A flow cytometer sort display simulation device

Abstract

The utility model relates to experimental simulation equipment field, specifically disclose a flow cytometer sorting display simulation equipment, including the flow chamber that is provided with the guide liquid input pipe and sample liquid input pipe, laser detection unit, the outflow transparent pipe is connected in the flow chamber, the circulating control liquid pump is connected in the outflow transparent pipe, and the sorting receiving pipe and the corresponding jet generator of sorting receiving pipe are set up on the outflow transparent pipe, and the part of sorting receiving pipe connection outflow transparent pipe forms the pipe mouth, and the end part that is away from the pipe mouth is provided with the open-close valve in sorting receiving pipe, the circulating control liquid pump is connected the guide liquid input pipe through the back pipe, the circulating control liquid pump is used for carrying out the pumping of analog liquid of different rate, the jet generator is used for producing liquid jet and pushes the sample in sample focus flow to the pipe mouth, and the open-close valve of jet generator corresponds and opens, and the sample is exported from sorting receiving pipe. Realize to flow cytometer sorting process carry out more close actual working principle's simulation, improve the teaching quality.

Description

Technical Field

[0001] This utility model relates to the field of flow cytometry cell sorting experiment simulation technology, specifically to a flow cytometer sorting demonstration simulation device. Background Technology

[0002] Currently, the design of teaching methods for flow cytometry sorting focuses more on conducting as many experimental classes as possible, giving students more opportunities to use the relevant testing instruments for flow cytometry sorting. At the same time, it optimizes teaching methods and uses pictures, videos and other methods to make classroom theoretical teaching more vivid and engaging.

[0003] Because the operation of flow cytometers for sorting and testing is complex, it is difficult for students to meet the requirements of operating the instruments. Consequently, they struggle to grasp the specific working principles of flow cytometry sorting and understand its operation. Furthermore, since cells are microscopic organisms, the sorting process cannot be directly observed with the naked eye. Current teaching methods often simply simulate the detection and sorting principles of flow cytometry by having spheres roll through a tube and then sorting them using the test results. This approach does not fully simulate the specific working principles of flow cytometry sorting and is therefore somewhat unreasonable. This results in students lacking a hands-on understanding, making the teaching of this technology increasingly difficult. Utility Model Content

[0004] The purpose of this invention is to provide a flow cytometer sorting demonstration simulation device to solve the technical problem that the lack of existing devices that effectively simulate the working principle of flow cytometer sorting leads to poor teaching quality in this area.

[0005] To solve the above-mentioned technical problems, this utility model specifically provides the following technical solution: A flow cytometer sorting demonstration simulation device includes a flow chamber with a guide liquid input tube and a sample liquid input tube, a laser detection unit, an outflow transparent tube connected to the output end at the bottom of the flow chamber, a circulating control pump at the bottom output end of the outflow transparent tube, at least one sorting receiving tube and a jet generator corresponding to each sorting receiving tube on the outflow transparent tube, the portion of the sorting receiving tube connected to the outflow transparent tube forming an opening, and an opening / closing valve at the end of the sorting receiving tube away from the opening; the circulating control pump is connected to the guide liquid input tube through a return pipe; and the laser detection unit is located on one side of the outflow transparent tube. The laser detection unit includes a laser source disposed on one side of the outflow transparent tube and a light guide tube disposed on the other side of the outflow transparent tube to receive the light signal. The light guide tube is composed of multiple optical fibers. The end of each optical fiber transmits the light signal to the photoresistor of a photosensitive sensor module through a filter. The photosensitive sensor module outputs a signal to the controller, and the controller generates the control signal for the jet generator. The circulating liquid control pump is used to pump simulated liquid at different rates so that the sample liquid input tube forms a sample focusing flow in the outflow transparent tube. The guide liquid input tube, flow chamber, circulating liquid control pump and return tube form a circulation loop for the simulated liquid. The jet generator is used to generate a liquid jet to push the sample in the focused sample stream to the nozzle. The opening and closing valve corresponding to the jet generator is opened, and the sample is output from the sorting and receiving tube.

[0006] In a preferred embodiment of the present invention, the flow chamber includes a cylindrical tube and a funnel tube connected to the bottom of the cylindrical tube. The bottom output end of the funnel tube is connected to the outflow transparent tube, and the sample liquid input tube is arranged in the middle of the top of the cylindrical tube along the axial direction of the cylindrical tube.

