A human organ chip microfluidic system and implementation method

Abstract

The present invention relates to the field of biological microfluidics technology, and provides a human organ chip microfluidics system and implementation method. The system includes an operating table, a flow control arm, and multiple human organ chips fixed on the operating table. The human organ chip is obtained by connecting multiple organ cell culture chambers through a diversion pipe; the flow control arm is used to control the tilt direction and tilt degree of the operating table to control the flow direction and overall flow rate of the perfusion fluid in the multiple human organ chips on the operating table; the inner wall of the diversion pipe is covered with micro-nano flagella, and when the flow rate of the perfusion fluid in the corresponding diversion pipe is less than the preset flow rate, the micro-nano flagella are controlled to move the perfusion fluid forward to speed up the flow rate of the perfusion fluid in the corresponding diversion pipe. The present invention realizes overall regulation of the flow rate by controlling the overall flow direction and overall flow rate of the perfusion fluid carrying the drug; at the same time, fine-tuning of the flow rate is realized; thereby being able to adjust the dosage and dosage rate of each organ cell culture chamber in the human organ chip.

Description

Technical Field

[0001] The present invention relates to the field of biological microfluidics technology, and in particular to a human organ chip microfluidics system and an implementation method thereof. Background Art

[0002] With the rapid development of tissue engineering and precision processing technology in recent years, in vitro organs-on-chips have become a unique and dynamic emerging field in biomedicine.

[0003] Organ chips can simulate the physiological and pathological conditions of the human body in vitro, thus predicting the response to drugs or other stimuli. This has wide application value in basic life science research, clinical disease simulation and new drug development.

[0004] One of the most important applications of organ chips is drug screening. Since drugs need to go through a whole set of processes including absorption, distribution, metabolism, and excretion in the human body, Figure 1 As shown, multiple organ cell culture chambers are connected by pipes to study the efficacy of drugs on different organs and the corresponding side effects. This is a new concept of human organ chips. The research on human organ chips provides an in vitro model that is closer to the physiological state for fields such as drug development, disease understanding, chemical and toxin detection, and has broad application value. When conducting drug screening, it is usually necessary to conduct drug testing on multiple sets of human organ chips to confirm the effectiveness of the drug. In human organ chips, especially when using multiple sets of human organ chips, the dosage and dosage speed required for each organ may be different. How to control the dosage of a single organ cell culture chamber to achieve the dosage required by the organ is a problem that needs to be solved when using human organ chips for drug research.

[0005] In view of this, overcoming the defects of the prior art is an urgent problem to be solved in the field of this technology. Summary of the invention

[0006] The technical problem to be solved by the present invention is that in the prior art, when a large number of human organ chips are used for drug delivery, it is impossible to accurately control the dosage and delivery speed of a single organ cell culture chamber in a single human organ chip.

[0007] The present invention adopts the following technical solution:

[0008] In a first aspect, the present invention provides a human organ chip microfluidic system, comprising an operating table 1, a flow control arm 2, and a plurality of human organ chips 3 fixed on the operating table 1, specifically comprising:

[0009] The human organ chip 3 is obtained by connecting a plurality of organ cell culture chambers 31 through a flow guide pipe 32;

[0010] The flow control arm 2 is used to control the tilt direction and tilt degree of the operating table 1, so as to control the flow direction and overall flow rate of the perfusion fluid in the multiple human organ chips 3 on the operating table 1; wherein the perfusion fluid carries drugs;

[0011] The inner wall of the diversion pipe 32 is covered with micro-nano flagella 320. When the flow rate of the perfusion fluid in the corresponding diversion pipe 32 is less than the corresponding preset flow rate, the micro-nano flagella 320 are controlled to push the perfusion fluid forward to accelerate the flow rate of the perfusion fluid in the corresponding diversion pipe 32.

[0012] Preferably, the flow control arm 2 specifically includes a base 21, a first rotating shaft 22, a first control arm 23, a second rotating shaft 24 and a second control arm 25;

[0013] One end of the first control arm 23 is connected to the base 21 through the first rotating shaft 22, the other end of the first control arm 23 is connected to one end of the second control arm 25 through the second rotating shaft 24, and the operating platform 1 is fixed to the other end of the second control arm 25;

[0014] The first control arm 23 is used to control the operating platform 1 to rotate and tilt along a first direction, and the second control arm 25 is used to control the operating platform 1 to rotate and tilt along a second direction, thereby controlling the tilt direction and tilt degree of the operating platform 1; wherein the axial direction of the first rotating shaft 22 is perpendicular to the axial direction of the second rotating shaft 24.

[0015] Preferably, the method of controlling the micro-nano flagella 320 to move the perfusion fluid forward to accelerate the flow rate of the perfusion fluid in the corresponding diversion pipe 32 specifically includes:

[0016] The outer wall of the diversion pipe 32 is arranged and wound with a plurality of electromagnetic coils 321, and the magnetic field of each electromagnetic coil 321 acts on the micro-nano flagella 320 in the corresponding area of ​​the inner wall of the diversion pipe 32;

[0017] The magnetic field direction and magnetic field size of each electromagnetic coil 321 on the outer wall of the diversion pipe 32 are controlled so that the micro-nano flagella 320 form a wave that propels from the first port of the diversion pipe 32 to the second port of the diversion pipe 32, thereby driving the perfusion fluid forward and accelerating the flow rate of the perfusion fluid; wherein the first port is the port for the perfusion fluid to enter the diversion pipe 32, and the second port is the port for the perfusion fluid to leave the diversion pipe 32.

[0018] Preferably, the controlling of the magnetic field direction and magnetic field magnitude of each electromagnetic coil 321 on the outer wall of the guide pipe 32 so that the micro-nano flagellum 320 forms a wave that propels from the first port of the guide pipe 32 to the second port of the guide pipe 32 specifically includes:

[0019] Control the direction and magnitude of the magnetic field of the first electromagnetic coil, so that under the action of the magnetic field of the first electromagnetic coil, the corresponding micro-nano flagella 320 are moved from the first port direction to the second port direction, and the moving speed is greater than the flow rate of the perfusion fluid in the diversion pipe 32;

[0020] From the direction of the first port of the guide pipe 32 to the direction of the second port of the guide pipe 32, the corresponding electromagnetic coils 321 are selected in turn as the first electromagnetic coils, and the corresponding micro-nano flagella 320 are controlled to move, so as to form a wave that propels the second port of the guide pipe 32 from the first port of the guide pipe 32.

