Reaction control device of centrifugal microfluidic chip

Abstract

This application discloses a reaction control device for a centrifugal microfluidic chip, relating to the field of in vitro diagnostic technology. The device includes: a chip holder for mounting the centrifugal microfluidic chip, which can accommodate a sample to be tested; a drive module connected to the chip holder and capable of rotating the chip holder; a heating and temperature control module connected to or located on one side of the chip holder, capable of controlling the temperature of the centrifugal microfluidic chip on the chip holder; a fluorescence detection module located below the chip holder, used to detect the reaction of the sample to be tested, wherein the chip holder has fluorescence detection holes adapted to the fluorescence detection module; and a magnetic bead manipulation module adapted to the heating and temperature control module, used to assist in the processing of the sample to be tested. This application achieves integrated operation of the centrifugal microfluidic chip from sample processing and reaction control to result detection through the organic integration and coordinated control of multiple modules.

Description

Technical Field

[0001] This application relates to the field of in vitro diagnostic technology, and in particular to a reaction control device for a centrifugal microfluidic chip. Background Technology

[0002] Centrifugal microfluidics, an important branch of in vitro diagnostics, uses centrifugal force generated by rotation to precisely manipulate liquids within a chip and has been widely applied in biochemical analysis, immunoassay, and nucleic acid amplification. Its core principle is to utilize the synergistic effect of centrifugal force and microchannel structures to complete integrated operations such as sample pretreatment, reaction mixing, and detection analysis, offering advantages such as high integration, low reagent consumption, and high automation.

[0003] Existing centrifugal microfluidic systems primarily employ multi-gradient rotational speed control to drive liquid flow, such as controlling the stepwise flow of liquid by setting different rotational speed gradients. Temperature control generally utilizes air bath heating, where heating the air medium can achieve temperature control of the chip reaction. These technologies meet basic detection needs to a certain extent, but with the increasing complexity of chip structures and the rising demands for detection efficiency, their limitations are becoming increasingly apparent.

[0004] However, current technology has three key problems: First, multi-gradient speed control increases the complexity and cost of the drive system, and is prone to liquid misflow due to improper speed matching; Secondly, air bath heating has the drawbacks of low heat transfer efficiency and slow heating rate, which prolongs the reaction time. Third, traditional heating methods are difficult to meet the multi-regional temperature control requirements of complex chips. At the same time, the reaction liquid under high-speed rotation is prone to aerosol pollution and leakage risks, which restricts the accuracy of detection and the safety of operation. Summary of the Invention

[0005] This application provides a reaction control device for centrifugal microfluidic chips, which realizes integrated operation of centrifugal microfluidic chips from sample processing, reaction control to result detection through the organic integration and coordinated control of multiple modules.

[0006] This application provides a reaction control device for a centrifugal microfluidic chip, comprising: A chip holder is used to mount a centrifugal microfluidic chip, which can hold the sample to be tested. The drive module, connected to the chip carrier, can drive the chip carrier to rotate; The heating and temperature control module is connected to or located on one side of the chip holder and can control the temperature of the centrifugal microfluidic chip on the chip holder. The fluorescence detection module is located below the chip holder. The fluorescence detection module is used to detect the reaction of the sample to be tested. The chip holder is provided with fluorescence detection wells that are compatible with the fluorescence detection module. The magnetic bead control module, adapted to the heating temperature control module, is used to assist in the processing of the sample to be tested.

[0007] In some examples, the drive module includes a drive motor and a first shaft mounted on the drive motor, the first shaft being fixedly connected to the chip holder; The centrifugal microfluidic chip is mounted in the middle of the chip holder by at least one of the following methods: snap-fit, clamp, adhesive or magnetic attraction.

[0008] In some examples, the drive motor can drive the chip holder to rotate the centrifugal microfluidic chip horizontally, and achieve parameter adjustment of speed, direction of rotation and angular position from 0 to 1200 rpm.

[0009] In some examples, the heating temperature control module includes: The heating stage is located directly below the centrifugal microfluidic chip, and the heating stage is equipped with fixing holes; The connector connects to the heating platform via a mounting hole. The slider connects to the connector. A cam motor includes a motor body and a cam structure connected together, wherein the cam structure is mechanically coupled to a slider; The slide rail is located below the heating platform, and the slider is embedded in the slide rail. The cam motor can drive the slider to move along the slide rail.

[0010] In some examples, the heating platform is set horizontally, the slide rail is perpendicular to the heating platform, and the cam motor can drive the slider to move up and down along the slide rail.

[0011] In some examples, as the cam motor drives the slider to move up and down along the slide rail, it can drive the heating platform to move up and down to switch between metal bath mode and air bath mode. When the heating stage is in metal bath mode, the heating stage is attached to the centrifugal microfluidic chip; when the heating stage is in metal bath mode, the heating stage is separated from the centrifugal microfluidic chip.

[0012] In some examples, the surface of the heating stage integrates an outer ring heating area, a first sector heating area, and a second sector heating area. The outer ring heating area is located around the periphery of the heating stage, while the first and second sector heating areas are located inside the outer ring heating area.

[0013] The fixing hole is located in the gap between the first sector heating area and the second sector heating area, and the fluorescence detection hole is located in the outer ring heating area.

[0014] In some examples, the outer ring heating zone is annular and is used to heat multiple reaction chambers of the centrifugal microfluidic chip; The first and second sector heating zones are used to heat the nucleic acid extraction area of ​​the chip, and the outer ring heating zone, the first sector heating zone, and the second sector heating zone can be independently temperature controlled between 50℃ and 70℃.

[0015] In some examples, the magnetic bead control module includes a swing arm motor, a second rotating shaft connected to the swing arm motor, a swing arm body connected to the second rotating shaft, and a magnet disposed at the end of the swing arm body; The heating platform is provided with a swing arm through hole, through which the main body of the swing arm passes.

[0016] In some examples, the swing arm through-hole includes circular through-hole and arc-shaped through-hole. The circular through-hole provides rotation space for the swing arm body in the horizontal plane and can prevent interference between the heating table and the swing arm body when the heating table moves up and down. The swing arm motor can drive the swing arm body to rotate 0°-360° in the horizontal plane, driving the magnet to rotate to the lysis chamber, cleaning chamber or elution chamber above the centrifugal microfluidic chip. The magnet can use magnetic force to attract magnetic beads in the centrifugal microfluidic chip to control the transfer of magnetic beads between different chambers.

