Dialysis instrument membrane aperture testing device

Abstract

The utility model discloses a membrane aperture testing device for a dialysis instrument, which is applied to the field of membrane aperture detection and comprises a storage part and a detection part, the main pipeline is used for purified water or simulated liquid to flow; one end of the branch pipeline is mounted on the shell and communicated with the dialysate chamber, and the other end of the branch pipeline is arranged in the storage part; the first pump is connected to the main pipeline and used for controlling the blood chamber inlet flow of the dialysis appliance; the second pump is connected to the branch pipeline and is used for controlling the ultrafiltration flow so as to drive the purified water or the simulated liquid to penetrate through the side wall of the hollow fiber membrane; the detection assembly is used for irradiating the simulation liquid in the storage part and collecting light scattering intensity of the simulation liquid in an initial state and a complete filling state; and the controller is used for calculating the pore size distribution of the hollow fiber membrane according to the light scattering intensity of the simulated liquid in the initial state and the complete filling state. The membrane aperture testing device for the dialysis device is convenient to operate, high in detection precision, good in repeatability in the testing process, small in error, simple in structure and low in cost.

Description

Technical Field

[0001] The utility model relates to the field of membrane pore size detection, in particular to a membrane pore size testing device for a dialysis appliance. Background Art

[0002] Hemodialysis is currently the main method for treating uremia. A dialyzer mainly consists of a hollow fiber membrane, and the pore size and its distribution of the hollow fiber membrane affect the dialysis effect.

[0003] There are many testing devices and methods for the pore size and its distribution of the hollow fiber membrane. For the hollow fiber membrane for hemodialysis, its pore channels are curved and the pore size is about below 10 nm. In the related art, the scanning electron microscope is used for testing. Since the scanning electron microscope ignores the influence of the non-through holes and tortuosity inside the membrane filaments of the hollow fiber membrane, this method has large errors. When using a gas adsorption instrument, it is generally used for testing the pore size distribution of mesoporous materials (50 nm). In the micropore range, when the pore size is less than 10 nm, the detection results of the gas adsorption instrument are inaccurate. In the related art, there is also a method of using the rejection rate experiment of dextrans with different molecular weights to test the pore size. However, since dextrans with different molecular weights are not regular spherical structures, the asymmetry of dextrans easily leads to an actual size larger than the equivalent Stokes diameter, and the existence of this difference will directly affect the measurement and analysis of the pore size, resulting in large errors.

[0004] Therefore, how to effectively improve the accuracy of testing the membrane pore size of the dialysis appliance is a technical problem that those skilled in the art need to solve currently. Content of the Utility Model

[0005] The purpose of the utility model is to provide a membrane pore size testing device for a dialysis appliance, which is used to improve the testing accuracy, reduce errors and simplify the operation.

[0006] To achieve the above purpose, the utility model provides the following technical solutions:

[0007] A membrane pore size testing device for a dialysis appliance, the dialysis appliance includes a housing and a hollow fiber membrane located inside the housing. The inner cavity of the hollow fiber membrane forms a blood chamber, and a dialysis fluid chamber is formed between the hollow fiber membrane and the housing. The device includes:

[0008] A storage component for containing purified water or a simulation liquid;

[0009] A main pipeline for the purified water or the simulation liquid to flow. Both ends of the main pipeline are placed inside the storage component. The blood chamber inlet and the blood chamber outlet of the blood chamber are connected to the main pipeline. The purified water or the simulation liquid can flow through the inner cavity of the hollow fiber membrane, and after partially passing through the membrane pores of the hollow fiber membrane, it enters the dialysis fluid chamber, and part of the silicon spheres in the simulation liquid fill into the membrane pores;

[0010] A branch pipeline, one end of which is installed on the housing and communicated with the dialysate chamber, and the other end is placed inside the storage component;

[0011] A first pump, connected to the main pipeline, for controlling the blood chamber inlet flow rate of the dialysis appliance;

[0012] A second pump, connected to the branch pipeline, for controlling the ultrafiltration flow rate to drive the purified water or the simulated liquid to permeate through the side wall of the hollow fiber membrane;

[0013] A detection component, for irradiating the simulated liquid in the storage component and collecting the light scattering intensities of the simulated liquid in the initial state and the fully filled state;

[0014] A controller, the controller is connected to both the first pump and the second pump, for controlling the flow rates of the first pump and the second pump; the controller is also connected to the detection component, and calculates the pore size distribution of the hollow fiber membrane according to the light scattering intensities of the simulated liquid in the initial state and the fully filled state.