[0021] Preferably, the controlling of the magnetic field direction and magnetic field magnitude of each electromagnetic coil 321 on the outer wall of the guide pipe 32 so that the micro-nano flagellum 320 forms a wave that propels from the first port of the guide pipe 32 to the second port of the guide pipe 32 also includes:

[0022] After the corresponding micro-nano flagella 320 is flicked, the magnetic field direction and magnetic field size of the corresponding electromagnetic coil 321 are controlled to restore the micro-nano flagella 320 to be tilted and bent toward the first port to wait for the next flick, so as to form a circulating wave that propels the first port of the self-guiding pipe 32 toward the second port of the guide pipe 32, wherein the recovery speed is less than the flow rate of the perfusion fluid in the guide pipe 32.

[0023] Preferably, the micro-nano flagella 320 covering the inner wall of the diversion channel 32 is composed of magnetic microspheres 3201 arranged and assembled, specifically comprising:

[0024] The suspension of magnetic microspheres 3201 is placed in a magnetic field in a preset direction, so that the magnetic microspheres 3201 form flagella array units arranged in a preset direction, and the flagella array units are covered and installed on the inner wall of the diversion pipe 32 .

[0025] Preferably, the surface of the magnetic microsphere 3201 is assembled with nano-hydrophobic particles 3202 to make the micro-nano flagella 320 have a hydrophobic effect, so as to push the perfusion fluid forward through the micro-nano flagella 320 .

[0026] Preferably, the system also includes a processor 4 and a driving module 5, wherein the driving module 5 is used to provide current to the electromagnetic coil 321 to drive the electromagnetic coil 321 to generate a corresponding magnetic field; the processor 4 is used to control the driving module 5 to control the magnetic field direction and magnetic field size of the corresponding electromagnetic coil 321.

[0027] Preferably, the system further comprises an ultraviolet emitter 6 and a fluorescence receiver 7, and the drug is marked by a fluorescent marking method. During the diversion process of the perfusion fluid carrying the drug, the ultraviolet emitter 6 is used to emit ultraviolet rays to excite the fluorescent substance to emit fluorescence, and the fluorescence receiver 7 is used to receive the fluorescence, so as to observe the flow direction and flow rate of the perfusion fluid in each diversion pipe 32.

[0028] In a second aspect, the present invention provides a method for implementing a human organ chip microfluidic system, comprising:

[0029] The flow control arm 2 is used to adjust the tilt direction and tilt degree of the operating table 1 so that the flow direction and overall flow rate of the perfusion fluid in the multiple human organ chips 3 remain consistent;

[0030] The diversion pipes 32 at the same position in each human organ chip 3 are divided into a control group, and the driving module 5 performs linkage control on the diversion pipes 32 in the control group;

[0031] One of the multiple human organ chips 3 is used as a reference chip. When administering medicine to the reference chip, the drug is labeled using a fluorescent labeling method. In the process of diversion of the perfusion fluid carrying the drug, the ultraviolet emitter 6 is used to emit ultraviolet rays to excite the fluorescent substance to emit fluorescence, and the fluorescence receiver 7 is used to receive the fluorescence, so as to observe the flow direction and flow rate of the perfusion fluid in each diversion pipe 32. If the flow rate of the perfusion fluid in the corresponding diversion pipe 32 is lower than the corresponding preset flow rate, the control group corresponding to the diversion pipe 32 is controlled so that the micro-nano flagella 320 on the inner wall of all the diversion pipes 32 in the control group drive the perfusion fluid forward, thereby accelerating the flow rate of the perfusion fluid in the corresponding diversion pipe 32.

[0032] Compared with the prior art, the present invention controls the inclination of multiple chips through the flow control arm 2 by combining the flow control arm 2 and the micro-nano flagella 320, so that under the action of gravitational potential energy, the overall flow direction and overall flow rate of the perfusion fluid carrying the drug are controlled, thereby realizing the overall regulation of the drug flow rate in multiple human organ chips 3; at the same time, the flow rate of the perfusion fluid carrying the drug in each diversion pipe 32 is controlled by the micro-nano flagella 320 on the inner wall of the diversion pipe 32, thereby realizing fine-tuning of the flow rate; thereby, the dosage and dosage rate of each organ cell culture chamber 31 in each human organ chip 3 can be accurately adjusted. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0034] Figure 1 is a schematic diagram of a human organ chip provided by an embodiment of the present invention;

[0035] Figure 2 is a schematic structural diagram of a human organ chip microfluidic system provided by an embodiment of the present invention;

[0036] Figure 3 is a schematic structural diagram of a human organ chip microfluidic system provided by an embodiment of the present invention;

[0037] Figure 4 Schematic diagram of the internal structure of the flow guide pipe in the human organ chip microfluidic system provided by an embodiment of the present invention;

[0038] Figure 5 It is a schematic diagram of the structure of an electromagnetic coil wound around the outer wall of a flow guide pipe in a human organ chip microfluidic system provided by an embodiment of the present invention;

[0039] Figure 6 It is a schematic diagram of the deformation structure of the micro-nano flagella on the inner wall when the perfusion fluid flows through the diversion pipe provided by an embodiment of the present invention;

[0040] Figure 7 It is a schematic diagram of the movement of micro-nano flagella on the inner wall of a flow guide channel provided by an embodiment of the present invention;

[0041] Figure 8 It is a schematic diagram of the magnetic field of the corresponding electromagnetic coil when the micro-nano flagella on the inner wall of the diversion pipe provided by the embodiment of the present invention are moved;

[0042] Fig. 9 It is a schematic diagram of the assembly process of the micro-nano flagella provided by an embodiment of the present invention;

[0043] Fig.10 It is a schematic diagram of a micro-nano flagella surface covered with nano-hydrophobic particles provided by an embodiment of the present invention;

[0044] Fig.11 It is a schematic diagram of the structure of the micro-nano flagella forming grid on the inner wall of the diversion channel provided by an embodiment of the present invention;

[0045] Fig.12 It is a schematic diagram of the magnetic field of the corresponding electromagnetic coil when the micro-nano flagella on the inner wall of the diversion pipe provided by the embodiment of the present invention form a grid;

[0046] Fig.13 is a schematic diagram of the module architecture of the processor and the driver module provided in an embodiment of the present invention;

[0047] Fig.14 is a schematic structural diagram of a human organ chip microfluidic system provided by an embodiment of the present invention;

[0048] Fig.15 1 is a flow chart of a method for implementing a human organ chip microfluidic system provided by an embodiment of the present invention;

[0049] Fig.16 is a schematic diagram of a human organ chip in an operating table in a human organ chip microfluidic system provided in an embodiment of the present invention;

[0050] Fig.17 1 is a flow chart of a method for implementing a human organ chip microfluidic system provided by an embodiment of the present invention;

[0051] Fig.18 1 is a flow chart of a method for implementing a human organ chip microfluidic system provided by an embodiment of the present invention;

[0052] Fig.19 It is a flow chart of a method for implementing a human organ chip microfluidic system provided by an embodiment of the present invention.

