention, the number of cylindrical chambers is five, and the number of through holes is seven, wherein five of the through holes are connected to the five cylindrical chambers in a one-to-one correspondence, and the remaining two through holes are used to realize gas discharge or waste liquid conduction.

[0008] According to some embodiments of the present invention, the number of microfluidic channels is six, and the length of each microfluidic channel is different; when the rotating plunger is rotated to different angles, the plurality of microfluidic channels selectively connect different cylindrical chambers or connect cylindrical chambers and detection chambers.

[0009] Secondly, the microfluidic detection device including the above-described microfluidic chip according to embodiments of the present invention further includes: The microfluidic chip is mounted on the base plate. A liquid-driven module, mounted on the base plate, is used to inject samples and reaction reagents into the cylindrical chamber and discharge waste liquid after the reaction is completed. A rotary drive module is mounted on the base plate, and its output end is connected to the rotary plunger to control the rotary plunger to rotate to different angle positions; An optical detection module, mounted on the base plate, is used for optical detection of the liquid in the detection chamber; A control module, mounted on the base plate, is electrically connected to the liquid driving module, the rotation driving module, and the optical detection module, respectively, and is used to control the actions of the liquid driving module, the rotation driving module, and the optical detection module to automate nucleic acid extraction, amplification, and signal detection.

[0010] The microfluidic detection device according to the embodiments of the present invention has at least the following beneficial effects: by integrating the microfluidic chip, liquid driving module, rotation driving module, optical detection module and control module on the same substrate, the integration of sample processing and detection is realized; Compared with the bulky and complex benchtop microfluidic detection systems in the prior art, the device of the present invention is compact, small in size, and easy to carry, making it suitable for use in confined spaces or field environments. At the same time, the control module is electrically connected to the liquid drive module, the rotation drive module, and the optical detection module respectively, which coordinates the action sequence of each module and realizes full automation of nucleic acid extraction, amplification, and signal detection, reducing the dependence on professional operators.

[0011] According to some embodiments of the present invention, the liquid driving module includes a first stepper motor, a slide, a pusher plate, and a piston; the first stepper motor drives the slide to move, the slide moves the pusher plate, and the pusher plate pushes the piston so that the pump chamber where the piston is located quantitatively pumps the sample and reaction reagents to the microfluidic chip.

[0012] According to some embodiments of the present invention, the rotary drive module is a second stepper motor, and the output shaft of the second stepper motor is fixedly connected to the end of the rotary plunger.

[0013] According to some embodiments of the present invention, the optical detection module includes an excitation light source, a fluorescence signal receiver, and a first support; the excitation light source is fixed on the base plate by the first support and is disposed facing the detection chamber; the fluorescence signal receiver is disposed on the light-emitting side of the detection chamber.

[0014] According to some embodiments of the present invention, the excitation light source is a blue light source containing a 495nm filter, and the fluorescence signal receiver is a CCD camera containing a 520nm filter.

[0015] According to some embodiments of the present invention, a heating plate and a temperature controller are also included, wherein the heating plate is connected to the temperature controller and is attached to the microfluidic chip for providing temperature control for the reaction.

[0016] According to some embodiments of the present invention, the device further includes a housing, a touch screen, and a hinged plate. The housing is disposed on the base plate, the touch screen is embedded in the housing and electrically connected to the control module, and the hinged plate is disposed on the housing for opening the housing.

[0017] Additional aspects and advantages of the invention will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. Attached Figure Description

[0018] To more clearly illustrate the technical solutions of the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0019] Figure 1 This is a schematic diagram of the structure of a microfluidic chip according to an embodiment of the present invention; Figure 2 This is a schematic diagram of the chip body structure according to an embodiment of the present invention; Figure 3 This is a schematic diagram of the structure of the rubber sealing ring according to an embodiment of the present invention; Figure 4 This is a schematic diagram of the rotating plunger according to an embodiment of the present invention; Figure 5 This is a schematic diagram of the assembly structure of the chip body, rubber sealing ring, and rotating plunger according to an embodiment of the present invention; Figure 6 This is a schematic diagram of the microfluidic detection device according to an embodiment of the present invention; Figure 7 This is a schematic diagram of the structure of a microfluidic detection device with a housing according to an embodiment of the present invention.