[0015] On the other hand, it further includes:

[0016] A pressure sensor, for detecting the pressure difference between the blood chamber and the dialysate chamber;

[0017] The controller is connected to the pressure sensor, and the controller is further used for judging whether the simulated liquid in the storage component is in the fully filled state according to the pressure difference.

[0018] On the other hand, the branch pipeline is connected to the dialysate chamber inlet of the dialysate chamber, and the pressure sensor is installed between the dialysate chamber inlet and the blood chamber outlet.

[0019] On the other hand, it further includes a simulated liquid storage barrel, the simulated liquid storage barrel is connected to the storage component through a liquid injection pipeline, and the simulated liquid storage barrel is used for storing the simulated liquid and adding the simulated liquid into the storage component.

[0020] On the other hand, a simulated liquid valve is provided on the liquid injection pipeline, the simulated liquid valve is connected to the controller, and the controller is further used for controlling the opening and closing of the simulated liquid valve to control the storage liquid in the simulated liquid storage barrel to flow into the storage component.

[0021] On the other hand, the height of the simulated liquid storage barrel is higher than the height of the storage component, and a drain port is provided at the bottom side of the storage component, and the drain port can be opened or closed.

[0022] On the other hand, both the first pump and the second pump are peristaltic pumps.

[0023] On the other hand, the dialysis device is a dialyzer or a hemofiltration device.

[0024] On the other hand, the detection component includes:

[0025] A light scattering component for irradiating the simulated liquid in the storage component;

[0026] A light sensor for collecting the light scattering intensity of the simulated liquid in real time. The light sensor is connected to the controller and sends the light scattering intensity to the controller.

[0027] On the other hand, the simulated liquid is a silica sol simulated liquid, and the simulated liquid contains a number of silicon spheres with a diameter of 1 - 15 nm.

[0028] The dialysis device membrane pore size testing device provided by the present utility model can transport the purified water or the simulated liquid through the setting of the main pipeline, and can collect a part of the liquid after the successful transmembrane transport of the simulated liquid through the setting of the branch pipeline; at the same time, through the setting of the first pump and the second pump, the first pump can provide power for the simulated liquid to enter the blood chamber, and the second pump provides power for the transmembrane transport of the simulated liquid in the hollow fiber membrane. When the simulated liquid undergoes transmembrane transport in the hollow fiber membrane, since a certain amount of the simulated liquid is adsorbed inside the membrane pores of the hollow fiber membrane, the silicon spheres in the simulated liquid will fill the membrane pores of the hollow fiber membrane. By obtaining the light scattering intensities of the simulated liquid in the initial state and the fully filled state, the difference in the number of silicon spheres of different sizes between the initial state and the fully filled state of the simulated liquid can be calculated, and then the pore size distribution of the hollow fiber membrane can be obtained; this dialysis device membrane pore size testing device is convenient to operate, has high detection accuracy, good repeatability in the testing process, small error, simple structure, and low cost. Description of the Drawings

[0029] In order to more clearly illustrate the technical solutions in the embodiments of the present utility model or the prior art, the following will briefly introduce the drawings required for use in the description of the embodiments or the prior art. Obviously, the following drawings are only some embodiments of the present utility model. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0030] Figure 1 It is a schematic structural diagram of a specific embodiment of the dialysis device membrane pore size testing device provided by the present utility model;

[0031] Figure 2 For Figure 1 A cross-sectional view of the dialysis device in the dialysis device membrane pore size testing device shown;

[0032] Figure 3 This is a flowchart of the method for testing the membrane pore size of a dialysis device provided by the present utility model;

[0033] Figures 4 to 6 These are the measurement results of three dialysis devices with different membrane pore sizes.

[0034] Reference numerals:

[0035] 1 - Storage component; 21 - Main pipeline; 22 - Branch pipeline; 23 - Liquid injection pipeline; 4 - First pump; 5 - Second pump; 6 - Dialysis device; 61 - Blood chamber inlet; 62 - Blood chamber outlet; 63 - Dialysate chamber inlet; 64 - Dialysate chamber outlet; 65 - Dialysate chamber; 66 - Blood chamber; 7 - Pressure sensor; 8 - Detection component; 9 - Controller; 10 - Simulated liquid storage bucket; 11 - Drain port. Detailed implementation manners

[0036] The core of the present utility model is to provide a dialysis device membrane pore size testing device, which can reduce costs, reduce errors, and significantly improve accuracy.