[0053] Throughout the drawings, the reference numerals are as follows, wherein:

[0054] 1. Operating table; 2. Flow control arm; 21. Base; 22. First rotating shaft; 23. First control arm; 24. Second rotating shaft; 25. Second control arm; 3. Human organ chip; 31. Organ cell culture chamber; 32. Flow diversion pipe; 320. Micro-nano flagella; 321. Electromagnetic coil; 3201. Magnetic microspheres; 3202. Nano-hydrophobic particles; 4. Processor; 5. Drive module; 6. Ultraviolet emitter; 7. Fluorescence receiver. DETAILED DESCRIPTION

[0055] In order to make the purpose, technical solution and advantages of the present invention more clearly understood, the present invention is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present invention and are not intended to limit the present invention.

[0056] In the description of the present invention, the terms "inside", "outside", "longitudinal", "lateral", "upper", "lower", "top", "bottom" and the like indicate orientations or positional relationships based on the orientations or positional relationships shown in the accompanying drawings. They are only for the convenience of describing the present invention and do not require that the present invention must be constructed and operated in a specific orientation. Therefore, they should not be understood as limitations on the present invention.

[0057] In addition, the technical features involved in the various embodiments of the present invention described below can be combined with each other as long as they do not conflict with each other.

[0058] Embodiment 1:

[0059] Embodiment 1 of the present invention provides a human organ chip microfluidic system, comprising an operating table 1, a flow control arm 2, and a plurality of human organ chips 3 fixed on the operating table 1, such as Figure 2 and Figure 4 As shown, specifically including:

[0060] The human organ chip 3 is obtained by connecting a plurality of organ cell culture chambers 31 via a guide pipe 32 .

[0061] The flow control arm 2 is used to control the tilt direction and tilt degree of the operating table 1 to control the flow direction and overall flow rate of the perfusion fluid in the multiple human organ chips 3 on the operating table 1; wherein the perfusion fluid carries drugs.

[0062] The inner wall of the diversion pipe 32 is covered with micro-nano flagella 320. When the flow rate of the perfusion fluid in the corresponding diversion pipe 32 is less than the corresponding preset flow rate, the micro-nano flagella 320 are controlled to push the perfusion fluid forward to accelerate the flow rate of the perfusion fluid in the corresponding diversion pipe 32.

[0063] The preset flow rate is obtained by technicians in this field based on the preset dosage, dosage time and dosage inlet position of the organ cell culture chamber 31 connected to the diversion pipe 32. For different organ cell culture chambers 31, the required dosage may be different, and the corresponding preset flow rate in the diversion pipe 32 is also different.

[0064] The degree of inclination is obtained by a technician in this field based on the preset dosage of each organ cell culture chamber 31 in the human organ chip 3, the position of each organ cell culture chamber 31 in the human organ chip 3, the dosage time of the human organ chip 3, and the location of the dosage entrance. This embodiment also provides an optional formulation standard for the degree of inclination, specifically: making the dosage of each organ cell culture chamber 31 in the human organ chip 3 as close as possible to the preset dosage of each organ cell culture chamber 31. The preset dosage is obtained by a technician in this field based on the analysis of drug screening needs.

[0065] The height, thickness and density of the micro-nano flagella 320 covering the inner wall of the diversion channel 32 are all analyzed by those skilled in the art based on the requirements of perfusion fluid transmission in the human organ chip 3 .

[0066] For example, the thickness and density of the micro-nano flagella 320 are determined according to factors such as the molecular weight of the diversion drug in the human organ chip 3 and the viscosity of the perfusion fluid, and the height of the micro-nano flagella 320 is determined according to the inner diameter of the diversion channel 32 in the human organ chip 3.

[0067] In this embodiment, the flow control arm 2 is combined with the micro-nano flagella 320 to control the inclination of multiple chips through the flow control arm 2, so that under the action of gravitational potential energy, the overall flow direction and overall flow rate of the perfusion fluid are controlled to achieve overall regulation of the drug flow rate in multiple human organ chips 3; at the same time, the micro-nano flagella 320 on the inner wall of the diversion pipe 32 controls the flow rate of the perfusion fluid in each diversion pipe 32 to achieve fine adjustment of the flow rate; thereby, the dosage and dosage rate of each organ cell culture chamber 31 in each human organ chip 3 can be accurately adjusted.

[0068] This embodiment also provides a specific implementation of the flow control arm 2, such as Figure 2 As shown, the flow control arm 2 includes a base 21 , a first rotating shaft 22 , a first control arm 23 , a second rotating shaft 24 and a second control arm 25 .

[0069] One end of the first control arm 23 is connected to the base 21 via the first rotating shaft 22 , the other end of the first control arm 23 is connected to one end of the second control arm 25 via the second rotating shaft 24 , and the operating platform 1 is fixed to the other end of the second control arm 25 .

[0070] The first control arm 23 is used to control the operating platform 1 to rotate and tilt along a first direction, and the second control arm 25 is used to control the operating platform 1 to rotate and tilt along a second direction, thereby controlling the tilt direction and tilt degree of the operating platform 1; wherein the axial direction of the first rotating shaft 22 is perpendicular to the axial direction of the second rotating shaft 24.

[0071] The first direction is the direction in which the first rotating shaft 22 is allowed to rotate, and the second direction is the direction in which the second rotating shaft 24 is allowed to rotate. In this embodiment, the tilt components of the human organ chip 3 in two directions are controlled by the first rotating shaft 22 and the second rotating shaft 24, which are perpendicular to the rotating shaft axis, so that the human organ chip 3 can achieve free tilting of the plane.

[0072] As a preferred implementation of the above embodiment, the flow rate of the drug in the corresponding diversion channel 32 is accelerated by controlling the micro-nano flagella 320 to move the perfusion fluid forward. Figure 5 , Figure 7 as well as Figure 8 As shown, specifically including:

[0073] A plurality of electromagnetic coils 321 are arranged and wound around the outer wall of the flow guiding pipe 32 , and the magnetic field of each electromagnetic coil 321 acts on the micro-nano flagella 320 in the corresponding area of ​​the inner wall of the flow guiding pipe 32 .

[0074] The magnetic field direction and magnetic field size of each electromagnetic coil 321 on the outer wall of the diversion pipe 32 are controlled so that the micro-nano flagella 320 form a wave that propels from the first port of the diversion pipe 32 to the second port of the diversion pipe 32, thereby driving the perfusion fluid forward and accelerating the flow rate of the drug; wherein the first port is the port where the perfusion fluid enters the diversion pipe 32, and the second port is the port where the perfusion fluid leaves the diversion pipe 32.

