Method for constructing multi-component heterogeneous fiber structure under assistance of acoustic tweezers

Abstract

The invention relates to the technical field of acoustic wave device application and biological tissue engineering, in particular to a method for constructing a multi-component heterogeneous fiber structure under the assistance of acoustic tweezers. According to the method, an acoustic tweezers technology and a microfluidic spinning technology are combined, an electric signal is converted into an acoustic surface wave through the piezoelectric effect of a piezoelectric material, and a beam-shaped acoustic standing wave field is formed in a microchannel of a specific structure; different target cells form a stable fiber configuration under the interaction of microchannel limitation and acoustic radiation force, and spatial precise classification and arrangement of multiple types of cells are realized. The low-temperature-sensitive hydrogel is introduced in the cell injection process, and the fiber scaffold is formed after ultraviolet curing, so that the fiber structure of the cells is still maintained after the sound field is removed. The cells treated by the surface acoustic wave can form a complex three-dimensional bionic tissue structure more easily, and the cell viability is remarkably improved. Various fiber structures can be formed by regulating and controlling sound field parameters, and great potential is shown in the field of in-vitro barrier model construction.

Description

Technical Field

[0001] This invention relates to the technical field of acoustic device applications and biological tissue engineering, specifically to a method for constructing multi-component heterogeneous fiber structures using acoustic tweezers. Background Technology

[0002] In the field of tissue engineering, constructing stable multi-component heterogeneous fibrous structures is fundamental for forming various tissue structures, such as in vitro barrier models, and is of great significance for drug screening and disease mechanism research. Traditional methods for constructing multi-component heterogeneous fibrous structures largely rely on spontaneous cell assembly or physical scaffold assistance, which suffers from problems such as imprecise cell control, low structural biomimicry, and low cell viability. In particular, the coordinated arrangement and functional maintenance of multiple cell types remains a challenge. In recent years, the combination of acoustic fluid dynamics technology and tissue engineering has provided a new approach to cell patterning: acoustic tweezers systems can utilize acoustic radiation forces to perform non-contact, non-damaging manipulation of micro- and nano-scale particles, offering flexible operation with minimal impact on cell viability and activity. However, existing acoustic tweezers systems are mostly used for manipulating single cell types, making it difficult to achieve the coordinated arrangement and stable shaping of multiple cell components, especially in constructing multi-component heterogeneous fibrous structures with complex spatial structures, where a technological gap still exists. Summary of the Invention

[0003] To address the problems existing in the prior art, this invention aims to provide a method for constructing multi-component heterogeneous fiber structures using acoustic tweezers. By utilizing the surface acoustic wave mechanism, different microscale biological particles within a multi-channel microcavity are guided to form an alternating linear arrangement, thereby improving the efficiency of constructing multi-component heterogeneous fiber structures and increasing cell viability.

[0004] The technical solution adopted in this invention is as follows: A method for constructing multi-component heterofiber structures using acoustic tweezers includes the following steps: S1. Using a low-temperature sensitive hydrogel, mix the required cell suspension for the target tissue model at a 1:1 ratio to obtain multiple cell mixtures, and load each mixture into a 1 mL syringe. The optimal hydrogel concentration after mixing is 5%-10% (w / v), and the optimal cell concentration is 1×10⁻⁶. 6 -5×10 6 cells / mL; S2. 2% (w / v) Pluronic.F127 modification solution was uniformly introduced into the multi-channel microchamber of the acoustic tweezers-assisted multi-component heterogeneous fiber structure device via a fluid drive unit for 1 hour to modify the inner wall of the multi-channel microchamber and reduce cell adhesion. S3. According to the cell distribution structure of the target tissue model to be constructed, connect the syringes loaded with different cell mixtures to different inlets of the multi-channel microchamber through the connecting tube, and use the fluid drive unit to uniformly introduce the fluid into the multi-channel microchamber of the acoustic tweezers-assisted multi-component heterogeneous fiber structure construction device. S4. In the acoustic tweezers-assisted construction device for multi-component heterogeneous fiber structures, the input power of the acoustic transducer module is greater than 0 dBm and less than or equal to 25 dBm to avoid damage to the device due to excessive power. After the signal is turned on, the acoustic transducer module can form multiple alternating one-dimensional linear cell patterns in the steady-flow zone at the front end of the multi-channel microchamber, which then flow into the integration zone of the multi-channel microchamber; then, the curing unit is used to irradiate the tail end of the multi-channel microchamber to solidify the cell mixture. S5. After solidification, the colloid of the mixed liquid is extruded along the outlet of the multi-channel microchamber to form multi-component heterogeneous fibers. The fibers are placed in a culture dish, and the corresponding culture medium is added according to the cell model to be constructed for culture.