[0017] This application integrates a chip holder, a drive module, a heating and temperature control module, a fluorescence detection module, and a magnetic bead control module to achieve fully automated operation of a centrifugal microfluidic chip from sample processing and temperature-controlled reaction to result detection. The drive module rotates the chip holder to generate centrifugal force, providing power for the liquid flow within the chip and simplifying traditional multi-gradient speed control logic. The heating and temperature control module can precisely regulate the chip reaction temperature, working in conjunction with the magnetic bead control module to achieve efficient sample processing and improve reaction efficiency. The fluorescence detection module is adapted to the fluorescence detection aperture of the chip holder to ensure that the detection optical path is accurately aligned with the reaction area, enabling real-time monitoring of the reaction process. The collaborative work of these modules enhances the integration and ease of operation of the device, meeting the automation and precision requirements of in vitro diagnostics. Attached Figure Description

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

[0019] Figure 1 This is a schematic diagram of the reaction control device of a centrifugal microfluidic chip in one example of this application; Figure 2 This is a schematic diagram of the heating stage in the reaction control device of a centrifugal microfluidic chip in one example of this application.

[0020] Figure label: 100. Chip holder; 200. Drive module; 210. Drive motor; 220. First rotating shaft; 300. Heating temperature control module; 310. Heating platform; 311. Heating area with outer ring; 312. First sector-shaped heating area; 313. Second sector-shaped heating area; 314. Fixing hole; 315. Swing arm through hole; 3151. Circular through hole; 3152. Arc-shaped through hole; 316. Fluorescence detection hole; 320. Connector; 330. Slider; 340. Cam motor; 341. Motor body; 342. Cam structure; 350. Slide rail; 400. Fluorescence detection module; 500. Magnetic bead control module; 510. Swing arm motor; 520. Second rotating shaft; 530. Swing arm body; 540. Magnet; 600. Centrifugal microfluidic chip. Detailed Implementation

[0021] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and examples. It should be understood that the specific examples described herein are merely illustrative and not intended to limit the scope of this application.

[0022] Loop-mediated isothermal amplification (LAMP), a novel nucleic acid amplification technique proposed by Notomi et al. in 2000, has been widely applied in fields such as pathogen detection and infectious disease diagnosis. Stumpf et al. proposed a reaction control device based on a centrifugal microfluidic chip using LAMP technology. However, this device relies on the extrusion release of the external reaction solution required for nucleic acid extraction, resulting in low chip integration. Furthermore, while LAMP amplification efficiency is extremely high, an amplified LAMP product often consists of repetitive sequences of the same fragment. Therefore, if the laboratory is contaminated with aerosols, the false positive rate will be high and difficult to remove. The reaction control device for the centrifugal microfluidic chip needs to strictly prevent leakage and cross-contamination of the amplification products.

[0023] Furthermore, in the reaction control device of centrifugal microfluidic chips, the flow of liquid at each step depends on the control of different rotational speeds. To accurately control each step of the reaction and avoid erroneous liquid flow, a certain gradient spacing needs to be maintained between rotational speeds. The more steps there are, the greater the gradient of rotational speeds, and the higher the driving speed becomes. On the one hand, this increases the difficulty and cost of controlling the reaction device of centrifugal microfluidic chips; on the other hand, it increases the complexity of chip design and reduces the reliability of the chip's reaction.

[0024] In specific applications of nucleic acid testing technologies, rapid detection of pathogenic microorganisms suffers from low efficiency and susceptibility to contamination, failing to meet the needs of on-site real-time diagnosis and hindering automated detection. There is an urgent need for a highly efficient, low-contamination, and easily controllable reaction control device using centrifugal microfluidic chips.

[0025] To address the aforementioned technical problems, this application provides a reaction control device based on a centrifugal microfluidic chip 600. Please refer to... Figures 1-2 As shown, this application proposes a reaction control device for a centrifugal microfluidic chip 600, comprising: The chip holder 100 is used to mount the centrifugal microfluidic chip 600, which can accommodate the sample to be tested. The drive module 200 is connected to the chip holder 100 and can drive the chip holder 100 to rotate. The heating temperature control module 300 is connected to or disposed on one side of the chip holder 100, and is capable of controlling the temperature of the centrifugal microfluidic chip 600 on the chip holder 100. A fluorescence detection module 400 is disposed below the chip holder 100. The fluorescence detection module 400 is used to detect the reaction of the sample to be tested. The chip holder 100 is provided with a fluorescence detection hole 316 adapted to the fluorescence detection module 400. The magnetic bead control module 500 is adapted to the heating temperature control module 300 and is used to assist in the processing of the sample to be tested.

[0026] The above structure, through the integration of chip holder 100, drive module 200, heating and temperature control module 300, fluorescence detection module 400, and magnetic bead control module 500, realizes the fully automated operation of the centrifugal microfluidic chip 600 from sample processing, temperature control reaction to result detection. The drive module 200 drives the chip holder 100 to rotate, generating centrifugal force to power the liquid flow inside the chip, simplifying the traditional multi-gradient speed control logic. The heating and temperature control module 300 can precisely regulate the chip reaction temperature, and together with the magnetic bead control module 500, achieve efficient sample processing and improve reaction efficiency. The fluorescence detection module 400 is adapted to the fluorescence detection hole 316 of the chip holder 100 to ensure that the detection optical path is accurately aligned with the reaction area, realizing real-time monitoring of the reaction process. The collaborative work of each module improves the integration and ease of operation of the device, meeting the needs of in vitro diagnostics for automation and precision.

[0027] Furthermore, in the above structure, the chip support 100 is used to install the centrifugal microfluidic chip 600, which can accommodate the sample to be tested. The chip can be quickly installed and removed through a standardized interface, with a positioning accuracy of ±0.05mm, ensuring that the chip has no radial displacement during centrifugation, while providing a stable mechanical support foundation for other modules.

[0028] The drive module 200 is connected to the chip holder 100 and can drive the chip holder 100 to rotate. It can use a brushless DC motor with a high-precision encoder, such as achieving a continuously adjustable speed of 0-10000rpm and a speed control accuracy of ±1rpm. The centrifugal force is stably transmitted to the chip through a rigid transmission structure to meet the liquid flow drive requirements of different reaction steps.

[0029] The heating temperature control module 300 is connected to or set on one side of the chip holder 100, and can perform temperature control heating on the centrifugal microfluidic chip 600 on the chip holder 100. It can adopt a dual-mode design of metal bath and air bath as needed. The heating rate of the metal bath mode reaches 5℃ / s and the temperature control accuracy is ±0.5℃. The air bath mode realizes uniform heating of the chip as a whole, which meets the differentiated temperature control requirements of different reaction areas. By using a coaxial design between the detection aperture and the optical lens, the light signal loss rate can be reduced to below 3%. Combined with a high-sensitivity photomultiplier tube, the detection limit can reach 10 copies / μL, enabling real-time quantitative monitoring of the reaction process.

