CN220618878U - Cell collection device and integrative equipment of cell enrichment dyeing - Google Patents
Cell collection device and integrative equipment of cell enrichment dyeing Download PDFInfo
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- CN220618878U CN220618878U CN202321920761.XU CN202321920761U CN220618878U CN 220618878 U CN220618878 U CN 220618878U CN 202321920761 U CN202321920761 U CN 202321920761U CN 220618878 U CN220618878 U CN 220618878U
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Abstract
The utility model provides a cell collecting device and cell enrichment and dyeing integrated equipment, wherein the cell collecting device comprises a microfluidic device and a buffer device, and the buffer device comprises: a peristaltic pump in communication with the microfluidic device for pumping liquid from the microfluidic device; the buffer is arranged between the microfluidic device and the peristaltic pump, a buffer cavity is formed in the buffer cavity, the buffer cavity is respectively communicated with the microfluidic device and the peristaltic pump, and at least part of cavity walls of the buffer cavity are made of materials capable of undergoing elastic deformation. According to the utility model, the sealed buffer is arranged between the microfluidic device and the peristaltic pump, and the microfluidic device and the peristaltic pump are communicated in sequence through the air pipe, so that pulse flow is generated when the peristaltic pump works, negative pressure is generated in the buffer, and the deformable elastic material contracts inwards, so that the effect of reducing the pulse flow is achieved, and the influence of the pulse flow on experimental results in the experimental process can be reduced.
Description
Technical Field
The utility model belongs to the technical field of cell detection and analysis, and particularly relates to a cell collecting device and cell enrichment and dyeing integrated equipment.
Background
In recent years, several emerging tumor diagnostic detection techniques, such as circulating tumor DNA (ctDNA), circulating Tumor Cells (CTCs) detection methods, referred to above as liquid biopsies, have emerged. The CTC detection is convenient to obtain materials, overcomes the defect that the histopathological detection is inconvenient to obtain materials and has a certain damage to patients, and can find the existence of CTC in peripheral blood before solid tumor formation according to researches, so that the CTC detection is very suitable for early screening and early diagnosis of malignant tumors, has good effects on prognosis of malignant tumors, disease progress monitoring, recurrence prediction, tiny focus monitoring after malignant tumor operation and design and treatment effect monitoring of targeted drug treatment, and is an advanced method for early screening and diagnosis of malignant tumors at present. The capture and recognition of CTCs in CTC assays is a great challenge due to the low CTC content in peripheral blood. The us FDA in 2004 approved the CTC detection device CellSearch for the diagnosis of breast, prostate and rectal cancer in the world, and this methodology was not widely used because of the poor specificity of the imported devices, which were expensive.
In addition, if a cell collecting device is designed, the target substance can be efficiently enriched and dyed, and the cell collecting device plays an important role in various detection and research in the field of biological medicine. For example, in immunological research, genetic research or microbial detection, the efficiency of sorting target cells, organisms or biomacromolecules can be improved, and further, the research and development of biochips and the research and development of organoids are facilitated. On the other hand, the cell collection device is also suitable for changing various eluents to realize the application scene of the chromatographic separation preparation method, or can be applied to the application scene of adding samples or reagents in a timed and quantitative manner, such as the induction expression of gene recombinants and the purification of products.
In the prior art, enrichment of nucleated cells such as CTCs is mostly achieved by drawing blood, however, blood belongs to a non-newtonian fluid to some extent, and if external force is applied, the external force is too large, and thus, filtration is difficult and hardening is easy, so that low-speed drawing is required.
In the prior art, peristaltic pumps are generally adopted for extraction, and in the process of enriching and staining nucleated cells, multiple times of extraction are required, so that the problem of liquid backflow is inevitably generated; meanwhile, the peristaltic pump can generate pulse flow when in operation, the generation of the pulse flow can influence the filtering process of the previous device, and particularly, under the condition that the filtered liquid is only a few milliliters, the generation of the pulse can greatly influence experimental results.
Therefore, designing a buffer device of a cell enrichment and dyeing integrated device which can prevent liquid backflow in the process of extracting blood for many times and can also prevent a peristaltic pump from generating pulse flow during operation becomes a technical problem to be solved urgently by those skilled in the art.
The present utility model has been made in view of this.
