Non-pipeline extensible magnetic rotor micropump chip

Abstract

The invention discloses a pipeline-free extensible magnetic rotor micropump chip in the field of micro-fluidic chips, and the chip comprises a cover plate layer, the bottom surface of which is provided with a medium channel; the substrate layer is fixedly arranged at the bottom of the channel layer and is used for closing the bottom of the medium channel and supporting the channel layer; the micro-rotor is rotationally clamped in the medium channel so as to rotate at a fixed position in the medium channel, and the micro-rotor rotates through the change of an external magnetic field so as to pump fluid in the medium channel; the micro-rotor pump has the beneficial effects that the micro-rotor is arranged in the circulation channel, the micro-rotor can be controlled to rotate through external magnetic field changes to achieve pumping of fluid media in the medium channel, redundant structures and lines do not exist in the medium channel, dependence on the external structure is lower, the pumping efficiency is improved, and the structure is simpler.

Description

Technical Field

[0001] This invention relates to the field of microfluidic chips, specifically to a tubing-free scalable magnetic rotor micropump chip. Background Technology

[0002] Microfluidics, as an advanced technique for precisely manipulating fluid behavior at the micro- and nano-scale, has been widely applied in recent years in various fields such as biomedical research, chemical synthesis and analysis, environmental monitoring, and food safety testing. Its core advantages lie in low reagent consumption, high reaction efficiency, and highly automated operation, making it particularly suitable for scenarios involving the precise processing of minute samples. In microfluidic systems, micropumps, as key units driving microfluidic motion, play a fundamental role in maintaining liquid flow, especially in high-precision applications such as dynamic cell culture, drug delivery, and blood microcirculation simulation. In the construction of biomimetic microenvironments, microfluidic chips can achieve efficient exchange of nutrients and metabolic waste, accurately simulating in vivo fluid perfusion conditions, such as pulsating flow, unidirectional flow, and periodic circulatory flow, thus providing technical support for the construction of in vitro organoids, disease models, and drug efficacy evaluation platforms. Therefore, achieving precise driving, stable control, and flexible adjustment of fluids within the microscale is one of the core challenges driving the further development of microfluidics.

[0003] Traditional microfluidic actuation methods often rely on external micro-rotors or electrically controlled valves, resulting in complex and bulky systems that are unfavorable for chip-level integration and low-power operation. Although various micro-pumping mechanisms have been proposed in recent years, including active micro-pumps based on mechanical components (such as piezoelectric actuation and diaphragm vibration) and passive micro-pumps relying on physical effects (such as capillary force, gravity, thermal bubbles, and surface tension actuation), these solutions still have many shortcomings: limited actuation precision, difficulty in further compressing the size of micro-rotors, strong dependence on external equipment, low pumping efficiency, and insufficient scalability in complex multi-channel systems. For example, in the construction of organoid chips, traditional pumping methods often require a large number of external pipelines, which not only increases the risk of contamination but also leads to problems such as blockage, large size, and difficult maintenance, limiting the miniaturization and high integration of the system.

[0004] To address this, we propose a tubing-free, scalable magnetic rotor micropump chip. Summary of the Invention

[0005] To address the aforementioned shortcomings of the prior art, this invention provides a tubing-free scalable magnetic rotor micropump chip.

[0006] To achieve the above-mentioned objectives, the technical solution adopted by this invention is as follows: A tubing-free, expandable magnetic rotor micropump chip includes: a cover layer with a medium channel on its bottom surface, the medium channel providing space for medium flow and cell culture; a base layer fixedly disposed at the bottom of the channel layer, sealing the bottom of the medium channel and supporting the channel layer; and a micro rotor rotatably mounted within the medium channel to achieve rotation at a fixed position within the medium channel, the micro rotor rotating through changes in an external magnetic field to pump fluid within the medium channel.

[0007] By setting a micro-rotor inside the medium channel, the micro-rotor is directly mounted and rotated within the medium channel without the need for additional fixing structures. This results in a simpler structure and easier installation. The micro-rotor is driven by an external magnetic field, and its rotation causes the fluid inside the medium channel to rotate. There is no need to set up active or passive micro-pumps inside the medium channel, nor is there any need for external piping. Driving the internal fluid can be accomplished simply by changing the external magnetic field. This design reduces dependence on external structures and significantly improves pumping efficiency.

[0008] Further defined, the medium channel includes an inlet, an inlet channel, a circulation channel, an outlet, and an outlet channel; the inlet is connected to one side of the circulation channel through the inlet channel, and the outlet is connected to the other side of the circulation channel through the outlet channel and the inlet channel, and the inlet and outlet are connected through the top surface of the cover plate layer.