[0075] The nano-flagella 320 covering the inner wall of the diversion channel 32 is composed of magnetic microspheres 3201 arranged and assembled. Fig. 9 As shown, specifically including:

[0076] The suspension of magnetic microspheres 3201 is placed in a magnetic field in a preset direction, so that the magnetic microspheres 3201 form flagella array units arranged in a preset direction, and the flagella array units are covered and installed on the inner wall of the diversion pipe 32 .

[0077] The preset direction is obtained by those skilled in the art based on the requirement analysis of the arrangement direction of the micro-nano flagella 320 of the flow guiding channel 32. The preset direction is usually a vertical direction.

[0078] The micro-nano flagellum 320 formed by the magnetic microspheres 3201 has the characteristic of directional bending following the direction of the magnetic field. When there is no magnetism or the direction of the magnetic field is perpendicular to the surface where the flagellum is located, the micro-nano flagellum 320 stands upright naturally. When the direction of the magnetic field is not perpendicular to the surface where the flagellum is located, the flagellum bends along the direction of the magnetic field, and when the direction of the magnetic field becomes vertical again or the magnetic field is removed, the flagellum resumes its natural uprightness. Theoretically, the angle of inclination and bending of the flagellum can reach 90°, but in actual use, the bending angle of the flagellum is related to its elasticity and the strength of the applied magnetic field. In this embodiment, the bending angle of the flagellum does not need to reach 90°, but can be analyzed by a technician in this field based on the specific scenario where the device is used, and is achieved by changing the size of the magnetic field or the manufacturing process of the flagellum to change the elasticity of the flagellum.

[0079] like Fig.10 As shown, the surface of the magnetic microsphere 3201 is assembled with nano-hydrophobic particles 3202, so that the micro-nano flagella 320 have a hydrophobic effect, so as to push the perfusion fluid forward through the micro-nano flagella 320.

[0080] This embodiment also provides a specific implementation method of the wave described in the above preferred embodiment, that is, the magnetic field direction and magnetic field magnitude of each electromagnetic coil 321 on the outer wall of the guide pipe 32 are controlled so that the micro-nano flagella 320 form a wave that propels from the first port of the guide pipe 32 to the second port of the guide pipe 32, such as Figure 7 and Figure 8 As shown, specifically including:

[0081] The magnetic field direction and magnitude of the first electromagnetic coil are controlled so that under the magnetic field of the first electromagnetic coil, the corresponding micro-nano flagella 320 are moved from the first port direction to the second port direction, and the moving speed is greater than the flow rate of the perfusion fluid in the diversion pipe 32.

[0082] From the direction of the first port of the guide pipe 32 to the direction of the second port of the guide pipe 32, the corresponding electromagnetic coils 321 are selected in turn as the first electromagnetic coils, and the corresponding micro-nano flagella 320 are controlled to move, so as to form a wave that propels the second port of the guide pipe 32 from the first port of the guide pipe 32.

[0083] Among them, in the diversion pipe 32, the first port direction and the second port direction are not fixed. According to the different inclination directions of the flow control arm 2 controlling the human organ chip 3, the first port direction and the second port direction of the diversion pipe 32 may also be different.

[0084] The control of the magnetic field direction and magnetic field magnitude of the first electromagnetic coil is specifically as follows: controlling the magnetic field direction of the first electromagnetic coil to change from the first port direction to the second port direction, during which the magnetic field magnitude decreases to no magnetism and then increases in the reverse direction again, and determining the speed of the magnetic field change according to the difference between the flow velocity of the perfusion fluid in the diversion pipe 32 and the ideal flow velocity, the ideal flow velocity being calculated by the dosage and administration time of the organ cell culture chamber 31 connected to the second port direction of the diversion pipe 32, and the speed of the magnetic field change determines the speed of the flagella moving, thereby determining the magnitude of the force pushing the perfusion fluid forward.

[0085] It should be noted that this embodiment is only one of the forms of realizing the wave. In actual use, it is feasible to control the electromagnetic coils 321 on the outer wall of the diversion pipe 32 to move together to form reciprocating waves, or to control the micro-nano flagella 320 corresponding to multiple electromagnetic coils 321 to move simultaneously. The implementation can be based on the concept of controlling the micro-nano flagella 320 with the electromagnetic coil 321, and should be covered within the scope of protection of the present invention.

[0086] In the above embodiment, the electromagnetic coils 321 other than the electromagnetic coil 322 may not be powered, so that they are in a non-magnetic state, so that the corresponding flagella follow the flow direction of the perfusion fluid. Relative to this scheme, in combination with the above embodiment, the following preferred embodiment is also provided, that is, the magnetic field direction and magnetic field magnitude of each electromagnetic coil 321 on the outer wall of the guide pipe 32 are controlled so that the micro-nano flagella 320 form a wave that propels from the first port of the guide pipe 32 to the second port of the guide pipe 32, and also includes:

[0087] After the corresponding micro-nano flagella 320 is flicked, the magnetic field direction and magnetic field size of the corresponding electromagnetic coil 321 are controlled to restore the micro-nano flagella 320 to be tilted and bent toward the first port to wait for the next flick, so as to form a circulating wave that propels the first port of the self-guiding pipe 32 toward the second port of the guide pipe 32, wherein the recovery speed is less than the flow rate of the perfusion fluid in the guide pipe 32.

[0088] In this embodiment, after the corresponding micro-nano flagella 320 finishes moving, it slowly recovers to the direction toward the first port, so that after forming the first wave of waves from the first port of the guide pipe 32 to the second port of the guide pipe 32, it can continue to start from the first port of the guide pipe 32 to control the corresponding flagella to move to form the second wave, the third wave, and even the Nth wave, thereby forming a cyclic wave and continuously pushing the perfusion fluid forward. At the same time, in order to prevent the flagella from affecting the flow of the perfusion fluid during recovery, the recovery speed is controlled to be less than the flow rate of the perfusion fluid in the guide pipe 32. The process of controlling the magnetic field direction and magnetic field magnitude of the corresponding electromagnetic coil 321 is the reverse operation of controlling the flagella to move the perfusion fluid forward. In this process, the magnetic field direction is changed from the second port direction to the first port direction, and the conversion speed can be as slow as possible within the allowable degree to reduce the impact on the advancement of the perfusion fluid. For example, the corresponding magnetic field conversion time can be formulated according to the cycle of the wave cycle to determine the speed of the magnetic field conversion.