[0007] As a preferred embodiment of this utility model, the jet generator includes a pump body, the output end of the pump body is connected to a jet port through a pipe, the jet port is connected to the transparent outflow tube and communicates with the interior of the transparent outflow tube, the input end of the pump body is connected to the output end of the opening and closing valve through a pipe, and a pressure equalization valve is provided on the pipe between the input end of the pump body and the output end of the opening and closing valve.

[0008] As a preferred embodiment of this utility model, it also includes an outer shell, in which the flow cytometer sorting and display simulation device is disposed. A transparent window is provided on the front surface of the outer shell, and a vertical guide rail is provided in the middle of the transparent window. A magnifying glass plate is provided on the guide rail, and the magnifying glass plate can move along the length of the guide rail.

[0009] Compared with the prior art, this utility model has the following advantages: This invention simulates the conditions for flow cytometry sample pooling by utilizing the flow chambers of the guide liquid inlet tube and the sample liquid inlet tube. It restricts the flow of sample liquid using a transparent outlet tube, allowing the sample in the guide liquid inlet tube and the sample liquid inlet tube to flow in layers. The process of sample pooling is simulated, and cell sorting is controlled using sorting and receiving tubes and jet generators corresponding to each sorting and receiving tube. This allows for a device simulation of the flow cytometry cell sorting process that closely matches its working principle. Attached Figure Description

[0010] To more clearly illustrate the embodiments of this utility model or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings in the following description are merely exemplary, and those skilled in the art can derive other embodiments based on the provided drawings without creative effort.

[0011] Figure 1 This is a schematic diagram of the overall structure of an embodiment of the present utility model; Figure 2 This is a schematic diagram of the structure of the transparent outflow tube with a hollow tube inside, according to an embodiment of the present invention. Figure 3 This is a schematic diagram of the overall structure of the guide rail and magnifying glass plate in an embodiment of this utility model.

[0012] The labels in the diagram represent the following: 1-Guide liquid inlet tube; 2-Sample liquid inlet tube; 3-Flow chamber; 4-Laser detection unit; 5-Outlet transparent tube; 6-Circulating liquid control pump; 7-Sorting receiving tube; 8-Jet generator; 9-Pipe port; 10-Opening and closing valve; 11-Return tube; 12-Outer shell; 13-Transparent window; 14-Guide rail; 15-Magnifying glass plate; 16-Perforated tube; 41-Laser source; 42-Light guide tube; 31-Cylindrical tube; 32-Functional tube; 81-Pump body; 82-Injection port; 83-Pressure equalizing valve. Detailed Implementation

[0013] 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.

[0014] like Figure 1 and Figure 2As shown, this utility model provides a flow cytometer sorting and demonstration simulation device. Specifically, it is structured based on the working principle of an experimental flow cytometer, including a flow chamber 3 with a guide fluid inlet tube 1 and a sample fluid inlet tube 2. The structure of the flow chamber 3 is the same as that of a typical flow cytometer flow chamber. Existing flow chambers 3 consist of a sample tube, a sheath fluid tube, and a nozzle, and are commonly made of transparent and stable materials such as optical glass and quartz. The sample tube stores the sample, and a single-cell suspension is ejected from the sample tube under the pressure of the fluid flow. The sheath fluid flows from the sheath fluid tube to the nozzle, surrounds the sample, and is then ejected from the nozzle. Due to the effect of the sheath fluid, the cells being detected are confined to the axis of the fluid flow. Of course, a laser detection unit 4 is also required.

[0015] In this embodiment, the purpose is to simulate flow cytometry. Therefore, instead of using a stable flow environment constructed with sheath fluid, liquid water is used. Of course, in order to make the experimental simulation as similar as possible in principle, a combination of silicone oil and water can be used. Water can be used as the sheath fluid, and silicone oil can be used as the sample solution mixed with the sample. In this experimental method, the sample solution can be a mixture of some plastic or silica gel beads and silicone oil.