[0005] Furthermore, the acoustic tweezers-assisted construction device for multi-component heterogeneous fiber structures includes an acoustic tweezers unit, a fluid drive unit, and a curing unit.

[0006] Specifically, the acoustic tweezers unit includes an acoustic transducer module, a control circuit board, and a base; Furthermore, the acoustic transducer module consists of a piezoelectric substrate, a pair of opposing interdigital electrodes, and a multi-channel microcavity chamber; the multi-channel microcavity chamber is located in the middle of the pair of opposing interdigital electrodes. Specifically, the piezoelectric substrate comprises a series of piezoelectric materials, including a 128°YX tangential lithium niobate crystal, capable of allowing sound waves to propagate on its surface. Through the piezoelectric effect, electrical signals can be converted into periodic mechanical deformations, i.e., surface acoustic waves, which then propagate on the surface of the piezoelectric material.

[0007] Specifically, the interdigitated electrodes appear in pairs, with a certain distance between them to accommodate the multi-channel microcavity chamber. To avoid the multi-channel microcavity chamber absorbing too much surface acoustic wave, the contact area between the multi-channel microcavity chamber and the piezoelectric substrate should be minimized while ensuring bonding effectiveness.

[0008] Specifically, the interdigitated electrodes are bonded to the piezoelectric substrate using magnetron sputtering technology. The materials used are typically aluminum, gold, silver, copper, chromium, etc. The electrode finger width and spacing determine the operating frequency of the acoustic transducer, the electrode aperture determines the width of the surface acoustic wave range, and the distance between the interdigitated electrode pairs significantly affects the patterning efficiency.

[0009] Specifically, the multi-channel microcavity is an inverted template created using an SU-8 mold.

[0010] Specifically, the multi-channel microcavity is made of PDMS material and is bonded to the piezoelectric substrate via oxygen plasma bonding, enabling the cell suspension to form patterns within the multi-channel microcavity.

[0011] Furthermore, the control circuit board comprises a corresponding PCB board designed according to the interdigitated electrodes, an RF interface, and metal spring pins for signal input.

[0012] Furthermore, the base is provided with corresponding grooves whose size and shape match the control circuit board and acoustic transducer module, which are used to restrict the position of the control circuit board and acoustic transducer module, thereby achieving a detachable connection.

[0013] Furthermore, the fluid drive unit involved in steps S2 and S3 includes a power source and a displacement actuator; the power source is a stepper motor; the displacement actuator is a syringe and a connecting tube connected to the stepper motor lead screw.

[0014] Furthermore, the widths of the stabilization zone and integration zone of the multi-channel microchamber are both integer multiples of half the wavelength of the input acoustic wave; the number of inlets of the multi-channel microchamber can be adjusted according to the cell model to be constructed. In this description, multi-channel microchambers with three and five inlets are used as examples.

[0015] Furthermore, in step S4, after the electrical signal is turned on, a pair of opposing interdigital electrodes generate two columns of surface acoustic waves traveling in opposite directions, and a standing wave is formed in the middle region of the interdigital electrodes; when the surface acoustic waves propagate into the mixed liquid in the multi-channel microcavity, they will be transformed into leakage waves in the vertical direction, thereby causing pressure fluctuations in the medium, pushing the suspended cells in the medium to the node position or the anti-node position of the acoustic standing wave field, and controlling the cells to form linear patterns of cell fibers.