[0089] The above preferred embodiment provides a method for controlling the micro-nano flagella 320 by the electromagnetic coil 321 to move the perfusion fluid forward to speed up the drug flow rate. In actual use, there is also a situation where the flow rate of the corresponding diversion pipeline 32 is too low, so that the amount of drug delivered to the corresponding organ cell culture chamber 31 is insufficient. At this time, based on the concept of controlling the micro-nano flagella 320 by the electromagnetic coil 321, there is also the following preferred embodiment, that is, by controlling the micro-nano flagella 320 to block the perfusion fluid from moving forward, such as Fig.11 and Fig.12 As shown, specifically including:

[0090] A plurality of electromagnetic coils 321 are arranged and wound around the outer wall of the flow guiding pipe 32 , and the magnetic field of each electromagnetic coil 321 acts on the micro-nano flagella 320 in the corresponding area of ​​the inner wall of the flow guiding pipe 32 .

[0091] The magnetic field direction and magnitude of each electromagnetic coil 321 on the outer wall of the diversion pipe 32 are controlled so that the micro-nano flagella 320 form a grid to block the perfusion fluid from moving forward.

[0092] The controlling of the magnetic field direction and magnetic field magnitude of each electromagnetic coil 321 on the outer wall of the flow guide pipe 32 so that the micro-nano flagella 320 form a grid specifically includes:

[0093] Select the corresponding electromagnetic coil 321, and control the magnetic field direction and magnetic force of the electromagnetic coil 321 according to the flow direction and flow rate of the perfusion fluid in the diversion pipe 32, so that the magnetic force applied by the electromagnetic coil 321 to the corresponding micro-nano flagella 320 is balanced with the force applied to the micro-nano flagella 320 by the flow of the perfusion fluid, so that the micro-nano flagella 320 in the corresponding area of ​​the inner wall of the diversion pipe 32 stands upright to form an upright grid to block the perfusion fluid from advancing.

[0094] The selection of the corresponding electromagnetic coils 321 may be to select all the electromagnetic coils 321 on the outer wall of the diversion tube, or to select some of the electromagnetic coils 321 to stand upright to form a grid. As a preferred implementation method, the number n of the electromagnetic coils 321 forming the grid is determined according to the flow rate of the perfusion fluid in the diversion tube 32, and n electromagnetic coils 321 evenly distributed are selected from the multiple electromagnetic coils 321 on the outer wall of the diversion tube 32, and the magnetic field of the electromagnetic coils 321 is controlled to form an upright grid with intervals, so that while reducing the flow rate of the perfusion fluid, other flagella that have not formed a grid form a passage for the flow of nutrients required for the physiological metabolism of the organ cell culture chamber 31.

[0095] On this basis, combined with the selection of the thickness of flagella and the density of flagella coverage, there is also a preferred embodiment, that is, according to the molecular weight of the nutrients and drugs in the nutrient solution and the viscosity of the perfusion solution, multiple flagella of different thicknesses are selected, so that the flagella of different thicknesses are distributed at intervals on the inner wall of the diversion pipe 32, or on the inner wall of the diversion pipe 32, the density of flagella coverage is controlled to be different, so that when the corresponding flagella stand upright to form a grid, the spacing of the grid allows the nutrients to pass through while blocking the drugs from passing through. This implementation method is only applicable to the case where the molecular weight of the drug is greater than the molecular weight of the nutrients.

[0096] like Fig.13 As shown, the system also includes a processor 4 and a driving module 5, wherein the driving module 5 is used to provide current to the electromagnetic coil 321 to drive the electromagnetic coil 321 to generate a corresponding magnetic field; the processor 4 is used to control the driving module 5 to control the magnetic field direction and magnetic field size of the corresponding electromagnetic coil 321.

[0097] Among them, in combination with the above preferred embodiments, Fig.13 As shown, the processor 4 is used to control the driving module 5 to control the electromagnetic coil 321 on the outer wall of each diversion pipe 32 in the human organ chip 3, and to control the electromagnetic coil 321 on the outer wall of the diversion pipe 32 whose corresponding perfusion fluid flow rate is less than the preset flow rate, so as to drive the perfusion fluid forward.

[0098] like Fig.14As shown, the system further includes an ultraviolet emitter 6 and a fluorescence receiver 7. The drug is labeled by a fluorescent labeling method. During the diversion process of the perfusion fluid carrying the drug, the ultraviolet emitter 6 is used to emit ultraviolet light to excite the fluorescent substance to emit fluorescence, and the fluorescence receiver 7 is used to receive the fluorescence, so as to observe the flow direction and flow rate of the perfusion fluid in each diversion pipe 32.

[0099] Due to the magnetic properties of the micro-nano flagella 320, they can form an electromagnetic induction system together with the electromagnetic coil 321 on the outer wall of the diversion pipe 32. Based on this principle, this embodiment also provides a preferred implementation method, which is:

[0100] Before a preset time after the human organ chip 3 is tilted and fixed, the corresponding electromagnetic coil 321 on the outer wall of the diversion pipe 32 is not intermittently powered, and the flow rate of the perfusion fluid in the diversion pipe 32 is detected by the deformation of the micro-nano flagella 320 on the inner wall of the diversion pipe 32. If it is detected that the flow rate is less than the corresponding preset flow rate, the electromagnetic coil 321 is powered to control the corresponding flagella to move the perfusion fluid forward.

[0101] The flow rate of the perfusion fluid in the diversion pipe 32 is detected by deformation of the micro-nano flagella 320 on the inner wall of the diversion pipe 32, specifically including:

[0102] When the perfusion fluid flows through the diversion pipe 32, the micro-nano flagella 320 is deformed due to the perfusion fluid. Within a preset time after the human organ chip 3 is tilted and fixed, the change in the tilt degree causes the flow rate of the perfusion fluid to change, thereby causing the micro-nano flagella 320 to deform and move, generating a changing magnetic field. The magnetic field acts on the electromagnetic coil 321 on the outer wall of the diversion pipe 32 to generate a weak induced current. By detecting the size of the induced current, the change in the flow rate of the perfusion fluid is monitored. When the induced current is no longer generated, it means that the flow rate of the perfusion fluid tends to be stable. The flow rate of the perfusion fluid is calculated by accumulating the change in the flow rate of the perfusion fluid before the flow rate of the perfusion fluid is stabilized.

[0103] The preset time is set by a person skilled in the art based on analysis of the time required for the perfusion fluid flow rate to stabilize after the human organ chip 3 is tilted and fixed.

[0104] Based on this method, the system further includes an induction module, which is used to receive the induced current generated by the electromagnetic coil 321 and transmit it to the processor 4 for processing to monitor the change in the flow rate of the perfusion fluid and the stable moment of the flow rate of the perfusion fluid, so as to calculate the flow rate of the perfusion fluid.

