A microfluidic handling platform for the synthesis of mrna lipid nanoparticles

Abstract

The utility model belongs to biological preparation equipment technical field especially for a kind of microfluidic control platform for synthesizing mRNA lipid nano-particle, including microfluidic chip main part, the microfluidic chip main part includes: base, the top surface of base is equipped with mounting groove, end face is equipped with at least two liquid inlets;Top cover, top cover is detachably fixed in mounting groove, and intercommunication flow channel is equipped on the opposite face of base and top cover, and one end of flow channel is communicated with the liquid inlet;Further include: micro turbine flowmeter, the liquid outlet of micro turbine flowmeter is connected with the liquid inlet;Micro electromagnetic valve;In the utility model, through detachable design, reduce processing cost, it is convenient to passageway cleaning, through micro turbine flowmeter and micro electromagnetic valve precision control flow rate, through flow channel structure optimization improves mixing efficiency, solve the problem of high cost, cleaning difficult of traditional microfluidic chip, avoid the cross infection problem caused by uneven channel cleaning of traditional integrated chip.

Description

Technical Field

[0001] This invention belongs to the field of biological agent equipment technology, specifically relating to a microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles. Background Technology

[0002] Besides inactivated antigens, a large portion of vaccine drugs are mRNA vaccines. These mRNA vaccines work by transcribing mRNA in the human body to produce immunogenic target proteins, thereby preventing or treating various diseases.

[0003] The preparation process of mRNA drugs is roughly as follows: First, Escherichia coli is cultured as a vector, and then concentrated through a hollow fiber column to obtain a high concentration of E. coli culture. Next, the stock solution is obtained through fermentation, alkaline lysis, filtration and clarification. The stock solution is then purified by chromatography to obtain a plasmid DNA template. The template is digested with enzymes and transcribed in vitro to obtain mRNA. Finally, the mRNA is encapsulated using lipid nanoparticle (LNP) technology to obtain the mRNA vaccine product.

[0004] LNP-mRNA is prepared by mixing ionizable cationic lipids, phospholipids, cholesterol, and PEG lipids with mRNA using microfluidic technology to form stable and highly efficient delivery nanoparticles.

[0005] Currently, the most common method for preparing LNPs in mRNA vaccines is microfluidic mixing or rapid liquid-phase mixing. The core principle is to achieve rapid turbulent mixing of the lipid organic phase (such as lipids dissolved in ethanol) and the aqueous phase (buffer solution containing mRNA) by controlling the liquid flow rate, and to utilize the self-assembly of lipids in the aqueous phase to form nanoparticles.

[0006] Among them, microfluidic technology is used in the production and preparation of mRNA lipid nanoparticles because of its precise control of fluid mixing and reaction conditions. Microfluidic chips are a technology platform that enables precise control of micro-volume fluids (usually nanoliters to microliters) through micrometer-level channel networks.

[0007] Traditional microfluidic chips are based on an integrated design and rely on silicon / glass materials and photolithography. They are suitable for laboratory research with high precision requirements but fixed scenarios. However, as microfluidic technology shifts from laboratory research to clinical testing and industrial applications, the requirements for flexibility, maintainability and cost control have increased significantly. The integrated design of microfluidic chips has a high processing cost, and for microfluidic chips that are used repeatedly, insufficient channel cleaning can easily lead to cross-contamination of materials.

[0008] To address the aforementioned issues, this application proposes a microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles. Utility Model Content

[0009] To address the aforementioned problems in the existing technology, this invention provides a microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles, which is convenient to use, has low processing cost, and is easy to clean.

[0010] To achieve the above objectives, this utility model provides the following technical solution: a microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles, comprising a microfluidic chip body, wherein the microfluidic chip body includes:

[0011] The substrate has a mounting groove on its top surface and at least two liquid inlets on its end face;

[0012] A top cover, detachably fixed within the mounting groove, and having interconnected flow channels on opposite surfaces of the base and the top cover, one end of which communicates with the liquid inlet; further comprising:

[0013] A miniature turbine flow meter, wherein the outlet end of the miniature turbine flow meter is connected to the inlet;

[0014] A miniature solenoid valve, wherein the outlet end of the miniature solenoid valve is connected to the inlet end of the miniature turbine flow meter.