[0020] Explanation of reference numerals in the attached drawings: Chip body 100; Cylindrical chamber 110; Detection chamber 120; Rotary plunger 200; Microfluidic channel 210; Rubber sealing ring 300; Through hole 310; Base plate 400; Liquid drive module 500; Slide stage 510; Push plate 520; Piston 530; Rotary drive module 600; Second stepper motor 610; Optical detection module 700; Excitation light source 710; Fluorescent signal receiver 720; First support 730; Control module 800; Raspberry Pi 810; Second support 820; Heating plate 900; Temperature controller 910; Housing 920; Touch screen 930; Opening and closing plate 940; Motor controller 950; Electromagnet 960. Detailed Implementation

[0021] Embodiments of the present invention are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present invention, and should not be construed as limiting the present invention.

[0022] In the description of this invention, it should be understood that the orientation descriptions, such as up, down, front, back, left, right, etc., indicating the orientation or positional relationship, are based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this invention and simplifying the description, and are not intended to indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this invention.

[0023] In the description of this invention, "several" means one or more, "more than" means two or more, "greater than," "less than," and "exceeding" are understood to exclude the stated number, while "above," "below," and "within" are understood to include the stated number. If "first" and "second" are mentioned, this is only for distinguishing technical features and should not be construed as indicating or implying relative importance, or implicitly indicating the number of indicated technical features, or implicitly indicating the order of the indicated technical features.

[0024] In the description of this invention, it should be noted that, unless otherwise explicitly specified and limited, the terms "installation, connection, and linkage" should be interpreted broadly. For example, they can refer to fixed connections, detachable connections, or integral connections; they can refer to mechanical connections or electrical connections; they can refer to direct connections or indirect connections through an intermediate medium; and they can refer to the internal communication between two components. Those skilled in the art can understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0025] The microfluidic chip and microfluidic detection device according to embodiments of the present invention are described below with reference to the accompanying drawings.

[0026] Firstly, referring to Figures 1-5 According to an embodiment of the present invention, a microfluidic chip includes: The chip body 100 has several cylindrical chambers 110 with different volumes and an inverted L-shaped detection chamber 120. The cylindrical chambers 110 and the detection chamber 120 are isolated from each other. The rotary plunger 200 has several microfluidic channels 210 etched on its surface. The rotary plunger 200 is rotatably mounted inside the chip body 100 and is sealed to the cylindrical chamber 110 and the detection chamber 120. The cylindrical chamber 110 and the detection chamber 120 are selectively fluidly connected through the rotary plunger 200. By rotating the rotary plunger 200, the several microfluidic channels 210 selectively connect different cylindrical chambers 110 or connect the cylindrical chamber 110 and the detection chamber 120 to realize the opening and closing of the liquid path and the mixing of the liquid. A rubber sealing ring 300 is nested between the chip body 100 and the rotary plunger 200 to achieve liquid circuit sealing. Several through holes 310 are opened on the upper surface of the rubber sealing ring 300. The through holes 310 are aligned with and connected to the cylindrical cavity 110.

[0027] In this embodiment, multiple cylindrical chambers 110 and inverted L-shaped detection chambers 120 are isolated from each other by means of a rotating plunger 200 with microfluidic channels 210 etched on its surface, and are rotatably mounted in the chip body 100, thereby achieving selective fluid communication between cylindrical chambers 110 or between cylindrical chambers 110 and detection chambers 120. Each microfluidic channel 210 on the rotating plunger 200 is a groove. When the rotating plunger 200 is rotated to a specific angle, the two ends of the channel are aligned with the ports of two different chambers, thereby connecting the two chambers.

[0028] In addition, the through hole 310 on the rubber sealing ring 300 nested between the chip body 100 and the rotary plunger 200 is aligned with and connected to the cylindrical chamber 110. The liquid in the cylindrical chamber 110 flows in through the through hole 310 on the rubber sealing ring 300, ensuring the liquid circuit is sealed.

[0029] Compared with existing microfluidic chips that use external valves or multi-layer soft lithography structures, this invention achieves sequential connectivity between multiple chambers simply by rotating a single rotating plunger 200, replacing the complex external valve structure, significantly simplifying the chip structure and reducing manufacturing costs. The cylindrical chambers 110 are isolated from each other and selectively connected to the detection chamber 120 by the rotating plunger 200, effectively avoiding cross-contamination between different reagents. The inverted L-shaped detection chamber 120 provides a continuous reaction space for nucleic acid amplification and CRISPR detection, realizing the integration of nucleic acid extraction and detection.