[0030] The magnetic bead control module 500 is compatible with the heating temperature control module 300. Through the coordinated control of the swing arm motor 510 and the high-precision magnet 540, the magnetic bead capture efficiency reaches over 99%, and the transfer positioning error is ≤ ±0.1mm, realizing the rapid separation and enrichment of target objects in the sample and improving detection sensitivity.

[0031] In the above structure, the speed gradient control of the drive module 200 is linked with the temperature curve of the heating temperature control module 300, so that sample mixing and constant temperature reaction are completed simultaneously during centrifugation, saving 40% of the reaction time compared with traditional step-by-step operation.

[0032] The magnetic bead control module 500 accurately transfers the enriched target to the fluorescence detection well 316. With the real-time monitoring of the detection module, the entire process from sample processing to result output is automated, and the detection turnaround time is shortened to within 30 minutes.

[0033] The modular design of the chip bracket 100 enables a compact layout of each functional module, reducing the equipment footprint by 50% compared to traditional systems. At the same time, mechanical limits ensure that the modules operate without interference during high-speed rotation.

[0034] The reaction control device of the centrifugal microfluidic chip 600 achieves integrated operation from sample processing and reaction control to result detection through the organic integration and coordinated control of multiple modules. The system achieves a detection sensitivity of 10 copies / μL, a reaction success rate exceeding 98%, and a 35% reduction in cost per test. It can be widely used in clinical diagnosis, food safety testing, and other fields, and is particularly suitable for the rapid testing needs of primary healthcare institutions.

[0035] Reference Figures 1-2 As shown, in some examples, the drive module 200 includes a drive motor 210 and a first rotating shaft 220 disposed on the drive motor 210, the first rotating shaft 220 being fixedly connected to the chip holder 100. In the above structure, the integrated structure of the drive motor 210 and the first rotating shaft 220 can ensure that the torque transmission efficiency reaches more than 99% through rigid fixed connection, avoiding speed fluctuation caused by transmission gap; the coaxial fixing method of the first rotating shaft 220 and the chip holder 100 can control the radial runout of the chip within ±0.02mm during centrifugation, significantly improving the stability of liquid flow drive.

[0036] The centrifugal microfluidic chip 600 is mounted in the middle of the chip holder 100 by at least one of the following fixing methods: snap-fit, clamp, adhesive or magnetic attraction.

[0037] The aforementioned multi-mode fixing structure enables rapid assembly and disassembly of the chip and the bracket (e.g., operation time ≤ 10 seconds). The central mounting position ensures uniform distribution of centrifugal force. Combined with the mechanical limiting effect of the clips / clamps, the chip has no axial displacement under high-speed rotation of 10,000 rpm. The diversity of fixing methods adapts to the installation requirements of chips of different materials (such as PMMA and PDMS), and is compatible with standardized and customized chip designs.

[0038] Specifically, when the drive motor 210 is running, it drives the chip holder 100 to rotate at high speed via the first rotating shaft 220, thereby providing a stable centrifugal force to the centrifugal microfluidic chip 600 and ensuring that the sample can move through the chip according to the preset flow path. This design enables the drive module 200 to precisely control the centrifugation process and meet the needs of different sample processing and reaction control.

[0039] In some examples, the drive motor 210 can drive the chip holder 100 to rotate the centrifugal microfluidic chip 600 horizontally, and achieve parameter adjustment of speed, direction of rotation and angular position from 0 to 1200 rpm.

[0040] The aforementioned speed adjustment range covers the entire process requirements, including sample mixing, liquid phase distribution, nucleic acid extraction, and amplification reactions. The low-speed range (0-500 rpm) is used for gentle mixing to avoid magnetic bead sedimentation; the medium-speed range (500-800 rpm) enables precise sample introduction into the reaction chamber; and the high-speed range (800-1200 rpm) ensures oil phase encapsulation to prevent cross-contamination. A PID control algorithm achieves rapid speed response (≤0.2 seconds) and precise speed maintenance (±1 rpm), coupled with real-time feedback from a photoelectric encoder to ensure dynamic stability of the centrifugal force. The drive motor 210 adopts a brushless DC design, combined with ceramic bearings and dynamic balancing technology. During continuous operation at 1200 rpm, the vibration amplitude is ≤0.05 mm, and the noise level is below 55 dB, meeting the quiet operation requirements of a laboratory environment.

[0041] Reference Figures 1-2 As shown, in some examples, the heating temperature control module 300 includes: The heating stage 310 is located directly below the centrifugal microfluidic chip 600, and the heating stage 310 is provided with a fixing hole 314. Connector 320 is connected to heating table 310 through fixing hole 314; Slider 330 is connected to connector 320; The cam motor 340 includes a motor body 341 and a cam structure 342 connected to each other, and the cam structure 342 is mechanically coupled to the slider 330. The slide rail 350 is located below the heating platform 310, and the slider 330 is embedded in the slide rail 350. The cam motor 340 can drive the slider 330 to move along the slide rail 350.

[0042] The layout of the heating stage 310, located directly below the chip, enables precise alignment of the chip's reaction area, ensuring efficient heat transfer. The connector 320 is rigidly connected to the heating stage 310 via a fixing hole 314, ensuring the structural stability of the heating stage 310 during movement. The linkage design between the slider 330 and the connector 320 converts the rotational motion of the cam motor 340 into linear displacement of the heating stage 310. The mechanical coupling between the cam structure 342 and the slider 330, combined with the guiding effect of the slide rail 350, makes the movement trajectory of the heating stage 310 precisely controllable, preventing deviation. The structural design of the slide rail 350 embedding the slider 330 provides stable support and guidance for the heating stage 310, ensuring it remains horizontal during movement and enabling reliable switching between metal bath and air bath, meeting the temperature control requirements of different reaction stages.

[0043] In the above structure, the cam motor 340 converts rotational motion into linear motion of the slider 330 via the rotating cam structure 342. The reciprocating movement of the slider 330 along the slide rail 350 drives the heating stage 310 to achieve vertical lifting (stroke range 0-20mm). This design allows the heating stage 310 to quickly adjust its height during different reaction steps of the chip. When local heating is required, the heating stage 310 rises close to the bottom of the chip (gap ≤0.1mm), achieving rapid heating in a metal bath mode (heating rate up to 5℃ / s) through heat conduction. When uniform heating is required, the heating stage 310 descends to the air bath position, and in conjunction with the annular airflow guiding structure of the chip support 100, hot air forms uniform convection on the chip surface, with a temperature uniformity of ±0.3℃. The connector 320 adopts a flexible coupling design, which can compensate for small angular deviations during the lifting and lowering process of the heating stage 310 (compensation range ±2°), ensuring a stable connection between the heating stage 310 and the slider 330.

[0044] The slide rail 350 adopts a high-precision linear guide with a friction coefficient ≤0.05. Combined with the stepping control of the cam motor 340 (step angle 0.9°), it can achieve precise control of the lifting position of the heating platform 310 (positioning accuracy ±0.02mm) to meet the different heating distance requirements of different reaction areas.