[0015] Preferably, the miniature solenoid valve comprises:

[0016] A liquid inlet channel, wherein the liquid inlet end of the liquid inlet channel is connected to the liquid inlet port;

[0017] The Y-shaped manifold has two inlet ends and one outlet end, and the two inlet ends of the Y-shaped manifold are respectively connected to the outlet ends of the two inlet channels.

[0018] A premixing channel, wherein the inlet end of the premixing channel is connected to the outlet end of the Y-shaped manifold.

[0019] Preferably, the inner diameter of the Y-shaped manifold is smaller than the inner diameter of the liquid inlet channel, and there is a frustum-shaped transition between the liquid inlet channel and the Y-shaped manifold.

[0020] Preferably, the premixed channel has an "S" shaped channel structure.

[0021] Preferably, the device further includes a fixing mechanism, wherein the top cover is fixed to the mounting groove by the fixing mechanism, and wherein the fixing mechanism includes:

[0022] A positioning screw is fixed in the mounting groove, and a positioning hole is provided on the top cover for the positioning screw to pass through.

[0023] A locking nut is installed on the protruding end of the positioning screw by means of thread engagement.

[0024] Preferably, the positioning screws are symmetrically distributed in two groups, and there are two positioning screws in the same group.

[0025] Preferably, it further includes:

[0026] A rubber sealing gasket is bonded and fixed to the inner bottom surface of the mounting groove.

[0027] Preferably, it further includes:

[0028] The sealing screw has an injection hole on the top cover that communicates with the liquid inlet channel, and the injection hole has an internal thread. The sealing screw is installed in the injection hole by thread engagement.

[0029] Compared with the prior art, the beneficial effects of this utility model are:

[0030] This invention reduces processing costs and facilitates channel cleaning through a detachable design, precisely controls flow rate through a micro turbine flow meter and a micro solenoid valve, and improves mixing efficiency through optimized flow channel structure. It solves the problems of high cost and difficult cleaning of traditional microfluidic chips and avoids cross-contamination caused by uneven channel cleaning in traditional integrated chips.

[0031] Other additional advantages and benefits of this application will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of this application. Attached Figure Description

[0032] The accompanying drawings are provided to further illustrate the present invention and form part of the specification. They are used together with the embodiments of the present invention to explain the present invention, but do not constitute a limitation thereof. In the drawings:

[0033] Figure 1 This is a schematic diagram of the structure of this utility model;

[0034] Figure 2 This is a schematic diagram of the base axonometric structure in this utility model;

[0035] Figure 3 This utility model Figure 1 Enlarged schematic diagram of the fixed mechanism in the diagram;

[0036] Figure 4 This utility model Figure 2 Enlarged structural diagram at point A in the diagram;

[0037] Figure 5 This is a partial cross-sectional view of the top cover in this utility model.

[0038] In the diagram: 1. Microfluidic chip body; 11. Substrate; 111. Mounting groove; 112. Liquid inlet; 12. Top cover; 121. Positioning hole; 122. Injection hole; 13. Flow channel; 131. Liquid inlet channel; 132. Y-shaped manifold channel; 133. Premixing channel; 134. Transition section; 2. Miniature turbine flow meter; 3. Miniature solenoid valve; 4. Fixing mechanism; 41. Positioning screw; 42. Locking nut; 5. Rubber sealing gasket; 6. Sealing screw. Detailed Implementation

[0039] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of the present utility model.

[0040] Please see Figures 1-5 The present invention provides the following technical solution: a microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles, comprising a microfluidic chip body 1, the microfluidic chip body 1 comprising: a substrate 11 and a top cover 12, and further comprising: a micro turbine flow meter 2 and a micro solenoid valve 3.