[0016] Furthermore, surface acoustic waves begin to play a role in the steady-flow region of the multi-channel microcavity. Since the width of each channel in the steady-flow region is λ / 2, only one sound pressure node can be formed in each channel, thus forming an alternating linear pattern after entering the integration region.

[0017] Furthermore, when controlling the formation of linear patterns of cell fibers, the signal parameters input to a pair of opposing interdigital electrodes are identical.

[0018] Furthermore, the cell suspension can be adjusted according to the cell model to be constructed, with an optimal concentration of 1×10⁻⁶. 6 -5×10 6 Cells / mL: below this concentration range, intermittent, discontinuous linear patterns will appear; if the concentration is too high, the cell bands will stick together.

[0019] Furthermore, the low-temperature sensitive hydrogel is mixed with the cell suspension at a volume ratio of 1:1, and the concentration of the mixed hydrogel is 5%-10% (w / v). If the concentration is lower than this, the low-temperature sensitive hydrogel will not be able to solidify, and if the concentration is higher than this, the solidified hydrogel fibers will be too hard, causing the cells to be unable to extend inside.

[0020] Furthermore, the curing unit is placed at a position greater than 1 cm at the tail end of the multi-channel micro-chamber to prevent the light source from illuminating the entire multi-channel micro-chamber.

[0021] Compared with the prior art, the present invention has the following significant advantages: 1. The interdigitated electrodes in this invention can generate frequency conversion signals. By changing the frequency, amplitude, phase and other parameters of the electrical signal, precise control of particles can be achieved in the same acoustic transducer module. At the same time, the acoustic parameters can be changed according to the spatial structure of the target tissue model, so that the spatial feature distribution of the in vitro model is highly close to the real situation in vivo, thereby better simulating the in vivo environment.

[0022] 2. Traditional cell 3D printing typically employs a point-by-point printing and layer-by-layer stacking approach. Printing different cell types requires changing printheads or cleaning channels, making the process cumbersome and difficult to achieve precise interweaving and arrangement of multiple cells on the same plane and at the same time. This invention utilizes the one-time forming capability of acoustic standing wave fields to simultaneously inject suspensions of different target cells into multi-channel microcavities. Under the action of the multi-channel microcavities and acoustic radiation force, different cells are simultaneously arranged to specific positions of the acoustic wave nodes, constructing a multi-component heterogeneous cell fiber structure in one step, achieving synchronous manipulation and spatial assembly of multiple cell types.

[0023] 3. To address the issue of low-affinity cells easily displacing from acoustic pressure nodes, this invention introduces a low-temperature sensitive hydrogel matrix before acoustic forceps manipulation. This allows cells to maintain their fibrous structure after the acoustic field is removed, supporting long-term in vitro culture. Cells subjected to surface acoustic waves are more likely to form biomimetic tissue structures, thus more accurately mimicking the in vivo microenvironment. The addition of hydrogel allows the cells to maintain their orderly arrangement after the acoustic field disappears and enables the complete removal of the constructed cell-gel hybrid structure from the multi-channel microchamber, facilitating long-term culture experiments and providing a possibility for subsequent in vivo implantation.

[0024] 4. This invention, by adjusting the frequency, power, and phase of the input electrical signal, can precisely change the position and number of nodes and anti-nodes in the acoustic standing wave field. Combined with corresponding multi-channel microcavities, it can flexibly control the number, spacing, and arrangement of cell fibers. This approach avoids the problem of traditional microfluidic technology, which relies on channel structures and fluid shear forces to control cell position, resulting in only a single cell layer or simple single-cell flow.

[0025] 5. This invention utilizes acoustic radiation to manipulate cells, a non-contact, label-free method with gentle mechanical effects and minimal impact on cell activity and function. It avoids damage to cell viability and activity caused by high shear forces from the nozzle, mechanical compression, or potential contamination during the printing process.