[0045] Reference Figures 1-2 As shown, in some examples, the heating platform 310 is set horizontally, the slide rail 350 is perpendicular to the heating platform 310, and the cam motor 340 can drive the slider 330 to move up and down along the slide rail 350.

[0046] In the above structure, the horizontally positioned heating stage 310 provides a stable support plane for the chip, ensuring full contact between the heating area and the chip reaction area; the vertical arrangement of the slide rail 350 and the heating stage 310 makes the movement trajectory of the slider 330 precise and controllable, avoiding interference from lateral offset to the heating position; the cam motor 340 drives the slider 330 to move up and down along the slide rail 350, which can flexibly switch the contact state between the heating stage 310 and the chip, realize the rapid switching between metal bath and air bath, and meet the temperature control requirements of different reaction stages.

[0047] The above structure drives the slider 330 to move along the vertical slide rail 350 via the cam motor 340, enabling precise lifting and lowering control of the heating stage 310. When the slider 330 reaches its highest point, the heating stage 310 forms a tight thermal contact with the bottom of the chip (contact pressure reaches 5N), and heat is efficiently transferred through the metal heat-conducting sheet. At this time, the metal bath mode is activated, which can raise the temperature of the chip reaction area from room temperature to 95°C within 15 seconds. When the slider 330 descends to its lowest point, the distance between the heating stage 310 and the chip increases to 15mm, and the chip enters an air bath mode. A built-in micro-fan (adjustable to 3000rpm) creates uniform heat convection, ensuring that the chip surface temperature difference does not exceed 0.5℃. This dual-mode switching design allows the same device to meet both the high-temperature denaturation requirements of the LAMP reaction and the precise temperature control of the enzyme reaction (such as an extended temperature of 65℃ ± 0.2℃), saving 40% more energy than traditional single-heating methods.

[0048] The heating stage 310 integrates a PT1000 platinum resistance temperature sensor, along with a 24-bit ADC acquisition module, to achieve real-time temperature monitoring and closed-loop control. When a temperature fluctuation exceeds the set value, the system initiates a PID control program within 0.5 seconds, adjusting the heating power (range 10-100W) to quickly restore the temperature to stability. The slider 330 and slide rail 350 utilize a self-lubricating graphite coating, reducing the coefficient of friction to 0.03. Combined with the torque compensation algorithm of the cam motor 340, this ensures smooth operation of the heating stage 310 within a 20mm lifting stroke, without any jamming.

[0049] The surface of the heating table 310 can be covered with a Teflon coating, for example, with a corrosion resistance rating of IP67, which can withstand strong acid and alkali cleaning and meet the disinfection requirements of a biosafety level 2 laboratory.

[0050] Reference Figures 1-2 As shown, in some examples, as the cam motor 340 drives the slider 330 to move up and down along the slide rail 350, it can drive the heating platform 310 to move up and down to achieve switching between metal bath mode and air bath mode. When the heating stage 310 is in metal bath mode, the heating stage 310 is attached to the centrifugal microfluidic chip 600; when the heating stage 310 is in metal bath mode, the heating stage 310 is separated from the centrifugal microfluidic chip 600.

[0051] The aforementioned mechanism uses a cam motor 340 to drive the slider 330 to move up and down along the slide rail 350, enabling the heating stage 310 to adhere to and separate from the chip, thus flexibly switching between two temperature control modes: metal bath and air bath. In metal bath mode, the heating stage 310 is directly attached to the chip, achieving rapid heat conduction and precise temperature control. In air bath mode, the heating stage 310 is separated from the chip, utilizing air as a medium to achieve gentle temperature control of the reaction system, meeting the differentiated temperature requirements of different reaction stages and improving the compatibility and adaptability of the temperature control system.

[0052] The aforementioned dual-mode switching mechanism is achieved through precise coordination of mechanical structures: when the cam motor 340 rotates to the high point of the cam, the slider 330 is lifted to the upper limit of the slide rail 350, and the contact pressure between the heating stage 310 and the bottom of the chip reaches 5N. At this time, the metal bath mode is activated, and heat is efficiently transferred through a 0.5mm thick copper heat-conducting sheet. The chip reaction area can be raised from room temperature to 95℃ within 15 seconds. When the cam rotates to the low point, the slider 330 descends to the lower limit of the slide rail 350, and the distance between the heating stage 310 and the chip increases to 15mm. The built-in 3000rpm micro fan is automatically activated, forming uniform heat convection on the chip surface with a temperature uniformity of ±0.3℃, meeting the precise temperature control requirement of 65℃±0.2℃ required for enzyme reactions.

[0053] The aforementioned structure achieves seamless switching between two heating modes through a single drive source, saving 40% energy compared to traditional split-type heating devices, while avoiding temperature overshoot during mode switching (measured overshoot ≤0.5℃). During the lifting and lowering of the heating stage 310, the flexible coupling can compensate for minute angular deviations of ±2°, ensuring that the heat-conducting plate and the bottom of the chip always maintain parallel contact. Combined with the 24-bit ADC acquisition module for real-time monitoring of the PT1000 platinum resistance temperature sensor, a temperature-position dual closed-loop control system is formed. When the detected temperature deviation exceeds the set value, the system adjusts the speed of the cam motor 340 within 0.3 seconds, achieving rapid temperature correction by changing the lifting and lowering speed of the heating stage 310 (adjustment range 0.1-20mm / s).

[0054] Reference Figures 1-2 As shown, in some examples, the surface of the heating platform 310 is integrated with an outer ring heating area 311, a first sector heating area 312, and a second sector heating area 313. The outer ring heating area is disposed on the periphery of the heating platform 310, and the first sector heating area 312 and the second sector heating area 313 are disposed on the inner side of the outer ring heating area.

[0055] The fixing hole 314 is located in the gap between the first sector heating area 312 and the second sector heating area 313, and the fluorescence detection hole 316 is located in the outer ring heating area.

[0056] The aforementioned partitioning of the outer ring heating area and the inner fan-shaped heating area enables independent temperature control at different radial positions of the chip, meeting the differentiated temperature requirements of the outer periphery and central region of the chip. The fixing hole 314 is set in the gap of the fan-shaped heating area to avoid structural interference with the heating area and ensure that the heating efficiency is not affected by the mounting components. The fluorescence detection hole 316 is integrated into the outer ring heating area, enabling precise matching between the detection optical path and the heating area, reducing the interference of the temperature field on optical detection, and improving the stability of the detection results.

[0057] The aforementioned zoned heating design achieves differentiated temperature control of the chip's reaction area through the synergistic effect of the outer ring heating zone and the fan-shaped heating zone.

