Micro-fluidic chip for cell sorting
By designing the streamlined deceleration focus separation structure and filtered array capture structure in the microfluidic chip, the problem of low cell sorting efficiency at high flow rates is solved, and efficient and safe cell capture is achieved.
Patent Information
- Application Number
- CN202422001355.4
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- Filing Date
- 2024-08-16
- Publication Date
- 2025-05-30
- Estimated Expiration
- 2034-08-16
AI Technical Summary
Existing cell sorting techniques are difficult to effectively capture target cells at high flow rates and may lead to cell damage and blockage problems.
A microfluidic chip is designed, including a streamline-based deceleration focus separation structure and a filter-based array capture structure to achieve efficient sorting and capture of target cells at high flow rates.
It realizes efficient capture of target cells at high flow velocity, avoids cell damage and blockage, and has the advantages of rapid, simple and efficient.
Smart Images
Figure CN222918713U_ABST
Abstract
Description
Technical Field
[0001] The utility model belongs to the technical field of cell sorting, and particularly relates to a microfluidic chip for efficiently capturing target cells under high flow rate conditions. Background Art
[0002] Cell sorting refers to the technology of separating a type of cell from a multi-cell sample, and is applied in many fields of biomedicine. For example, in the Assisted Reproductive Technique (ART), it is necessary to obtain a large number of sperm with high viability through cell sorting, which is one of the key steps in the implementation of ART. Currently, the commonly used sperm sorting techniques in clinics include centrifugation, electrophoresis, etc. Although these methods are simple to operate and low in cost, they may cause damage to sperm.
[0003] With the progress of micro-nano technology, microfluidic technology has avoided the possible sperm damage caused by traditional methods and has gradually become a recognized effective sperm sorting means. Currently, there are many cases of microfluidic chips designed for cell sorting. Through the structural design in the microfluidic chip, the integrity of the cells to be selected is ensured as much as possible, and high-throughput and non-destructive screening of target cells can be achieved. However, in these microfluidic solutions, a large amount of sample dilution or buffer is generally required, and blockage may be caused; in addition, the whole process is sensitive to changes in flow rate, and the separation effect under high flow rate conditions cannot be effectively guaranteed. Summary of the Utility Model
[0004] In view of this, the primary object of the present utility model is to provide a microfluidic chip for cell sorting, which contains a streamline-based deceleration focusing separation structure and a filtration-based array capture structure, so as to achieve efficient sorting and capture of target cells at high fluid velocity, and has the advantages of being fast, simple and efficient.
[0005] To achieve the above object, the present utility model adopts the following technical solutions:
[0006] The present utility model first provides a microfluidic chip for cell sorting, including a chip layer, and the chip layer includes:
[0007] A first sample addition pool for introducing a sample containing cells to be selected into the microfluidic chip;
[0008] A cell focusing separation module communicated with the outlet of the first sample addition pool, which is composed of several groups of focusing separation units connected in series, and each group of focusing separation units includes a separation structure, a focusing structure and several separation deceleration channels connected in sequence;
[0009] and a cell capture module communicated with the outlet of the separation and deceleration flow channel, which is used to capture candidate cells.
[0010] In a further solution, the separation structure described herein refers to a structural unit that can distinguish between larger-sized cells and smaller-sized cells in a sample liquid, achieve spatial separation of cells of different sizes, and enable the larger-sized cells to be focused and separated downstream of the main channel. It can be in the shape of an hourglass, a snake, a K shape, etc.
[0011] In a preferred embodiment of the present invention, in the direction of microfluidic flow, the separation structure is in the shape of an hourglass, which is composed of a first flow channel, a second flow channel, and a third flow channel connected in series in sequence. Among them, the width of the second flow channel is the smallest.
[0012] Preferably, the width of the first flow channel > the width of the third flow channel > the width of the second flow channel, so as to obtain a better separation effect.
[0013] In a further solution, the focusing structure is composed of several groups of focusing units connected in series. Each group of focusing units includes a central flow channel and branch flow channels located on both sides of the central flow channel. The branch flow channels are connected in series with the central flow channel in sequence, and the outlets of the branch flow channels are communicated with the inlets of the central flow channel; and in the direction of microfluidic flow, the lengths of the branch flow channels gradually decrease.