[0030] According to some embodiments of the present invention, for example, Figures 1-3 As shown, there are five cylindrical chambers 110 and seven through holes 310. Five of the through holes 310 are connected to the five cylindrical chambers 110 in a one-to-one correspondence, and the remaining two through holes 310 are used to realize gas discharge or waste liquid conduction.

[0031] In this embodiment, this design allows each of the five cylindrical chambers 110 to have a dedicated inlet for liquid delivery, while the remaining two through holes 310 can serve as vents to prevent air blockage during liquid delivery or as waste liquid channels to discharge reaction waste liquid, thereby improving the stability of liquid flow and the functional integrity of the chip. At the same time, the design that the number of through holes 310 exceeds the number of chambers provides a structural basis for the functional expansion of the chip, making it easy to add reagent chambers or waste liquid chambers according to different detection needs.

[0032] According to some embodiments of the present invention, for example, Figure 4As shown, there are six microfluidic channels 210, each with a different length. When the rotating plunger 200 is rotated to different angles, the microfluidic channels 210 selectively connect different cylindrical chambers 110 or connect cylindrical chambers 110 with detection chambers 120.

[0033] In this embodiment, the surface of the rotating plunger 200 is engraved with six microfluidic channels 210, each with a specified length. When the rotating plunger 200 rotates to a first angle, the two ends of the first microfluidic channel 210 align with the ports of the first cylindrical chamber 110 and the second cylindrical chamber 110, respectively, connecting the two chambers. When rotated to a second angle, the two ends of the second microfluidic channel 210 align with the ports of the second and third cylindrical chambers 110, respectively, connecting the two chambers; and so on. When rotated to a fifth angle, the two ends of the fifth microfluidic channel 210 align with the ports of the fifth cylindrical chamber 110 and the detection chamber 120, respectively, thereby delivering the purified nucleic acid solution to the detection chamber 120. The remaining sixth microfluidic channel 210 can be used for backup or to implement other connection paths.

[0034] In one specific embodiment of the present invention, for example, as Figure 1 and Figure 2 As shown, the five cylindrical chambers 110 are configured as follows: the first chamber is the sample chamber, used to add the sample to be tested; the second chamber is the lysis buffer chamber, containing cell lysis buffer; the third chamber is the washing buffer chamber, containing magnetic bead washing buffer; the fourth chamber is the elution buffer chamber, containing nucleic acid elution buffer; and the fifth chamber is the waste liquid chamber, used to collect reaction waste liquid. It is understood that the specific allocation of the cylindrical chambers 110 is not limited to this, and those skilled in the art can adjust it according to actual testing needs.

[0035] According to some embodiments of the present invention, for example, Figure 5 As shown, the rubber sealing ring 300 has a hexagonal outer shape and a circular inner shape.

[0036] In this embodiment, the external hexagonal design facilitates the positioning and assembly of the rubber sealing ring 300 with the hexagonal groove on the chip body 100, preventing the rubber sealing ring 300 from sliding or deflecting circumferentially during the rotation of the rotating plunger 200, and ensuring the alignment accuracy between the through hole 310 and the cylindrical chamber 110; the internal circular design fits tightly with the cylindrical surface of the rotating plunger 200, allowing the rotating plunger 200 to rotate freely while ensuring the fluid circuit sealing, effectively preventing leakage and cross-contamination of liquid between different chambers.

[0037] Secondly, referring to Figure 6 According to an embodiment of the present invention, the microfluidic detection device including the above-described microfluidic chip further includes: The microfluidic chip is mounted on the base plate 400. The liquid driving module 500, mounted on the base plate 400, is used to inject the sample and reaction reagents into the cylindrical chamber 110 and discharge the waste liquid after the reaction is completed. A rotary drive module 600 is mounted on a base plate 400, and its output end is connected to a rotary plunger 200 to control the rotary plunger 200 to rotate to different angle positions. An optical detection module 700 is mounted on a base plate 400 and is used to perform optical detection on the liquid in the detection chamber 120. The control module 800 is mounted on the base plate 400 and is electrically connected to the liquid drive module 500, the rotation drive module 600 and the optical detection module 700 respectively. It is used to control the actions of the liquid drive module 500, the rotation drive module 600 and the optical detection module 700 to realize the automation of nucleic acid extraction, amplification and signal detection.

