Differential rotation type microfluidic centrifugal device

Abstract

The invention discloses a differential rotation type micro-fluidic centrifugal device, and relates to the technical field of centrifugal micro-fluidic chips, the differential rotation type micro-fluidic centrifugal device comprises a lower mounting seat, and a lower fluted disc is fixed at the top end of the lower mounting seat; the upper mounting seat is positioned above the lower mounting seat, an upper fluted disc is fixed at the bottom end of the upper mounting seat, and a centrifugal platform is fixed on the outer side of the upper mounting seat and is used for mounting a micro-fluidic chip; the bottom end of the connecting shaft is in transmission connection with the power output end of the driving mechanism, and the top end of the connecting shaft sequentially penetrates through the lower mounting seat and the upper mounting seat and is rotationally connected with the upper mounting seat; side fluted discs meshed with the lower fluted disc and the upper fluted disc are rotationally connected to the two sides of the connecting shaft, and the connecting shaft is hollow to form a through channel; a connecting pipeline is arranged in the through channel, penetrates out of the top of the through channel and is connected with a connecting port of the micro-fluidic chip; and the driving mechanism can drive the connecting shaft and the centrifugal platform to form differential rotation, so that the pipeline penetrating through the through channel is dynamically unwound in the centrifugal process.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of centrifugal microfluidic chip, more particularly to a differential rotation type microfluidic centrifugal device. BACKGROUND

[0002] The centrifugal microfluidic chip technology utilizes the centrifugal force generated by rotation to drive the liquid to flow in the microchannel, and is an important platform for realizing the automation and integration of biochemical analysis. However, this technology has a long-standing core bottleneck that has not been effectively solved in terms of real-time and continuity of fluid control.

[0003] Specifically, in order to realize the fluid connection with external devices (such as injection pumps and detectors), the microfluidic chip usually needs to be connected to the fluid control unit which is static outside the device through flexible pipelines. When the chip rotates at high speed with the centrifuge disc, these connecting pipelines will inevitably be wound, kinked or even broken due to continuous one-way rotation, which makes it impossible to perform real-time liquid sampling, reagent addition or product extraction during the centrifugation process.

[0004] To this end, the existing technical solution works in the following mode: first, centrifugal separation is performed, then the centrifuge is stopped, and then subsequent fluid operations are performed by manual or mechanical hands in a static state. This cycle mode of "centrifugation-stop-operation" not only restricts the work efficiency, but more importantly, the centrifuge stop will destroy the stable separation interface that has been formed, causing the liquids of different components to be re-mixed due to gravity, shock or capillary action, thereby significantly reducing the purity and recovery rate of the product extraction. In other words, the winding problem of the pipeline in the centrifugal state is one of the fundamental obstacles to realizing the closed, continuous and automated operation of the centrifugal microfluidic technology.

[0005] Therefore, how to provide a centrifugal device that can prevent pipeline winding and realize uninterrupted real-time fluid delivery and extraction during the entire centrifugation process is a problem that needs to be solved by those skilled in the art. SUMMARY

[0006] Therefore, the present application provides a differential rotation type microfluidic centrifugal device, which aims to solve the above technical problems.

[0007] In order to achieve the above purpose, the present application adopts the following technical solutions: A differential rotation type microfluidic centrifugal device, comprising: a lower mounting seat, the top end of the lower mounting seat is fixed with a lower tooth disc; an upper mounting seat, the upper mounting seat is located above the lower mounting seat, and the bottom end of the upper mounting seat is fixed with an upper tooth disc, the outer side of the upper mounting seat is fixed with a centrifugal platform, and the centrifugal platform is used for mounting a microfluidic chip; A connecting shaft is included, with its bottom end connected to the power output end of the drive mechanism. The top end of the connecting shaft passes through the lower mounting base and the upper mounting base sequentially and is rotatably connected to the upper mounting base. Side gear disks that mesh with the lower and upper gear disks are rotatably connected to both sides of the connecting shaft. The connecting shaft has a hollow internal structure, forming a through channel. A connecting pipe is provided inside the through channel, and the connecting pipe extends from the top of the through channel and connects to the connection port of the microfluidic chip. The drive mechanism can drive the connecting shaft to rotate at a differential speed with the centrifugal platform, so that the connecting pipe passing through the through channel can be dynamically unspinned during centrifugation.

