Cell pumping mechanism and droplet microfluidic sorter

Abstract

The utility model relates to the technical field of micro-droplet sorting, and discloses a cell pumping mechanism and a droplet microfluidic sorter. The cell pumping mechanism provided by the utility model comprises a turncap, a first channel used for circulating cell suspension and a second channel used for circulating gas are formed on the turncap; the liquid containing assembly is used for containing cell suspension, and the liquid containing assembly is communicated with the first channel and the second channel respectively; the pneumatic connector is arranged on the turncap and communicated with the second channel, the pneumatic connector introduces gas into the liquid loading assembly through the second channel, and the cell suspension is pumped into the first channel; the uniform mixing assembly is in transmission connection with the turncap, and the turncap is rotated by the uniform mixing assembly. The liquid drop micro-fluidic sorter disclosed by the utility model comprises the cell pumping mechanism. The utility model solves the problem that the cells are easy to agglomerate and precipitate during pumping, and realizes the technical effect of uniformly conveying the cells.

Description

Technical Field

[0001] This utility model belongs to the field of microdroplet sorting technology, specifically relating to a cell pumping mechanism and a droplet microfluidic sorting instrument. Background Technology

[0002] Microdroplet sorting technology is a high-throughput screening method based on droplet microfluidics. By encapsulating single cells or molecules in microdroplets at the piculum level and combining fluorescence detection with sorting mechanisms, it achieves efficient screening and analysis of target cells or molecules. Due to its high throughput, low consumption and high precision, it has broad application prospects in biomedical research, drug screening and environmental monitoring.

[0003] Cell sorting is typically performed using a droplet microfluidic sorter, which mainly consists of a liquid-driven mechanism for delivering the cell suspension. This mechanism injects the cell suspension into a microdroplet chip, where the cells are encapsulated by the droplets, which act as miniature reactors for the cells. Currently, the liquid-driven mechanism is usually a microsyringe, which is used by researchers to manually inject the cell suspension.

[0004] However, during the process of the microinjector propelling the cell suspension into the microdroplet chip, the cells are prone to uneven dispersion and aggregation, making it difficult to pump the aggregated cells into the microdroplet chip at the set speed. Summary of the Invention

[0005] To address the shortcomings of the prior art, this invention provides a cell pumping mechanism and a droplet microfluidic sorter. The mixing component rotates the cap to disperse the cells in the channel, and the pneumatic connector pumps the cells uniformly through air pressure, which helps to solve the problems of cell aggregation and precipitation, and achieves uniform cell delivery.

[0006] The technical effects to be achieved by this utility model are realized through the following technical aspects:

[0007] In a first aspect, this utility model provides a cell pumping mechanism, including a cap forming a first channel for circulating cell suspension and a second channel for gas circulation; a liquid-filling assembly for holding the cell suspension, the liquid-filling assembly being connected to the first channel and the second channel respectively; a pneumatic connector disposed on the cap and connected to the second channel, the pneumatic connector introducing gas into the liquid-filling assembly through the second channel, the cell suspension being pumped into the first channel; and a mixing assembly drivingly connected to the cap, the mixing assembly rotating the cap.

[0008] In some implementations, the cap has an inlet and an outlet, wherein the inlet and the outlet are connected through the first channel, the inlet is connected to the second channel, and the liquid filling assembly is located at the inlet; the diameter of the inlet is larger than the diameter of the outlet.

[0009] In some implementations, the cap is provided with an output component at the output port for the outflow of cell suspension, and the output component is connected to the first channel.

[0010] In some implementations, the output component includes an output connector inserted into the output port, the output connector being detachably connected to the cap; and an inverted conical connector, one end of which is inserted into the output connector and the other end of which is sealed to the output port, wherein the cell suspension in the first channel flows sequentially through the inverted conical connector and the output connector.

[0011] In some implementations, the cap has an abutment platform inside, and both the first channel and the second channel are located on the abutment platform. The liquid filling assembly is sealed to the cap at the abutment platform.

[0012] In some implementations, the liquid-filling assembly includes a container for holding a cell suspension, the container being connected to the first channel and the second channel respectively; and an adapter sleeved on the outside of the container and fixing the container, the adapter being detachably connected to the cap and sealingly connected to the cap.

[0013] In some implementations, a first gasket is provided between the abutment platform and the adapter.