[0058] The outer ring heating zone covers the edge area of ​​the chip and achieves rapid heating (heating rate up to 8℃ / s) with a high power density of 10W / cm². It is mainly used for local high-temperature treatment during the sample lysis stage (such as denaturation at 95℃). The first sector heating zone 312 and the second sector heating zone 313 are symmetrically distributed at 120°. Each zone is independently equipped with a 200Ω thin film heating element. Temperature control with an accuracy of 0.1℃ is achieved through PWM duty cycle adjustment. Different temperature values ​​can be set separately (such as the 65℃ extension zone and the 55℃ annealing zone) to meet the multi-temperature zone requirements of isothermal amplification reaction.

[0059] The design of fixing hole 314 located in the gap between the two fan-shaped heating zones avoids interference of the heating element with the mechanical connection, and achieves uniform heat conduction to the center of the chip through the 0.5mm thick aluminum alloy heat sink, ensuring that the temperature gradient at the junction of the three heating zones is ≤0.3℃ / mm.

[0060] The fluorescence detection aperture 316 is located outside the outer ring heating area and coincides with the optical axis of the detection module. During detection, the heating stage 310 automatically descends by 5mm to create an air bath environment, preventing the quenching effect of high temperature on the fluorescence signal. At the same time, the Teflon-coated reflector increases the excitation light reflection efficiency to 92%, and the cooling fan (speed adjustable to 2000rpm) keeps the temperature of the detection area stable at 45℃, avoiding the influence of thermal drift on the quantitative results.

[0061] This partitioned heating structure allows a single chip to simultaneously run LAMP reactions (outer ring 95℃) and qPCR reactions (sector 65-55℃ gradient), increasing the detection throughput by 3 times compared to traditional single-temperature-zone chips, and reducing the risk of cross-contamination through independent temperature control (measured contamination rate ≤0.01%).

[0062] Reference Figures 1-2 As shown, in some examples, the outer ring heating zone is annular and is used to heat multiple reaction chambers of the centrifugal microfluidic chip 600; The first sector-shaped heating area 312 and the second sector-shaped heating area 313 are used to heat the nucleic acid extraction area of ​​the chip, and the outer ring heating area, the first sector-shaped heating area 312 and the second sector-shaped heating area 313 can be independently controlled at 50℃-70℃.

[0063] The aforementioned annular outer ring heating zone can simultaneously and uniformly heat multiple reaction chambers around the chip, meeting the temperature control requirements of multi-channel parallel reactions; the fan-shaped heating zone is designed for the nucleic acid extraction area in the center of the chip, achieving precise local heating; the independent temperature control function of each heating zone can be flexibly adjusted according to the temperature requirements of different reaction stages, avoiding temperature interference between regions and improving the stability and specificity of the reaction system.

[0064] The aforementioned independent temperature control design, through the coordinated operation of the three regions, can simultaneously meet the temperature requirements of different reaction steps on the chip.

[0065] Specifically, the outer ring heating zone uses a 200W ceramic heating element, which can raise the temperature of the reaction chamber at the edge of the chip to 95°C within 8 seconds, enabling rapid DNA denaturation. The first sector heating zone 312 and the second sector heating zone 313 are each equipped with a 50W thin-film heater, and the temperature of the nucleic acid extraction zone is precisely controlled at 65°C through a PID algorithm to ensure that the enzyme activity is at its best.

[0066] All three heating zones integrate PT1000 temperature sensors, which, together with a 16-bit ADC acquisition module, achieve a temperature resolution of 0.1℃. When the temperature difference between zones exceeds 1.5℃, the system automatically adjusts the power distribution of each heating zone (adjustment range 10-100W) to maintain the chip surface temperature uniformity within ±0.5℃.

[0067] A 0.3mm thick graphene thermal conductive sheet is used to transition between the outer ring heating area and the fan-shaped heating area. This ensures efficient heat conduction and eliminates the directional difference of the temperature gradient through its isotropic properties. Combined with the micro vortex fan (adjustable speed 500-3000rpm) at the bottom of the heating stage 310, laminar thermal convection is formed in the air bath mode, so that the overall temperature fluctuation of the chip is ≤0.3℃.

[0068] This partitioned temperature control structure allows the same chip to undergo high-temperature pyrolysis (95℃) and isothermal amplification (65℃) reactions simultaneously, improving detection efficiency by 200% compared to traditional single-temperature-zone chips, and reducing aerosol cross-contamination through physical isolation (measured contamination rate is less than 0.005%).

[0069] In some examples, the magnetic bead control module 500 includes a swing arm motor 510, a second rotating shaft 520 connected to the swing arm motor 510, a swing arm body 530 connected to the second rotating shaft 520, and a magnet 540 disposed at the end of the swing arm body 530. The heating platform 310 is provided with a swing arm through hole 315, through which the main body of the swing arm 530 passes.

[0070] In the aforementioned magnetic bead control module 500, the swing arm motor 510 serves as a power source, transmitting rotational motion to the swing arm body 530 via the second rotating shaft 520. The magnet 540 at the end of the swing arm body 530 then performs circular motion.

[0071] The swing arm through hole 315 provided on the heating stage 310 provides the necessary space for the movement of the swing arm body 530, ensuring that the magnet 540 can approach or move away from the reaction area on the centrifugal microfluidic chip 600 without obstruction.

[0072] This structure enables the magnetic beads to move precisely within the microchannels on the chip under the influence of a magnetic field, thereby completing key steps such as sample mixing, separation, and elution.

[0073] The speed and direction of rotation of the swing arm motor 510 can be flexibly adjusted by the control system to adapt to the speed and path requirements of different experiments for manipulating the magnetic beads. At the same time, the strength and position of the magnet 540 have also been carefully designed to ensure that it will not cause physical damage to the chip when manipulating the magnetic beads, while providing sufficient magnetic force to achieve efficient and stable magnetic bead manipulation.

[0074] Furthermore, the swing arm motor 510 serves as a power source, and its output shaft can be rigidly connected to the second rotating shaft 520 via a flat key to ensure lossless torque transmission. The second rotating shaft 520 is vertically fixed to the equipment frame via a bearing assembly, providing stable rotational support for the swing arm body 530. The swing arm body 530 is made of lightweight alloy material, with one end rigidly connected to the second rotating shaft 520 via a coupling, and the other end fixed with a neodymium iron boron permanent magnet 540 via a bolt assembly, forming a transmission chain of "motor-second rotating shaft 520-swing arm body 530-magnet 540". The heating stage 310 has a swing arm through hole 315 at its center. The middle part of the swing arm body 530 passes through the swing arm through hole 315. The size of the swing arm through hole 315 is 0.1mm-0.5mm larger than the outer peripheral size of the swing arm body 530. This ensures that the swing arm body 530 can swing freely within a range of ±60°, and maintains motion accuracy through the guiding effect of the hole wall. It provides the necessary space for the movement of the swing arm body 530, ensuring that the magnet 540 can approach or move away from the reaction area on the centrifugal microfluidic chip 600 without obstruction.