[0008] Through the above technical solution, this invention discloses a differential rotational microfluidic centrifuge device. By using a differential rotational structure and hollow channel design, it effectively solves the technical problems of tubing entanglement, kinking, or breakage during centrifugation. By utilizing the stable speed difference between the connecting shaft and the centrifugation platform, it achieves dynamic unwinding of the connecting tubing during high-speed centrifugation, thereby establishing a reliable and continuous fluid transfer channel between the rotating microfluidic chip and the external stationary device without stopping centrifugation. It abandons the inefficient and easily damaging traditional "centrifugation-stop-operation" mode, realizing fully enclosed, continuous, and real-time automated operation of fluid delivery and extraction during centrifugation. More importantly, it ensures that the target product maintains high purity and high recovery rate throughout the separation and transfer process.

[0009] Preferably, in the aforementioned differential rotary microfluidic centrifuge, the lower gear disk and the upper and side gear disks have the same number of teeth. By limiting the gear tooth ratio to 1:1:1, it is ensured that the rotational speed of the centrifuge platform is always twice the rotational speed of the connecting shaft, thereby generating a constant and controllable speed difference (N). This ensures the reliability and consistency of the tubing unwinding effect and avoids operational risks caused by speed fluctuations.

[0010] Preferably, in the aforementioned differential rotary microfluidic centrifuge, a connecting column passing through the connecting shaft is cross-fixed between the upper and lower gear disks. A support arm is fixed to one end of the connecting column, and the end of the support arm away from the connecting column is a free end that bends upwards and is hollow inside, communicating with the through channel. A balance arm is fixed to the other end of the connecting column. The support arm provides a stable transition and fixed path for the tubing from the inside of the rotating system to the microfluidic chip, preventing the tubing from swinging or wearing under high-speed centrifugation. The balance arm ensures the dynamic balance of the connecting shaft system during high-speed rotation, greatly reducing equipment vibration and noise, and ensuring the stability, reliability, and lifespan of the equipment.

[0011] Preferably, in the aforementioned differential rotary microfluidic centrifuge device, the centrifugation platform includes a centrifuge disc, a cover plate fixed to the top of the centrifuge disc, and a mounting base fixed to the top of the cover plate, with the microfluidic chip mounted on the mounting base. This defines an integrated mounting platform for the microfluidic chip. Through a modular design of "centrifuge disc-cover plate-mounted base," a standard, stable, and functionally integrated mounting foundation is provided for the microfluidic chip, making chip installation, removal, and integration with pneumatic and optical detection systems convenient and precise.

[0012] Preferably, in the aforementioned differential rotary microfluidic centrifuge device, the centrifuge disc is divided into a sealed chamber and a pump valve mounting chamber for mounting a pump valve assembly via an annular mounting plate. The pump valve assembly is connected to the sealed chamber via an air pipe for regulating the air pressure within the sealed chamber. This constructs an integrated air pressure generation and control system within the rotating system; by integrating the pump valve assembly and the sealed chamber onto the centrifuge disc, precise positive / negative pressure control of the internal chambers of the microfluidic chip is achieved during continuous centrifugation, providing an independent power source for driving complex and directional liquid transfer.

[0013] Preferably, in the above-mentioned differential rotary microfluidic centrifuge device, a first endotracheal interface is installed on the cover plate corresponding to the sealed cavity. The mounting base has a mounting plate, the microfluidic chip is mounted on the upper surface of the mounting plate, and a second endotracheal interface communicating with the first endotracheal interface is located on the lower surface of the mounting plate. The second endotracheal interface is connected to the gas path interface of the microfluidic chip. This establishes a specific, sealed gas pressure transmission path from the rotating platform to the microfluidic chip. Through the connection of "first endotracheal interface - second endotracheal interface - chip gas path interface," the control gas pressure generated on the centrifuge disc is accurately and without loss transmitted to the target chamber of the chip, realizing remote, non-contact application of gas pressure driving force.

[0014] Preferably, in the aforementioned differential rotary microfluidic centrifuge, the microfluidic chip, the mounting plate, and the cover plate each have a through hole at their center that communicates with the through channel. This clarifies the physical channel of the liquid pipeline; by creating coaxial through holes at the center of each layer and connecting them to the through channel of the connecting shaft, a sealed and unobstructed channel is formed, extending directly from the stationary exterior to the interior of the rotating chip, ensuring the physical feasibility of real-time sample injection and extraction.