[0014] In some implementations, the mixing assembly includes a rotating plate with the rotating cap disposed on the rotating plate; and a driving member, which is throttle connected to the rotating plate and drives the rotating plate to rotate.

[0015] In some implementations, the cap has an aerodynamic hole on one side of the cell suspension in the pumping direction within the first channel, the aerodynamic hole is connected to the second channel, and the aerodynamic connector is located at the aerodynamic hole.

[0016] Secondly, this utility model provides a droplet microfluidic sorting device, including the cell pumping mechanism described above.

[0017] In summary, this utility model has at least the following advantages:

[0018] 1. The cell pumping mechanism provided by this utility model includes a liquid-filling assembly that holds a cell suspension. During pumping, a pneumatic connector first introduces compressed gas into the second channel, and by adjusting the pressure, different stable gas pressures are generated. After the gas enters the liquid-filling assembly through the second channel, it pushes the cell suspension to uniformly pump the cells into the first channel, and then transports them along the first channel to the microdroplet chip for sorting. Simultaneously with the pneumatic connector introducing gas to pump the cells, the mixing assembly rotates its cap. This rotation of the cap causes the cell suspension to shake evenly, allowing for the uniform dispersion of agglomerated cells. This effectively solves the problem of cell agglomeration, which makes it difficult for the micro-injector to pump cells at the set speed when infusing cells into the microdroplet chip using traditional micro-injectors.

[0019] 2. The droplet microfluidic sorter provided by this utility model disperses and uniformly pumps cells through a cell pumping mechanism, which helps to reduce the influence of cell aggregates on droplet generation or sorting signals, improves sorting efficiency, and the uniform flow rate helps to reduce the risk of cell damage caused by pumping. Attached Figure Description

[0020] Figure 1 This is a schematic diagram of the overall structure of a cell pumping mechanism according to a specific embodiment of the present invention.

[0021] Figure 2 This is a schematic diagram of the structure of the rotating cap according to a specific embodiment of the present utility model.

[0022] Figure 3 for Figure 2 A structural diagram from another angle.

[0023] Figure 4 This is a schematic diagram of the output component in a specific embodiment of the present invention.

[0024] Figure 5 This is a front view of the output component of a specific embodiment of the present utility model.

[0025] Figure 6 for Figure 5 A schematic diagram of the AA section.

[0026] Figure 7 This is a front view of the liquid-filling assembly according to a specific embodiment of the present invention.

[0027] Figure 8 for Figure 7 Schematic diagram of the BB section.

[0028] Figure 9 This is a schematic diagram of the mixing component according to a specific embodiment of the present invention.

[0029] Marked in the image:

[0030] 1. Rotary cap; 11. First channel; 12. Second channel; 13. Inlet; 14. Outlet; 15. Abutment platform; 16. Pneumatic port;

[0031] 2. Liquid filling assembly; 21. Container; 22. Adapter; 221. Hole; 222. Pressing end; 23. First gasket;

[0032] 3. Pneumatic connector;

[0033] 4. Mixing component; 41. Rotating plate; 411. Locking position; 42. Driving component; 43. Partition plate; 44. Sensor;

[0034] 5. Output component; 51. Output connector; 52. Inverted conical connector; 53. Second gasket; 54. Infusion tubing. Detailed Implementation

[0035] To make the objectives, technical solutions, and advantages of the embodiments of this utility model clearer, the technical solutions of the embodiments of this utility model will be clearly and completely described below with reference to the accompanying drawings. The described embodiments are only some embodiments of this utility model, not all embodiments.

[0036] Therefore, the following detailed description of the embodiments of the present invention provided in the accompanying drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without inventive effort are within the scope of protection of the present invention.

[0037] Example 1:

[0038] Please see Figures 1-3 The cell pumping mechanism of this invention can be used in cell separation, sorting or dispensing equipment, especially in droplet microfluidic sorters. It can uniformly disperse and pump cells, which helps to improve the impact of cell aggregation and precipitation on microdroplet sorting operations.

[0039] Please see Figure 1 and Figure 2 The cell pumping mechanism of this invention includes a first channel 11 for circulating cell suspension and a second channel 12 for circulating gas formed inside the cap 1. In some specific embodiments, the first channel 11 and the second channel 12 are arranged in parallel and isolated from each other. The cap 1 has independent channels for gas circulation and cell fluid circulation, which helps to reduce the influence of gas on the circulation of cell suspension and achieve uniform cell pumping.