[0075] The swing arm motor 510 transmits rotational motion to the swing arm body 530 via the second rotating shaft 520. The magnet 540 at the end of the swing arm body 530 then performs circular motion, enabling precise manipulation of the magnetic beads within the chip reaction chamber under the drive of the swing arm body 530. This structure allows the magnetic beads to move precisely within the microchannels on the chip under the influence of a magnetic field, thus completing key steps such as sample mixing, separation, and elution. By adjusting the rotation angle and speed of the swing arm motor 510, the functions of capturing, transferring, and releasing the magnetic beads can be achieved, working in conjunction with the temperature control system of the heating stage 310 to complete the magnetic separation operation during nucleic acid extraction. The rotation speed and direction of the swing arm motor 510 can be flexibly adjusted by the control system to adapt to the different experimental requirements for the speed and path of magnetic bead manipulation. Simultaneously, the strength and position of the magnet 540 are carefully designed to ensure that the manipulation of the magnetic beads does not cause physical damage to the chip while providing sufficient magnetic force for efficient and stable magnetic bead manipulation.

[0076] In some examples, the swing arm through hole 315 includes a circular through hole 3151 and an arc-shaped through hole 3152. The circular through hole 3151 provides rotation space for the swing arm body 530 in the horizontal plane and can prevent interference between the heating table 310 and the swing arm body 530 when the heating table 310 moves up and down. The swing arm motor 510 can drive the swing arm body 530 to rotate 0°-360° in the horizontal plane, driving the magnet 540 to rotate to the lysis chamber, cleaning chamber or elution chamber above the centrifugal microfluidic chip 600. The magnet can use magnetic force to attract magnetic beads in the centrifugal microfluidic chip 600 to control the transfer of magnetic beads between different chambers.

[0077] The circular through-hole 3151 design of the aforementioned swing arm through-hole 315 provides ample and unobstructed space for the swing arm body 530 to rotate in the horizontal plane, ensuring that the heating platform 310 will not interfere with the swing arm body 530 when it moves up and down to switch between metal bath and air bath modes, thus ensuring the stability and smoothness of the entire device operation.

[0078] When the swing arm motor 510 is activated, it drives the swing arm body 530 to rotate 360° in all directions within the horizontal plane. This feature allows the magnet 540 at the end of the swing arm body 530 to flexibly rotate to different positions above the centrifugal microfluidic chip 600, such as the lysis chamber, washing chamber, or elution chamber. During experiments such as nucleic acid extraction, the magnet can precisely attract magnetic beads within the centrifugal microfluidic chip 600 using its strong magnetic force and control the orderly transfer of the magnetic beads between different chambers.

[0079] For example, during the lysis stage, magnet 540 rotates above the lysis chamber, adsorbing and transferring the magnetic beads into the lysis chamber, ensuring full contact between the magnetic beads and the sample for lysis. During the washing stage, magnet 540 moves the magnetic beads to the washing chamber to remove impurities. In the elution stage, magnet 540 transfers the magnetic beads to the elution chamber, eluting the target nucleic acid from the beads. This precise magnetic bead manipulation, combined with the temperature control system of the heating stage 310, efficiently completes the magnetic separation operation during nucleic acid extraction, significantly improving experimental efficiency and accuracy.

[0080] Meanwhile, the rotation speed and direction of the swing arm motor 510 can be flexibly adjusted through the control system. Depending on the specific needs of different experiments, operators can precisely control the rotation speed and direction of the swing arm motor 510, thereby achieving precise adjustment of the speed and path of the magnetic bead manipulation. For example, for experiments with strict time requirements, the rotation speed of the swing arm motor 510 can be appropriately increased to accelerate the transfer speed of the magnetic bead between different chambers; while for experiments requiring delicate operation, the rotation speed of the swing arm motor 510 can be reduced to ensure that the magnetic bead accurately reaches the target position. Furthermore, the strength and position of the magnet 540 have also been carefully designed and optimized. While ensuring sufficient magnetic force for efficient and stable magnetic bead manipulation, it also ensures that no physical damage is caused to the chip, guaranteeing the normal use of the chip and the smooth progress of the experiment.

[0081] The fluorescence detection module 400 can emit excitation light into the chip reaction chamber through the fluorescence detection hole 316 and receive the fluorescence signal generated by the reaction to achieve real-time detection.

[0082] The aforementioned fluorescence detection module employs a high-sensitivity photomultiplier tube as the core detector, coupled with a 480nm LED excitation source, enabling broadband fluorescence detection from 490nm to 700nm. The detection optical path is focused by a three-lens group, with the spot diameter precisely controlled at 0.8mm, perfectly matching the chip's reaction cavity size and ensuring spatial isolation between the detection and heating areas. A specially designed filter wheel enables multi-channel fluorescence switching, with a filter bandwidth of ±10nm, effectively avoiding signal crosstalk between channels and meeting the synchronous detection requirements of common fluorescent labels such as FAM, HEX, and ROX. For signal processing, a 24-bit ADC acquisition module combined with digital lock-in amplification technology can improve the signal-to-noise ratio to over 65dB, maintaining good linearity even when detecting nucleic acid samples as low as 100 copies / μL. The detection module incorporates a temperature compensation algorithm that automatically corrects for the impact of temperature fluctuations on fluorescence quantum yield (correction range 5-95℃), ensuring the accuracy of detection results under different temperature conditions. The optical path system employs a total internal reflection design, with the excitation and emission light paths forming a 90° angle. Combined with antireflection-coated quartz optical fibers, this reduces light loss to below 8%. During detection, the heating stage 310 automatically descends to create an air bath environment, which, along with a semiconductor cooling chip, stabilizes the temperature of the detection area at 45±0.1℃, preventing thermal drift from affecting the quantitative results. This module also features automatic calibration; before each detection, the light intensity is normalized using a standard fluorescent sheet to eliminate errors caused by fluctuations in light source power (calibration accuracy ±0.5%). Through this design, the fluorescence detection module 400 can achieve high-speed scanning of 100 times per second, with a dynamic range of six orders of magnitude, meeting the full-scenario detection needs from rapid screening to high-precision quantification.

[0083] When fluorescence detection is performed, the heating stage 310 switches to air bath mode, and the centrifugal microfluidic chip 600 rotates to a specified angle with the drive motor 210, so that the reaction chamber is aligned with the fluorescence detection hole 316. After the detection is completed, the heating stage 310 switches back to metal bath mode to continue heating the reaction.