[0016] In the technical implementation of this simulation device, if two liquids are immiscible (such as oil and water), surface tension will maintain a clear interface, forming a distinct boundary. In laminar flow (low Reynolds number), streamlines are stable, and the interface is even clearer. In turbulent flow (high Reynolds number), vigorous mixing will disrupt the boundary. The injection rate of silicone oil needs to be matched with the injection rate of water. If the rate is too high, a jet may form and induce turbulence; if the rate is too low, it will be entrained and mixed by the first liquid. If the two liquids have different densities, buoyancy or sedimentation effects will cause deviation from the axis (such as heavy liquid sinking or light liquid floating). Density matching can avoid this problem. In laminar flow, the center velocity is high, and inertial force dominates, making it easier for the second liquid to maintain its axial position. In turbulent flow, random vortices will disrupt the channel. In vertical pipes, i.e., the outflow transparent pipe 5 in this embodiment, buoyancy has a significant impact. In horizontal pipes, density differences may lead to lateral stratification, which needs to be offset by flow rate adjustment.

[0017] Therefore, under laminar flow conditions, with matched density and viscosity, immiscibility or low diffusivity, moderate surface tension, and coordinated flow rate, silicone oil can form a stable core flow with a clear interface. This embodiment is intended to provide a simulated cell sorting device; the specific liquids forming the "sheath fluid" and sample solution can be selected and set according to actual conditions.

[0018] Of course, in a specific implementation, a perforated tube 16 can also be set in the outflow transparent tube. The top of the perforated tube 16 is connected to the sample liquid input tube 2 located at the bottom of the flow chamber 3, and the perforation diameter of the perforated tube 16 is larger than the small ball in the sample liquid.

[0019] To achieve sample focusing flow, i.e., the sample solution of silica gel microspheres and silicone oil enters the flow chamber through the sample solution input tube 2, and then enters the outflow transparent tube 5 connected to the output end at the bottom of the flow chamber 3, a circulating liquid control pump 6 is required to allow the sample solution to enter the sample solution input tube 2 in a jet manner and to be installed at the bottom output end of the outflow transparent tube 5. The circulating liquid control pump 6 is specifically a 12V DC brushless micro water pump. The purpose of the circulating liquid control pump 6 is to circulate the water input from the guide liquid input tube 1. The circulating liquid control pump 6 is connected to the guide liquid input tube 1 through the return tube 11.

[0020] The control circuit of the circulating liquid control pump 6, such as a DC motor speed controller of model CCMHCN with a speed range of 0-10000 rpm, a speed change rate of 0-99%, a speed stability accuracy of 0-99%, and a voltage of 36V, can be used to adjust the speed of the circulating liquid control pump 6, thereby controlling the flow rate of water in the transparent tube 5. In this embodiment, since the water circulation is constructed by the circulating liquid control pump 6, the circulating liquid control pump 6 can be used to pump simulated liquid at different rates, so that the sample liquid input pipe 2 forms a sample focusing flow in the transparent tube 5. The guide liquid input pipe 1, the flow chamber 3, the circulating liquid control pump 6, and the return pipe 11 form a simulated liquid circulation loop, reducing the water flow speed to zero. The state of the liquid in the transparent tube 5 is filled, which is a relatively static state, thereby achieving control over the state of the liquid in the transparent tube 5.

[0021] In the above detection method, the working principle of the laser detection unit 4 is as follows: The system uses silicone microspheres, which can be transparent microspheres with a core inside, to replace white blood cells. Five different fluorescent dyes, namely purple, green, yellow, red, and white, such as granular or planar, are used to mark the surface or inside of the microspheres, so that the microspheres appear as different forms of white blood cells, and can be distinguished by different combinations of fluorescence.

[0022] Specifically, the sample liquid flows through the outflow transparent tube and passes through the focal point of the laser beam emitted by the laser detection unit 4. Fluorescently labeled cells are stimulated to emit fluorescence, while unlabeled cells mainly produce scattered light. The light signal reception and separation of the laser detection unit 4 generally includes: Forward scattering (FSC) detection: A photodiode located directly in front of the laser path detects scattered light at small angles (1-10°) to reflect cell size; Side scattering (SSC) detection: A photomultiplier tube (PMT) at a 90° angle is used to detect the complexity or granularity of cells. Fluorescence detection: Multiple PMTs are used to collect fluorescence signals at different wavelengths; And dichroic mirrors: reflect light below a specific wavelength and transmit longer wavelengths, guiding the light path to the corresponding detector and bandpass filters: allow only the target fluorescence wavelength (such as 530 / 30nm for FITC) to pass through, reducing background noise.