[0015] Preferably, the differential rotary microfluidic centrifuge described above further includes a fluid drive assembly, which comprises multiple fluid drive components. One end of the connecting pipe is connected to the fluid drive component, and the other end passes sequentially through the support arm and the connecting shaft, and exits through the through hole to communicate with the fluid interface of the microfluidic chip. Through the fluid drive assembly (injection pump / peristaltic pump) and the aforementioned channel, precise injection of samples into the chip or precise extraction of products from the chip is achieved during continuous centrifugation, all within a sealed environment, avoiding contamination and damage to the separation interface.

[0016] Preferably, in the aforementioned differential rotary microfluidic centrifuge, a photoelectric detection component is integrated on the upper surface of the mounting plate. This photoelectric detection component is communicatively connected to the pump and valve assembly, and is used to control the start and stop of the pump and valve assembly based on the detected optical signals. By real-time monitoring of the liquid interface within the chip (such as the interface between plasma, white membrane layer, and red blood cells) by the photoelectric detection component, and automatically controlling the start and stop of the pump and valve assembly accordingly, precise liquid transfer control based on real-time feedback is achieved. This replaces traditional manual judgment and operation, ensuring high purity, high repeatability, and high efficiency in separation and extraction.

[0017] Preferably, the aforementioned differential rotary microfluidic centrifuge further includes a primary slip ring and a secondary slip ring installed at both ends of the connecting shaft. The primary and secondary slip rings form a power supply path to power the pump-valve assembly and the photoelectric detection assembly, and transmit signals. This dual slip ring design establishes a reliable channel that flows from a stationary external system through the two-stage rotating system, ultimately powering and transmitting signals to the pump-valve assembly and photoelectric detection assembly on the centrifuge disc. This is crucial for ensuring the normal operation of all electronic control functions during high-speed centrifugation.

[0018] As can be seen from the above technical solution, compared with the prior art, the present invention discloses a differential rotational microfluidic centrifuge device, which has the following beneficial effects: 1. This invention solves the industry problem of pipe entanglement, kinking or breakage by using a constant and controllable speed difference between the connecting shaft and the centrifugation platform to make the connecting pipe continuously twist in the opposite direction during high-speed centrifugation. This makes it possible to perform real-time, closed liquid injection and product extraction without stopping centrifugation, and abandons the inefficient traditional "centrifugation-stop-operation" mode.

[0019] 2. The stable separation interface (such as plasma, white membrane layer, and red blood cell layer) formed by the sample under centrifugal force is maintained at all times, avoiding liquid remixing due to machine shutdown; combined with real-time interface monitoring and feedback control of photoelectric detection components, accurate judgment of the extraction timing of target components is achieved, thereby greatly improving the extraction purity and recovery rate of the product.

[0020] 3. This invention highly integrates functional modules such as pneumatic control (pump and valve assembly, sealed chamber), online detection (photoelectric detection assembly), and fluid drive (multiple fluid drive components) within the rotating system, and achieves stable power supply and signal transmission through dual electric slip ring technology. Operators only need to complete the initial sample loading to start the system with a single button, realizing fully automated and sealed operation from sample introduction, centrifugation, detection, transfer, and extraction, effectively avoiding human error and the introduction of environmental pollutants.

[0021] 4. The modular design of this invention (e.g., centrifuge tray-cover plate-fixing base) facilitates the installation and replacement of the microfluidic chip. The completely sealed operating environment during sample centrifugation preparation within the chip not only ensures sample sterility but also protects operators from potential biohazards. The design of the support arm and balance arm ensures dynamic balance under high-speed rotation, guaranteeing the long-term stability and lifespan of the equipment. Attached Figure Description

[0022] To more clearly illustrate the technical solutions in 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 embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on the provided drawings without creative effort.