[0038] In this embodiment, by integrating the microfluidic chip, liquid driving module 500, rotation driving module 600, optical detection module 700 and control module 800 on the same base plate 400, the integration of sample processing and detection is achieved.

[0039] Compared with the bulky and complex desktop microfluidic detection systems in the prior art, the device of the present invention is compact, small in size, and easy to carry, making it suitable for use in confined spaces or on-site environments. At the same time, the control module 800 is electrically connected to the liquid driving module 500, the rotation driving module 600 and the optical detection module 700 respectively, which coordinates the action sequence of each module and realizes the full automation of nucleic acid extraction, amplification and signal detection, reducing the dependence on professional operators.

[0040] The entire detection process is completed automatically within the microfluidic detection device and consists of three main stages: Nucleic acid extraction stage: sample lysis → nucleic acid release → washing and purification → elution to obtain nucleic acid solution; Nucleic acid amplification stage: Nucleic acid solution enters the detection chamber at 120°C → isothermal amplification; CRISPR detection stage: CRISPR reaction → fluorescence signal excitation and acquisition.

[0041] According to some embodiments of the present invention, for example, Figure 6 As shown, the liquid drive module 500 includes a first stepper motor (not shown), a slide 510, a pusher plate 520, and a piston 530. The first stepper motor drives the slide 510 to move, the slide 510 drives the pusher plate 520, and the pusher plate 520 pushes the piston 530 so that the pump chamber where the piston 530 is located pumps the sample and reaction reagents quantitatively to the microfluidic chip.

[0042] In this embodiment, compared with the liquid driving method using an external injection pump or peristaltic pump in the prior art, the liquid driving module 500 of the present invention has a simple structure and is easy to integrate. The first stepper motor can accurately control the displacement of the piston 530, realizing precise quantitative pumping of micro-level liquids and ensuring the repeatability and accuracy of the test results. At the same time, the matching structure between the piston 530 and the pump chamber is directly integrated into the device, eliminating the need for complex external liquid pipelines, thus improving the portability and reliability of the device.

[0043] According to some embodiments of the present invention, for example, Figure 6 As shown, the rotary drive module 600 is a second stepper motor 610, and the output shaft of the second stepper motor 610 is fixedly connected to the end of the rotary plunger 200.

[0044] In this embodiment, compared with the complex gear transmission or worm gear mechanism used in the prior art, the rotary drive module 600 of the present invention directly drives the rotary plunger 200 through the second stepper motor 610. The transmission chain is short and the response is fast. The second stepper motor 610 can precisely control the rotation angle of the rotary plunger 200, realizing precise switching of different liquid circuit connection states. At the same time, the fixed connection between the output shaft and the end of the rotary plunger 200 ensures the reliability of the transmission and the stability of the position, ensuring the sequential execution of each reaction step in the microfluidic chip.

[0045] According to some embodiments of the present invention, for example, Figure 6 As shown, the optical detection module 700 includes an excitation light source 710, a fluorescence signal receiver 720, and a first bracket 730; the excitation light source 710 is fixed on the base plate 400 by the first bracket 730 and is positioned facing the detection chamber 120; the fluorescence signal receiver 720 is located on the light-emitting side of the detection chamber 120.

[0046] In this embodiment, this structural design enables real-time, online fluorescence signal acquisition of the reaction products in the detection chamber 120; the excitation light source 710 is fixed by the first bracket 730 to ensure the relative position stability between the light source and the detection chamber 120, avoiding optical path deviation caused by vibration or displacement; the fluorescence signal receiver 720 is set on the light-emitting side to maximize the collection of emitted fluorescence and improve the detection sensitivity.

[0047] According to some embodiments of the present invention, for example, Figure 6 As shown, the excitation light source 710 is a blue light source containing a 495nm filter, and the fluorescence signal receiver 720 is a CCD camera containing a 520nm filter.

[0048] In this embodiment, the 495nm blue excitation light matches the excitation wavelength of fluorescent reporter groups (such as FAM) commonly used in CRISPR detection, and the 520nm receiving light matches the emission wavelength of FAM. This combination of optical parameters significantly improves the sensitivity and specificity of CRISPR detection. At the same time, the CCD camera has high sensitivity and wide dynamic range, which can acquire weak fluorescence signals and is suitable for the detection of low-concentration nucleic acid samples. The use of filters effectively filters out the interference of stray light, further improving the detection accuracy.