[0041] Furthermore, by Figure 1 , Figure 2 and Figure 5 As shown in this embodiment, the top surface of the substrate 11 is provided with an installation groove 111, and the end face is provided with at least two liquid inlets 112. The top cover 12 is detachably fixed in the installation groove 111, and a flow channel 13 is provided on the opposite surfaces of the substrate 11 and the top cover 12. One end of the flow channel 13 is connected to the liquid inlet 112. The outlet end of the micro turbine flow meter 2 is connected to the liquid inlet 112, and the outlet end of the micro solenoid valve 3 is connected to the inlet end of the micro turbine flow meter 2. With the above scheme, when in use, the lipid solution and mRNA solution to be mixed are first delivered to the inlet end of the micro solenoid valve 3 by an external injection pump. As the core component of fluid control, the micro solenoid valve 3 can be precisely adjusted by electrical signals to achieve preliminary control and on / off switching of the input volume of the two solutions.

[0042] When the miniature solenoid valve 3 is opened, fluid enters the miniature turbine flow meter 2. The turbine blades inside rotate under the push of the fluid. The rotation speed signal is converted into an electrical signal by the electromagnetic induction device. After being processed by the circuit, the signal is fed back to the external control system in real time, thereby accurately monitoring the current volumetric flow rate of the fluid.

[0043] After being metered by the micro turbine flow meter 2, the two solutions enter the flow channel 13 through at least two inlets 112 on the substrate 11.

[0044] Since the base 11 and the top cover 12 have interconnected flow channels 13 on their opposite surfaces, and the top cover 12 is detachably fixed in the mounting groove 111, a closed and stable microchannel environment is formed. In the microchannel, the two solutions are in a laminar flow state due to the small size of the flow channels (usually at the micrometer level), and preliminary mixing is achieved through diffusion. At this time, the external control system compares the flow data fed back by the micro turbine flow meter 2 in real time according to the preset mixing ratio parameters, and ensures that the two solutions are continuously input into the flow channel with a precise volume flow ratio by adjusting the opening of the micro solenoid valve 3.

[0045] As the fluid flows within the channel 13, components such as phospholipids in the lipid solution and mRNA form lipid nanoparticles through self-assembly under specific flow rates, flow ratios, and mixing conditions. Because the micron-scale channel 13 of the microfluidic chip body 1 has a huge specific surface area, it can effectively control the shear force and reaction time during the mixing process, thereby precisely regulating the particle size, distribution, and encapsulation efficiency of the lipid nanoparticles.

[0046] Throughout the entire operation, the synergistic effect of the micro turbine flow meter 2 and the micro solenoid valve 3 enables high-precision control of fluid input. The flow channel 13 structure inside the microfluidic chip body 1 provides an ideal microenvironment for the efficient mixing of lipids and mRNA and the synthesis of nanoparticles. The removable top cover 12 design facilitates the cleaning and maintenance of the internal flow channels of the chip, meeting the needs of different batch synthesis processes, thereby achieving controllable and efficient synthesis of mRNA lipid nanoparticles.

[0047] This invention reduces processing costs and facilitates cleaning of the flow channel 13 through a detachable design. It precisely controls the flow rate through a micro turbine flow meter 2 and a micro solenoid valve 3, and improves mixing efficiency through the optimized structure of the flow channel 13. It solves the problems of high cost and difficult cleaning of traditional microfluidic chips, and avoids the cross-contamination problem caused by uneven channel cleaning in traditional integrated chips.

[0048] Preferably, by Figure 1 , Figure 2 and Figure 5 As shown in this embodiment, the miniature solenoid valve 3 includes: an inlet channel 131, a Y-shaped manifold channel 132, and a premixing channel 133. The inlet end of the inlet channel 131 is connected to the inlet port 112. The Y-shaped manifold channel 132 has two inlet ends and one outlet end. The two inlet ends of the Y-shaped manifold channel 132 are respectively connected to the outlet ends of the two inlet channels 131. The inlet end of the premixing channel 133 is connected to the outlet end of the Y-shaped manifold channel 132. With the above scheme, when in use, the lipid solution and mRNA solution to be mixed are input from the two independent inlet ends of the miniature solenoid valve 3, and after being measured by the miniature turbine flow meter 2, they first enter their respective inlet channels 131.

[0049] After passing through the inlet channel 131, the two solutions enter from the two inlet ends of the Y-shaped confluence channel 132. The Y-shaped structure design allows the two fluids to converge at the confluence point at a symmetrical angle. This geometric configuration can avoid turbulence caused by excessive impact angle and enhance the interfacial contact area through the lateral compression effect between the fluids. At this time, the two fluids initially form a "layered" flow at the outlet end of the Y-shaped confluence channel 132. The lipid solution and the mRNA solution flow in parallel in the form of parallel thin layers, and molecular diffusion begins to occur at the interface, laying the foundation for subsequent mixing.