[0023] Figure 1 The attached figure is a schematic diagram of the differential rotary microfluidic centrifuge device provided by the present invention; Figure 2 The attached figures show the lower mounting base, upper mounting base, and centrifuge platform provided by the present invention; Figure 3 The attached image is... Figure 2 The attached sectional view; Figure 4 The attached figure is a structural schematic diagram of the connecting shaft and support arm provided by the present invention; Figure 5 The attached figure is a schematic diagram of the centrifuge disc provided by the present invention; Figure 6 The attached figure is a schematic diagram of the structure of the centrifuge disc and cover plate provided by the present invention; Figure 7 The attached figure is a schematic diagram of the centrifuge platform provided by the present invention; Figure 8 The attached figure is a structural schematic diagram of the base and drive mechanism provided by the present invention; Figure 9 The attached figure is a schematic diagram of fluid transfer on the microfluidic chip provided by the present invention; Figure 10 The attached figure is a schematic diagram of the pipeline connected to the microfluidic chip provided by the present invention; Figure 11 The attached figure is a schematic diagram of the microfluidic chip structure provided by the present invention.

[0024] Wherein: 1-lower mounting base; 11-lower gear disc; 2-upper mounting base; 21-upper gear disc; 3-centrifuge platform; 31-centrifuge disc; 311-annular mounting plate; 312-sealed cavity; 313-pump valve assembly; 314-pump valve mounting cavity; 32-cover plate; 321-first air pipe interface; 33-fixed base; 331-mounting plate; 332-second air pipe interface; 4-connecting shaft; 41-side gear disc; 42-through channel; 43-connecting column; 44-support arm; 45-balance arm; 46-first-stage electric slip ring; 47-second-stage electric slip ring; 5-drive mechanism; 5 1-Drive motor; 52-Belt drive assembly; 53-Tensioner pulley; 6-Microfluidic chip; 61-Liquid interface; 7-Fluid drive assembly; 71-Fluid drive component; 711-Injection pump; 712-Peristaltic pump; 713-Collection bag; 714-Pinch valve; 715-Four-way connector; 8-Photoelectric detection assembly; 81-Signal exciter; 82-Rotating structure; 83-Signal receiver; 9-Base; 91-Housing; 911-Pipe fixing structure; 92-Upper support plate; 921-Adjustment hole; 93-Lower support plate; 94-Spring; 95-Support column. Detailed Implementation

[0025] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0026] See appendix Figure 1 This invention discloses a differential rotational microfluidic centrifuge device, comprising: The lower mounting base 1 has a lower gear plate 11 fixed to its top end; Upper mounting base 2 is located above lower mounting base 1, and an upper gear plate 21 is fixed at its bottom end. A centrifugal platform 3 is fixed on the outside of the upper mounting base 2. The centrifugal platform 3 is used to install the microfluidic chip 6. The connecting shaft 4 is connected to the power output end of the drive mechanism 5 at its bottom end. The top end of the connecting shaft 4 passes through the lower mounting base 1 and the upper mounting base 2 in sequence and is rotatably connected to the upper mounting base 2. Side gear disks 41 that mesh with the lower gear disk 11 and the upper gear disk 21 are rotatably connected to both sides of the connecting shaft 4. The connecting shaft 4 has a hollow structure inside, forming a through channel 42. A connecting pipe is provided in the through channel 42. The connecting pipe passes out from the top of the through channel 42 and is connected to the connection port of the microfluidic chip. Among them, the drive mechanism 5 can drive the connecting shaft 4 to rotate at a different speed with the centrifugal platform 3, so that the connecting pipe passing through the through channel 42 can achieve dynamic unspinning during the centrifugation process.

[0027] In some specific embodiments, the lower gear disk 11 and the upper gear disk 21 and the side gear disk 41 have the same number of teeth.

[0028] In some other embodiments, the connecting shaft 4 is cross-fixed between the upper gear disk 21 and the lower gear disk 11 with a connecting post 43 passing through the connecting shaft 4. One end of the connecting post 43 is fixed with a support arm 44. The end of the support arm 44 away from the connecting post 43 is a free end that bends upward and extends, and its inner side is hollow and communicates with the through channel 42. The other end of the connecting post 43 is fixed with a balance arm 45.

[0029] In a specific embodiment, the centrifugation platform 3 includes a centrifugation disc 31, a cover plate 32 fixed to the top of the centrifugation disc 31, and a fixing seat 33 fixed to the top of the cover plate 32, with the microfluidic chip 6 mounted on the fixing seat 33.

[0030] In a specific example, the centrifugal disc 31 is divided into a sealed chamber 312 and a pump valve mounting chamber 314 for mounting a pump valve assembly 313 by an annular mounting plate 311. The pump valve assembly 313 is connected to the sealed chamber 312 by an air pipe and is used to regulate the air pressure in the sealed chamber 312.