[0037] In order to enable those skilled in the art to better understand the solution of the present utility model, the present utility model will be further described in detail below with reference to the accompanying drawings and specific implementation manners.

[0038] Please refer to Figure 1 and Figure 2 , Figure 1 This is a schematic structural diagram of a specific implementation manner of the dialysis device membrane pore size testing device provided by the present utility model; Figure 2 For Figure 1 This is a cross-sectional view of the dialysis device in the dialysis device membrane pore size testing device shown.

[0039] In this implementation manner, the dialysis device membrane pore size testing device is used to detect the membrane pore size of the hollow fiber membrane of the dialysis device 6. The dialysis device 6 includes a housing and a hollow fiber membrane located inside the housing. The inner cavity of the hollow fiber membrane forms the blood chamber 66, which is the place where blood flows. The space between the hollow fiber membrane and the housing forms the dialysate chamber 65, which is the place where dialysate flows.

[0040] The dialysis device membrane pore size testing device includes:

[0041] A storage component 1 for containing purified water or simulated liquid;

[0042] The main pipeline 21 allows purified water or a simulated fluid to flow. Both ends of the main pipeline 21 are placed inside the storage component 1. The blood chamber inlet 61 and the blood chamber outlet 62 of the blood chamber 66 are connected to the main pipeline 21. The purified water or the simulated fluid can flow through the inner cavity of the hollow fiber membrane. And a part of the liquid in the purified water or the simulated fluid enters the dialysate chamber 65 after passing through the membrane pores of the hollow fiber membrane. When a part of the liquid in the simulated fluid passes through the membrane pores of the hollow fiber membrane, a part of the silicon spheres in the simulated fluid fills into the membrane pores;

[0043] The branch pipeline 22 has one end installed on the housing and communicating with the dialysate chamber 65, and the other end placed inside the storage component 1;

[0044] The first pump 4 is connected to the main pipeline 21 and is used to control the flow rate of the blood chamber inlet 61 of the dialysis device 6, driving the purified water or the simulated fluid to flow into the dialysis device 6;

[0045] The second pump 5 is connected to the branch pipeline 22 and is used to control the ultrafiltration flow rate to drive the purified water or the simulated fluid to pass through the side wall of the hollow fiber membrane;

[0046] The detection component 8 is used to irradiate the simulated fluid in the storage component 1 and collect the light scattering intensities of the simulated fluid in the initial state and the fully filled state. The fully filled state refers to the state when the membrane pores in the hollow fiber membrane are completely filled with the silicon spheres in the simulated fluid;

[0047] The controller 9 is connected to both the first pump 4 and the second pump 5 and is used to control the flow rates of the first pump 4 and the second pump 5. The controller 9 is also connected to the detection component 8 and calculates the pore size distribution of the hollow fiber membrane according to the light scattering intensities of the simulated fluid in the initial state and the fully filled state.

[0048] Specifically, the storage component 1 can be cylindrical, and any structure capable of containing liquid is acceptable. The inlet of the main pipeline 21 should be placed below the liquid level in the storage component 1 to facilitate sucking the liquid in the storage component 1. The outlet of the main pipeline 21 can be higher or lower than the liquid level of the storage component 1. The dialysis device 6 is connected to the main pipeline 21, and the blood chamber inlet 61 and the blood chamber outlet 62 of the dialysis device 6 are connected to the main pipeline 21. The storage component 1, the main pipeline 21, and the blood chamber 66 of the dialysis device 6 together form a circulation loop. The hollow fiber membrane and the housing form the dialysate chamber 65. The dialysate chamber 65 includes a dialysate chamber inlet 63 and a dialysate chamber outlet 64. One end of the branch pipeline 22 communicates with the dialysate chamber 65, and the other end is placed inside the storage component 1 to allow the liquid in the dialysate chamber 65 to flow back into the storage component 1. Before the formal test, first pre-rinse the blood chamber 66 and the dialysate chamber 65 with purified water, and then simulate the flow of blood through the simulated fluid. By using the change in the number of silicon spheres of different sizes in the simulated fluid, the pore size distribution of the hollow fiber membrane is calculated.

[0049] Further, the first pump 4 is used to provide power for purified water or simulated liquid to flow through the dialysis device 6. To facilitate the pre-filling of purified water and bubble removal, the set flow rate of the first pump 4 is generally 90 - 110 ml / min, for example, 100 ml / min; during the test, to provide power, the set flow rate of the first pump 4 is generally 200 - 250 ml / min; if the set flow rate of the first pump 4 is too small, the pore blocking process may not be completed, and the experimental purpose cannot be achieved. If the set flow rate of the first pump 4 is too large, the silica spheres in the simulated liquid will cause impact and damage the structure of the hollow fiber membrane.