[0023] Since this embodiment simulates sorting, the laser detection unit 4 is placed on one side of the outflow transparent tube 5. The laser detection unit 4 includes a laser source 41 placed on one side of the outflow transparent tube 5 and a light guide tube 42 placed on the other side of the outflow transparent tube 5 to receive the light signal. The light guide tube 42 is composed of multiple optical fibers. The end of each optical fiber transmits the light signal to the photoresistor of a photosensitive sensor module through a filter. The photosensitive sensor module outputs a signal to the controller. The controller generates a control signal for the jet generator 8 and obtains the fixed spectral signal of the small balls using five different fluorescent dyes (purple, green, yellow, red, and white). This also includes the spectral signal that is set to be sorted. The obtained corresponding spectral signal is converted into the control signal of the jet generator 8 and the opening and closing valve 10.

[0024] Therefore, in the cell sorting process, at least one sorting receiving tube 7 and a jet generator 8 corresponding to each sorting receiving tube 7 are provided on the outflow transparent tube 5. The portion of the sorting receiving tube 7 connected to the outflow transparent tube 5 forms an opening 9, and an opening / closing valve 10 is provided at the end of the sorting receiving tube 7 away from the opening 9. The jet generator 8 is used to generate a liquid jet to push the sample in the focused sample stream to the opening 9. The opening / closing valve 10 corresponding to the jet generator 8 opens, and the sample (i.e., the small ball) is output from the sorting receiving tube 7.

[0025] The sorting and receiving tube 7 and the jet generator 8 are located on the outflow transparent tube 5 below the laser detection unit 4. The jet generator 8 includes a pump body 81, specifically a pulse water pump or a peristaltic pump. The output end of the pump body 81 is connected to a jet port 82 through a pipe. The jet port 82 is connected to the outflow transparent tube 5 and communicates with the inside of the outflow transparent tube 5. The input end of the pump body 81 is connected to the output end of the on / off valve 10 through a pipe. Its function is to propel the small balls in the sample liquid toward the tube opening 9, that is, to emit a water jet into the outflow transparent tube 5.

[0026] Of course, in this embodiment, the output end of the sorting and receiving pipe 7 and the input end of the jet generator 8 can also be connected by a pipe to form a loop.

[0027] A pressure equalization valve 83 is installed on the pipeline between the input end of the pump body 81 and the output end of the opening and closing valve 10. Specifically, it is an electric butterfly valve that opens and closes the sorting and receiving pipe 7 at the rear end of the opening and closing valve 10. That is, two valves are installed on the sorting and receiving pipe 7 for opening and closing the sorting and receiving pipe 7. The opening and closing valve 10 is also an electric butterfly valve.

[0028] Its specific working principle is as follows: after the jet generator 8 receives the control signal generated by the controller, it simultaneously opens the opening and closing valve 10 and the equalizing valve 83. Then, after the ball is introduced into the sorting and receiving pipe 7 by negative pressure and passes through the opening and closing valve 10, the opening and closing valve 10 and the jet generator 8 are closed. At this time, the equalizing valve 83 is in the normally open state.

[0029] The flow chamber 3 includes a cylindrical tube 31 and a funnel tube 32 connected to the bottom of the cylindrical tube 31. The bottom output end of the funnel tube 32 is connected to the outflow transparent tube 5. The sample liquid input tube 2 is arranged in the middle of the top of the cylindrical tube 31 along the axial direction of the cylindrical tube 31.

[0030] Furthermore, such as Figure 3 As shown, this embodiment also requires a structure or device to package the entire simulation device. For this purpose, it also includes an outer shell 12. The flow cytometer sorting and display simulation device is set inside the outer shell 12. A transparent window 13 is provided on the front surface of the outer shell 12. A guide rail 14 along the vertical direction is provided in the middle of the transparent window 13. A magnifying glass plate 15 is provided on the guide rail 14. The magnifying glass plate 15 can move along the length direction of the guide rail 14. The purpose is to allow the part that needs to be magnified to be observed by operating the movement of the magnifying glass plate 15 on the guide rail 14.