[0105] After determining the flow rate of the perfusion fluid, it is determined whether the flow rate of the perfusion fluid in the corresponding diversion pipe 32 is less than the preset flow rate. If it is less than the preset flow rate, the sensing module stops working, and the driving module 5 supplies power to the electromagnetic coil 321 to speed up the flow rate of the perfusion fluid. Whenever the flow control arm 2 controls the tilt direction and tilt degree of the human organ chip 3 to change, the driving module 5 stops working and the sensing module works to detect the flow rate of the perfusion fluid.

[0106] Since a plurality of electromagnetic coils 321 are wound around the outer wall of the diversion pipe 32, there is also a preferred implementation method: some of the electromagnetic coils 321 are not powered, so that the induction module receives the induced current generated by the electromagnetic coils 321, monitors the change in the flow rate of the perfusion fluid in real time, and calculates the flow rate of the perfusion fluid; the other electromagnetic coils 321 are controlled by the driving module 5, and when the flow rate of the perfusion fluid is less than the preset flow rate, the electromagnetic coils 321 are powered to speed up the flow rate of the perfusion fluid.

[0107] The "first" and "second" in this embodiment do not have any special limiting meanings. They are used for description only to facilitate the description of different individuals in a category of objects and should not be interpreted as having special limiting meanings in order or other aspects.

[0108] Embodiment 2:

[0109] After providing a human organ chip microfluidic system described in Example 1, the present invention will further provide a method for implementing the human organ chip microfluidic system, in order to make relevant elaborations on the implementation method of the corresponding structural functions in Example 1, and further make relevant in-depth analysis on its design principles. It should be noted that the device structure in Example 1 is applicable to this Example 2, and its structure will not be repeated in this embodiment.

[0110] like Fig.15 As shown, the implementation method includes:

[0111] In step 201 , the tilt direction and tilt degree of the operating platform 1 are adjusted by the flow control arm 2 to control the flow direction and overall flow rate of the perfusion fluid in the multiple human organ chips 3 on the operating platform 1 .

[0112] In step 202 , the diversion pipes 32 at the same position in each human organ chip 3 are divided into a control group, and the driving module 5 performs linkage control on the diversion pipes 32 in the control group.

[0113] In step 203, one of the multiple human organ chips 3 is used as a reference chip. When administering medicine to the reference chip, the drug is labeled using a fluorescent labeling method. In the process of diversion of the perfusion fluid carrying the drug, the ultraviolet emitter 6 is used to emit ultraviolet rays to excite the fluorescent substance to emit fluorescence, and the fluorescence receiver 7 is used to receive the fluorescence, so as to observe the flow direction and flow rate of the perfusion fluid in each diversion pipe 32. If the flow rate of the perfusion fluid in the corresponding diversion pipe 32 is lower than the corresponding preset flow rate, the control group corresponding to the diversion pipe 32 is controlled so that the micro-nano flagella 320 on the inner wall of all the diversion pipes 32 in the control group drive the perfusion fluid forward, thereby accelerating the flow rate of the perfusion fluid in the corresponding diversion pipe 32.

[0114] This embodiment is applicable to the use of a large number of human organ chips 3 with the same structure for drug administration, and for the scenario where the drug administration speed and dosage are the same in the same organ cell culture chamber 31. In this scenario, it is considered that the preset flow rates corresponding to the diversion pipes 32 at the same position in different human organ chips 3 are the same.

[0115] The control group corresponding to the diversion pipe 32 is controlled so that the micro-nano flagella 320 on the inner wall of all the diversion pipes 32 in the control group push the perfusion fluid forward through the control of the processor 4 and the driving module 5. For example, when the outer wall of the diversion pipe 32 in the corresponding control group is arranged and wound with N electromagnetic coils 321, the implementation specifically includes:

[0116] A plurality of current supply ports are provided in the driving module 5, and the electromagnetic coils 321 at the same position in all the flow guide pipes 32 in the control group are connected to the same supply port of the driving module 5, so as to provide them with currents of the same direction and magnitude, such as connecting the nth electromagnetic coil 321 on the outer walls of all the flow guide pipes 32 in the control group to the nth supply port.

[0117] The processor 4 determines the corresponding first current magnitude, second current magnitude and first transition duration according to the flow direction and flow velocity of the perfusion fluid in the corresponding flow conduit 32 of the reference chip. The processor 4 controls the driving module 5 to control the first, second, ... nth supply ports in sequence to form a first wave, so that the corresponding supply port provides the electromagnetic coil 321 with a current that changes within the first transition duration, and the direction of the current changes from the first current direction to the second current direction, and the current magnitude decreases from the first current magnitude to 0A, and then increases in the opposite direction to the second current magnitude. The first current direction is determined by the winding method of the electromagnetic coil 321, so that the magnetic field direction of the electromagnetic coil 321 is the first port direction, and the second current direction is determined by the winding method of the electromagnetic coil 321, so that the magnetic field direction of the electromagnetic coil 321 is the second port direction, so that under the action of the corresponding electromagnetic coil 321, the corresponding flagellum is toggled from the first port direction to the second port direction.

[0118] After the corresponding flagella are flicked, the product of the value obtained by subtracting 1 from the number of electromagnetic coils 321 wrapped around the outer wall of the diversion pipe 32 and the transition time is used as the second transition time, and the current of the corresponding supply port is controlled to change within the second transition time, and the direction of the current is changed from the second current direction to the first current direction, and the current magnitude is reduced from the second current magnitude to 0A, and then increased in the opposite direction to the first current magnitude, so that the flagellum slowly recovers to bend obliquely toward the first port, waiting for the next flick. Specifically, after the first wave is formed, the first, second, ... nth supply ports are controlled in turn in a cyclic form to form subsequent waves, so as to continuously flick the perfusion fluid forward and accelerate the flow rate of the drug in the corresponding diversion pipe 32.

[0119] The "first" and "second" in this embodiment do not have any special limiting meanings. They are used for description only to facilitate the description of different individuals in a category of objects and should not be interpreted as having special limiting meanings in order or other aspects.