[0014] In a further solution, multiple groups of the separation and deceleration flow channels described herein can be designed as needed, as long as the flow resistance of each flow channel is ensured. In some specific embodiments of the present invention, to ensure the simplification of the chip structure and the separation effect, it is preferably designed with two separation and deceleration flow channels. Further, in the direction of microfluidic flow, the lengths of the separation and deceleration flow channels gradually decrease.
[0015] In a further solution, in the cell focusing and separation module, arc-shaped corners are adopted at the corners to optimize the flow path of the fluid and minimize the risk of cell damage.
[0016] In a further solution, the cell capture module is composed of several groups of micro-column barrier arrays. In the direction of microfluidic flow, the gaps between the groups of micro-column barrier arrays gradually decrease.
[0017] Among them, the microcolumns described in this article are not particularly limited and can be common cylinders, regular hexagonal prisms or regular triangular prisms in the art. Preferably, in some specific embodiments of the present invention, the microcolumn is a regular triangular prism. First, the tip structure of the regular triangular prism helps to generate microscale disturbances in the fluid, and this kind of disturbance can effectively slow down the fluid velocity, making it easier for cells to be captured. Second, the regular triangular prism has a high surface area to volume ratio, which means that more capture points can be provided in the same space, thereby increasing the capture efficiency. Third, the shape of the regular triangular prism helps to reduce the resistance when the fluid flows, making the fluid pass through the cell capture module more smoothly. Fourth, the regular triangular prism is suitable for manufacturing using microfabrication technology. For the above reasons, in some preferred embodiments of the present invention, the microcolumn adopts a regular triangular prism.
[0018] In a further solution, the chip layer further includes a second sample addition pool, and the outlets of the second sample addition pool are respectively communicated with the outlet of the separation and deceleration flow channel and the inlet of the cell capture module. Through the second sample addition pool, a buffer solution or a cell capacitation solution is introduced into the microfluidic chip to better achieve the capture of candidate cells.
[0019] In a further solution, the chip layer further includes a first collection pool and a second collection pool. The first collection pool is communicated with the outlet of the cell focusing and separation module for collecting the waste liquid after focusing and separation; the second collection pool is communicated with the outlet of the cell capture module for collecting the sorted candidate cells.
[0020] It can be understood that the microfluidic chip described in this article further includes a base layer and a cover layer, both of which are conventional structures in the art. Among them, the cover layer is respectively provided with addition holes and collection holes corresponding to each addition pool and collection pool of the chip layer as needed, which will not be elaborated one by one here.
[0021] The beneficial effects of the present invention:
[0022] The microfluidic chip in the present invention contains a cell focusing and separation module based on the principle of streamline focusing separation and a cell capture module based on a filtration mechanism, and simultaneously achieves high flow rate and high capture efficiency. Among them, the cell focusing and separation module can concentrate the larger cells (such as white blood cells, red blood cells, etc.) in the sample to the central flow channel and remove them from the outlet; at the same time, it can create favorable conditions for the capture of candidate cells entering the cell capture module by reducing the velocity of the high-speed fluid entering the chip.
[0023] The microfluidic chip in the present invention focuses, decelerates and captures by using the physical characteristics of candidate cells through structural design, so as to quickly, simply and efficiently achieve the sorting and capture of candidate cells, providing a new implementation path for cell sorting. Brief Description of the Drawings
[0024] Figure 1 This is an exploded view of the microfluidic chip for cell sorting in Embodiment 1 of the present utility model.
[0025] Figure 2 It is Figure 1 a schematic plan view of the chip layer 10 in
[0026] Figure 3 It is Figure 2 an enlarged schematic view of part A in
[0027] Figure 4 It is Figure 2 an enlarged three-dimensional schematic view of part A in
[0028] Figure 5 It is Figure 2 an enlarged schematic view of part B in
[0029] In the figure: 10 - chip layer, 11 - first sample addition pool, 12 - second sample addition pool, 13 - first collection pool, 14 - second collection pool, 15 - cell focusing and separation module, 151 - separation structure, 1511 - first flow channel, 1512 - second flow channel, 1513 - third flow channel, 152 - focusing structure, 1521 - central flow channel, 1522 - branch flow channel, 153 - separation deceleration flow channel, 16 - cell capture module, 161 - first array, 162 - second array, 163 - third array, 164 - fourth array;
[0030] 20 - cover plate, 21 - first sample addition hole, 22 - second sample addition hole, 23 - first collection hole, 24 - second collection hole. Detailed Embodiments
[0031] The microfluidic chip provided by the present utility model will be further described in detail below in conjunction with the accompanying drawings of the specification.
