Peristaltic pump

Abstract

The utility model discloses a peristaltic pump, which belongs to the technical field of microfluid accurate transportation, aims to solve the problems of low precision and flow pulse of the existing mechanical peristaltic micropump, and comprises a micro-fluidic chip, a clamp component and a driving mechanism, wherein the clamp assembly and the driving mechanism are both connected with the shell, and the micro-fluidic chip is fixed on the outer side of the driving mechanism through the clamp assembly; a flow channel is arranged on one side, wound on the driving mechanism, of the micro-fluidic chip, and the driving mechanism is in fluctuating contact with the flow channel during pumping and is used for extruding fluid in the flow channel in a fluctuating manner; an air cavity is formed in the tail end of the flow channel, microfluid can be stored and released in real time, and pulse fluctuation of the fluid is compensated. According to the utility model, flow fluctuation real-time compensation can be carried out on fluid in the flow channel, the flow pulse error of peristaltic fluid is effectively reduced, the device has the advantages of no pulse, high precision, continuous pumping of microfluid and the like, and stable driving and control of the microfluid are met.

Description

Technical Field

[0001] This utility model relates to a peristaltic pump, belonging to the field of microfluidic precision transport technology. Background Technology

[0002] Microfluidic precision transport technology is crucial for dosage control of biochemical samples. Among them, micropumps based on microfluidic chip technology have advantages such as small size, high integration, and low cost, and are widely used in droplet generation, drug delivery, cell culture, and medical diagnostics. Based on the driving principle of micropumps, they can be divided into two main types: non-mechanical and mechanical.

[0003] Non-mechanical micropumps achieve fluid movement through the conversion of physicochemical energy such as electroosmosis, electrofluid, and electrowetting effects. While they feature low power consumption and simple manufacturing processes, they require complex external driving devices and are susceptible to the influence of electric field environments. Mechanical micropumps, on the other hand, generate driving force through mechanical motion such as piezoelectric actuation, shape memory alloy actuation, and electromagnetic actuation. Although they pose risks of mechanical wear and leakage, they offer advantages such as high driving force and fast response, making them more widely applicable.

[0004] Mechanical micropumps are primarily based on the principle of fluid peristalsis. They utilize external physical fields or electromechanical drives to vibrate or deform a flexible pump membrane, causing a contraction-expansion effect in the microchannels, thereby achieving continuous pumping of fluids. For example, piezoelectric-driven micropumps use the vibration of piezoelectric crystals to drive the pump membrane, offering fast response but suffering from high voltage requirements and difficulties in self-breathing. Shape memory alloy-driven pumps generate large driving forces through thermally induced phase changes, but suffer from low driving frequencies and difficulties in controlling membrane deformation. Therefore, while mechanical micropumps based on flexible pump membranes offer good driving performance, the integration of flexible films into the flow channels is complex, and the films are prone to fatigue failure over long periods, making it difficult to guarantee long-term stability. Another type of mechanical micropump uses motor-driven rollers or balls to compress the flow channels in a microfluidic chip, achieving fluid drive through contraction-expansion caused by the compression of the flow channels. These micropumps offer advantages such as strong driving force, good stability, and long-term operation, but the periodic compression of the microfluidic chip by the rolling elements generates flow pulses, preventing real-time and precise flow control. Utility Model Content

[0005] The purpose of this invention is to provide a peristaltic pump that solves the problems of low precision and flow pulse in existing mechanical peristaltic micropumps, and realizes continuous, stable and high-precision pumping of microfluidics.

[0006] To solve the above-mentioned technical problems, the present invention is implemented using the following technical solution.

[0007] A peristaltic pump includes: a microfluidic chip, a clamping assembly disposed on one side of the microfluidic chip, and a drive mechanism disposed on the other side of the microfluidic chip;

[0008] The microfluidic chip has a flow channel arranged around one side of the drive mechanism;

[0009] The drive mechanism makes undulating contact with the flow channel during pumping, and is used to undulate and squeeze the fluid in the flow channel.

[0010] An air chamber is provided at the end of the flow channel.