[0120] Embodiment 3:

[0121] In Example 2, a method for implementing unified drug delivery using multiple human organ chips 3 with the same structure is provided. Due to the consistency of the structures of the human organ chips 3, multiple human organ chips 3 can be uniformly controlled by using the flow rate of the reference chip as a reference and linking the control group. However, in actual use, there is still a more complicated scenario, that is, when conducting drug testing to determine the effective drug delivery amount, multiple human organ chips 3 with the same structure need to be used for drug delivery, but there are differences in the drug delivery amounts of the same category of organ cell culture chambers 31. Or when testing the effectiveness of drugs and the effective delivery amount of drugs for different diseases or different symptoms, or even for organ cells loaded with different cells, human organ chips 3 with different structures may be used. And due to the fixing method of the human organ chip 3 on the operating table 1 and the process error of the human organ chip 3, even if the human organ chip 3 has the same structure, the flow rate of the drug in the corresponding diversion channel 32 may be inconsistent with the flow rate of the drug in the diversion channel 32 at the same position in other chips, such as Fig.16 As shown, when four human organ chips 3 with the same structure are fixed on the operating table 1, they are arranged from left to right and from top to bottom as the first human organ chip 3, the second human organ chip 3, the third human organ chip 3 and the fourth human organ chip 3. Among them, for the diversion pipe 32 at the same position, the flow rates of the first, second and third human organ chips 3 remain consistent, but the flow rate of the third human organ chip 3 is lower than the expected flow rate. Fig.16The size of the arrow represents the flow rate of the drug in the pipeline. Due to the precision requirements of drug screening, even a slight deviation in drug flow may affect the drug screening results.

[0122] Therefore, considering the possibility of various types of drug testing and drug screening in actual situations, the present invention, based on the human organ chip microfluidic system described in Example 1, also provides a preferred embodiment of a drug delivery scenario using multiple human organ chips 3. It should be noted that the device structure in Example 1 is applicable to this Example 3, and its structure will not be repeated in this embodiment. The implementation method is as follows Fig.17 As shown, specifically including:

[0123] In step 301 , the tilt direction and tilt degree of the operating platform 1 are adjusted by the flow control arm 2 to control the tilt direction and tilt degree of the plurality of human organ chips 3 on the operating platform 1 .

[0124] In step 302 , for each human organ chip 3 , the flow rate of the perfusion fluid in each of the flow conduits 32 is detected.

[0125] In step 303, among all the diversion pipes 32 with the same perfusion fluid flow direction, a first number of the diversion pipes 32 with a perfusion fluid flow rate less than the corresponding preset flow rate is counted, and a first proportion of the first number in the total number of the diversion pipes 32 in the same direction is calculated. According to the first proportion, it is determined whether to adjust the flow control arm 2 or to propel the perfusion fluid forward by wave propulsion, such as Fig.18 As shown, specifically:

[0126] In step 401, when the first proportion is greater than the first preset proportion, the flow control arm 2 is adjusted to tilt the multiple human organ chips 3 in the direction of the perfusion fluid flow to speed up the overall flow rate of the perfusion fluid; at the same time, for the diversion pipe 32 whose corresponding perfusion fluid flow rate after adjustment is higher than the preset flow rate, the micro-nano flagella 320 on the inner wall of the diversion pipe 32 is controlled to form a grid to block the perfusion fluid from moving forward, so as to reduce the flow rate of the corresponding diversion pipe 32.

[0127] In step 402, if the first proportion is less than or equal to the first preset proportion, the flow control arm 2 is not adjusted, and for the diversion pipe 32 whose corresponding perfusion fluid flow rate is lower than the preset flow rate, the perfusion fluid is moved forward by controlling the micro-nano flagella 320 on the inner wall of the diversion pipe 32 to speed up the flow rate of the corresponding diversion pipe 32.

[0128] The first preset ratio is obtained by a technician in this field based on analysis of medication requirements.

[0129] As a more complex implementation scenario, when the flow rate of the perfusion fluid needs to be controlled within an ideal flow rate range, but among all the diversion pipes 32, there are both diversion pipes 32 with a relatively high perfusion fluid flow rate and diversion pipes 32 with a relatively low perfusion fluid flow rate, this embodiment further includes:

[0130] Among all the diversion pipes 32 with the same perfusion fluid flow direction, the second number of the diversion pipes 32 with a relatively small perfusion fluid flow rate and the third number of the diversion pipes 32 with a relatively large perfusion fluid flow rate are counted, and a second proportion of the second number in the total number of the co-directing pipes 32 and a third proportion of the third number in the total number of the co-directing pipes 32 are calculated. According to the second proportion and the third proportion, it is determined whether to adjust the flow control arm 2, or to propel the perfusion fluid forward by waves, or to block the perfusion fluid from advancing by a grid, such as Fig.19 As shown, specifically:

[0131] In step 501, when the second proportion and the third proportion are both less than or equal to 50%, the flow control arm 2 is not adjusted, and for the diversion pipe 32 whose corresponding perfusion fluid flow rate is lower than the preset flow rate, the perfusion fluid is moved forward by controlling the micro-nano flagella 320 on the inner wall of the diversion pipe 32 to speed up the flow rate of the corresponding diversion pipe 32; for the diversion pipe 32 whose corresponding perfusion fluid flow rate is higher than the preset flow rate, the perfusion fluid is blocked by controlling the micro-nano flagella 320 on the inner wall of the diversion pipe 32 to reduce the flow rate of the corresponding diversion pipe 32.

[0132] In step 502, when the second proportion is greater than 50%, the flow control arm 2 is adjusted to tilt the multiple human organ chips 3 in the direction of the flow of the perfusion fluid to speed up the overall flow rate of the perfusion fluid; at the same time, for the diversion pipe 32 whose corresponding perfusion fluid flow rate after adjustment is higher than the preset flow rate, the micro-nano flagella 320 on the inner wall of the diversion pipe 32 is controlled to form a grid to block the forward movement of the perfusion fluid, so as to reduce the flow rate of the corresponding diversion pipe 32.

[0133] In step 503, when the third proportion is greater than 50%, the flow control arm 2 is adjusted to tilt the multiple human organ chips 3 in the opposite direction of the flow of the perfusion fluid to reduce the overall flow rate of the drug; at the same time, for the diversion pipe 32 whose corresponding perfusion fluid flow rate after adjustment is lower than the preset flow rate, the perfusion fluid is moved forward by controlling the micro-nano flagella 320 on the inner wall of the diversion pipe 32 to speed up the flow rate of the corresponding diversion pipe 32.

[0134] The control method of the flow control arm 2 and the micro-nano flagellum 320 is based on the same concept as the implementation method in Example 1. For the specific content, please refer to the description in Example 1 of the present invention, which will not be repeated here.

[0135] The "first", "second" and "third" in this embodiment do not have any special limiting meanings. They are used for description only to facilitate the description of different individuals in a category of objects and should not be interpreted as having special limiting meanings in order or other aspects.

[0136] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions and improvements made within the spirit and principles of the present invention should be included in the protection scope of the present invention.