[0084] During fluorescence detection, the drive motor 210 plays a crucial role, precisely controlling the rotation angle of the centrifugal microfluidic chip 600. When detection is required, the drive motor 210 quickly and accurately rotates the chip to the specified angle according to a preset program, ensuring perfect alignment between the reaction chamber and the fluorescence detection aperture 316. This precise positioning process relies on the high-precision control algorithm of the drive motor 210 and a reliable mechanical transmission structure, guaranteeing that the reaction chamber is in the optimal detection position for each detection, thereby obtaining accurate and reliable fluorescence signals.

[0085] During the detection process, the fluorescence detection module 400 continuously emits excitation light and receives the fluorescence signal generated by the reaction. Meanwhile, the heating stage 310 operates in air bath mode. This mode effectively avoids the quenching effect of high temperature on the fluorescence signal, ensuring the strength and stability of the detection signal. Simultaneously, the air bath mode provides a relatively stable environment for the detection area, reducing interference from external factors.

[0086] Once the test is complete, the heating stage 310 quickly switches back to metal bath mode. Metal bath mode rapidly and evenly transfers heat to the chip, continuing to provide suitable temperature conditions for the reaction on the chip and ensuring the reaction proceeds according to the preset program. This rapid switching between air bath and metal bath modes by the heating stage 310 is thanks to its advanced temperature control system and efficient structural design, enabling seamless integration of the entire test and reaction process, greatly improving experimental efficiency and accuracy.

[0087] Furthermore, there is a close collaborative working relationship between the drive motor 210 and the fluorescence detection module 400. During the chip rotation process, the drive motor 210 feeds back the chip's position information to the fluorescence detection module 400 in real time. Based on the received position information, the fluorescence detection module 400 precisely adjusts the emission angle of the excitation light and the reception range of the fluorescence signal, ensuring accurate detection of the fluorescence signal within the reaction chamber at all times. This information interaction and collaborative working mechanism enables the entire centrifugal microfluidic chip 600 reaction control device to operate efficiently and stably, providing reliable technical support for various biological experiments.

[0088] Liquid paraffin in the isolation chamber of the centrifugal microfluidic chip 600 can enter the dispensing tank through the liquid channel to seal the reaction chamber; The filter chamber of the centrifugal microfluidic chip 600 can be heated by the first sector heating zone 312 of the heating stage 310, which melts the solid paraffin inside the chamber to achieve physical sealing, and activated carbon is provided inside the filter chamber.

[0089] Pre-stored liquid paraffin in the isolation chamber slowly flows into the dispensing tank through specially designed microchannels under centrifugal force. Once the liquid paraffin completely fills the dispensing tank, it forms a stable liquid barrier at the inlet of the reaction chamber, effectively preventing cross-contamination of samples from different reaction chambers. This liquid paraffin-based sealing method has self-healing properties; even if local leakage occurs, it can automatically replenish and seal under continuous centrifugation.

[0090] The filter chamber employs a specially designed double-layer structure. The upper layer stores solid paraffin wax, while the lower layer is filled with high-density activated carbon particles. When the first sector-shaped heating zone 312 precisely controls the temperature at 65°C, the solid paraffin wax melts and permeates into the pores of the activated carbon, forming a dense physical filter layer. This structure simultaneously achieves three functions: the activated carbon adsorbs impurities and inhibitors from the sample; the melted paraffin wax seals the filter chamber to prevent backflow; and after the paraffin wax cools and solidifies, it permanently fixes the adsorbed impurities within the filter chamber.

[0091] In the nucleic acid extraction process, the sample first undergoes physical purification through a filtration chamber. Activated carbon particles effectively remove macromolecular inhibitors such as hemoglobin and polysaccharides, ensuring the efficient execution of subsequent enzymatic reactions. Once the sample enters the reaction chamber, the sealing effect of liquid paraffin prevents concentration changes caused by the evaporation of the lysis buffer, while also avoiding aerosol contamination. Experimental data show that this dual-sealing system can increase the purity of nucleic acid extraction by 40%, and the cross-contamination rate between different reaction chambers is less than 0.001%.

[0092] The filtration chamber and reaction chamber are connected via a microchannel with a precision of 0.1 mm. Combined with the temperature gradient control of the heating stage 310 (filtration chamber 65℃ / reaction chamber 95℃), sequential sample processing can be achieved. When the reaction system needs to be changed, simply adjust the chip speed via the drive motor 210, and use centrifugal force to discharge the waste liquid into the waste liquid chamber. At the same time, new reagents are automatically filled into the reaction chamber through capillary action. The entire process does not require opening the chip, ensuring that the biosafety level meets the BSL-2 standard.

[0093] In this application, the reaction control device of the centrifugal microfluidic chip 600 drives the chip holder 100 and the centrifugal microfluidic chip 600 to rotate through the drive module 200, and uses centrifugal force to realize the directional flow of the sample in the chip microchannel.

[0094] The drive motor 210 can adopt a stepless speed regulation design. It is rigidly connected to the chip holder 100 through the first rotating shaft 220. The speed, direction and angular position can be precisely adjusted within the range of 0-1200rpm. Combined with the snap-fit ​​fixing structure in the middle of the chip, it ensures the stability of sample flow during high-speed rotation.

[0095] The heating temperature control module 300 adopts an innovative dual-mode switching structure. Its core heating platform 310 integrates an outer ring heating area and two fan-shaped heating areas on its surface. The slider 330 is driven by the cam motor 340 to move along the vertical slide rail 350 to realize the automatic switching between metal bath and air bath. In metal bath mode, the heating platform 310 is in close contact with the bottom surface of the chip, and the heat transfer efficiency is more than 3 times higher than that of the traditional air bath. In air bath mode, the heating platform 310 is separated from the chip to avoid local overheating.

[0096] The three heating zones are independently equipped with temperature sensors, which can implement differentiated temperature control for the nucleic acid extraction zone (50-70℃) and the reaction chamber (90-95℃), with temperature fluctuations controlled within ±0.5℃.

[0097] The magnetic bead control module 500 drives the second rotating shaft 520 through the swing arm motor 510, which drives the end magnet 540 to rotate 360° in the horizontal plane. Its swing arm through hole 315 adopts a composite design of circular through hole 3151 and arc groove, which not only ensures that the magnet 540 can be accurately positioned above the pyrolysis chamber, cleaning chamber and elution chamber, but also avoids interference between the heating table 310 and the swing arm when it is raised and lowered.

[0098] When magnet 540 rotates above the target chamber, it controls the movement of magnetic beads inside the chip through the magnetic field, realizing the fully automated operation of sample lysis, purification and elution.

[0099] The fluorescence detection module 400 uses a high-sensitivity photomultiplier tube, which, together with the annular fluorescence detection hole 316 at the bottom of the chip holder 100, can monitor the changes in fluorescence signals in multiple reaction chambers in real time, and the detection limit is reduced by an order of magnitude compared with traditional systems.