[0032] It should be noted that when an element is referred to as being "fixed to", "arranged on", or "mounted on" another element, it can be directly on the other element or indirectly on the other element. However, when an element is referred to as being "connected to" or "linked to" another element, it can be directly connected to the other element or indirectly connected to the other element. Additionally, connection generally refers to a fixing function, and the fixing here can be any conventional fixing method in the art, such as "threaded connection", "riveting", "welding", "adhesive bonding", etc.
[0033] It should be understood that the orientation or positional relationship indicated by terms such as "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc. is based on the orientation or positional relationship shown in the accompanying drawings of the specification. It is only for the convenience of describing the embodiments of the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed or operated in a specific orientation, and therefore should not be construed as a limitation to the present invention.
[0034] In addition, the "several" mentioned herein means at least containing one or a group of the described structures, modules or units, and there is no specific limitation on its upper limit. Those skilled in the art can make corresponding designs based on the design needs of the product.
[0035] Embodiment 1
[0036] In this embodiment, a microfluidic chip for cell sorting is provided. Please refer to Figure 1 , the microfluidic chip includes a chip layer 10, a cover plate 20 and a substrate (not shown in the figure). The chip layer 10 is mainly composed of flow channels for microfluid to flow, which constitutes the main part of the microfluidic chip. A microfluidic chip can be obtained by pressing and sealing the cover plate 20, the chip layer 10 and the substrate. Among them, the cover plate 20 and the substrate can be conventional structures and materials in the art respectively, and the pressing and sealing methods can all adopt conventional methods in the art, so they will not be specifically described herein.
[0037] Please combine Figure 2 , the chip layer 10 is respectively provided with a first sample addition pool 11, a second sample addition pool 12, a first collection pool 13 and a second collection pool 14. Correspondingly, the cover plate 20 is respectively provided with corresponding first sample addition holes 21, second sample addition holes 22, first collection holes 23 and second collection holes 24.
[0038] Furthermore, as the main structure of the microfluidic chip, the first sample addition pool 11 of the chip layer 10 is used to introduce a sample solution containing cells to be selected into the microfluidic chip.
[0039] Continue to refer to Figure 2 and combine with Figure 3, the chip layer 10 includes a cell focusing and separation module 15 communicating with the outlet of the first sample addition pool 11, which is one of the main structures of the chip layer 10. According to the microfluidic flow direction, the cell focusing and separation module 15 is composed of several groups of focusing and separation units connected in series. Each group of focusing and separation units consists of a separation structure 151, a focusing structure 152, and two separation and deceleration channels 153. Among them, the outlet of the separation structure 151 communicates with the inlet of the focusing structure 152, and the outlet of the focusing structure 152 communicates with the inlet of the separation and deceleration channel 153. Through such a cell focusing and separation module 15, the separation, focusing, and deceleration of cells are realized, creating favorable conditions for the sorting and capture of candidate cells under high flow rate conditions.
[0040] Furthermore, in this embodiment, the separation structure 151 is configured as a structure similar to an hourglass shape. For details, please refer to Figure 3 , that is, according to the microfluidic flow direction, the separation structure 151 is composed of a first channel 1511, a second channel 1512, and a third channel 1513 connected in series in sequence. Among them, the width of the second channel 1512 is the smallest, thus forming a structure similar to an hourglass shape. The separation structure 151 is arranged at the initial end of each focusing structure 152, that is, the inlet of the focusing structure 152, so as to separate cells with larger sizes and cells with smaller sizes before cell focusing, realizing the spatial separation of cells with different sizes, and enabling cells with larger sizes to be focused and separated downstream of the main channel.