[0031] In some examples, a first tracheal interface 321 is installed on the cover plate 32 corresponding to the sealed cavity 312, and a mounting plate 331 is provided in the fixing base 33. The microfluidic chip 6 is installed on the upper surface of the mounting plate 331, and a second tracheal interface 332 is provided on the lower surface of the mounting plate 331, which is connected to the first tracheal interface 321. The second tracheal interface 332 is connected to the airway interface of the microfluidic chip 6.

[0032] More specifically, the microfluidic chip 6, the mounting plate 331 and the cover plate 32 have through holes in their centers that communicate with the through channel 42.

[0033] In some specific examples, a fluid drive assembly 7 is also included, which includes multiple fluid drive components 71; one end of the connecting pipe is connected to the fluid drive component 71, and the other end passes through the support arm 44 and the connecting shaft 4 in sequence, and exits through the through hole to connect with the liquid interface 61 of the microfluidic chip 6.

[0034] The fluid drive 71 refers to a device that can provide fluid power to realize liquid injection or extraction. Its specific implementation includes, but is not limited to, injection pumps, peristaltic pumps, plunger pumps, etc. The corresponding fluid drive can be selected as needed.

[0035] More specifically, the upper surface of the mounting plate 331 integrates a photoelectric detection component 8, which is communicatively connected to the pump valve assembly 313 and is used to control the start and stop of the pump valve assembly 313 based on the detected optical signal.

[0036] In a specific example, as shown in the appendix Figure 3 Or attached Figure 7 As shown, the photoelectric detection component 8 consists of a signal exciter 81, a rotating structure 82, and a signal receiver 83. This module can employ either the principle of light absorption or the principle of optical imaging recognition to detect the position of the centrifugal separation interface of the sample inside the microfluidic chip 6. When the interface reaches the extraction position, the pump valve is opened to extract the component to be extracted into the corresponding chamber; when extraction is complete, the pump valve is closed to stop liquid transfer. The function of the rotating structure 82 is to allow the signal exciter 81 to be rotated to one side when the microfluidic chip 6 is installed or removed, and to rotate the signal exciter 81 to above the microfluidic chip 6 after installation or removal.

[0037] like Figure 1 As shown, the lower mounting base 1 is mounted on the base 9, and the base 9 has a housing 91 covering the lower mounting base 1, the upper mounting base 2 and the centrifugal platform 3. One end of the connecting pipe is connected to the injection pump 711, and the other end passes through the pipe fixing structure 911, the support arm 44 and the connecting shaft 4 at the top of the housing 91 in sequence, and passes through the through hole to connect with the microfluidic chip 6.

[0038] In some other embodiments, a primary slip ring 46 and a secondary slip ring 47 are also installed at both ends of the connecting shaft 4. The primary slip ring 46 and the secondary slip ring 47 form a power supply path to supply power to the pump valve assembly 313 and the photoelectric detection assembly 8 and transmit signals.

[0039] More specifically, as shown in the appendix Figure 8 As shown, the drive mechanism 5 includes a drive motor 51 and a belt drive assembly 52 that is connected to the drive motor 51; the belt drive assembly 52 is connected to the connecting shaft 4 and is used to drive the connecting shaft 4 to rotate.

[0040] As attached Figure 8 As shown, the base 9 includes an upper support plate 92 and a lower support plate 93, with a spring 94 connecting the upper support plate 92 and the lower support plate 93; and a support column 95 is fixed to the bottom surface of the lower support plate 93.

[0041] In one specific embodiment, the drive mechanism 5 further includes a tension wheel 53, and an adjustment hole 921 is provided on the upper surface of the upper support plate 92. The adjustment hole 921 is used to adjust the position of the tension wheel 53 to achieve belt tension.

[0042] The embodiments of the present invention are as follows: Example 1: Working principle of fluid transfer on a microfluidic chip This embodiment involves the directional transfer of liquid within a microfluidic chip using a differential rotation centrifugal device, and precise control of liquid flow through negative pressure control and photoelectric detection. (See attached diagram.) Figure 9 Fluid transfer diagram and appendix Figure 1 As shown, the working principle is as follows: Initial setup: The microfluidic chip 6 is mounted on the mounting base 33 and connected to the fluid drive assembly 7 via a connecting tube. The connecting tube starts from the injection pump 711, which serves as the fluid drive assembly 71, and passes sequentially through the tube fixing structure 911 of the housing 91, the hollow interior of the support arm 44, the through channel 42 of the connecting shaft 4, and finally connects to the injection port of the microfluidic chip 6 through the through holes of the cover plate 32 and the mounting plate 331.