[0009] Further defined, the circulation channel includes a main channel, a pump chamber, and a culture chamber; the main channel is rectangular, with the sample inlet channel and the sample outlet channel connected opposite each other on both sides of the main channel; there are several pump chambers connected in series on the main channel between the sample inlet channel and the sample outlet channel; the micro rotor is mounted in the pump chamber; there are also several culture chambers, which are connected in parallel on the main channel opposite to the pump chamber and located between the sample inlet channel and the sample outlet channel.

[0010] A pump chamber and a culture chamber are set up in the circulation channel. The micro rotor is locked in the pump chamber so that it will not leave the pump chamber and will only rotate inside the pump chamber without moving to other positions in the circulation channel. The culture chamber is used to culture cells. The fluid medium is driven by the micro rotor to circulate in the circulation channel to simulate the environment of human organs. By setting up several pump chambers and micro rotors, the pumping efficiency of a single micro rotor can be achieved by controlling the speed of multiple micro rotors to a relatively low speed. If the speed of a single micro rotor is too high, it will destroy the structure of active substances in the fluid medium. Using multiple micro rotors to pump together can achieve higher pumping efficiency at a lower speed.

[0011] Further defining the micro rotor, it includes a base at the bottom and a pumping section at the top; by setting the base, the installation and rotation of the micro rotor can be made more stable, and the pumping section can be designed in shape as needed to achieve the required pumping efficiency.

[0012] Further defining, the pumping section includes a central shaft and blades arranged circumferentially around the shaft.

[0013] Further defining the pumping section, it includes a central shaft and a rotating block arranged circumferentially around the shaft, the rotating block being fan-shaped.

[0014] Further defining the pumping section, it includes a central shaft and a rotating block arranged around the circumference of the shaft, the rotating block being elongated.

[0015] Further specified, the inner diameter width of the main channel is 10~10000μm, the length of the main channel is 100~10000 mm, the inner diameter height of the main channel is 1~1000 mm, and the inner diameter width of the sample inlet channel and the sample outlet channel is 0.1~1 mm and the height is 0.1~2 mm.

[0016] Further specified, the height of the micro rotor is 30~9000μm and the maximum radius is 30~3000μm, the height of the pump chamber is 40~10000μm and the radius is 40~4000μm, the culture chamber is roughly circular with an inner diameter width of 100~20000μm and a height of 1~10000mm.

[0017] Further, it also includes an alternating magnetic field control module and an imaging module. The cover layer is made of transparent material. The imaging module is suspended above the cover layer to acquire images of the micro rotor's rotation process. The alternating magnetic field control module is fixed below the base layer to drive the micro rotor. By fixing the alternating magnetic field control module below the base layer, the structure is more integrated. The imaging module allows for a clearer understanding of the micro rotor's rotation speed, facilitating the experiment.

[0018] The beneficial effects of this invention are as follows: by setting a micro rotor in the circulation channel, the rotation of the micro rotor can be controlled by the change of the external magnetic field to realize the pumping of the fluid medium in the medium channel. There are no extra structures and lines in the medium channel, the dependence on external structures is lower, the pumping efficiency is improved, and the structure is simpler. Attached Figure Description

[0019] Figure 1 This is a perspective view of the present invention from the frontal viewpoint; Figure 2 This is a top view of the cover plate layer; Figure 3 This is a schematic diagram of the micro rotor structure in Example 1; Figure 4 This is a schematic diagram of the micro rotor structure in Example 2; Figure 5 This is a schematic diagram of the micro rotor structure in Example 3; Figure 6 A white light image of the micro-rotor's rotational state captured by the imaging module; Figure 7 A white light image showing the micro-rotor in a stopped state and the medium fluid in a static state; Figure 8 White light image showing the micro-rotor in rotation and the medium fluid in flow. Figure 9 White light images showing a comparison of the results of dynamic and static cell culture after 48 hours using the present invention.

[0020] The symbols for each component are as follows: 1. Cover plate layer, 2. Base layer, 3. Micro rotor, 31. Base, 32. Shaft, 33. Paddle, 34. Rotating block, 4. Alternating magnetic field control module, 5. Imaging module, 6. Medium channel, 61. Inlet, 62. Inlet channel, 63. Circulation channel, 63. Main channel, 631. Pump chamber, 632. Culture chamber, 633. Outlet, 64. Outlet channel, 65. Detailed Implementation

[0021] The specific embodiments of the present invention are described below to enable those skilled in the art to understand the present invention. However, it should be understood that the present invention is not limited to the scope of the specific embodiments. For those skilled in the art, various changes are obvious as long as they are within the spirit and scope of the present invention as defined and determined by the appended claims. All inventions utilizing the concept of the present invention are protected.