[0026] In the field of traditional cell 3D printing, the point-by-point printing and layer-by-layer stacking working mode is not only cumbersome to operate, but also unable to achieve precise, synchronous arrangement of multiple cell types on the same plane, easily resulting in misalignment and low efficiency. Compared with existing technologies in cell manipulation and biomimetic construction, this invention achieves a breakthrough in the construction of complex spatial dimensions. Relying on the one-time forming capability of acoustic standing wave fields, multiple types of target cell suspensions can be simultaneously injected into multi-channel microcavities. Through acoustic radiation force, the cells are precisely arranged to acoustic wave nodes according to their physical characteristics, forming a multi-component heterogeneous cell fiber structure in one step. In terms of traditional microfluidic technology, it relies on channel structure and fluid shear force to control cell position, which can only form a single cell layer or a simple single-cell flow, making it difficult to meet the needs of complex tissue construction. This invention can precisely adjust the position and number of acoustic standing wave field nodes / anti-nodes by regulating the input electrical signal parameters, effectively controlling the number, spacing, and arrangement pattern of cell fibers. In addition, this invention, based on the non-contact, label-free manipulation method of acoustic radiation force, has a gentle mechanical effect and can significantly improve cell activity and viability.

[0027] This invention offers a novel solution to problems in the field of bioengineering. By optimizing acoustic signal parameters and hydrogel composition, it improves the adaptability and assembly precision of multi-cell systems, meeting the needs of constructing complex biomimetic tissues such as micro-organs and in vitro barrier models. Simultaneously, this invention deeply integrates acoustic tweezers cell manipulation technology with microfluidic chips, laying the technological foundation for constructing in vitro biomimetic models with dynamic fluid circulation and multi-organ interaction functions. In the future, it can provide a high-precision experimental platform for drug toxicity assessment and disease mechanism research. Attached Figure Description

[0028] Figure 1 A diagram of the combined device for constructing multi-component heterogeneous fiber structures with acoustic tweezers provided in this application example; Figure 2 An exploded view of the acoustic transducer module in the combined device diagram of the acoustic tweezers-assisted construction of a multi-component heterogeneous fiber structure provided in this application example; Figures 3 to 7 A schematic diagram of the linear arrangement of heterogeneous biological particles formed by the acoustic tweezers-assisted construction device for constructing a multi-component heterogeneous fiber structure provided in this application example; Figure 8 A diagram of a three-channel, multi-channel microchamber for an acoustic tweezers-assisted construction device for a multi-component heterogeneous fiber structure provided in this application example.

[0029] Figure 9A diagram of a five-channel multi-channel microchamber for an acoustic tweezers-assisted device for constructing multi-component heterogeneous fiber structures, provided in this application example.

[0030] In the diagram: 1. Acoustic transducer module; 2. Control circuit board; 3. Base; 4. Piezoelectric substrate; 5. Interdigitated electrode; 6. Multi-channel microchamber; 7. PCB board; 8. RF interface; 9. Spring pin; 10. Bolt; 11. Groove; 12. Square through slot; 13. Stepper motor; 14. Injector; 15. Connecting tube; 16. Curing unit. Detailed Implementation

[0031] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them. All other embodiments obtained by those skilled in the art based on the embodiments of this application without creative effort are within the scope of protection of this application.

[0032] like Figure 2 As shown in the exploded view, the acoustic tweezers unit of the device for constructing multi-component heterogeneous fiber structures using acoustic tweezers according to the present invention includes three parts: an acoustic transducer module 1, a control circuit board 2, and a base 3. The base 3 of the device is detachably connected to both the control circuit board 2 and the acoustic transducer module 1. The control circuit board 2 and the acoustic transducer module 1 are connected by metal spring pins, and the control circuit board 2 and the base 3 are connected by bolts 10.

[0033] The base 3 has grooves of matching size and shape to the control circuit board 2 and the acoustic transducer module 1, used to restrict the position of the control circuit board 2 and the acoustic transducer module 1. The groove 11 in the center of the base 3 allows for the replacement of different acoustic transducer modules as needed. A square through slot 12 in the center of the groove 11 is used for observation with a microscope during experimental research, facilitating real-time observation of the fiber structure formation process in subsequent experimental studies. The base 3 can be made of aluminum plate or 3D printed.