[0050] Furthermore, the second pump 5 provides power for the transmembrane transport of the simulated liquid by setting the ultrafiltration flow rate. The principle of the set flow rate of the second pump 5 is generally less than that of the first pump 4. To provide a flow rate less than that of the blood flow and achieve the dehydration process and increase internal filtration, generally, the set flow rate of the second pump 5 is preferably half of the set flow rate of the first pump 4; if the flow rate of the second pump 5 is too small, it is not conducive to the transmembrane transport of the silica spheres and blocking the pore diameter. Therefore, appropriately increasing the flow rate of the second pump 5 generally cannot exceed the flow rate of the first pump 4.

[0051] The dialysis device membrane pore size testing device provided by the present utility model can achieve the transportation of purified water or simulated liquid through the main pipeline setting, and can collect a part of the liquid after the successful transmembrane transport of the simulated liquid through the setting of the branch pipeline 22; at the same time, through the setting of the first pump 4 and the second pump 5, the first pump 4 can provide power for the simulated liquid to enter the blood chamber 66, and the second pump 5 provides power for the transmembrane transport of the simulated liquid in the hollow fiber membrane. When the simulated liquid undergoes transmembrane transport in the hollow fiber membrane, since a certain amount of simulated liquid is adsorbed inside the membrane pores of the hollow fiber membrane, the silica spheres in the simulated liquid will fill the membrane pores of the hollow fiber membrane. By obtaining the light scattering intensities of the simulated liquid in the initial state and the fully filled state, the difference in the number of silica spheres of different sizes in the initial state and the fully filled state of the simulated liquid can be calculated, and then the pore size distribution of the hollow fiber membrane can be obtained; this dialysis device membrane pore size testing device is convenient to operate, has high detection accuracy, good repeatability in the testing process, small error, simple structure, and low cost.

[0052] In some embodiments, it further includes:

[0053] A pressure sensor 7 for detecting the pressure difference between the blood chamber 66 and the dialysate chamber 65;

[0054] The controller 9 is connected to the pressure sensor 7, and the controller 9 is further used to determine whether the simulated liquid in the storage component 1 is in a fully filled state according to the pressure difference.

[0055] Specifically, the pressure sensor 7 can measure the pressure difference between the blood chamber 66 and the dialysate chamber 65, and transmit signals according to the pressure change. Due to the transmembrane transport of the simulated fluid, a certain amount of simulated fluid will be adsorbed inside the membrane pores of the dialysis device 6, causing blockage. At this time, if the set flow rate remains unchanged, the pressure difference will increase. Therefore, the pressure displayed by the pressure sensor 7 increases. When the pressure change of the pressure sensor 7 tends to be stable, it is used as a marker to indicate the end of the membrane blockage detection process, that is, to mark the fully filled state of the simulated fluid. Of course, in some cases, the start time of the second pump 5 can also be used to determine whether the fully filled state is entered. Of course, it is preferably to use the pressure detection method, which has high accuracy and can determine whether the membrane pores of the hollow fiber membrane are in the fully filled state in the first time. The controller 9 is integrated with a signal collection component, which can collect the signals in the pressure sensor 7 and the detection component 8. The controller 9 receives the signals of the pressure sensor 7 and the detection component 8 and records them in real time. The controller 9 is embedded with a data processor, which processes and converts the light intensity data in the detection component 8 into the size and quantity distribution of the silica spheres. According to the signal change in the pressure sensor 7, it is used as the judgment basis for whether the simulated fluid in the storage component 1 is in the fully filled state. According to the change in the light scattering intensity of the simulated fluid detected by the detection component 8, the quantity change of the silica spheres of different sizes in the simulated fluid is obtained, and the quantity difference of the silica spheres of different sizes in the initial state and the fully filled state is automatically calculated, and further the percentage of the pore size of the hollow fiber membrane is obtained.

[0056] Furthermore, signal transmission lines are provided between the controller 9 and the detection component 8, the first pump 4, the second pump 5, and the pressure sensor 7 to be responsible for transmitting signals. Of course, wireless transmission can also be used, which can be set according to needs.