Disclosure of Invention
The utility model aims to overcome the defects of the prior art, and provides a cell collecting device and a cell enrichment dyeing integrated device, which are sequentially communicated through an air pipe by arranging a sealed buffer between a microfluidic device and a peristaltic pump, wherein pulse flow is generated when the peristaltic pump works, negative pressure is generated in the buffer, and a deformable elastic material contracts inwards, so that the effect of reducing the pulse flow is achieved, and the influence of the pulse flow on experimental results in the experimental process can be reduced.
In order to solve the technical problems, the utility model adopts the basic conception of the technical scheme that:
a cell collection device comprising a microfluidic device and a buffer device, the buffer device comprising:
a peristaltic pump in communication with the microfluidic device for pumping liquid from the microfluidic device;
the buffer is arranged between the microfluidic device and the peristaltic pump, a buffer cavity is formed in the buffer cavity, the buffer cavity is respectively communicated with the microfluidic device and the peristaltic pump, and at least part of cavity walls of the buffer cavity are made of materials capable of undergoing elastic deformation.
Further, the buffer comprises a bracket with a hollow inside and a buffer film capable of generating elastic deformation; the support is provided with a plurality of through holes, and the buffer film is attached to the support and at least covers the through holes; the buffer membrane and the support enclose the buffer chamber.
Further, the bracket is of a hollow cylinder structure, and the through holes are formed in the side wall of the cylinder structure; the buffer film is sleeved on the side wall of the column structure so as to cover the through hole.
Further, the bracket comprises two end walls which are arranged at intervals, and a plurality of supporting rods which are used for connecting the two end walls; one end of the supporting rod is connected to the periphery of one end wall, and the other end of the supporting rod is connected to the periphery of the other end wall; the through holes are formed between the two support rods.
Further, the support rods are arranged in an extending mode along the direction parallel to the axis of the column structure.
Further, two air ports are respectively arranged on the two end walls, the air ports are connected with air pipes in a sealing mode, one air pipe is communicated with the microfluidic device, and the other air pipe is communicated with the peristaltic pump.
Further, the buffer is arranged below the liquid outlet end of the microfluidic device and is communicated with the liquid outlet end of the microfluidic device through a first gas pipe.
Further, the buffer is communicated with the peristaltic pump through a second air pipe, and the second air pipe penetrates through the peristaltic pump to be communicated with the atmosphere.
Further, a one-way valve which is communicated in a one-way from the microfluidic device to the peristaltic pump is arranged between the microfluidic device and the peristaltic pump.
The utility model also provides a cell enrichment and staining integrated device comprising the cell collecting device.
After the technical scheme is adopted, compared with the prior art, the utility model has the following beneficial effects:
1. according to the utility model, the sealed buffer is arranged between the microfluidic device and the peristaltic pump, and the microfluidic device and the peristaltic pump are communicated in sequence through the air pipe, so that pulse flow is generated when the peristaltic pump works, negative pressure is generated in the buffer, and the deformable elastic material contracts inwards, so that the effect of reducing the pulse flow is achieved, and the influence of the pulse flow on experimental results in the experimental process can be reduced.
2. According to the utility model, the one-way valve is arranged on the second air pipe, so that liquid can only flow from the buffer to the peristaltic pump, and the liquid backflow generated during the repeated extraction of the device is prevented.
Drawings
The accompanying drawings, which are included to provide a further understanding of the utility model and are incorporated in and constitute a part of this specification, illustrate embodiments of the utility model and together with the description serve to explain the utility model. It is evident that the drawings in the following description are only examples, from which other drawings can be obtained by a person skilled in the art without the inventive effort. In the drawings:
FIG. 1 is a schematic diagram of the overall structure of the present utility model;
fig. 2 is a cross-sectional view of a buffer according to the present utility model.
The main elements in the figure are illustrated:
320. a microfluidic device; 330. a peristaltic pump; 340. a buffer; 341. a first air tube; 342 a second trachea; 3421. a one-way valve; 343. a bracket; 3431. a support rod; 344. a buffer film; 345. an end wall.
Detailed Description
For the purpose of making the objects, technical solutions and advantages of the embodiments of the present utility model more apparent, the technical solutions in the embodiments will be clearly and completely described with reference to the accompanying drawings in the embodiments of the present utility model, and the following embodiments are used to illustrate the present utility model, but are not intended to limit the scope of the present utility model.
In the description of the present utility model, it should be noted that the directions or positional relationships indicated by the terms "upper", "lower", "front", "rear", "left", "right", "vertical", "inner", "outer", etc. are based on the directions or positional relationships shown in the drawings, are merely for convenience of describing the present utility model and simplifying the description, and do not indicate or imply that the devices or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present utility model.