[0041] Furthermore, please continue to refer to Figure 2 and Figure 3 , the focusing structure 152 is composed of several groups of focusing units connected in series. Each group of focusing units includes a central channel 1521 and branch channels 1522 located on both sides of the central channel 1521. The branch channels 1522 and the central channel 1521 are connected in series in sequence. Among them, the outlet of the branch channel 1522 communicates with the inlet of the central channel 1521. In this embodiment, according to the microfluidic flow direction, the length L of the branch channel 1522 支 gradually decreases. Through such a structural design, part of the liquid at the edge of the flow field is introduced into the branch channel 1522, while the liquid in the central region flows into the central channel 1521. Such a flow rate distribution mechanism enables cells with larger volumes (such as white blood cells, epithelial cells, etc.) to gradually concentrate and migrate near the center line of the main channel after continuously passing through multiple focusing units, effectively separating cells with larger sizes and cells with smaller sizes, and obtaining a target liquid with a higher density of cells with smaller sizes in the separation and deceleration channel 153. Furthermore, the outlet of each focusing structure 152 communicates with the inlets of two separation and deceleration channels 153. According to the microfluidic flow direction, the length L of the separation and deceleration channel 153 支Decrease step by step. By designing the number of cell focusing and separation modules, the number of focusing and separation units and / or focusing units, and the dimensions of their central flow channels 1521 and branch flow channels 1522, as well as the dimensions of the separation and deceleration flow channels 153, the flow resistance in the flow channels is controlled to achieve cell focusing, separation, and deceleration. Preferably, in this embodiment, the corners of the cell focusing and separation module 15 are treated with arcs to optimize the fluid flow path and minimize the risk of cell damage.
[0042] Furthermore, please refer to Figure 2 and Figure 5 The chip layer 10 includes a number of cell capture modules 16 connected to the outlet of the separation and deceleration flow channels 153. The cell capture module 16 is composed of several groups of micro-column barrier arrays. In this embodiment, the cell capture module 16 is successively composed of a first array 161, a second array 162, a third array 163, and a fourth array 164. The minimum gap between the micro-columns in each group of arrays is equal, and in the direction of micro-fluid flow, the gaps between the groups of micro-column barrier arrays decrease step by step, that is, the gap C1 of the first array 161 > the gap C2 of the second array 162 > the gap C3 of the third array 163 > the gap C4 of the fourth array 164. Through this step-by-step filtering mechanism, cells with a large radius will be blocked between the micro-columns with a small spacing, while cells with a small radius can pass through each group of micro-column barrier arrays to ensure the capture and collection of high-purity target cells and significantly improve the overall efficiency. Among them, the shape of the micro-columns in this embodiment is a regular triangular prism.
[0043] In addition, please continue to refer to Figure 2 In this embodiment, the first collection pool 13 is connected to the outlet of the focusing structure 152 in the cell focusing and separation module 15 for collecting the waste liquid obtained after focusing and separation. The outlet of the second sample addition pool 12 is respectively connected to the outlet of the separation and deceleration flow channels 153 and the inlet of the cell capture module 16. By introducing buffer solution, cell capacitation solution, etc. into the second sample addition pool 12, the capture of candidate cells can be better achieved. The outlet of the cell capture module 16 is connected to the second collection pool 14, and the second collection pool 14 is used to collect the candidate cells obtained after focusing, deceleration, and capture.
[0044] In this embodiment, a preferred method of the microfluidic chip in the present invention is given. Based on the performance differences of different candidate cells and the different states of sorted cells, the structures, the dimensions of each module, unit, or flow channel can be designed to achieve the corresponding cell sorting purpose.
[0045] The microfluidic chip in this embodiment ensures stability and high capture efficiency under different flow rate conditions, and simplifies the operation process of cell sorting. Only one simple step is required to inject the sample liquid into the chip and complete the processing within a few minutes.
[0046] In this embodiment, the focusing and separation technology of the microfluidic chip does not require a large amount of semen dilution and buffer usage, nor does it cause clogging problems. Moreover, the microfluidic chip is not sensitive to changes in flow rate and can maintain a stable separation effect within a wide flow rate range. Meanwhile, in the designed micro-column barrier array structure, tiny cells can smoothly pass through the gaps between each micro-column and are finally collected at the outlet, while other types of cells with relatively larger volumes are blocked by the prisms and cannot pass through, thus being effectively separated.
[0047] Example 2
[0048] Based on the microfluidic chip in Example 1, this embodiment designs a microfluidic chip for sorting highly motile sperm in semen.