[0034] The acoustic transducer module 1 consists of three parts: a piezoelectric substrate 4, a pair of opposing interdigital electrodes 5, and a multi-channel microcavity 6. The interdigital electrodes 5 are bonded to the piezoelectric material substrate 4 using magnetron sputtering technology.

[0035] The multi-channel microchamber 6 is an inverted mold created using an SU-8 mold. The prepared PDMS solution is poured into the mold of the multi-channel microchamber 6, and heating for one hour yields a PDMS multi-channel microchamber 6 with a complex structure. The multi-channel microchamber 6 is bonded to the piezoelectric substrate 4 via oxygen plasma bonding, allowing the cell suspension to form patterns within the multi-channel microchamber 6. This multi-channel microchamber 6 is designed with multiple independent inlets, allowing different types of cell suspensions to be connected via tubing according to the target cell pattern requirements. The flow rate is controlled by a fluid drive unit, and the micro-vibration of the piezoelectric substrate 4 assists in cell arrangement, ultimately enabling different cells to form stable patterns within the multi-channel microchamber 6 according to a preset ratio, meeting the needs of cell culture and detection.

[0036] The acoustic transducer module 1 can perform linear alignment of cells, promoting the efficient formation of multi-component heterogeneous fiber structures. By changing the parameters of the input electrical signal, the characteristics of the multi-component heterogeneous fiber structure can be changed: changing the amplitude can control the realization time of cell patterning, changing the frequency can change the spacing between cell strips, and changing the phase can control the overall horizontal movement of cell strips.

[0037] The control circuit board 2 integrates an RF interface 8 and metal spring pins 9, which are connected to the PCB board 7 by soldering. The RF interface 8 connects to a signal source. The signal received by each RF interface 8 can be applied to one or more interdigital electrodes 5 according to the configuration of the acoustic transducer module 1.

[0038] like Figure 1 The figure shown is an overall assembly diagram of the device of the present invention. Figure 2 The acoustic tweezers unit, the fluid drive unit, and the curing unit were assembled together.

[0039] Example 1: Acoustic tweezers-assisted construction of single-strip (N=1) structural fibers In this implementation, both three-inlet and five-inlet multi-channel microchambers can be used to construct single-strip fiber structures. 10-micrometer polystyrene microspheres are used to simulate cells. The multi-channel microchamber is bonded to a piezoelectric substrate, with the current-stabilizing region positioned between the interdigitated electrodes during bonding, allowing acoustic waves to act on it. After forming strips in the current-stabilizing region, the particles enter the integration region and are cured into hydrogel fibers under UV light at the outlet. Using a three-inlet multi-channel microchamber with a width of 450 μm and interdigitated electrodes at a frequency of 13 MHz, theoretically, three particle strips can be formed within the chamber. After connecting the acoustic tweezers device, inlet 1 of the multi-channel microchamber is connected to a syringe loaded with water (particle-free liquid), and inlet 2 is connected to a syringe loaded with biological particles. Liquid is injected into the multi-channel microchamber at a rate of 1 μL / min. Without an acoustic field, under the influence of the liquid flow, the particle stream is compressed by the laminar flow on both sides, forming a relatively wide (140 μm) particle strip, as shown in Figure 3. After the acoustic tweezers are activated, the particles are compressed into particle strips with a width of approximately 78 μm in the steady-flow region, as shown in the image. Figure 4 As shown.

[0040] When using a five-inlet channel, water can be introduced into inlet 1 and inlet 2, and then the particle mixture can be introduced into inlet 3, thus forming a single particle band within the five-inlet channel. A narrower particle band increases the probability of contact between cells, significantly reducing cell interactions and the time required for later differentiation and fusion.