In the description of the present utility model, it should be noted that, unless explicitly specified and limited otherwise, the terms "mounted," "connected," and "connected" are to be construed broadly, and may be either fixedly connected, detachably connected, or integrally connected, for example; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium. The specific meaning of the above terms in the present utility model will be understood in specific cases by those of ordinary skill in the art.
Example 1
As shown in fig. 1 and 2, the cell collection device includes a microfluidic device 320 for filtering enriched cells in a blood sample and a buffer device including: peristaltic pump 330 is in communication with the microfluidic device 320 for pumping liquid from the microfluidic device 320; a buffer 340 is disposed between the microfluidic device 320 and the peristaltic pump 330, and a buffer chamber is formed in the interior of the buffer chamber, and the buffer chamber is respectively communicated with the microfluidic device 320 and the peristaltic pump 330, and at least part of the cavity wall of the buffer chamber is made of a material capable of undergoing elastic deformation.
In particular, peristaltic pump 330 is in communication with the microfluidic device 320 for pumping liquid from the microfluidic device 320; a buffer 340 is disposed between the microfluidic device 320 and the peristaltic pump 330, and a buffer chamber is formed in the interior of the buffer chamber, and the buffer chamber is respectively communicated with the microfluidic device 320 and the peristaltic pump 330, and at least part of the cavity wall of the buffer chamber is made of a material capable of undergoing elastic deformation.
Specifically, the buffer 340 includes a hollow support 343, a buffer film 344 capable of elastically deforming is disposed outside the support 343, and a plurality of through holes are disposed on the support 343, and the buffer film 344 covers the through holes entirely.
Specifically, the buffer 340 is a hollow cylinder structure, and the through hole is disposed on a side wall of the cylinder structure; the buffer film 344 is sleeved on the side wall of the column structure to cover the through hole.
Specifically, the buffer film 344 is sleeved on the support 343, the diameter of the buffer film 344 in the original state is slightly smaller than that of the support 343, so that the buffer film 344 and the support 343 are in interference fit, and the tightness is improved.
Specifically, the bracket 343 includes two end walls 345 disposed at opposite intervals, and a plurality of support rods 3431 for connecting the two end walls 345; one end of the supporting rod 3431 is connected to the outer circumference of one of the end walls 345, and the other end is connected to the outer circumference of the other end wall 345; the through holes are formed between the two support rods 3431, the support rods 3431 are uniformly arranged in plurality on the surface of the cylinder, and the respective support rods 3431 are parallel to each other.
Specifically, in some possible embodiments, the supporting rods 3431 may be configured such that one end is connected to the outer periphery of one of the end walls 345, and the other end is connected to the outer periphery of the other end wall 345, and any two supporting rods 3431 are intersected or not intersected with each other, so as to be arranged irregularly, thereby ensuring that a through hole is left on the surface of the cylinder.
Specifically, in some possible embodiments, two ends of the support 343 are closed, an air port is disposed at the center of the two ends, at this time, the air tube is configured to have one end in a horn shape, the other end is in a conventional shape, the conventional end of the air tube passes through the air port from the inside of the support 343 to be connected with the microfluidic device 320 or the peristaltic pump 330, and when the air tube extends to a certain length, one end of the horn is clamped at the air port position, and the horn end and the air port can be fixedly connected and sealed in an adhesive manner.
Specifically, in some possible embodiments, the two ends of the support 343 are opened, at this time, the air tube is set to have a horn-shaped end, the other end is in a conventional shape, the conventional end of the air tube is connected with the microfluidic device 320 or the peristaltic pump 330, one end of the horn-shaped end is connected with the two ends of the support 343, the shape and the size of the end with a large diameter of the horn-shaped end are matched with the shape and the size of the two ends of the support 343, the air tube at the horn-shaped end is sleeved or inserted into the one end of the support 343, and the tightness between the air tube and the support 343 can be ensured by using an adhesive mode.
Specifically, the buffer 340 is disposed below the microfluidic device 320, the first air tube 341 of the buffer 340 is connected to the liquid outlet end of the microfluidic device 320, and the second air tube 342 of the buffer 340 extends from the buffer 340 toward the peristaltic pump 330, and passes through the peristaltic pump 330 to be in communication with the atmosphere.