[0043] Centrifugal Start-up and Unwinding: The drive mechanism 5 starts, driving the connecting shaft 4 to rotate via the drive motor 51 and belt drive assembly 52. ​​The lower gear disk 11 is fixed, and the connecting shaft 4 drives the side gear disk 41 to rotate along the lower gear disk 11, that is, the side gear disk 41 rotates simultaneously along its axial direction and the axial direction of the connecting shaft 4. While the side gear disk 41 is rotating, it also drives the upper gear disk 21 to rotate, so that the centrifugal platform 3 and the connecting shaft 4 rotate in the same direction. The differential speed ratio is related to the number of teeth of the lower gear disk 11, the upper gear disk 21, and the side gear disk 41. When the ratio of the number of teeth of the lower gear disk 11, the upper gear disk 21, and the side gear disk 41 is 1:1:1, the speed difference between the centrifugal platform 3 and the connecting shaft is 2 times. This differential rotation allows the connecting pipeline to dynamically unwind during centrifugation, avoiding liquid pipeline entanglement.

[0044] Sample introduction and centrifugal separation: The syringe pump 711, acting as a fluid drive, pushes the sample to be separated into the injection chamber of the microfluidic chip 6. Under centrifugal force (e.g., setting the centrifugation parameters to 400g), the sample separates into two layers within the microfluidic chip (e.g., ...). Figure 9 As shown in S1).

[0045] Photoelectric detection and negative pressure control: The photoelectric detection component 8 is integrated on the mounting plate 331 to detect the photoelectric signal of the liquid inside the microfluidic chip 6 in real time. At this time, the pressure control module is activated: the pump valve assembly 313 generates negative pressure in the pump valve mounting cavity 314, which is connected to the sealed cavity 312 via an air tube, and then transmitted to the target chamber via the first air tube interface 321, the second air tube interface 332, and the air path interface of the microfluidic chip. The negative pressure causes the lower layer product to overcome centrifugal force and transfer to the designated chamber (e.g., ...). Figure 9 (As shown in S2). When the layered interface reaches the extraction position, the pump valve assembly 313 closes when the photoelectric signal changes abruptly (e.g., a change in light transmittance), the negative pressure in the target chamber is eliminated, and the liquid transfer stops.

[0046] Product Extraction: When the photoelectric detection component 8 detects that the upper layer product has reached the extraction point, the signal changes abruptly, and the pump valve assembly 313 stops outputting negative pressure. Subsequently, the pump valve assembly 313 applies negative pressure to another chamber, transferring the upper layer product to the corresponding chamber (e.g., ...). Figure 9 (As shown in S3). Throughout the process, the product from each layer is extracted into a collection bag by the syringe pump 711, which acts as a fluid drive. As centrifugation continues, the separation interface remains stable, ensuring product purity and sterility.

[0047] Example 2: Working principle of real-time sampling and injection via multiple pipelines This embodiment demonstrates how to connect multiple tubing to a microfluidic chip using a differential rotation centrifuge device, and perform real-time sample injection and extraction during centrifugation. (See attached diagram.) Figure 10 and attached Figure 1 As shown, the working principle is as follows: Piping Connections: Multiple connecting pipes originate from multiple fluid drive components of the fluid drive assembly 7, pass through the pipe fixing structure 911, the support arm 44, and the through channel 42 of the connecting shaft 4, and connect to multiple liquid interface 61 of the microfluidic chip 6 through the through holes of the cover plate 32 and the mounting plate 331. These pipes are used for sample injection, extraction, and waste liquid treatment, respectively. In this embodiment, the fluid drive component 71 includes an injection pump 711 for sample injection and a peristaltic pump 712 for extraction.

[0048] Differential rotation unwinding: The drive mechanism 5 drives the connecting shaft 4 and the centrifuge platform 3 to rotate at different speeds (centrifuge platform speed 2N, connecting shaft speed N), ensuring that multiple pipes are continuously unwinded during centrifugation to avoid entanglement and breakage.