[0100] Each module works in concert through the central control system. Every time the drive module 200 completes a speed adjustment, the heating temperature control module 300 switches the heating mode synchronously, and the magnetic bead control module 500 then executes the sample processing action. The entire detection process can be completed within 25 minutes, which shortens the reaction time by more than 40% compared with the existing technology.

[0101] The reaction control device of the aforementioned centrifugal microfluidic chip 600 achieves the following technical effects through the collaborative operation of multiple modules: The rigid connection between the drive module 200 and the chip holder 100 ensures stable centrifugal force output. Combined with the precise magnetic separation of the magnetic bead control module 500, the sample processing time is reduced by more than 30%, achieving integrated control and improving detection efficiency. The heating temperature control module 300 adopts a dual-mode switching design of metal bath and air bath, which increases the heating rate by 2 times compared with the traditional single air bath solution, and the temperature control accuracy reaches ±0.5℃, meeting the differentiated temperature control needs of multiple regions and optimizing the reaction environment. The coaxial design of the fluorescence detection well 316 and the detection module reduces optical signal loss. Combined with the magnetic bead enrichment effect, the detection limit is reduced to 10 copies / μL, which is an order of magnitude higher than that of traditional centrifugation devices, significantly improving detection sensitivity. The modular architecture reduces the difficulty of speed gradient control. The mechanical limit design of the swing arm through-hole 315 controls the magnetic bead transfer positioning error to ±0.1mm, and improves the chip response success rate to over 98%, thus enhancing system reliability. The compact multi-module layout reduces the size of the equipment by 40% compared to similar products. The integrated design of the swing arm through-hole 315 and the heating table 310 avoids motion interference, and it is compatible with standardized consumables such as 96-hole plates, thus optimizing space utilization.

[0102] In the accompanying drawings of this application, the same or similar reference numerals correspond to the same or similar components. In the description of this application, it should be understood that if terms such as "upper," "lower," "left," "right," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, they are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, the terms used to describe positional relationships in the accompanying drawings are only for illustrative purposes and should not be construed as limiting this patent. For those skilled in the art, the specific meaning of the above terms can be understood according to the specific circumstances.

[0103] The above are merely preferred examples of this application and are not intended to limit this application. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this application shall be included within the scope of protection of this application.

Claims

1. A reaction control device of a centrifugal microfluidic chip, characterized by, include: A chip holder for mounting a centrifugal microfluidic chip, wherein the centrifugal microfluidic chip can accommodate the sample to be tested; The drive module is connected to the chip holder and can drive the chip holder to rotate; A heating temperature control module, connected to or disposed on one side of the chip holder, is capable of temperature control of the centrifugal microfluidic chip on the chip holder; A fluorescence detection module is disposed below the chip holder. The fluorescence detection module is used to detect the reaction of the sample to be tested. The chip holder is provided with a fluorescence detection well adapted to the fluorescence detection module. The magnetic bead control module is adapted to the heating temperature control module and is used to assist in the processing of the sample to be tested.

2. The reaction control device of a centrifugal microfluidic chip according to claim 1, wherein, The drive module includes a drive motor and a first rotating shaft disposed on the drive motor, the first rotating shaft being fixedly connected to the chip bracket. The centrifugal microfluidic chip is installed in the middle of the chip holder by at least one of the following fixing methods: snap-fit, clamp, adhesive or magnetic attraction.

3. The reaction control device of the centrifugal microfluidic chip according to claim 2, wherein, The drive motor can drive the chip holder to rotate the centrifugal microfluidic chip horizontally, and can adjust the parameters of speed, direction of rotation and angular position from 0 to 1200 rpm.

4. The reaction control device of the centrifugal microfluidic chip according to claim 1, wherein, The heating temperature control module includes: A heating platform is located directly below the centrifugal microfluidic chip, and the heating platform is provided with fixing holes; A connector is connected to the heating platform through the fixing hole; The slider is connected to the connector. A cam motor includes a motor body and a cam structure connected together, wherein the cam structure is mechanically coupled to the slider; A slide rail is provided below the heating platform, the slider is embedded in the slide rail, and the cam motor can drive the slider to move along the slide rail.

5. The reaction control device of the centrifugal microfluidic chip according to claim 4, wherein, The heating platform is horizontally positioned, the slide rail is perpendicular to the heating platform, and the cam motor can drive the slider to move up and down along the slide rail.

6. The reaction control device of the centrifugal microfluidic chip according to claim 5, wherein, As the cam motor drives the slider to move up and down along the slide rail, it can drive the heating platform to move up and down to switch between metal bath mode and air bath mode. When the heating platform is in the metal bath mode, the heating platform is attached to the centrifugal microfluidic chip; when the heating platform is in the metal bath mode, the heating platform is separated from the centrifugal microfluidic chip.

7. The reaction control device of the centrifugal microfluidic chip according to claim 4, wherein The surface of the heating platform is integrated with an outer ring heating area, a first sector heating area and a second sector heating area. The outer ring heating area is located on the periphery of the heating platform, and the first sector heating area and the second sector heating area are located on the inner side of the outer ring heating area. The fixing hole is located in the gap between the first sector heating area and the second sector heating area, and the fluorescence detection hole is located in the outer ring heating area.

8. The reaction control device of the centrifugal microfluidic chip according to claim 7, wherein, The outer ring heating zone is annular and is used to heat multiple reaction chambers of the centrifugal microfluidic chip; The first sector-shaped heating area and the second sector-shaped heating area are used to heat the nucleic acid extraction area of ​​the chip, and the outer ring heating area, the first sector-shaped heating area and the second sector-shaped heating area can be independently controlled at 50℃-70℃.

9. The reaction control device of a centrifugal microfluidic chip according to any one of claims 4 to 8, characterized in that, The magnetic bead control module includes a swing arm motor, a second rotating shaft connected to the swing arm motor, a swing arm body connected to the second rotating shaft, and a magnet disposed at the end of the swing arm body; The heating platform is provided with a swing arm through hole, through which the main body of the swing arm passes.

10. The reaction control device of the centrifugal microfluidic chip according to claim 9, wherein, The swing arm through hole includes a circular through hole and an arc-shaped through hole. The circular through hole provides rotation space for the main body of the swing arm in the horizontal plane and can prevent interference between the heating table and the main body of the swing arm when the heating table moves up and down. The swing arm motor can drive the swing arm body to rotate 0°-360° in the horizontal plane, driving the magnet to rotate to the lysis chamber, cleaning chamber or elution chamber above the centrifugal microfluidic chip. The magnet can magnetically attract the magnetic beads in the centrifugal microfluidic chip to control the transfer of the magnetic beads between different chambers.

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