In particular, peristaltic pump 330 has the advantage of: clean and pollution-free; the repeated precision is high, the stability performance is strong, the flow is convenient to adjust, and the pumped volume is constant for each revolution of the peristaltic pump 330, so that the highest direct current of the discharged liquid reproduction precision can reach about 5 percent and the stepping energy can be within 2 percent; peristaltic pump 330 can run for a long time without water, and can also convey air, gas-liquid-solid three-phase mixture; the peristaltic pump 330 can self-suction without pumping and emptying, because the pump wheel can compress the pump pipe due to the principle of the peristaltic pump 330, and the liquid can be sucked by the negative pressure generated at the inlet end of the pump pipe in the displacement of the pump wheel, so that the peristaltic pump 330 can self-suction without pumping and emptying; has good sealing performance and has the functions of stopping and unidirectional conduction. The peristaltic pump 330 has the pump wheel to compress the pump pipe all the time in the working process, so that the liquid only flows towards the direction of the movement of the pump wheel and does not flow backwards to form a one-way conduction function, when the pump stops working, the liquid does not flow backwards and siphons to stop, the peristaltic pump 330 does not need any mechanical sealing piece, and under the condition that external force is applied to blood, if the external force is too large, the problems of difficult filtration and easy hardening exist, and therefore low-speed extraction is needed, and the peristaltic pump 330 becomes the preference of the device.
Specifically, because the peristaltic pump 330 operates in a pulsed manner, the peristaltic pump 330 is required to alternately release the rotating wheel during pumping, and thus a liquid is sucked back at the moment of release, resulting in a sudden decrease in the discharged liquid, which may cause the peristaltic pump 330 to generate a pulsed flow during operation.
Specifically, a buffer 340 is disposed between the microfluidic device 320 and the peristaltic pump 330 to solve the problem of pulse flow of the peristaltic pump 330, since the buffer 340 is sealed integrally and hollow, the second air tube 342 passes through the peristaltic pump 330 to communicate with the atmosphere, the peristaltic pump 330 works to continuously pump the air in the buffer 340 out of the atmosphere, the buffer membrane 344 is covered at the position of the through hole on the support 343 to shrink inwards, so that the buffer membrane 344 stores a certain elastic potential energy, and negative pressure is formed in the buffer 340, so that filtered liquid in the microfluidic device 320 connected with the first air tube 341 is pumped out, and due to the buffer membrane 344, the pressure in the buffer 340 is continuously adjusted by shrinking and expanding when pulse flow is generated, thereby counteracting the pulse flow and realizing the buffering effect.
Specifically, in the process of absorbing, printing, enriching and dyeing the nucleated cells by the device, multiple extractions are required, so that the problem of liquid backflow can be inevitably generated, and a one-way valve 3421 is required to be arranged between the peristaltic pump 330 and the microfluidic device 200 to solve the backflow problem.
Specifically, when the peristaltic pump 330 is operated, the pump head rotates to continuously pump air to the outside, the buffer membrane 344 is contracted inwards, and at this time, the buffer 340 is in a negative pressure state, and as the buffer 340 is in a sealed state, the buffer 340 generates a suction force to the first air tube 341 along with the increasing of the negative pressure, so that the liquid, the non-nucleated cells, and the like in the blood, which cannot pass through the microfluidic device 320, are sucked into the first air tube 341, flow through the buffer 340 and the second air tube 342, and finally are pumped by the peristaltic pump 330.
Specifically, when the peristaltic pump 330 is operated, a negative pressure is continuously generated in the buffer 340, and then a continuous suction force is generated to the first air tube 341, and when the peristaltic pump 330 is suddenly stopped, the buffer 340 still maintains a negative pressure state, but the blood in the second air tube 342 flows back to the buffer 340 due to the fact that the negative pressure is not increased.
Preferably, a one-way valve 3421 is provided on the second air tube 342 between the peristaltic pump 330 and the buffer 340, such that blood can only flow from the buffer 340 in the direction of the peristaltic pump 330 and cannot flow back from the peristaltic pump 330 to the buffer 340.
Specifically, the check valve 3111 includes a valve body, and a valve flap disposed inside the valve body, where the valve flap is connected inside the valve body by a torsion spring, and the valve flap is unidirectionally opened from the microfluidic device 320 toward the buffer bottle 310, and the torsion spring is used to maintain a state where the valve flap seals the valve body.
Specifically, when the peristaltic pump does not work, the valve clack is abutted to the inlet end, the valve clack can only rotate around the torsion spring in the direction of the buffer bottle from the direction of the microfluidic device 320, when the peristaltic pump 330 starts to work, negative pressure is generated in the buffer bottle, the valve clack of the one-way valve 3421 rotates around the torsion spring in the direction of the buffer bottle, the water inlet of the one-way valve 3421 is opened, and then liquid of the microfluidic device 320 can be extracted, and because the valve clack can only rotate around the torsion spring in the direction of the buffer bottle from the direction of the microfluidic device 320 in one direction, the occurrence of liquid backflow generated when the device performs multiple extraction is prevented.