[0011] Optionally, the portion of the microfluidic chip near the clamping assembly and the drive mechanism is an arc-shaped segment, and the microfluidic chip extends from the end of the arc-shaped segment to a planar segment away from the clamping assembly and the drive mechanism;

[0012] The air cavity is located in the planar section.

[0013] Optionally, the flow channel includes an annular flow channel formed on the arc segment of the microfluidic chip, a fluid inlet formed at the beginning of the annular flow channel, a curved flow channel connecting the annular flow channel on the planar segment, and a fluid outlet connected to the end of the annular flow channel and located at the end of the planar segment away from the drive mechanism.

[0014] The annular flow channel is close to the drive mechanism, with one side of the drive mechanism in contact with the annular flow channel and the other side not in contact;

[0015] The curved flow channel is also connected to the air chamber.

[0016] Optionally, the gas chamber stores a preset amount of gas, and the number of gas chambers is more than one, and the more than one gas chamber is arranged on the planar section and symmetrically arranged on both sides of the annular flow channel.

[0017] Optionally, the number of air chambers on each side of the annular flow channel is more than one, and they are connected in series through curved flow channels.

[0018] Optionally, a first damping structure is connected to the side of the microfluidic chip near the clamping assembly, and a limiting groove is formed on the microfluidic chip for fitting with the clamping assembly.

[0019] Optionally, the drive mechanism includes a pump head located close to the microfluidic chip, a bearing connected to the pump head by a connecting pin, multiple through-hole balls fitted on the bearing, and a motor connected to the end of the pump head away from the microfluidic chip.

[0020] The multiple through-hole balls are arranged in a circle, with the center of the circle coinciding with the center of the annular flow channel. The apex of each through-hole ball that enters the microfluidic chip is pressed against the annular flow channel, and the through-hole balls that leave the microfluidic chip do not contact the annular flow channel.

[0021] The motor's power output shaft is connected to the pump head via a coupling, thereby the power output by the motor drives the pump head, bearings, and through-hole ball bearings to rotate in and out relative to the microfluidic chip. After rotating into the microfluidic chip, the through-hole ball bearings oscillate and compress the annular flow channel.

[0022] Optionally, the annular flow channel is elastic, undergoes elastic deformation after being squeezed by the through-hole balls, and generates negative pressure inside the flow channel when it recovers.

[0023] When the annular flow channel is subjected to undulating compression by the through-hole ball bearings, the annular flow channel undergoes undulating contraction and expansion, thereby continuously generating negative pressure, which ultimately drives the fluid to be continuously pumped from the fluid inlet to the fluid outlet.

[0024] Optionally, the clamping assembly is mounted on the outside of the housing and includes a fixed clamping plate mounted on the housing and a movable clamping device connected to the fixed clamping plate.

[0025] Optionally, the movable fixture includes an arc-shaped segment that is close to and adapted to the microfluidic chip and two connecting seats respectively connected to both ends of the arc-shaped segment;

[0026] A second damping structure is provided on the inner wall of the arc-shaped segment;

[0027] Each of the two connecting seats is provided with a connecting hole;

[0028] The fixing plate is connected to bumps facing the microfluidic chip.

[0029] Compared with the prior art, the beneficial effects achieved by this utility model are as follows:

[0030] By storing and releasing microfluids in the air chamber in real time, the flow fluctuations of the fluid in the flow channel can be compensated in real time, effectively reducing the flow pulse error of the peristaltic fluid. The drive mechanism can make alternating contact with the flow channel to squeeze the flow channel and dynamically adjust the flow cross section, so that the continuous peristaltic wave passively formed by the fluid can offset the periodic pulse force.

[0031] The microfluidic chip displacement is prevented by the dual fixing mechanism of friction damping and slots in the clamping assembly, ensuring long-term operational reliability. This peristaltic pump has advantages such as pulse-free operation, high precision, and continuous pumping of microfluidics, meeting the requirements for stable drive and control of microfluidics. Attached Figure Description

[0032] Figure 1 This is an overall structural diagram of the peristaltic pump in this embodiment;

[0033] Figure 2 This is a schematic diagram of the flow channel structure of the microfluidic chip in this embodiment;

[0034] Figure 3 This is a schematic diagram of the drive mechanism in this embodiment;

[0035] Figure 4 This is a schematic diagram of the flow channel of the through-hole ball extrusion microfluidic chip in this embodiment;

[0036] Figure 5 This is an assembly drawing of the fixture assembly in this embodiment;

[0037] Figure 6 This is a schematic diagram of the structure of the movable fixture in this embodiment;

[0038] Figure 7 Figure a is a cross-sectional schematic diagram of the unextended annular flow channel in this embodiment, and Figure b is a cross-sectional schematic diagram of the extruded annular flow channel in this embodiment.