[0040] Please see Figure 2 and Figure 3In a preferred embodiment, the cap 1 has an inlet 13 and an outlet 14, wherein the inlet 13 and the outlet 14 are respectively connected to the first channel 11, and the inlet 13 is connected to the second channel 12. The diameter of the inlet 13 is larger than the diameter of the outlet 14. The larger diameter of the inlet 13 facilitates the smooth entry of the cell suspension into the channel, while the smaller diameter of the outlet 14 compared to the inlet 13 allows the cells to be delivered one by one into the microdroplet chip, which can further improve the problems of cell aggregation and precipitation.

[0041] Please see Figure 1 and Figure 2 The cap 1 is equipped with a liquid-filling component 2 at the inlet 13. The large diameter of the inlet 13 facilitates the assembly of the liquid-filling component 2. The liquid-filling component 2 holds the cell suspension. After the cell suspension is pumped into the first channel 11, it flows out of the cap 1 along the first channel 11 and enters the microdroplet chip for cell sorting.

[0042] A pneumatic connector 3 is provided on the cap 1, which is connected to the second channel 12. Specifically, when the pneumatic connector 3 is connected to a gas compression or delivery device, such as an air pump, the pneumatic connector 3 delivers compressed gas into the second channel 12. By adjusting the air pressure, different air pressures are formed in the channel, which can uniformly pump out cells, which is beneficial for cell sorting. In a preferred embodiment, a pneumatic hole 16 is provided on one side of the cap 1 along the pumping direction of the cell suspension in the first channel 11. The pneumatic hole 16 is connected to the second channel 12, and the pneumatic connector 3 is located at the pneumatic hole 16 and is detachably connected to the cap 1. The channel of the pneumatic hole 16 is set perpendicular to the channel of the second channel 12. At this time, the gas flow path in the pneumatic hole 16 and the second channel 12 is L-shaped, which can help reduce air pressure fluctuations and achieve uniform cell pumping.

[0043] A mixing component 4 is connected to the rotating cap 1. The mixing component 4 rotates the rotating cap 1 to shake the cells evenly and reduce cell aggregation and precipitation.

[0044] During cell pumping, pneumatic connector 3 introduces gas into the second channel 12. The gas enters the liquid loading assembly 2 along the second channel 12, pushing the cell suspension. Under the action of gas pressure, the cells are stably pushed into the first channel 11. The cell suspension maintains a stable flow rate and eventually flows out of the cap 1 along the first channel 11. Pneumatic connector 3 uniformly pumps cells into the first channel 11, which is beneficial for cell sorting. At the same time, the mixing assembly 4 rotates the cap 1 to shake and mix the cells, which can effectively solve the problem of cell aggregation and difficulty in pumping cells at the set speed. The uniform delivery of cells improves the efficiency of cell sorting.

[0045] Example 2:

[0046] The difference between this embodiment and Embodiment 1 is that, please refer to... Figure 2In this embodiment, the rotating cap 1 is provided with an abutment platform 15, which is specifically a cylindrical platform adapted to the rotating cap 1. The first channel 11 and the second channel 12 are both opened on the abutment platform 15.

[0047] Please see Figures 2-6 In a preferred embodiment, the cap 1 is provided with an output component 5 for the outflow of cell suspension at the output port 14. The output component 5 includes an output connector 51, which is inserted into the output port 14 and is detachably connected to the cap 1. Specifically, the output connector 51 can be snapped into the cap 1; simply inserting the output connector 51 into the output port 14 achieves assembly between the output connector 51 and the cap 1, resulting in a simple and easy-to-operate structure. An inverted conical connector 52 is inserted into the output connector 51 and is sealed to the cap 1. Specifically, the open end of the inverted conical connector 52 is close to the abutment platform 15, while the narrow end is located inside the output connector 51. The inverted conical connector 52 facilitates tubing connection without the need for external tools, achieving fixation by hand tightening. An infusion tube 54 is connected to the narrow end of the inverted conical connector 52, and the infusion tube 54 is inserted into the output connector 51. The infusion tube 54 is preferably, but not limited to, a polyetheretherketone (PEEK) tube or a Teflon tube.

[0048] The pneumatic connector 3 pumps compressed gas into the second channel 12. The gas flows into the liquid-filling assembly 2 along the second channel 12 and pushes the cell suspension into the first channel 11. The cell suspension flows along the first channel 11 to the inverted conical connector 52, and then flows into the infusion tube 54 through the inverted conical connector 52, i.e., through the output connector 51, and finally enters the microdroplet chip along the infusion tube 54. The cell suspension flows stably and can be delivered through the infusion tube 54 at a specified flow rate.