[0041] Example 2: Acoustic tweezers-assisted construction of multi-strip fiber structures Three-band (N=3) arrangement: A three-inlet multi-channel microchamber, 450 μm wide, is used, theoretically capable of forming three particle bands within the chamber. Inlet 1 and inlet 2 of the multi-channel microchamber are both connected to a syringe loaded with bioparticles. After the liquid flows into the steady-flow zone of the multi-channel microchamber, acoustic tweezers are activated, forming three particle bands within the integration zone, as shown in Figure 5. If the solution flowing into inlet 1 is replaced with other bioparticles, alternating A / B / A phase particle bands can be formed.

[0042] Five-band (N=5) arrangement: Using a five-inlet multi-channel microchamber with a channel width of 750 μm and interdigitated electrodes at a frequency of 13 MHz, theoretically, five particle bands can be formed within the chamber. Inlet 1, inlet 2, and inlet 3 of the multi-channel microchamber are all connected to a syringe loaded with biological particles. After liquid flows into the chamber, acoustic tweezers are activated, forming five particle bands within the chamber, as shown in Figure 6. Single-band and three-band arrangements can also be achieved using the five-inlet multi-channel microchamber. The types and arrangements of cells to be introduced can be freely combined according to the cell model to be constructed, as shown in Figure 7.

[0043] The method for constructing multi-component heterogeneous fiber structures using acoustic tweezers provided by this invention can utilize the nodal effect of acoustic waves to precisely push cells from different entry points to predetermined positions, thereby forming a more regular, compact, and periodic arrangement. This represents an active microfluidic manipulation upgrade to "passive laminar flow stratification." The lubricated and modified PDMS channels exhibit enhanced biocompatibility, avoiding the problem of multi-channel microchamber blockage. The addition of hydrogel facilitates transfer after fibrosis. This invention can construct fiber structures with different spatial distribution states by changing acoustic wave parameters and the types of cells introduced, further enabling the formation of complex and precise in vitro tissue models. This provides a label-free, highly biocompatible physical control strategy for building miniature, high-precision biomimetic experimental platforms. Furthermore, it can also provide insights for the development of microfluidic chips in interdisciplinary fields such as tissue engineering, drug screening, disease mechanism analysis, and life sciences.

[0044] While the above describes specific embodiments of the present invention, the scope of protection of the present invention is not limited thereto. Any modifications or substitutions made by those skilled in the art within the scope of the technology disclosed in this invention should be considered to fall within the scope of protection of this invention.

[0045] Finally, it should be noted that the scope of protection of this application is not limited to the applications and technical solutions disclosed in the embodiments. Any person skilled in the art can make appropriate changes and substitutions within the scope of the technology disclosed in this application, according to specific application needs and environmental conditions. These possible changes and substitutions, including but not limited to the selection of materials, adjustment of structure, expansion of function, and integration with other technologies, should all be considered as part of the scope of protection of this application.

Claims

1. A method for constructing a multi-component heterofiber structure with the aid of acoustic tweezers, characterized by, It comprises the following steps: S1, using low temperature sensitive hydrogel is mixed with the target model required cell suspension respectively according to 1:1 ratio, a plurality of groups of cell mixed solution is obtained, and is loaded into 1 mL syringe respectively; S2, Pluronic F127 modification liquid is uniformly passed into the multi-channel microcavity (6) of the acoustic tweezer assisted multi-component heterogeneous fiber structure device, and lasts for 1h, so as to reduce cell adhesion; S3, according to the set target model, the syringe (14) loaded with different cell mixed solution is connected with the different inlet of the multi-channel microcavity (6) through the connecting pipe (15); S4, the cell mixed solution is uniformly passed into the multi-channel microcavity (6) of the acoustic tweezer assisted multi-component heterogeneous fiber structure device by using the fluid driving module; S5, the input power of the acoustic wave transducer module (1) in the acoustic tweezer assisted multi-component heterogeneous fiber structure device is greater than 0dBm and less than or equal to 25 dBm; after the signal is turned on, the acoustic wave transducer module (1) can control the formation of a plurality of one-dimensional cell linear patterns arranged alternately in the multi-channel microcavity (6); then the tail of the multi-channel microcavity (6) is irradiated by using the solidification unit (16), so that the cell mixed solution is solidified; S6, after solidification, the mixed solution colloid is extruded along the outlet of the multi-channel microcavity (6) to form a multi-component heterogeneous fiber, the fiber is placed in a culture dish, and the corresponding culture medium is added according to the required cell model to culture.