[0049] First, in combination with Figure 2 、 Figure 3 and Figure 4 , the flow channel height of the chip layer 10 in this embodiment is configured to be h = 60 μm. In this embodiment, a total of 7 sets of series-connected cell focusing and separation modules 15 are designed for the microfluidic chip. Among them, the dimensions of each flow channel in the separation structure 151 are configured such that the width D1 of the first flow channel 1511 is 200 μm, the width D2 of the second flow channel 1512 is 30 μm, and the width D3 of the third flow channel 1513 is 90 μm. In this parameter design, larger cells such as white blood cells and epithelial cells with a radius of about 15 μm are distinguished from sperm cells with a radius of about 5 μm. Using this hourglass-shaped structure, when the center line of the main flow channel is used as the reference benchmark (i.e., zero point), the centroid of other cells will be effectively concentrated in the region from -30 μm to 30 μm. Through this configuration, the separation structure 151 promotes the spatial separation of cells of different sizes, enabling larger cells to be focused and separated downstream of the main channel.
[0050] Furthermore, the focusing structure 152 is configured with five focusing units. Among them, in the five focusing units, the length L 中 of the central flow channel 1521 is 100 μm for all; following the direction of microfluidic flow, the length L 支 of the branch flow channels 1522 gradually decreases, Figure 3 and are 1200 μm, 1100 μm, 720 μm, 520 μm, and 410 μm from top to bottom in sequence; in addition, in the focusing structure 152, Figure 3 in the second, third, fourth, and fifth focusing units from top to bottom, the width W 支 of the branch flow channels 1522 is 40 μm for all, while the width W 支is 30 μm. In this embodiment, the normalized resistance R of the central flow channel 1521 is set to 1, and the flow resistances of the branch flow channels 1522 in the five focusing units can be calculated as 12, 5.73, 3.75, 2.71, and 2.14.
[0051] Furthermore, in this embodiment, the parameters of the separation and deceleration flow channel 153 are designed and calculated simultaneously. Figure 2 From top to bottom, the length L of the separation and deceleration flow channel 分 is designed as 72552 μm, 68170 μm, 63874 μm, 59658 μm, 55532 μm, 51406 μm, and 47280 μm in sequence, and the width W 分 is designed as 220 μm, 200 μm, 180 μm, 160 μm, 140 μm, 110 μm, and 90 μm in sequence. According to the above calculation process, the normalized flow resistances of the separation and deceleration flow channel 153 are 17.8, 19.3, 21.3, 24, 27.8, 38.7, and 56.8 respectively, and the R inside the separation and deceleration flow channel 153 can be regarded as 8.76, 9.18, 9.79, 10.8, 13, 16.6, and 22.1.
[0052] By designing the fluid resistance in this way, it is allowed to introduce a part of the liquid located at the edge of the flow field into the branch flow channel 1522, while the liquid in the central region flows into the central flow channel 1521. This flow rate distribution mechanism enables larger cells (such as white blood cells, epithelial cells, etc.) to gradually concentrate and migrate near the center line of the main channel after continuously passing through multiple focusing units. This process effectively separates large cells from small cells such as sperm, so that the target liquid with a higher density of small cells can be obtained in the separation and deceleration flow channel 153.
[0053] Furthermore, please combine Figure 2 and Figure 5 , in this embodiment, 16 independent cell capture modules 16 are configured. According to the microfluidic flow direction, each cell capture module 16 is composed of a first array 161, a second array 162, a third array 163, and a fourth array 164 connected in series. Among them, the gap C1 between the micro-columns in the first array 161 is 40 μm, the gap C2 between the micro-columns in the second array 162 is 25 μm, the gap C3 between the micro-columns in the third array 163 is 15 μm, and the gap C4 between the micro-columns in the fourth array 164 is 10 μm. Different-sized cells are separated and captured by gradually reducing the gap of the micro-column arrays in this way, and the micro-columns are in the shape of regular triangular prisms to achieve efficient sorting of different-sized cells and precise separation of cells.
[0054] Example 3
[0055] In this embodiment, an experimental process for sorting highly motile sperm in semen based on the microfluidic chip in Embodiment 2 is provided. Taking Figure 1 the schematic diagram in
[0056] as an example, the specific working steps are as follows:
[0057] (1) Place the human tubal fluid (HTF) and the microfluidic chip in an incubator at 37°C for 15 minutes, and at the same time, put the collected semen sample into a water bath at 37°C for liquefaction.
[0058] (2) After mixing the liquefied semen sample, divide it into four equal groups, and process the four groups of semen samples according to steps (3) to (5).
[0058] (3) Use a pipette to take 0.45 mL of the liquefied semen sample and inject it into the first sample addition pool 11 of the microfluidic chip through the first sample addition hole 21. During the addition of the semen sample, the generation of air bubbles needs to be avoided.