[0057] In some embodiments, the branch pipeline 22 can be connected to the dialysate chamber inlet 63 or the dialysate chamber outlet 64 of the dialysate chamber 65. One end of the pressure sensor 7 is connected to the branch pipeline 22, and the other end is connected to a position on the main pipeline close to the blood chamber outlet 62. For the convenience of arranging the pressure sensor 7, the branch pipeline 22 is preferably connected to the dialysate chamber inlet 63 of the dialysate chamber 65.

[0058] In some embodiments, a simulated fluid storage bucket 10 is further included. The simulated fluid storage bucket 10 is connected to the storage component 1 through a liquid injection pipeline 23. The simulated fluid storage bucket 10 is used to store the simulated fluid and add the simulated fluid into the storage component 1. Specifically, when the purified water in the storage component 1 is emptied, through the setting of the simulated fluid storage bucket 10, the simulated fluid is added into the storage component 1, which is convenient for replacing the liquid in the storage component 1, and thus convenient for the smooth progress of the two operations of priming and testing.

[0059] In some embodiments, a simulation liquid valve is provided on the liquid injection pipeline 23. The simulation liquid valve is connected to the controller 9, and the controller 9 is further configured to control the opening and closing of the simulation liquid valve to control the storage liquid in the simulation liquid storage barrel 10 to flow into the storage component 1. Specifically, through the setting of the simulation liquid valve, the controller 9 can control the simulation liquid valve. After the purified water in the storage component 1 is emptied, the controller 9 controls the simulation liquid valve to open, adding the storage liquid in the simulation liquid storage barrel 10 into the storage component 1, realizing the automatic addition of the simulation liquid and improving the degree of automation.

[0060] In some embodiments, the height of the simulation liquid storage barrel 10 is higher than that of the storage component 1, and a drain port 11 is provided at the bottom of the side of the storage component 1. The drain port 11 can be opened or closed. Specifically, by setting the height of the simulation liquid storage barrel 10 to be higher than that of the storage component 1, it is to ensure that the simulation liquid is added into the storage component 1 under the action of gravity, facilitating operation; an electric valve can also be provided on the drain port 11, and the controller 9 controls the electric valve to realize the automatic discharge of the liquid in the storage component 1.

[0061] In some embodiments, both the first pump 4 and the second pump 5 are peristaltic pumps. Using peristaltic pumps can improve accuracy and have good sealing performance, which is beneficial to improving the accuracy of membrane pore size detection. Of course, the first pump 4 and the second pump 5 can also select other power components that can drive the flow of liquid.

[0062] In some embodiments, the dialysis appliance 6 is a dialyzer or a hemofilter, or other devices that need to detect the membrane pore size are also acceptable.

[0063] In some embodiments, the detection component 8 includes:

[0064] A light scattering component for irradiating the simulation liquid in the storage component 1;

[0065] A light sensor for collecting the light scattering intensity of the simulation liquid in real time. The light sensor is connected to the controller 9 and sends the light scattering intensity to the controller 9.

[0066] Specifically, the light sensor can be a DLS (Dynamic Light Scattering) sensor, which is built into the light scattering device. The light scattering device is responsible for irradiating the simulation liquid in the storage component 1, and the light sensor is responsible for collecting the light scattering intensity and transmitting it to the controller 9; using the light scattering principle to obtain the size and quantity changes of silicon spheres in the simulation liquid is convenient to operate, has low cost, and high detection accuracy.

[0067] In some embodiments, the simulated liquid is a silica sol simulated liquid, which contains a number of silica spheres with a diameter of 1-15 nm. The wider the size range of the silica spheres, the more accurate the detected membrane pore size distribution. When selecting the simulated liquid, it can be selected according to the general range of the pore size of the hollow fiber membrane, and a simulated liquid that matches the pore size of the hollow fiber membrane should be selected as much as possible to improve the detection accuracy.

[0068] This dialysis appliance membrane pore size testing device operates using the membrane pore size testing method for dialysis appliance 6. The membrane pore size testing method for dialysis appliance 6 includes the following steps:

[0069] Step S1: Connect the dialysis appliance 6 to the main pipeline 21 and the branch pipeline 22.

[0070] Step S2: Add purified water to the storage component 1, and set the priming parameters and the flow rates of the first pump 4 and the second pump 5; the priming parameters include the priming flow rate and the priming time.

[0071] Step S3: Start the first pump 4, prime the blood chamber 66 of the dialysis appliance 6 using the priming parameters, and then start the second pump 5 to flush the dialysis fluid chamber 65.