[0039] In the diagram: 1-Microfluidic chip; 2-Drive mechanism; 3-Clamping assembly; 4-Housing; 11-Fluid inlet; 12-Annular flow channel; 13-Bent flow channel; 14-Gas chamber; 15-Fluid outlet; 16-First damping structure; 17-Limiting groove; 21-Stepper motor; 22-Pump head; 23-Through-hole ball bearing; 24-Bearing; 25-Connecting pin; 31-Modible clamp; 32-Fixed clamp; 33-Bolt; 34-Positioning pin; 35-Protrusion; 36-Second damping structure. Detailed Implementation

[0040] The present invention will be further described below with reference to the accompanying drawings. The following embodiments are only used to more clearly illustrate the technical solution of the present invention, and should not be used to limit the scope of protection of the present invention.

[0041] Example 1

[0042] This embodiment proposes a peristaltic pump, such as Figure 1 The device includes: a microfluidic chip 1, a clamping assembly 3, and a driving mechanism 2; wherein, both the clamping assembly 3 and the driving mechanism 2 are connected to the housing 4, and the microfluidic chip 1 is fixed to the outside of the driving mechanism 2 by the clamping assembly 3; the microfluidic chip 1 has a flow channel arranged around one side of the driving mechanism 2, and the driving mechanism 2 makes undulating contact with the flow channel during pumping to undulate and squeeze the fluid in the flow channel; an air chamber 14 is provided at the end of the flow channel, which can store and release microfluidic fluid in real time to compensate for the pulse fluctuation of the fluid.

[0043] Optional, such as Figure 2The portion of the microfluidic chip 1 near the clamping assembly 3 and the drive mechanism 2 is an arc-shaped segment. From the end of the arc-shaped segment, the microfluidic chip 1 extends a planar segment away from the clamping assembly 3 and the drive mechanism 2; the air cavity 14 is located in the planar segment. In this embodiment, the arc-shaped segment is circular, and its curvature matches the side of the drive mechanism 2. The arc-shaped segment contacts the drive mechanism 2 at multiple points, allowing the drive mechanism 2 to alternately and repeatedly contact the flow channel on the arc-shaped segment during rolling, oscillatingly squeezing the fluid in the flow channel to form a peristaltic flow rate. This peristaltic flow can overcome fluid pulses, ensuring precise and continuous uniform and stable fluid intake.

[0044] In this embodiment, the microfluidic chip 1 is formed by mixing and curing PDMS prepolymer and crosslinking agent in an optimized mass ratio. The flow channel mold of the microfluidic chip 1 is made by 3D printing, and then the microfluidic chip 1 is made by molding. Based on obtaining a high-quality flow channel mold, the detailed structure of the flow channel can be replicated with high precision. The chip produced has high flow channel dimensional accuracy and good tensile strength and fatigue resistance.

[0045] Optionally, the flow channel includes: an annular flow channel 12, a fluid inlet 11, a curved flow channel 13, and a fluid outlet 15; wherein, the annular flow channel 12 is formed on the arc-shaped segment of the microfluidic chip 1, the fluid inlet 11 is formed at the beginning of the annular flow channel 12, the curved flow channel 13 is connected to the annular flow channel 12 and located on the planar segment, and the fluid outlet 15 is connected to the end of the annular flow channel 12 and located at the end of the planar segment away from the drive mechanism 2; the annular flow channel 12 corresponds to the drive mechanism 2, with one side of the drive mechanism 2 contacting the annular flow channel 12 and the other side not in contact; The curved flow channel 13 is also connected to the air chamber 14. In this embodiment, the fluid inlet 11 is used to receive the microfluidic fluid, which then flows into the annular flow channel 12. The annular flow channel 12 is squeezed by the drive mechanism 2, which generates negative pressure inside, thereby continuously driving the fluid to continuously peristalse towards the fluid outlet 15. When the peristaltic fluid is transported to the fluid outlet 15 on the planar section, it is buffered again by the curved flow channel 13 and the air chamber 14, and finally completely absorbs the fluid force and obtains a uniform and stable microfluidic fluid at the outlet, further improving the precision of microfluidic transport.