[0050] The confluenced layered fluids then enter the premixing channel 133, where they undergo preliminary diffusion and mixing.

[0051] Preferably, by Figure 1 , Figure 2 and Figure 4 As shown, in this embodiment, the inner diameter of the Y-shaped confluence channel 132 is smaller than the inner diameter of the inlet channel 131, and there is a frustum-shaped transition portion 134 between the inlet channel 131 and the Y-shaped confluence channel 132. With this design, during use, when the lipid solution and mRNA solution flow through the inlet channel 131 and are about to enter the Y-shaped confluence channel 132, the frustum-shaped transition portion 134 and the inner diameter difference design will simultaneously trigger precise regulation of the fluid dynamics characteristics.

[0052] First, since the inner diameter of the Y-shaped confluence channel 132 is smaller than the inner diameter of the inlet channel 131, the cross-sectional area of ​​the flow channel gradually decreases when the fluid enters the transition section 134. Under constant flow rate, the fluid velocity will increase linearly as the cross-sectional area decreases. This gradual velocity change is achieved through the smooth guidance of the frustum-shaped transition section 134, avoiding the turbulent vortex or bubble accumulation that may be caused by the traditional right-angle transition, and maintaining a stable laminar flow state.

[0053] Secondly, after the two fluids are accelerated by their respective frustum transition sections 134, they enter the two inlet ends of the Y-shaped confluence channel 132 symmetrically at a higher flow rate. At this time, because the inner diameter of the confluence channel is smaller, the distance between the flow cores of the two fluids is compressed, the interface contact area is significantly increased, and the shear force brought about by the flow rate difference is simultaneously increased, which makes the interface layer of the two solutions thinner, the molecular diffusion path is shortened, and the premixing efficiency is significantly improved.

[0054] Preferably, by Figure 1 and Figure 2As shown in this embodiment, the premixing channel 133 is an "S"-shaped channel structure. After adopting the above scheme, in the microfluidic laminar flow-dominated environment, the fluid originally only achieves slow mixing through molecular diffusion. However, the continuous tortuous design of the "S"-shaped premixing channel 133 induces Dean flow (Dean flow refers to the phenomenon in a tortuous channel where the fluid velocity is faster near the center of the channel and slower near the wall, resulting in a radial pressure gradient in the tortuous section, thus forming a secondary flow phenomenon, which is called Dean flow).

[0055] When the fluid flows through the curved section, the centrifugal force causes the fluid to generate double vortices on the cross-section of the premixing channel 133, forming a secondary flow perpendicular to the mainstream direction. This lateral disturbance will continuously "stretch and fold" the interface layer between the lipid solution and the mRNA solution, cutting the original layered distribution into a thinner and more complex interface, and the mixing efficiency will be significantly improved.

[0056] In addition, the "S"-shaped premixing channel 133 has a longer path, which can ensure that the fluid has enough residence time to complete premixing, and avoid excessive pressure loss caused by excessively long flow channels (because the pressure drop is greater in long straight channels).

[0057] Optionally, by Figure 1 and Figure 3 As shown, this embodiment further includes a fixing mechanism 4. The top cover 12 is fixed in the mounting groove 111 by the fixing mechanism 4. The fixing mechanism 4 includes a positioning screw 41 and a locking nut 42. The positioning screw 41 is fixed in the mounting groove 111. A positioning hole 121 is provided on the top cover 12 for the positioning screw 41 to pass through. The locking nut 42 is installed on the protruding end of the positioning screw 41 by thread engagement. With the above scheme, during use and installation, firstly, the positioning hole 121 of the top cover 12 is aligned with the positioning screw 41 in the mounting groove 111. Then, the top cover 12 is placed in the mounting groove 111. At this time, the positioning screw 41 passes through the positioning hole 121, accurately positioning the installation position of the top cover 12. Finally, the locking nut 42 is tightened at the protruding end of the positioning screw 41. The locking nut 42 moves downward along the axial direction of the positioning screw 41 under the thread engagement, and at the same time presses down on the top cover 12, so that the top cover 12 is tightly fitted with the base 11, ensuring the stability and sealing of the installation.