[0059] (4) After the semen passes through the cell focusing separation module 15, open the second sample addition hole 22 and the second collection hole 24, take 0.25 mL of HTF and inject it into the second sample addition pool 12 of the microfluidic chip through the second sample addition hole 22, and directly act on the cell capture module 16.
[0060] (5) Place the microfluidic chip with the semen sample and HTF horizontally in an incubator at 37°C for incubation, and wait quietly for sampling. During this process, the highly motile sperm in the sample will pass through the cell focusing separation module 15 and the cell capture module 16, and then flow out into the second collection pool 14, and sampling and sperm quality evaluation are carried out through the second collection hole 24.
[0061] It can be seen from the above embodiments that the microfluidic chip designed in the present utility model realizes high flow rate and high capture efficiency, and improves the efficiency of sperm selection in clinical assisted reproduction. It should be noted that in the present utility model, the channel size, structure, parameters, etc. are mainly described with human sperm cells as model cells, but it does not mean that the microfluidic chip is only limited to the sorting of sperm cells. By designing the number of each module, unit, structure, the size of the flow channel, and the arrangement gap of the micro-columns, etc., the purpose of sorting different-sized cells can be achieved.
[0062] The technical features of the above-described embodiments can be combined arbitrarily. For the sake of brevity of description, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, it should be considered as the scope described in this specification.
[0063] The above-described embodiments merely represent several implementation manners of the present utility model. The description thereof is relatively specific and detailed, but it should not be construed as a limitation to the scope of the utility model patent. It should be noted that for those of ordinary skill in the art, without departing from the concept of the present utility model, several modifications and improvements can still be made, and these all fall within the protection scope of the present utility model. Therefore, the protection scope of the present utility model patent shall be subject to the appended claims.
Claims
1. A microfluidic chip for cell sorting, comprising a chip layer, characterized in that: The chip layer comprises: A first sample addition pool is used to introduce a sample containing cells to be selected into the microfluidic chip; A cell focusing and separation module connected to the outlet of the first sample addition pool, which is composed of a plurality of groups of focusing and separation units connected in series, each group of focusing and separation units comprising a separation structure, a focusing structure and a plurality of separation and deceleration flow channels connected in sequence; And a cell capture module communicated with the outlet of the separation deceleration flow channel, which is used to capture the cells to be selected.
2. The microfluidic chip for cell sorting according to claim 1, characterized in that: According to the flow direction of the microfluid, the separation structure consists of a first flow channel, a second flow channel and a third flow channel connected in series, wherein the width of the second flow channel is the smallest.
3. The microfluidic chip for cell sorting according to claim 2, characterized in that: The width of the first flow channel>the width of the third flow channel>the width of the second flow channel.
4. The microfluidic chip for cell sorting according to claim 1, characterized in that: The focusing structure is composed of a plurality of groups of focusing units connected in series, each group of focusing units includes a central flow channel and branch flow channels located on both sides of the central flow channel, the branch flow channels are connected in series with the central flow channel in sequence, the outlets of the branch flow channels are connected to the inlet of the central flow channel; and according to the flow direction of the microfluid, the lengths of the branch flow channels decrease step by step.
5. The microfluidic chip for cell sorting according to claim 1, characterized in that: According to the flow direction of the microfluid, the length of the separation and deceleration flow channel decreases step by step.
6. The microfluidic chip for cell sorting according to any one of claims 1, 4 or 5, characterized in that: In the cell focusing separation module, arc-shaped corners are used at the corners.
7. The microfluidic chip for cell sorting according to claim 1, characterized in that: The cell capture module is composed of a plurality of groups of micro-column barrier arrays, and the gaps between the groups of micro-column barrier arrays are gradually reduced according to the flow direction of the microfluid.
8. The microfluidic chip for cell sorting according to claim 7, characterized in that: The microcolumn is a regular triangular prism.
9. The microfluidic chip for cell sorting according to claim 1, characterized in that: The chip layer further includes a second sample adding pool, the outlet of which is respectively connected to the outlet of the separation deceleration channel and the inlet of the cell capture module.
10. The microfluidic chip for cell sorting according to claim 1, characterized in that: The chip layer also includes a first collecting pool and a second collecting pool. The first collecting pool is connected to the outlet of the cell focusing and separation module and is used to collect waste liquid after focusing and separation. The second collecting pool is connected to the outlet of the cell capture module and is used to collect the selected cells obtained by sorting.