[0046] Optionally, the gas chamber 14 stores a preset amount of gas. There is one or more gas chambers 14, which are arranged on the planar section and symmetrically installed on both sides of the annular flow channel 12. In this embodiment, when the peristaltic fluid experiences excessive impact, the gas in the gas chamber 14 is compressed through the curved flow channel 13, causing the curved flow channel 13 to store microfluidic fluid. When the fluid pressure is too low, the gas expands into the curved flow channel 13, delivering pressure to the annular flow channel 12 through the curved flow channel 13, thereby releasing the microfluidic fluid stored in the curved flow channel 13 and further balancing the stability of continuous fluid output. The curved flow channel 13 is also symmetrically arranged on both sides of the annular flow channel 12, thus forming a parallel buffer structure on both sides of the annular flow channel 12, avoiding uneven buffering on one side.

[0047] Optionally, the number of air chambers 14 on each side of the annular flow channel 12 is more than one, and they are connected in series through the curved flow channel 13. This can form a multi-stage buffer, and the progressive absorption of impact force makes the device more widely applicable.

[0048] Optionally, a first damping structure 16 is connected to the side of the microfluidic chip 1 near the clamping assembly 3, and a limiting groove 17 is formed on the microfluidic chip 1 for fitting with the clamping assembly 3. In this embodiment, the first damping structure 16 is located on the curved part of the outer surface, and its engagement with the clamping assembly 3 can prevent displacement of the microfluidic chip 1 due to squeezing motion during pumping.

[0049] Optional, such as Figure 3 The drive mechanism 2 shown includes: a pump head 22, a bearing 24, multiple through-hole ball bearings 23 and a stepper motor 21; the pump head 22 is disposed close to the microfluidic chip 1, the bearing 24 is connected to the pump head 22 by a connecting pin 25, the multiple through-hole ball bearings 23 are mounted on the bearing 24, and the stepper motor 21 is connected to the end of the pump head 22 away from the microfluidic chip 1.

[0050] Multiple through-hole balls 23 are arranged in a circle, with their centers coinciding with the center of the annular flow channel 12. The apex of each through-hole ball 23 that enters the microfluidic chip 1 is pressed against the annular flow channel 12, and the through-hole balls 23 that leave the microfluidic chip 1 do not contact the annular flow channel 12.

[0051] The motor's power output shaft is connected to the pump head 22 via a coupling. The power output from the motor drives the pump head 22, bearing 24, and through-hole ball bearings 23 to rotate in and out of the microfluidic chip 1. The through-hole ball bearings 23 then oscillate and compress the annular flow channel 12 within the microfluidic chip 1. In this embodiment, the pump head 22 is made of resin, with multiple mounting holes evenly distributed around its front circumference. A connecting pin 25 is inserted into the mounting holes of the pump head 22, and a miniature bearing 24 is connected in series on the connecting pin 25. The through-hole ball bearings 23 are fitted over the miniature bearing 24, forming a low-friction rolling structure. The rear end of the pump head 22 is equipped with a coupling structure that can be engaged with the stepper motor 21 shaft to drive the pumping mechanism. During pumping, the through-hole ball bearings 23 on one side synchronously compress the flow channel of the microfluidic chip 1 to form a continuous peristaltic wave, while the through-hole ball bearings 23 on the other side remain in a non-contact state. This two-stage alternating pressure method keeps the cross-sectional area of ​​the flow channel in dynamic balance. Compared with the single-point extrusion method, it can greatly suppress fluid pulses, significantly reduce flow error, and improve pumping stability.