[0022] Example 1: like Figures 1-3 and Figures 6-9As shown, a tubing-free scalable magnetic rotor micropump chip includes a cover plate layer 1, a substrate layer 2, a micro rotor 3, an alternating magnetic field control module 4, and an imaging module 5. The cover plate layer 1 is made of transparent material. A medium channel 6 is formed at the bottom of the cover plate layer 1, which provides space for the flow of medium and cell culture. The medium channel 6 includes an inlet 61, an inlet channel 62, a circulation channel 63, an outlet 64, and an outlet channel 65. The inlet 61 is connected to one side of the circulation channel 63 through the inlet channel 62, and the outlet 64 is connected to the other side of the circulation channel 63 through the outlet channel 65. The sample port 64 is disposed on the top surface of the cover layer 1; the circulation channel 63 includes a main channel 631, a pump chamber 632, and a culture chamber 633; ​​the main channel 631 is rectangular, with the sample inlet channel 62 and the sample outlet channel 65 connected opposite each other on both sides of the main channel 631; the pump chamber 632 has two pumps connected in series on the main channel 631 between the sample inlet channel 62 and the sample outlet channel 65; the micro rotor 3 is rotatably mounted in the pump chamber 632; there are also three culture chambers 633, which are connected in parallel on the main channel 631 opposite to the pump chamber 632 and located between the sample inlet channel 62 and the sample outlet channel 65; the base layer 2 is fixedly disposed at the bottom of the channel layer. The bottom of the medium channel 6 is sealed and the channel layer is supported; the micro rotor 3 is rotatably locked inside the medium channel 6 to achieve fixed rotation within the medium channel 6. The micro rotor 3 rotates through changes in the external magnetic field and pumps the fluid within the medium channel 6. The micro rotor 3 includes a lower base 31 and an upper pumping unit; the pumping unit includes a central shaft 32 and blades 33 arranged circumferentially around the shaft 32; the imaging module 5 is suspended above the cover plate layer 1 to acquire images of the micro rotor 3 during rotation; the alternating magnetic field control module 4 is fixed below the base layer 2 to drive the micro rotor 3; the inner... The diameter width is 10~10000μm, the length of the main channel 631 is 100~10000mm, the inner diameter height of the main channel 631 is 1~1000mm, the inner diameter width of the sample inlet channel 62 and the sample outlet channel 65 is 0.1~1mm, and the height is 0.1~2mm; the height of the micro rotor 3 is 30~9000μm, the maximum radius is 30~3000μm, the height of the pump chamber 632 is 40~10000μm, the radius is 40~4000μm, the culture chamber 633 is roughly circular, the inner diameter width is 100~20000μm, and the height of the culture chamber 633 is 1~10000mm.

[0023] In this application, the imaging module 5 uses a high-speed camera, and the alternating magnetic field control module 4 uses a magnetic stirrer.

[0024] By placing a micro-rotor 3 within the media channel 6, the micro-rotor 3 is directly rotated and secured within the media channel 6 without the need for additional fixing structures, resulting in a simpler structure and easier installation. The micro-rotor 3 is driven by an external magnetic field, causing the fluid inside the media channel 6 to rotate. This eliminates the need for active and passive micro-pumps within the media channel 6, as well as external piping. Driving the internal fluid is achieved simply by changing the external magnetic field, reducing reliance on external structures and significantly improving pumping efficiency. A pump chamber 632 and a culture chamber 633 are set within the circulation channel 63. The micro-rotor 3 is secured within the pump chamber 632, ensuring it does not detach and rotates only within it, preventing it from moving to other locations within the circulation channel 63. The culture chamber 633 is used for culturing cells. The micro-rotor 3 drives the fluid medium to circulate within the circulation channel 63 to simulate the environment of human organs. By setting up several pump chambers 632 and micro-rotors 3, the pumping efficiency of a single micro-rotor 3 can be achieved by controlling the rotation speed of multiple micro-rotors 3 at relatively low speeds. If the rotation speed of a single micro-rotor 3 is too high, it will destroy the structure of active substances in the fluid medium. Using multiple micro-rotors 3 in combination can achieve higher pumping efficiency at lower speeds. The base 31 makes the installation and rotation of the micro-rotor 3 more stable. The pumping part can be designed in shape as needed to achieve the required pumping efficiency. In this way, the alternating magnetic field control module 4 is fixedly set below the base layer 2, resulting in higher structural integration. The imaging module 5 can more clearly understand the rotation speed of the micro-rotor 3, which facilitates the experiment.