[0058] When it is necessary to disassemble the top cover 12 and the base 11, simply unscrew the locking nut 42 to facilitate the separation of the top cover 12 and the base 11, and to facilitate thorough cleaning of the flow channel 13.

[0059] Preferably, by Figure 1 and Figure 2As shown in this embodiment, there are two sets of symmetrically distributed positioning screws 41, and two positioning screws 41 in the same set are symmetrically distributed. After adopting the above scheme, when in use, the four positioning screws 41 make the force at each connection point between the top cover 12 and the base 11 uniform, avoid the tilting problem caused by uneven local force, and ensure the stability and sealing of the connection between the top cover 12 and the base 11.

[0060] Preferably, by Figure 1 and Figure 3 As shown, in this embodiment, it further includes a rubber sealing gasket 5, which is bonded and fixed to the inner bottom surface of the mounting groove 111. With the above solution, when the locking nut 42 is tightened, the locking nut 42 moves downward along the axial direction of the positioning screw 41 under the screwing action, and at the same time presses down the top cover 12. At this time, the rubber sealing gasket 5 shrinks, which further improves the sealing performance of the connection between the top cover 12 and the base 11.

[0061] Preferably, by Figure 1 , Figure 2 and Figure 5 As shown, in this embodiment, it further includes: a sealing screw 6, and an injection hole 122 communicating with the liquid inlet channel 131 is provided on the top cover 12, and the injection hole 122 has an internal thread. The sealing screw 6 is installed in the injection hole 122 by thread engagement. With the above solution, when it is necessary to flush the flow channel 13 during use, if it is not necessary to disassemble the top cover 12 and the base 11, the sealing screw 6 can be unscrewed, and cleaning agent can be injected into the flow channel 13 through the injection hole 122 to flush the flow channel 13.

[0062] It should be noted that both the miniature turbine flow meter 2 and the miniature solenoid valve 3 are commercially available conventional devices. Those skilled in the art can make conventional selections according to their needs. Their working principles are common knowledge known to those skilled in the art and have been fully disclosed in the prior art, so they will not be elaborated on further in this article.

[0063] The circuit connection involved in this utility model is a common method used by those skilled in the art, and technical inspiration can be obtained through a limited number of experiments. It belongs to the widely used prior art.

[0064] Components not described in detail in this article are existing technologies.

[0065] The working principle and usage process of this utility model: When using the microfluidic control platform of this utility model, the lipid solution and mRNA solution to be mixed are first delivered to the inlet end of the micro solenoid valve 3 by an external injection pump. As the core component of fluid control, the micro solenoid valve 3 can be precisely adjusted by electrical signals to achieve preliminary control and on / off switching of the input volume of the two solutions.

[0066] When the miniature solenoid valve 3 is opened, fluid enters the miniature turbine flow meter 2. The turbine blades inside rotate under the push of the fluid. The rotation speed signal is converted into an electrical signal by the electromagnetic induction device. After being processed by the circuit, the signal is fed back to the external control system in real time, thereby accurately monitoring the current volumetric flow rate of the fluid.

[0067] After being metered by the micro turbine flow meter 2, the two solutions enter the flow channel 13 through at least two inlets 112 on the substrate 11;

[0068] Since the base 11 and the top cover 12 have interconnected flow channels 13 on their opposite surfaces, and the top cover 12 is detachably fixed in the mounting groove 111, a closed and stable microchannel environment is formed. In the microchannel, the two solutions are in a laminar flow state due to the small size of the flow channels (usually at the micrometer level), and preliminary mixing is achieved through diffusion. At this time, the external control system compares the flow data fed back by the micro turbine flow meter 2 in real time according to the preset mixing ratio parameters, and adjusts the opening of the micro solenoid valve 3 to ensure that the two solutions are continuously input into the flow channel at a precise volume flow ratio.

[0069] As the fluid flows within the channel 13, components such as phospholipids in the lipid solution and mRNA form lipid nanoparticles through self-assembly under specific flow rates, flow ratios, and mixing conditions. Since the micron-scale channel 13 of the microfluidic chip body 1 has a huge specific surface area, it can effectively control the shear force and reaction time during the mixing process, thereby precisely regulating the particle size, distribution, and encapsulation efficiency of the lipid nanoparticles.