[0052] Optional, such as Figure 4 As shown, multiple through-hole balls 23 are circumferentially distributed on the bearing 24, with the through-hole balls 23 on one half of the arc surface in contact with the flow channel, while the through-hole balls 23 on the other half of the arc surface do not contact the flow channel. For example... Figure 7 As shown in Figure b, the annular flow channel 12 is elastic and undergoes elastic deformation after being squeezed by the through-hole ball 23. In Figure a, after the through-hole ball 23 moves away from the annular flow channel 12, it rebounds from its compressed state to its original shape. When the annular flow channel 12 rebounds, the flow channel moves outward, thereby generating negative pressure. When the annular flow channel is squeezed by the through-hole ball in a wavy manner, the annular flow channel undergoes wavy and continuous contraction and expansion, thereby continuously and wavyly generating negative pressure, ultimately driving the fluid to be continuously pumped from the fluid inlet 11 to the fluid outlet. The through-hole ball 23 is pressed against the microfluidic chip 1 and rolls continuously along the annular flow channel 12 in the microfluidic chip 1. The annular flow channel 12 undergoes continuous contraction-expansion deformation due to the squeeze of the ball, generating negative pressure inside the annular flow channel 12. Driven by the negative pressure inside the annular flow channel 12, the sample liquid flows in from the inlet centrifuge tube of the microfluidic chip 1, and flows out from the outlet centrifuge tube of the microfluidic chip 1 after passing through the annular flow channel 12, thereby realizing the continuous pumping of the sample liquid. In this embodiment, the inner surface of the microfluidic chip 1 is in close contact with the drive mechanism 2. Fluid enters the flow channel from the fluid inlet 11 at the upper end of the microfluidic chip 1, and the fluid inlet 11 buffers the fluid impact. The through-hole ball bearing 23 periodically squeezes the annular flow channel of the microfluidic chip 1 to form a continuous peristaltic wave, driving the fluid transport.

[0053] Optional, such as Figure 5 and Figure 6The fixture assembly 3 shown is mounted on the outside of the housing 4 and includes a fixed clamping plate 32 and a movable clamping plate 31. The fixed clamping plate 32 is mounted on the housing 4, and the movable clamping plate 31 is connected to the fixed clamping plate 32. In this embodiment, the movable clamping plate 31 is mounted on one side of the microfluidic chip 1 through the fixed clamping plate 32, and is located outside the through-hole ball 23 of the drive mechanism 2. It is connected to the fixed clamping plate 32 through a positioning pin 34 and a hand-tightening bolt 33.

[0054] Optionally, the movable clamp 31 includes: an arc-shaped segment and two connecting seats; the arc-shaped segment is close to and adapted to the microfluidic chip 1, and the two connecting seats are respectively connected to the two connecting seats at both ends of the arc-shaped segment; a second damping structure 36 is provided on the inner wall of the arc-shaped segment, which can be fitted with the first damping structure 16 of the microfluidic chip 1; the two connecting seats are respectively provided with connecting holes for fitting with the positioning pin 34 and the hand-tightening bolt 33. The fixed clamp 32 is connected with a protrusion 35 facing the microfluidic chip 1; the fixed clamp 32 is installed on the front surface of the housing 4 by hexagonal socket head cap screws 33, and there are two protrusions 35 arranged vertically, which can fit into the limiting grooves 17 at the upper and lower ends of the microfluidic chip 1, thereby fixing the microfluidic chip 1 to the fixed clamp 32. In this embodiment, the microfluidic chip 1 is initially fixed to the fixed clamping plate 32 through the cooperation of the protrusion 35 and the limiting groove 17. After the bent microfluidic chip 1 is installed, the movable clamping plate 31 is tightened to the fixed clamping plate 32 by hand-tightening the bolts 33, thereby achieving secondary fixation of the microfluidic chip 1. The interlocking structure of the first damping structure 16 and the second damping structure 36 can prevent the microfluidic chip 1 from being displaced due to the squeezing motion during pumping. In addition, this connection design ensures that the curvature of the microfluidic chip 1, the movable clamping plate 31 and the pump head 22 of the drive mechanism 2 are always consistent, so that the through-hole ball bearings 23 on the pump head 22 always accurately squeeze the annular flow channel 12.