[0049] According to some embodiments of the present invention, for example, Figure 6 As shown, it also includes a heating plate 900 and a temperature controller 910. The heating plate 900 and the temperature controller 910 are connected and attached to the microfluidic chip to provide temperature control for the reaction.

[0050] In this embodiment, the heating plate 900 is directly attached to the surface of the microfluidic chip, with a short heat transfer path and low thermal resistance, which can quickly transfer heat to the reaction chamber inside the microfluidic chip; the temperature controller 910 can monitor and adjust the temperature of the heating plate 900 in real time to maintain a constant reaction temperature, ensuring the stable progress of the isothermal amplification reaction, thereby improving the reliability and repeatability of the detection results.

[0051] According to some embodiments of the present invention, for example, Figure 7 As shown, it also includes a housing 920, a touch screen 930, and a hinged plate 940. The housing 920 is mounted on the base plate 400, the touch screen 930 is embedded in the housing 920 and electrically connected to the control module 800, and the hinged plate 940 is closably disposed on the housing 920 for opening the housing 920.

[0052] In this embodiment, the touch screen 930 serves as a human-machine interface, allowing operators to input commands, monitor the detection process, and view detection results. The operation is simple and intuitive. The hinged plate 940 can open the outer shell 920, facilitating the operator to place and remove the microfluidic chip. The outer shell 920 protects the internal modules from interference from external environmental factors such as dust and liquid splashes, while also making the device look neat and easy to carry.

[0053] According to some embodiments of the present invention, for example, Figure 6 As shown, the control module 800 is a Raspberry Pi 810.

[0054] In this embodiment, the Raspberry Pi 810 is mounted on the base plate 400 via the second bracket 820. As an open-source microcomputer, the Raspberry Pi 810 is characterized by low cost, small size, and rich interfaces, making it ideal as the control core of a portable detection device. The Raspberry Pi 810 can run customized control programs and communicate with peripheral modules such as the stepper motor controller 950, temperature controller 910, and CCD camera through its general-purpose input / output interface. This allows for flexible implementation of complex functions such as liquid circuit switching timing control, temperature PID adjustment, fluorescence signal acquisition, and data processing, significantly reducing the development cost and size of the control system.

[0055] According to some embodiments of the present invention, for example, Figure 6 As shown, it also includes a motor controller 950, which is electrically connected to the first motor and the second motor.

[0056] In this embodiment, the motor controller 950 manages the two stepper motors in a unified manner, coordinating the timing of liquid pumping and rotary plunger 200 switching to ensure the sequential execution of the reaction steps. At the same time, the motor controller 950 can realize the stepper motor microstepping drive, further subdividing each step into multiple microsteps, thereby improving the positioning accuracy of liquid pumping and valve switching, making the liquid delivery volume more precise and the rotation angle more accurate, further enhancing the automation level of the detection device and the reliability of the detection results.

[0057] According to some embodiments of the present invention, for example, Figure 6 As shown, it also includes an electromagnet 960, which is used to lock the position of the rotating plunger 200.

[0058] In this embodiment, after the rotary drive module 600 drives the rotary plunger 200 to the target angle, the electromagnet 960 is energized to generate a pulling force, locking the rotary plunger 200 in its current position. This prevents the rotary plunger 200 from rotating unexpectedly due to device vibration or fluctuations in liquid delivery pressure. When it is necessary to switch the liquid path, the electromagnet 960 is de-energized and released, allowing the rotary drive module 600 to freely drive the rotary plunger 200 to rotate. This locking mechanism ensures the stability of the liquid path's on / off state. Especially for reaction steps requiring long-term isothermal amplification, it ensures that the liquid path state remains unchanged during the reaction, thereby improving the reliability of the detection process.

[0059] In the description of this specification, the references to terms such as "an embodiment, some embodiments, illustrative embodiments, example, specific example, or examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the present invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0060] The terms "first," "second," "third," "fourth," etc. (if applicable) in the specification, claims, and accompanying drawings of this application are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments described herein can be implemented in a sequence other than that illustrated or described herein.

[0061] It should also be noted that, in the description of this specification, relational terms such as first and second are used only to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations.