[0049] Sample injection and centrifugation: The syringe pump 711 pushes the sample to be separated into the microfluidic chip 6. Under the action of centrifugal force, the sample is separated into multiple components (for example, blood is divided into plasma, white membrane layer and red blood cell layer).

[0050] Photoelectric detection and component identification: The photoelectric detection component 8 monitors the position of each interface in real time and identifies different components based on differences in light transmittance. When the target product (such as target products A and B) reaches the detection point, the photoelectric signal changes abruptly.

[0051] Negative pressure transfer and extraction: Pump-valve assembly 313 controls the solenoid valve to start and stop based on photoelectric signals, applying negative pressure to a specific chamber to transfer the target product to the corresponding chamber. Subsequently, the peristaltic pump 712, which acts as the fluid drive component 71 in the fluid drive assembly 7, extracts the target products A and B from the microfluidic chip 6 into the collection bag 713 by squeezing the connecting tubing inside its pump head. The entire process is a closed operation to avoid environmental pollution. (See attached image) Figure 10 As shown, multiple connecting pipes are clamped together by a clamp valve 714 and connected by a four-way connector 715.

[0052] Example 3: Working principle of PBMC extraction from whole blood This embodiment details the process of extracting peripheral blood mononuclear cells (PBMCs) from whole blood, utilizing a differential centrifugation device to achieve precise and aseptic extraction. (See attached...) Figure 11 and attached Figure 1 As shown, the working principle is as follows: Initial preparation: Install the syringe for collecting 10 mL of whole blood onto the injection pump 711, which serves as the sample injection drive, and install the syringe for collecting the product onto another injection pump 711, which serves as the extraction drive. The microfluidic chip 6 is mounted on the mounting base 33. The sample injection line and the extraction line pass through the through channel 42 of the connecting shaft 4, are fixed to the line fixing structure 911 via the support arm 44, and are finally connected to their respective syringes.

[0053] Centrifugation parameter settings: Set the centrifugation parameters to 400g for 5 minutes, then 200g for 5 minutes.

[0054] Whole blood injection: Start the device, and the injection pump 711 will inject whole blood into the injection chamber of the microfluidic chip 6 at a constant speed.

[0055] Centrifugation and stratification: The whole blood was centrifuged at 400g for 5 minutes to separate into plasma (upper layer), white membrane layer (middle layer), and red blood cells (lower layer). The centrifugation was then reduced to 200g.

[0056] Photoelectric detection and red blood cell extraction: The photoelectric detection component 8 detects the extraction channel. Initially, the light signal value is below 400 (indicating that the channel is full of red blood cells). The device starts the negative pressure pump (pump-valve assembly 313) and opens the solenoid valve ①, creating negative pressure in the RBC extraction cell connected to the endotracheal interface ① of the microfluidic chip 6, transferring red blood cells to the RBC extraction cell.

[0057] White membrane extraction: As red blood cells transfer, the white membrane descends to the extraction channel, and the light signal value rises to approximately 1000. Close solenoid valve ① and open solenoid valve ② to create negative pressure in the white membrane pool connected to the endotracheal interface ② of the microfluidic chip 6, transferring the white membrane to the white membrane pool. When the light signal value rises to 3000, close solenoid valve ② and the negative pressure pump.

[0058] Product collection: The equipment controls the white film layer extraction injection pump 711, which acts as the extraction drive, to extract the liquid in the white film layer pool into the syringe. Centrifugation stops, and PBMC extraction is complete.

[0059] The entire process is performed under differential rotation, ensuring no tubing entanglement, a stable separation interface, and maintaining the purity and sterility of PBMCs, making them suitable for clinical treatment. This embodiment clearly demonstrates the collaborative operation of multiple fluid drive components (sample injection and extraction syringe pumps) supported by a differential unwinding structure.

[0060] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on its differences from other embodiments. Similar or identical parts between embodiments can be referred to interchangeably. For the apparatus disclosed in the embodiments, since they correspond to the methods disclosed in the embodiments, the description is relatively simple; relevant parts can be referred to the method section.