[0049] In some specific embodiments, a second gasket 53 is provided between the inverted conical connector 52 and the abutment platform 15. The second gasket 53 is preferably, but not limited to, a sealing silicone gasket. The inverted conical connector 52 presses the second gasket 53 onto the abutment platform 15, and a sealed connection is achieved between the inverted conical connector 52 and the rotating cap 1, reducing the possibility of leakage of cell suspension from the output port 14 when the mixing component 4 shakes the rotating cap 1.

[0050] Please see Figures 2-4 , Figure 7 and Figure 8In a preferred embodiment, the liquid-filling assembly 2 includes a container 21 for holding the cell suspension. Specifically, the container 21 can be a centrifuge tube, which passes through the inlet 13 and is connected to the first channel 11 and the second channel 12 respectively. An adapter 22 is fitted onto the outside of the container 21, clamping the container 21 and detachably connected to the cap 1. In some specific embodiments, the container 21 includes a raised edge at its opening, which engages with the adapter 22 when the container 21 is inserted into it. The adapter 22 includes a clamping end 222, with a perforated hole 221 in the clamping end 222. When the container 21 is inserted into the adapter 22, the perforated hole 221 provides clearance for insertion. Specifically, the outer wall of the adapter 22 can be threaded to the inner wall of the cap 1. When the adapter 22 is inserted into the cap 1 and connected to it, the cap 1 presses against the clamping end 222 of the adapter 22, thus clamping the container 21 and fixing it inside the inlet 13. The adapter 22 has a simple structure and is easy to assemble and disassemble, facilitating the addition of cell suspension to the container 21.

[0051] Specifically, a first gasket 23 is provided between the adapter 22 and the abutment platform 15. The first gasket 23 is preferably, but not limited to, a sealing silicone gasket. The adapter 22 squeezes the first gasket 23 onto the abutment platform 15, and a sealed connection is achieved between the adapter 22 and the rotating cap 1, reducing the possibility of leakage of cell suspension from the inlet 13 when the mixing component 4 shakes the rotating cap 1.

[0052] Please see Figure 9 In a preferred embodiment, the mixing component 4 includes a partition 43, with a rotating plate 41 rotatably mounted on one side of the partition 43. Specifically, the rotating plate 41 has a locking position 411, through which the rotating cap 1 passes and engages with the rotating plate 41. The rotating plate 41 is driven by a driving member 42 for rotating the rotating plate 41. The driving member 42 is preferably, but not limited to, a rotary motor, with its output end connected to the rotating plate 41. The driving member 42 can be mounted on the partition 43, driving the rotating plate 41 and the rotating cap 1 to rotate relative to the partition 43, thereby shaking the cell suspension contained in the container 21. In some specific embodiments, a sensor 44 is provided on the partition 43. The sensor 44 is used to return the driving member 42 to its original position. It is understood that the method by which the driving member 42 cooperates with the sensor 44 to return to its original position is known to those skilled in the art and is achievable, and will not be described in detail in this embodiment.

[0053] Example 3:

[0054] This embodiment, based on the above embodiments, provides a droplet microfluidic sorting instrument. Please refer to [link to relevant documentation]. Figure 9 .

[0055] This invention discloses a droplet microfluidic sorting device, comprising the aforementioned cell pumping mechanism. A microdroplet chip is disposed on one side of the output component 5, allowing cells to be pumped along the delivery component to the microdroplet chip. A detection system is disposed on one side of the cell pumping mechanism, comprising an excitation light source module and an imaging module. The excitation light source module excites cells in the droplet using the excitation light source, thereby identifying cell markers. The imaging module can track the droplet position and cell state in real time. A sorting system is disposed on one side of the microdroplet chip, sorting the cells at the microdroplet chip. It is understood that the detection method of the detection system and the sorting method of the sorting system are known to those skilled in the art and are achievable, and will not be described in detail in this embodiment.

[0056] Dispersing and uniformly pumping cells through a cell pumping mechanism helps reduce the influence of cell aggregates on droplet generation or sorting signals, improves sorting efficiency, and the uniform flow rate helps reduce the risk of cell damage caused by pumping.