[0031] The magnifying glass plate 15 is specifically a fixed frame in which a magnifying glass is disposed. The fixed frame is a planar frame structure. The outer side of the magnifying glass plate 15 cooperates with the guide rail 14 and can slide on the guide rail 14. The specific structure is not specifically designed in this embodiment.

[0032] Furthermore, in this embodiment, silicone oil is used as the sample solution and water as the "sheath fluid." Naturally, after circulation by the circulating control pump 6, the two are mixed to a certain extent. Therefore, this embodiment intentionally includes a separation device. The separation method used in the separation device can be centrifugation or vacuum filtration. Further details will not be elaborated in this embodiment.

[0033] The above embodiments are merely exemplary embodiments of this application and are not intended to limit this application. The scope of protection of this application is defined by the claims. Those skilled in the art can make various modifications or equivalent substitutions to this application within its substance and scope of protection, and such modifications or equivalent substitutions should also be considered to fall within the scope of protection of this application.

Claims

1. A flow cytometer sorting and demonstration simulation device, comprising a flow chamber (3) with a guide liquid inlet tube (1) and a sample liquid inlet tube (2), and a laser detection unit (4), characterized in that, An outflow transparent tube (5) is connected to the output end located at the bottom of the flow chamber (3). A circulating liquid control pump (6) is provided at the bottom output end of the outflow transparent tube (5). At least one sorting receiving tube (7) and a jet generator (8) corresponding to the sorting receiving tube (7) are provided on the outflow transparent tube (5). The part of the sorting receiving tube (7) connected to the outflow transparent tube (5) forms a pipe opening (9). An opening and closing valve (10) is provided at the end of the sorting receiving tube (7) away from the pipe opening (9). The circulating liquid control pump (6) is connected to the guide liquid input pipe (1) through a return pipe (11). The laser detection unit (4) is located on one side of the outflow transparent tube (5). The laser detection unit (4) includes a laser source (41) disposed on one side of the outflow transparent tube (5) and a light guide tube (42) disposed on the other side of the outflow transparent tube (5) to receive light signals. The light guide tube (42) is composed of multiple optical fibers. The end of each optical fiber transmits the light signal to the photoresistor of a photosensitive sensor module through a filter. The photosensitive sensor module outputs a signal to the controller, and the controller forms the control signal of the jet generator (8). The circulating liquid pump (6) is used to pump simulated liquid at different rates so that the sample liquid input pipe (2) forms a sample focusing flow in the outflow transparent pipe (5). The guide liquid input pipe (1), flow chamber (3), circulating liquid pump (6) and return pipe (11) form a circulation loop of the simulated liquid. The jet generator (8) is used to generate a liquid jet to push the sample in the sample focusing stream to the port (9). The opening and closing valve (10) corresponding to the jet generator (8) is opened, and the sample is output from the sorting and receiving tube (7).

2. The flow cytometer sorting and display simulation device according to claim 1, characterized in that, The flow chamber (3) includes a cylindrical tube (31) and a funnel tube (32) connected to the bottom of the cylindrical tube (31). The bottom output end of the funnel tube (32) is connected to the outflow transparent tube (5). The sample liquid input tube (2) is arranged in the middle of the top of the cylindrical tube (31) along the axial direction of the cylindrical tube (31).

3. The flow cytometer sorting and display simulation device according to claim 1, characterized in that, The jet generator (8) includes a pump body (81), the output end of which is connected to a jet port (82) via a pipe. The jet port (82) is connected to the transparent outflow tube (5) and communicates with the interior of the transparent outflow tube (5). The input end of the pump body (81) is connected to the output end of the opening and closing valve (10) via a pipe. A pressure equalization valve (83) is installed on the pipe between the input end of the pump body (81) and the output end of the opening and closing valve (10).

4. The flow cytometry sorting and display simulation device according to claim 1, characterized in that, It also includes an outer shell (12), in which the flow cytometer sorting and display simulation device is installed. A transparent window (13) is provided on the front surface of the outer shell (12), and a vertical guide rail (14) is provided in the middle of the transparent window (13). A magnifying glass plate (15) is provided on the guide rail (14), and the magnifying glass plate (15) can move along the length direction of the guide rail (14).

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