2. The method of claim 1, wherein: The acoustic tweezer assisted multi-component heterogeneous fiber structure device comprises an acoustic tweezer unit, a fluid driving unit and a solidification unit; The acoustic tweezer unit comprises an acoustic wave transducer module (1), a control circuit board (2) and a base (3); The acoustic wave transducer module (1) comprises a piezoelectric substrate (4), a pair of opposite interdigital electrodes (5) and a multi-channel microcavity (6); the multi-channel microcavity (6) is arranged in the middle of the pair of opposite interdigital electrodes (5); the control circuit board (2) comprises a PCB board (7), a radio frequency interface (8) and a metal spring needle (9); the base (3) has a groove (11) in the center, which is used for limiting the acoustic wave transducer module (1) and the control circuit board (2), and a square through slot (12) is used for observation; the base (3) is fixed with the acoustic wave transducer module (1) and the control circuit board (2) by using bolts (10). The piezoelectric substrate (4) and the interdigital electrode (5) are combined in a magnetron sputtering manner; the piezoelectric substrate (4) and the multi-channel microcavity (6) are combined in an oxygen plasma bonding manner.

3. The method of claim 1, wherein: The fluid driving module comprises a power source and a displacement execution mechanism; The power source is a stepping motor (13), and the displacement execution mechanism is a syringe (14) connected with the stepping motor screw; the syringe (14) is connected with the multi-channel microcavity (6) through the connecting pipe (15).

4. The method of claim 1, wherein: The multi-channel microcavity (6) is provided with a steady flow area and an integration area; the cells are linearly arranged in the steady flow area and then enter the integration area; the width of the steady flow area and the integration area is an integer multiple of the half wavelength of the input acoustic wave; the number of inlets of the multi-channel microcavity (6) is adjusted according to the cell model to be constructed.

5. The method of claim 1, wherein: The front end of the multi-channel micro-chamber (6) has a steady flow area, and the interdigital electrodes (5) are arranged on both sides of the steady flow area, so that the cells in the steady flow area can be captured by the acoustic tweezers, and a linear pattern in a regular arrangement is formed, and then the structure is maintained to enter the integration area of the multi-channel micro-chamber (6).

6. The method of claim 1, wherein: In the step S4, after the electric signal is turned on, two opposite interdigital electrodes (5) generate two rows of opposite traveling surface acoustic waves, and a standing wave is formed in the middle area of the interdigital electrode (5); when the surface acoustic wave propagates into the mixed liquid in the multi-channel micro-chamber (6), it is converted into a leak wave in the vertical direction, and then a pressure fluctuation in the medium is induced, which pushes the suspended cells in the medium to the node position or the anti-node position of the acoustic standing wave field, thereby forming a one-dimensional cell linear pattern.

7. The method of claim 1, wherein: The optimal concentration of the cell suspension in step S1 is 1 x 10 6 -5 x 10 6 cells / mL, below this concentration range, discontinuous linear patterns appear; and above this concentration range, the cells in each band adhere to each other.

8. The method of claim 1, wherein: In the step S1, the concentration of the low-temperature sensitive hydrogel is 5% (w / v) to 10% (w / v), and below the concentration, the low-temperature sensitive hydrogel cannot be solidified, and above the concentration, the hardness of the solidified hydrogel is too high, so that the cells cannot be extended in the interior.

9. The method of claim 1, wherein: In the step S5, the solidification unit (16) is an ultraviolet light source with a wavelength of 365-395 nm, and the use power is 10 mW; the solidification unit (16) is placed at a position more than 1 cm away from the tail end of the multi-channel micro-chamber (6), so as to prevent the light source from irradiating the whole multi-channel micro-chamber (6).

10. The method of claim 1, wherein: When the multi-component heterogeneous fiber structure pattern is formed, the signal parameters input by the two opposite interdigital electrodes (5) are the same.

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