[0057] In this utility model, unless otherwise explicitly specified and limited, the terms "installation," "connection," "joining," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model according to the specific circumstances.

[0058] In the description of this utility model, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, or the orientation or positional relationship commonly used when the product of this utility model is in use. They are only for the convenience of describing this utility model and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model. In addition, the terms "first," "second," and "third," etc., are only used to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0059] Furthermore, terms such as "horizontal," "vertical," and "sag" do not imply that components must be absolutely horizontal or suspended, but rather that they can be slightly tilted. For example, "horizontal" simply means that its direction is more horizontal relative to "vertical," and does not mean that the structure must be completely horizontal, but can be slightly tilted.

[0060] In this invention, unless otherwise expressly specified and limited, "above or below" the first feature may include direct contact between the first and second features, or contact between the first and second features through another feature between them. Furthermore, "above," "over," and "on" the first feature includes the first feature directly above or diagonally above the second feature, or simply indicates that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the first feature includes the first feature directly below or diagonally below the second feature, or simply indicates that the first feature is at a lower horizontal level than the second feature.

[0061] Although the description of this utility model has been given in conjunction with the specific embodiments described above, it is obvious to those skilled in the art that many substitutions, modifications, and variations can be made based on the above description. Therefore, all such substitutions, modifications, and variations are included within the spirit and scope of the appended claims.

Claims

1. A cell pumping mechanism, characterized by, include The spiral cap (1) has a first channel (11) for the flow of cell suspension and a second channel (12) for the flow of gas; The liquid-filling assembly (2) is used to hold cell suspension, and the liquid-filling assembly (2) is connected to the first channel (11) and the second channel (12) respectively; A pneumatic connector (3) is provided on the cap (1) and connected to the second channel (12). The pneumatic connector (3) introduces gas into the liquid-filling assembly (2) through the second channel (12), and the cell suspension is pumped into the first channel (11). The mixing component (4) is connected to the rotating cap (1) in a transmission manner, and the mixing component (4) rotates the rotating cap (1).

2. The cell pumping mechanism of claim 1, wherein, The cap (1) is provided with an inlet (13) and an outlet (14), wherein the inlet (13) and the outlet (14) are connected through the first channel (11), the inlet (13) is connected to the second channel (12), and the liquid filling component (2) is located at the inlet (13); The diameter of the input port (13) is larger than the diameter of the output port (14).

3. The cell pumping mechanism of claim 2, wherein, The cap (1) is provided with an output component (5) for cell suspension to flow out at the output port (14), and the output component (5) is connected to the first channel (11).

4. The cell pumping mechanism of claim 3, wherein, The output component (5) includes An output connector (51) is inserted into the output port (14), and the output connector (51) is detachably connected to the swivel cap (1); and The inverted cone connector (52) has one end inserted into the output connector (51) and the other end sealed to the output port (14). The cell suspension in the first channel (11) flows sequentially through the inverted cone connector (52) and the output connector (51).

5. The cell pumping mechanism of claim 1, wherein, The cap (1) is provided with an abutment platform (15), and the first channel (11) and the second channel (12) are both located on the abutment platform (15). The liquid filling assembly (2) is sealed to the cap (1) at the abutment platform (15).

6. The cell pumping mechanism of claim 5, wherein, The liquid filling assembly (2) includes Container (21) for holding cell suspension, wherein container (21) is connected to the first channel (11) and the second channel (12) respectively; and The adapter (22) is fitted onto the outside of the container (21) and fixes the container (21). The adapter (22) is detachably connected to the swivel cap (1) and is sealed to the swivel cap (1).

7. The cell pumping mechanism according to claim 6, characterized in that, A first gasket (23) is provided between the abutment platform (15) and the adapter (22).

8. The cell pumping mechanism of claim 1, wherein, The mixing component (4) includes Rotating plate (41), the rotating cap (1) is disposed on the rotating plate (41); as well as The driving component (42) is connected to the rotating plate (41) in a transmission manner, and the driving component (42) drives the rotating plate (41) to rotate.

9. The cell pumping mechanism of claim 1, wherein, The cap (1) has an aerodynamic hole (16) on one side of the cell suspension in the first channel (11) along the pumping direction. The aerodynamic hole (16) is connected to the second channel (12). The aerodynamic connector (3) is located at the aerodynamic hole (16).

10. A droplet microfluidic sorter characterized in that, Includes the cell pumping mechanism as described in any one of claims 1-9.

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