[0070] Throughout the entire operation, the synergistic effect of the micro turbine flow meter 2 and the micro solenoid valve 3 enables high-precision control of fluid input. The flow channel 13 structure inside the microfluidic chip body 1 provides an ideal microenvironment for the efficient mixing of lipids and mRNA and the synthesis of nanoparticles. The removable top cover 12 design facilitates the cleaning and maintenance of the internal flow channels of the chip, meeting the needs of different batch synthesis processes, thereby achieving controllable and efficient synthesis of mRNA lipid nanoparticles.

[0071] This invention reduces processing costs and facilitates cleaning of the flow channel 13 through a detachable design. It precisely controls the flow rate through a micro turbine flow meter 2 and a micro solenoid valve 3, and improves mixing efficiency through the optimized structure of the flow channel 13. It solves the problems of high cost and difficult cleaning of traditional microfluidic chips, and avoids the cross-contamination problem caused by uneven channel cleaning in traditional integrated chips.

[0072] Finally, it should be noted that the above description is merely a preferred embodiment of this utility model and is not intended to limit the utility model. Although the utility model has been described in detail with reference to the foregoing embodiments, those skilled in the art can still modify the technical solutions described in the foregoing embodiments or make equivalent substitutions for some of the technical features. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this utility model should be included within the protection scope of this utility model.

Claims

1. A microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles, comprising a microfluidic chip body (1), characterized in that, The microfluidic chip body (1) includes: The base (11) has a mounting groove (111) on its top surface and at least two liquid inlets (112) on its end face; A top cover (12), which is detachably fixed in the mounting groove (111), and a communicating flow channel (13) is provided on the opposite surfaces of the base (11) and the top cover (12), one end of which communicates with the liquid inlet (112); It also includes: A miniature turbine flow meter (2), the outlet end of which is connected to the inlet (112); A miniature solenoid valve (3) is provided, with its outlet end connected to the inlet end of the miniature turbine flow meter (2).

2. The microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles according to claim 1, characterized in that: The miniature solenoid valve (3) includes: Liquid inlet channel (131), the liquid inlet end of which is connected to the mounting groove (111); Y-shaped manifold (132), the Y-shaped manifold (132) has two liquid inlet ends and one liquid outlet end, and the two liquid inlet ends of the Y-shaped manifold (132) are respectively connected to the liquid outlet ends of the two liquid inlet channels (131); A premixing channel (133) is provided, the inlet end of which is connected to the outlet end of the Y-shaped manifold channel (132).

3. The microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles according to claim 2, characterized in that: The inner diameter of the Y-shaped manifold (132) is smaller than the inner diameter of the liquid inlet channel (131), and there is a frustum-shaped transition portion (134) between the liquid inlet channel (131) and the Y-shaped manifold (132).

4. The microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles according to claim 2, characterized in that: The premixed channel (133) has an "S" shaped channel structure.

5. The microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles according to claim 1, characterized in that: The top cover (12) is further included in a fixing mechanism (4), wherein the fixing mechanism (4) is fixed to the mounting groove (111), and wherein the fixing mechanism (4) includes: A positioning screw (41) is fixed in the mounting groove (111), and a positioning hole (121) is provided on the top cover (12) for the positioning screw (41) to pass through. A locking nut (42) is installed on the protruding end of the positioning screw (41) by means of thread engagement.

6. The microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles according to claim 5, characterized in that: The positioning screws (41) are symmetrically distributed in two groups, and there are two positioning screws (41) in the same group.

7. The microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles according to claim 1, characterized in that: Further includes: A rubber sealing gasket (5) is bonded and fixed to the inner bottom surface of the mounting groove (111).

8. The microfluidic manipulation platform for synthesizing mRNA lipid nanoparticles according to claim 2, characterized in that: Further includes: The sealing screw (6) has an injection hole (122) on the top cover (12) that communicates with the liquid inlet channel (131), and the injection hole (122) has an internal thread. The sealing screw (6) is installed in the injection hole (122) by thread engagement.

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