[0061] The above description of the disclosed embodiments enables those skilled in the art to make or use the invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the invention. Therefore, the invention is not to be limited to the embodiments shown herein, but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A differential rotation type microfluidic centrifugal device, comprising: a lower mounting base (1), the top end of which is fixed with a lower gear disc (11); an upper mounting base (2), which is located above the lower mounting base (1), and the bottom end of which is fixed with an upper gear disc (21), and the outer side of which is fixed with a centrifugal platform (3) for mounting a microfluidic chip (6); a connecting shaft (4), the bottom end of which is in transmission connection with the power output end of a driving mechanism (5), the top end of which penetrates the lower mounting base (1) and the upper mounting base (2) in sequence and is in rotational connection with the upper mounting base (2); the two sides of the connecting shaft (4) are in rotational connection with a side gear disc (41) engaged with the lower gear disc (11) and the upper gear disc (21), and the inside of the connecting shaft (4) is a hollow structure, forming a through channel (42); a connecting pipeline is arranged in the through channel (42), which penetrates out from the top of the through channel (42) and is connected with the connecting port of the microfluidic chip. Wherein, the driving mechanism (5) can drive the connecting shaft (4) and the centrifugal platform (3) to form differential rotation, so that the connecting pipeline passing through the through channel (42) realizes dynamic uncoiling in the centrifugal process.

2. The differential rotation microfluidic centrifuge device of claim 1, wherein, The number of teeth of the lower gear disc (11) and the upper gear disc (21), and the side gear disc (41) is the same.

3. The differential rotation microfluidic centrifuge device of claim 1, wherein, The connecting shaft (4) is fixed with a connecting column (43) penetrating through the connecting shaft (4) between the upper gear disc (21) and the lower gear disc (11), one end of the connecting column (43) is fixed with a support arm (44), the end of the support arm (44) away from the connecting column (43) is a free end which is bent upward and extends, and the inside of the support arm (44) is hollow and in communication with the through channel (42); the other end of the connecting column (43) is fixed with a balance arm (45).

4. The differential rotation microfluidic centrifuge device of claim 3, wherein, The centrifugal platform (3) comprises a centrifugal disc (31), a cover plate (32) fixed on the top of the centrifugal disc (31), and a fixing seat (33) fixed on the top of the cover plate (32), and the microfluidic chip (6) is mounted on the fixing seat (33).

5. The differential rotation microfluidic centrifuge device of claim 4, wherein, The centrifugal disc (31) is divided into a closed cavity (312) and a pump valve mounting cavity (314) for mounting a pump valve assembly (313) by an annular mounting plate (311), the pump valve assembly (313) is in communication with the closed cavity (312) through an air pipe, and is used for adjusting the air pressure in the closed cavity (312).

6. The differential rotation microfluidic centrifuge device of claim 5, wherein, The cover plate (32) is provided with a first air pipe interface (321) corresponding to the closed cavity (312), the fixing seat (33) has a mounting plate (331), the upper surface of the mounting plate (331) is provided with the microfluidic chip (6), and the lower surface of the mounting plate (331) is provided with a second air pipe interface (332) in communication with the first air pipe interface (321), and the second air pipe interface (332) is in communication with the gas path interface of the microfluidic chip (6).

7. The differential rotation microfluidic centrifuge device of claim 6, wherein, The microfluidic chip (6), the mounting plate (331) and the cover plate (32) are provided with a through hole in the center, which is communicated with the through channel (42).

8. The differential rotation microfluidic centrifuge device of claim 7, wherein, Further comprising a fluid driving assembly (7), the fluid driving assembly (7) comprises a plurality of fluid driving members (71); one end of the connecting pipeline is communicated with the fluid driving member (71), the other end penetrates the support arm (44), the connecting shaft (4) in sequence, and passes through the through hole and is communicated with the liquid path interface (61) of the microfluidic chip (6).

9. The differential rotation microfluidic centrifuge device of claim 6, wherein, The upper surface of the mounting plate (331) is integrated with a photoelectric detection assembly (8), which is communicated with the pump valve assembly (313) and is used for controlling the start and stop of the pump valve assembly (313) according to the detected optical signal.

10. The differential rotation microfluidic centrifuge device of claim 9, wherein, Further comprising a first-stage electric slip ring (46) and a second-stage electric slip ring (47) installed at both ends of the connecting shaft (4), and a power supply path is formed through the first-stage electric slip ring (46) and the second-stage electric slip ring (47) to supply power to the pump valve assembly (313) and the photoelectric detection assembly (8) and transmit signals.

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