[0025] Example 2: like Figure 1 , Figure 2 , Figure 4 and Figures 6-9 As shown, the difference between Embodiment 2 and Embodiment 1 is only that the pumping section includes a central shaft 32 and a rotating block 34 arranged around the shaft 32, with the rotating block 34 being fan-shaped.

[0026] Example 3: like Figure 1 , Figure 2 , Figures 5-9 As shown, the difference between Embodiment 3 and Embodiment 1 is only that the pumping section includes a central shaft 32 and a rotating block 34 arranged around the shaft 32, and the rotating block 34 is elongated.

Claims

1. A tubing-free, scalable magnetic rotor micropump chip, characterized in that, include: The cover plate layer (1) has a medium channel (6) on its bottom surface, which is used to provide space for the flow of medium and cell culture; The base layer (2) is fixedly disposed at the bottom of the channel layer to seal the bottom of the medium channel (6) and to support the channel layer; The micro rotor (3) is rotatably mounted in the medium channel (6) to achieve rotation in a fixed position within the medium channel (6). The micro rotor (3) rotates by changes in the external magnetic field and pumps the fluid within the medium channel (6).

2. The tubing-free scalable magnetic rotor micropump chip according to claim 1, characterized in that, The medium channel (6) includes an inlet (61), an inlet channel (62), a circulation channel (63), an outlet (64), and an outlet channel (65); the inlet (61) is connected to one side of the circulation channel (63) through the inlet channel (62), and the outlet (64) is connected to the inlet channel (62) on the other side of the circulation channel (63) through the outlet channel (65), and the inlet (61) and the outlet (64) are connected through the top surface of the cover plate layer (1).

3. The tubing-free scalable magnetic rotor micropump chip according to claim 2, characterized in that, The circulation channel (63) includes a main channel (631), a pump chamber (632), and a culture chamber (633). The main channel (631) is rectangular. The sample inlet channel (62) and the sample outlet channel (65) are connected to each other on both sides of the main channel (631). The pump chamber (632) is provided in several units and connected in series between the sample inlet channel (62) and the sample outlet channel (65) on the main channel (631). The micro rotor (3) is rotated and locked in the pump chamber (632). The culture chamber (633) is also provided in several units. The several culture chambers (633) are connected in parallel on the main channel (631) opposite to the pump chamber (632) and located between the sample inlet channel (62) and the sample outlet channel (65).

4. The tubing-free scalable magnetic rotor micropump chip according to claim 3, characterized in that, The micro rotor (3) includes a base (31) below and a pumping section above.

5. The tubing-free scalable magnetic rotor micropump chip according to claim 4, characterized in that, The pumping unit includes a central shaft (32) and blades (33) arranged circumferentially around the shaft (32).

6. The tubing-free scalable magnetic rotor micropump chip according to claim 4, characterized in that, The pumping unit includes a central shaft (32) and a rotating block (34) arranged around the shaft (32) in a fan shape.

7. The tubing-free scalable magnetic rotor micropump chip according to claim 4, characterized in that, The pumping unit includes a central shaft (32) and a rotating block (34) arranged around the shaft (32) in a long strip shape.

8. The tubing-free scalable magnetic rotor micropump chip according to any one of claims 5-7, characterized in that, The inner diameter of the main channel (631) is 10~10000μm, the length of the main channel (631) is 100~10000mm, the inner diameter height of the main channel (631) is 1~1000mm, and the inner diameter of the sample inlet channel (62) and the sample outlet channel (65) is 0.1~1mm and 0.1~2mm respectively.

9. The tubing-free scalable magnetic rotor micropump chip according to claim 8, characterized in that, The height of the micro rotor (3) is 30~9000μm and the maximum radius is 30~3000μm. The height of the pump chamber (632) is 40~10000μm and the radius is 40~4000μm. The culture chamber (633) is roughly circular with an inner diameter width of 100~20000μm and a height of 1~10000mm.

10. The tubing-free scalable magnetic rotor micropump chip according to claim 1, characterized in that, It also includes an alternating magnetic field control module (4) and an imaging module (5). The cover plate layer (1) is made of transparent material. The imaging module (5) is suspended above the cover plate layer (1) to collect images of the micro rotor (3) during its rotation. The alternating magnetic field control module (4) is fixed below the base layer (2) to drive the micro rotor (3).

Images