Claims

1. A human organ chip microfluidic system, characterized in that: The device comprises an operating table (1), a flow control arm (2), and a plurality of human organ chips (3) fixed on the operating table (1), and specifically comprises: The human organ chip (3) is obtained by connecting a plurality of organ cell culture chambers (31) via a flow guide pipe (32); The flow control arm (2) is used to control the tilt direction and tilt degree of the operating table (1) so as to control the flow direction and overall flow rate of the perfusion fluid in the plurality of human organ chips (3) on the operating table (1); wherein the perfusion fluid carries drugs; The inner wall of the diversion pipe (32) is covered with micro-nano flagella (320), and when the flow rate of the perfusion fluid in the corresponding diversion pipe (32) is less than the corresponding preset flow rate, the micro-nano flagella (320) are controlled to move the perfusion fluid forward, thereby accelerating the flow rate of the perfusion fluid in the corresponding diversion pipe (32); The flow control arm (2) specifically comprises a base (21), a first rotating shaft (22), a first control arm (23), a second rotating shaft (24) and a second control arm (25); One end of the first control arm (23) is connected to the base (21) via the first rotating shaft (22), the other end of the first control arm (23) is connected to one end of the second control arm (25) via the second rotating shaft (24), and the operating table (1) is fixed to the other end of the second control arm (25); The first control arm (23) is used to control the operating platform (1) to rotate and tilt in a first direction, and the second control arm (25) is used to control the operating platform (1) to rotate and tilt in a second direction, thereby controlling the tilt direction and tilt degree of the operating platform (1); wherein the axis of rotation of the first rotating shaft (22) is perpendicular to the axis of rotation of the second rotating shaft (24); The method of controlling the micro-nano flagella (320) to move the perfusion fluid forward and accelerating the flow rate of the perfusion fluid in the corresponding diversion pipe (32) specifically includes: A plurality of electromagnetic coils (321) are arranged and wound around the outer wall of the flow guiding pipe (32), and the magnetic field of each electromagnetic coil (321) acts on the micro-nano flagella (320) in the corresponding area of ​​the inner wall of the flow guiding pipe (32); Controlling the magnetic field direction and magnetic field magnitude of each electromagnetic coil (321) on the outer wall of the diversion pipe (32) so that the micro-nano flagella (320) form a wave that propels from the first port of the diversion pipe (32) to the second port of the diversion pipe (32), thereby driving the perfusion fluid forward and accelerating the flow rate of the perfusion fluid; wherein the first port is the port through which the perfusion fluid enters the diversion pipe (32), and the second port is the port through which the perfusion fluid leaves the diversion pipe (32); The micro-nano flagella (320) covering the inner wall of the diversion channel (32) are assembled by arranging magnetic microspheres (3201), specifically comprising: Placing a suspension of magnetic microspheres (3201) in a magnetic field in a preset direction, so that the magnetic microspheres (3201) form flagella array units arranged in a preset direction, and covering and mounting the flagella array units on the inner wall of the diversion pipe (32); The system further comprises an ultraviolet emitter (6) and a fluorescence receiver (7), wherein the drug is marked by a fluorescent marking method, and during the diversion process of the perfusion fluid carrying the drug, the ultraviolet emitter (6) is used to emit ultraviolet light to excite the fluorescent substance to emit fluorescence, and the fluorescence receiver (7) is used to receive the fluorescence, thereby observing the flow direction and flow rate of the perfusion fluid in each diversion pipe (32).

2. The human organ chip microfluidic system according to claim 1, characterized in that: The controlling of the magnetic field direction and magnetic field magnitude of each electromagnetic coil (321) on the outer wall of the guide pipe (32) so that the micro-nano flagellum (320) forms a wave that propels from the first port of the guide pipe (32) to the second port of the guide pipe (32) specifically includes: Controlling the direction and magnitude of the magnetic field of the first electromagnetic coil so that, under the action of the magnetic field of the first electromagnetic coil, the corresponding micro-nano flagella (320) are moved from the direction of the first port to the direction of the second port, and the moving speed is greater than the flow rate of the perfusion fluid in the diversion pipe (32); From the direction of the first port of the flow-guiding conduit (32) to the direction of the second port of the flow-guiding conduit (32), the corresponding electromagnetic coils (321) are selected in sequence as the first electromagnetic coils, and the corresponding micro-nano flagella (320) are controlled to move, thereby forming a wave that propels the first port of the flow-guiding conduit (32) toward the second port of the flow-guiding conduit (32).

3. The human organ chip microfluidic system according to claim 2, characterized in that: The controlling of the magnetic field direction and magnetic field magnitude of each electromagnetic coil (321) on the outer wall of the flow guiding pipe (32) so that the micro-nano flagellum (320) forms a wave that propels from the first port of the flow guiding pipe (32) to the second port of the flow guiding pipe (32) also includes: After the corresponding micro-nano flagella (320) is moved, the magnetic field direction and magnetic field size of the corresponding electromagnetic coil (321) are controlled to restore the micro-nano flagella (320) to be inclined and bent toward the first port to wait for the next movement, so as to form a wave that propels the first port of the self-guiding pipe (32) toward the second port of the guide pipe (32), wherein the recovery speed is less than the flow rate of the perfusion fluid in the guide pipe (32).

4. The human organ chip microfluidic system according to claim 1, characterized in that: The system further comprises a processor (4) and a drive module (5); the drive module (5) is used to provide current to the electromagnetic coil (321) so as to drive the electromagnetic coil (321) to generate a corresponding magnetic field; the processor (4) is used to control the drive module (5) so as to control the magnetic field direction and magnetic field magnitude of the corresponding electromagnetic coil (321).

5. A method for implementing the human organ chip microfluidic system according to any one of claims 1 to 4, characterized in that: include: The tilt direction and tilt degree of the operating table (1) are adjusted by the flow control arm (2) to control the flow direction and overall flow rate of the perfusion fluid in the plurality of human organ chips (3) on the operating table (1); The diversion pipes (32) at the same position in each human organ chip (3) are divided into a control group, and the driving module (5) performs linkage control on the diversion pipes (32) in the control group; One of the plurality of human organ chips (3) is used as a reference chip. When administering medicine to the reference chip, the drug is labeled using a fluorescent labeling method. In the process of diverting the drug with the perfusion fluid, the ultraviolet emitter (6) is used to emit ultraviolet light to excite the fluorescent substance to emit fluorescence. The fluorescence is received by a fluorescence receiver (7) to observe the flow direction and flow rate of the perfusion fluid in each diversion pipe (32). If the flow rate of the perfusion fluid in the corresponding diversion pipe (32) is lower than the corresponding preset flow rate, the control group corresponding to the diversion pipe (32) is controlled so that the micro-nano flagella (320) on the inner wall of all the diversion pipes (32) in the control group move the perfusion fluid forward, thereby accelerating the flow rate of the perfusion fluid in the corresponding diversion pipe (32).

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