[0055] Work methods:

[0056] The stepper motor 21 is started, driving the pump head 22 to rotate. The rotation of the pump head 22 drives the through-hole ball bearings 23 on the micro-bearing 24 to perform circumferential motion. During the movement of the through-hole ball bearings 23, they sequentially compress the annular flow channel 12. The annular flow channel 12 undergoes continuous contraction-expansion deformation due to the compression of the ball bearings, creating a negative pressure inside the annular flow channel 12. Driven by the negative pressure inside the annular flow channel 12, the sample liquid flows into the inlet centrifuge tube of the microfluidic chip 1 and flows out from the outlet centrifuge tube of the microfluidic chip 1 after passing through the annular flow channel 12, thereby realizing the continuous pumping of the sample liquid.

[0057] The microfluidic chip 1 continuously supplies microfluidic fluid through the fluid inlet 11. When the microfluidic fluid flows through the annular channel 12 on the arc segment, it is squeezed by the through-hole ball 23 to form a continuous peristaltic wave. In addition, the flow cross section of the fluid in the channel changes passively in a wave-like manner, which can suppress the pulsation of the fluid itself, avoid pressure sudden changes, and dynamically adjust the fluid pressure. Compared with the single-point squeezing method, it can actively control the fluid pulsation to a large extent, greatly reduce the flow error, and improve the stability of pumping.

[0058] When the peristaltic fluid is transported to the fluid outlet 15 on the planar section, it is buffered again through the curved flow channel 13 and the air chamber 14. Specifically, when there is too much impact on the peristaltic fluid, the gas in the air chamber 14 is compressed through the curved flow channel 13, so that the curved flow channel 13 stores microfluid. When the fluid pressure is too low, the gas expands into the curved flow channel 13 and delivers pressure to the annular flow channel 12 through the curved flow channel 13, thereby releasing the microfluid stored in the curved flow channel 13 and further balancing the stability of the continuous liquid output.

[0059] Finally, the outflowing fluid is buffered by the buffer structure composed of the air chamber 14 and the curved flow channel 13. The number and layout of the air chamber 14 and the curved flow channel 13 can be improved according to the actual situation to ensure that the buffer structure can completely absorb the fluid force and obtain a uniform and stable microfluidic at the outlet, and further refine the transport of the microfluidic.

[0060] Example 2

[0061] This example provides a peristaltic pump, with the basic concept being the same as in Embodiment 1, including: a microfluidic chip, a clamping assembly, and a drive mechanism; wherein, both the clamping assembly and the drive mechanism are connected to a housing, and the microfluidic chip is fixed to the outside of the drive mechanism via the clamping assembly; the microfluidic chip has a flow channel arranged around one side of the drive mechanism, and the drive mechanism makes undulating contact with the flow channel during pumping to undulate and squeeze the fluid in the flow channel; an air chamber is provided at the end of the flow channel, which can store and release microfluidic fluid in real time to compensate for the pulsating fluctuations of the fluid.

[0062] Optionally, in this embodiment, the stepper motor in the drive mechanism is electrically connected to the drive system. The drive system consists of an input device, a microcontroller, a driver, and a controller. The drive system is installed inside the housing, or it can be modified according to an existing control terminal. The input device is a control panel or remote control handle and control terminal installed on the housing, used to interact with the drive system to realize the power control of the stepper motor and accurately adjust the rolling speed of the peristaltic pump, ultimately achieving accurate control of the fluid flow rate.

[0063] In summary, by storing and releasing microfluidics in the air chamber in real time, the flow fluctuations of the fluid in the flow channel can be compensated in real time, effectively reducing the flow pulse error of the peristaltic fluid. The drive mechanism can make alternating contact with the flow channel to squeeze the flow channel and dynamically adjust the flow cross section, so that the continuous peristaltic wave passively formed by the fluid can offset the periodic pulse force.

[0064] The microfluidic chip displacement is prevented by the dual fixing mechanism of friction damping and slots in the clamping assembly, ensuring long-term operational reliability. This peristaltic pump has advantages such as pulse-free operation, high precision, and continuous pumping of microfluidics, meeting the requirements for stable drive and control of microfluidics.

[0065] The embodiments of the present utility model have been described above with reference to the accompanying drawings. However, the present utility model is not limited to the specific embodiments described above. The specific embodiments described above are merely illustrative and not restrictive. Those skilled in the art can make many other forms under the guidance of the present utility model without departing from the spirit and scope of the claims. All of these forms are within the protection scope of the present utility model.