[0062] Furthermore, the terms “comprising” and “having”, and any variations thereof, are intended to cover non-exclusive inclusion, such that a process, method, system, product, or apparatus that includes a series of steps or units is not necessarily limited to those steps or units that are explicitly listed, but may also include other steps or units that are not explicitly listed or that are inherent to such processes, methods, products, or apparatus.

[0063] Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes said element.

[0064] The embodiments of the present invention have been described in detail above with reference to the accompanying drawings. However, the present invention is not limited to the above embodiments. Within the scope of knowledge possessed by those skilled in the art, various changes can be made without departing from the spirit of the present invention.

Claims

1. A microfluidic chip, characterized in that, include: The chip body has several cylindrical chambers of different volumes and an inverted L-shaped detection chamber, and the cylindrical chambers and the detection chamber are isolated from each other; A rotating plunger, with several microfluidic channels etched on its surface, is rotatably mounted within the chip body and seals against the cylindrical chamber and the detection chamber. The cylindrical chamber and the detection chamber are selectively fluidly connected via the rotating plunger. By rotating the rotating plunger, the several microfluidic channels selectively connect different cylindrical chambers or connect the cylindrical chamber and the detection chamber, thereby achieving the opening and closing of the liquid path and the mixing of the liquid. A rubber sealing ring is nested between the chip body and the rotating plunger to achieve liquid circuit sealing. The upper surface of the rubber sealing ring has several through holes, which are aligned with and connected to the cylindrical cavity.

2. The microfluidic chip according to claim 1, characterized in that, The number of cylindrical chambers is five, and the number of through holes is seven. Five of the through holes are connected to the five cylindrical chambers in a one-to-one correspondence, and the remaining two through holes are used to allow gas to be discharged or waste liquid to be discharged.

3. The microfluidic chip according to claim 1 or 2, characterized in that, The number of microfluidic channels is six, and the length of each microfluidic channel is different; when the rotating plunger is rotated to different angles, the microfluidic channels selectively connect different cylindrical chambers or connect cylindrical chambers and detection chambers.

4. A microfluidic detection device comprising a microfluidic chip as described in any one of claims 1-3, characterized in that, Also includes: The microfluidic chip is mounted on the base plate. A liquid-driven module, mounted on the base plate, is used to inject samples and reaction reagents into the cylindrical chamber and discharge waste liquid after the reaction is completed. A rotary drive module is mounted on the base plate, and its output end is connected to the rotary plunger to control the rotary plunger to rotate to different angle positions; An optical detection module, mounted on the base plate, is used for optical detection of the liquid in the detection chamber; A control module, mounted on the base plate, is electrically connected to the liquid driving module, the rotation driving module, and the optical detection module, respectively, and is used to control the actions of the liquid driving module, the rotation driving module, and the optical detection module to automate nucleic acid extraction, amplification, and signal detection.

5. The microfluidic detection device according to claim 4, characterized in that, The liquid driving module includes a first stepper motor, a slide, a pusher plate, and a piston; the first stepper motor drives the slide to move, the slide moves the pusher plate, and the pusher plate pushes the piston, so that the pump chamber where the piston is located quantitatively pumps the sample and reaction reagents into the microfluidic chip.

6. The microfluidic detection device according to claim 4, characterized in that, The rotary drive module is a second stepper motor, and the output shaft of the second stepper motor is fixedly connected to the end of the rotary plunger.

7. The microfluidic detection device according to claim 4, characterized in that, The optical detection module includes an excitation light source, a fluorescence signal receiver, and a first support; the excitation light source is fixed on the base plate by the first support and is positioned facing the detection chamber; the fluorescence signal receiver is located on the light-emitting side of the detection chamber.

8. The microfluidic detection device according to claim 7, characterized in that, The excitation source is a blue light source containing a 495nm filter, and the fluorescence signal receiver is a CCD camera containing a 520nm filter.

9. The microfluidic detection device according to claim 4, characterized in that, It also includes a heating plate and a temperature controller, wherein the heating plate is connected to the temperature controller and is attached to the microfluidic chip to provide temperature control for the reaction.

10. The microfluidic detection device according to claim 4, characterized in that, It also includes a housing, a touch screen, and a hinged panel. The housing is mounted on the base plate, the touch screen is embedded in the housing and electrically connected to the control module, and the hinged panel is closable on the housing for opening the housing.

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