Example two
The embodiment of the utility model also provides a cell enrichment and staining integrated device, which comprises the cell collecting device.
Specifically, the cell collecting device comprises a microfluidic device and a buffer device, the cell enrichment and dyeing integrated equipment can send a blood sample of a patient into the microfluidic device to complete filtration of the blood sample, and reagents required for filtering and enriching cells can be added into the microfluidic device, so that cells to be detected are obtained, and the buffer device is used for reducing interference of external factors on experiments.
The foregoing description is only a preferred embodiment of the present utility model, and the present utility model is not limited to the above-mentioned embodiment, but is not limited to the above-mentioned embodiment, and any simple modification, equivalent change and modification made by the technical matter of the present utility model can be further combined or replaced by equivalent embodiments within the scope of the technical proposal of the present utility model without departing from the scope of the technical proposal of the present utility model.
Claims (10)
1. A cell collection device comprising a microfluidic device (320) and a buffer device, the buffer device comprising:
-a peristaltic pump (330) in communication with the microfluidic device (320) for pumping liquid from the microfluidic device (320);
the buffer (340) is arranged between the microfluidic device (320) and the peristaltic pump (330), a buffer cavity is formed in the interior of the buffer cavity, the buffer cavity is respectively communicated with the microfluidic device (320) and the peristaltic pump (330), and at least part of the cavity wall of the buffer cavity is made of a material capable of undergoing elastic deformation.
2. A cell collection device according to claim 1, wherein the buffer (340) comprises a hollow interior support (343) and an elastically deformable buffer membrane (344); the support (343) is provided with a plurality of through holes, the buffer film (344) is attached to the support (343) and at least covers the through holes; the cushioning membrane (344) and the support (343) enclose the cushioning chamber.
3. A cell collection device according to claim 2, wherein the support (343) is a hollow cylindrical structure, the through-holes being provided in a side wall of the cylindrical structure; the buffer film (344) is sleeved on the side wall of the column structure so as to cover the through hole.
4. A cell collecting device according to claim 3, wherein the bracket (343) comprises two end walls (345) arranged at opposite intervals, and a number of support rods (3431) for connecting the two end walls (345); one end of the supporting rod (3431) is connected to the periphery of one end wall (345), and the other end is connected to the periphery of the other end wall (345); the through hole is formed between the two support rods (3431).
5. A cell collecting device according to claim 4, wherein the support bar (3431) is arranged extending in a direction parallel to the axis of the cylinder structure.
6. A cell collection device according to claim 4, wherein the two end walls (345) are each provided with an air port, and wherein the air ports are sealingly connected to air tubes, one of which is in communication with the microfluidic device (320) and the other of which is in communication with the peristaltic pump.
7. A cell collection device according to any one of claims 1-6, wherein a buffer (340) is arranged below the liquid outlet end of the microfluidic device (320) and is in communication with the liquid outlet end of the microfluidic device (320) via a first gas tube (341).
8. A cell collection device according to any one of claims 1-6, wherein the buffer (340) is in communication with the peristaltic pump (330) via a second air tube (342), the second air tube (342) being in communication with the atmosphere through the peristaltic pump (330).
9. A cell collection device according to any one of claims 1-6, wherein a one-way valve (3421) is arranged between the microfluidic device (320) and the peristaltic pump (330) for unidirectional communication from the microfluidic device (320) to the peristaltic pump (330).
10. A cell enrichment staining apparatus comprising a cell collection device according to any of claims 1 to 9.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321920761.XU CN220618878U (en) | 2023-07-20 | 2023-07-20 | Cell collection device and integrative equipment of cell enrichment dyeing |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321920761.XU CN220618878U (en) | 2023-07-20 | 2023-07-20 | Cell collection device and integrative equipment of cell enrichment dyeing |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN220618878U true CN220618878U (en) | 2024-03-19 |
Family
ID=90219421
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202321920761.XU Active CN220618878U (en) | 2023-07-20 | 2023-07-20 | Cell collection device and integrative equipment of cell enrichment dyeing |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN220618878U (en) |
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2023
- 2023-07-20 CN CN202321920761.XU patent/CN220618878U/en active Active
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