Claims

1. A peristaltic pump characterized by, The application relates to a micro-fluidic chip, a clamp assembly arranged on one side of the micro-fluidic chip and a driving mechanism arranged on the other side of the micro-fluidic chip. The micro-fluidic chip is provided with a flow channel on one side of the driving mechanism. The driving mechanism is in fluctuant contact with the flow channel during pumping, and is used for fluctuant extrusion of fluid in the flow channel. The end of the flow channel is provided with an air cavity. The part of the micro-fluidic chip close to the clamp assembly and the driving mechanism is an arc segment, and the micro-fluidic chip extends from the end of the arc segment to a plane segment away from the clamp assembly and the driving mechanism.

2. The peristaltic pump of claim 1, wherein, The air cavity is arranged on the plane segment. The flow channel comprises a ring-shaped flow channel opened on the arc segment of the micro-fluidic chip, a fluid inlet opened at the beginning of the ring-shaped flow channel, a curved flow channel connected to the ring-shaped flow channel and located on the plane segment, and a fluid outlet connected to the end of the ring-shaped flow channel and located on the plane segment away from the driving mechanism.

3. The peristaltic pump of claim 2, wherein, The ring-shaped flow channel is close to the driving mechanism, and one side of the driving mechanism is in contact with the ring-shaped flow channel, and the other side is not in contact. The curved flow channel is further connected with the air cavity. The air cavity stores a preset amount of gas, and the number of the air cavities is more than one, and the more than one air cavities are arranged on the plane segment and are symmetrically arranged on both sides of the ring-shaped flow channel.

4. The peristaltic pump of claim 2, wherein, The number of the air cavities on each side of the ring-shaped flow channel is more than one, and the air cavities are connected in series through the curved flow channel.

5. The peristaltic pump of claim 4 wherein, The micro-fluidic chip is connected with a first damping structure on the side close to the clamp assembly, and a limiting groove is opened on the micro-fluidic chip and is used for adapting with the clamp assembly.

6. The peristaltic pump of claim 1 wherein, The driving mechanism comprises a pump head arranged close to the micro-fluidic chip, a bearing connected to the pump head through a connecting pin, a plurality of through-hole balls sleeved on the bearing, and a motor connected to the end of the pump head away from the micro-fluidic chip.

7. The peristaltic pump of claim 1 wherein, The plurality of through-hole balls are arranged in a circle, the center of the circle coincides with the center of the ring-shaped flow channel, and the vertex of each through-hole ball rotating into the micro-fluidic chip is in pressure contact with the ring-shaped flow channel, and the through-hole ball out of the micro-fluidic chip is not in contact with the ring-shaped flow channel. The power output shaft of the motor is connected with the pump head through a shaft coupling, so that the power output by the motor drives the pump head, the bearing and the through-hole balls to rotate into and rotate out of the micro-fluidic chip, and the through-hole balls extrude the ring-shaped flow channel in a fluctuant mode after rotating into the micro-fluidic chip. The ring-shaped flow channel has elasticity, and is elastically deformed after being extruded by the through-hole balls, and generates negative pressure in the flow channel when recovering.

8. The peristaltic pump of claim 7, wherein, When the ring-shaped flow channel is extruded by the through-hole balls in a fluctuant mode, the ring-shaped flow channel is contracted and expanded in a fluctuant mode to continuously generate negative pressure, and finally drives the fluid to be continuously pumped from the fluid inlet to the fluid outlet. The clamp assembly is installed on the outside of the shell and comprises a fixed clamp plate installed on the shell and a movable clamp connected to the fixed clamp plate.

9. The peristaltic pump of claim 1 wherein, The movable clamp comprises an arc segment close to and adapted to the micro-fluidic chip and two connecting seats connected to the two ends of the arc segment respectively.

10. The peristaltic pump of claim 9, wherein, The inner wall of the arc segment is provided with a second damping structure. Connecting holes are respectively arranged on the two connecting seats. The fixed clamp plate is connected with a protruding block towards the micro-fluidic chip. ​

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