[0072] Step S4: Turn off the first pump 4 and the second pump 5, drain the purified water in the storage component 1, add the simulated liquid to the storage component 1, and obtain the light scattering intensity of the simulated liquid in the initial state.

[0073] Step S5: When starting the first pump 4 and the second pump 5 until the simulated liquid is in a fully filled state, detect the light scattering intensity of the simulated liquid in the storage component 1 in the fully filled state.

[0074] Step S6: According to the light scattering intensities of the simulated liquid in the initial state and the fully filled state, obtain the number of silica spheres of different sizes in the initial state and the fully filled state of the simulated liquid, and based on the difference in the number of silica spheres of different sizes in the initial state and the fully filled state of the simulated liquid, obtain the pore size distribution of the hollow fiber membrane.

[0075] Specifically, the priming flow rate and the priming time can be set as needed, which belong to industry standards. Priming the dialysis appliance 6 with purified water can infiltrate the hollow fiber membrane, remove impurities, and infiltrate the main pipeline 21, the branch pipeline 22, the blood chamber 66 of the dialysis appliance 6, and the dialysis fluid chamber 65. Regarding the flow rate control of the first pump 4 and the second pump 5, reference can be made to the above text and will not be elaborated here.

[0076] The method for testing the membrane pore size of the dialysis device 6 can infiltrate and purify the main pipeline 21, the branch pipeline 22, the blood chamber 66 and the dialysate chamber 65 of the dialysis device 6 through the pre-filling and flushing with purified water. Then, the flow of blood is simulated by the simulated liquid. By setting the flow rates of the first pump 4 and the second pump 5, power is provided for the transmembrane transport of the simulated liquid on the hollow fiber membrane. When the silicon spheres in the simulated liquid complete the filling of the membrane pores of the hollow fiber membrane, that is, when the simulated liquid reaches the fully filled state, the light scattering intensities of the simulated liquid in the initial state and the fully filled state are collected, so as to calculate the difference in the number of silicon spheres of different sizes in the initial state and the fully filled state of the simulated liquid, and then the pore size distribution of the hollow fiber membrane is obtained. This testing method has high accuracy. By irradiating the simulated liquid in the storage component 1, the size and quantity distribution of the silicon spheres in the simulated liquid can be obtained. It has low cost, is easy to operate, and has small errors.

[0077] In some embodiments, the step of starting the second pump 5 until the simulated liquid is in the fully filled state includes:

[0078] Detecting the pressure difference between the blood chamber 66 and the dialysate chamber 65;

[0079] When the pressure difference no longer changes within the target time, it is determined that the simulated liquid in the storage component 1 is in the fully filled state.

[0080] Specifically, a pressure sensor 7 is used to detect the pressure difference between the blood chamber 66 and the dialysate chamber 65 and send the pressure difference to the controller 9. The controller 9 transmits signals according to the pressure change. Due to the transmembrane transport of the simulated liquid, a certain amount of simulated liquid silicon spheres will be adsorbed inside the membrane pores of the dialysis device 6, causing blockage. At this time, the set flow rate remains unchanged, so the pressure difference will increase. Therefore, the pressure displayed in the pressure sensor 7 increases. When the pressure change of the pressure sensor 7 tends to be stable, it is used as a mark for the end of the membrane blockage detection process, that is, a mark for the fully filled state of the simulated liquid in the hollow fiber membrane pores.

[0081] In a specific embodiment, the method for testing the membrane pore size of the dialysis device 6 includes the following steps:

[0082] Connect the dialysis device 6 to the dialysis device membrane pore size testing device;

[0083] In the simulated liquid storage bucket 10, simulate liquids of different sizes are prepared in advance. The simulated liquid is a silica sol simulated liquid, and the size N of the silicon spheres is 1 - 15 nm, ΔN = 0.1 nm. Connect the simulated liquid storage bucket 10 to the dialysis device membrane pore size testing device and inject a certain amount of purified water into the storage component 1;

[0084] Set the priming flow rate and priming time in the controller 9, and set the flow rates of the first pump 4 and the second pump 5; turn on the switch of the controller 9, control to turn on the first pump 4, and the purified water in the storage component 1 enters the main pipeline 21 to prime the dialysis appliance 6 for 10 minutes.

[0085] Control the operation of the first pump 4 and the second pump 5 to be turned off through the controller 9, drain the purified water in the storage component 1 through the drain port 11, and then convey the excessive simulated liquid with silicon balls of mixed sizes in the simulated liquid storage bucket 10 to the storage component 1 through the controller 9. The detection component 8 automatically detects the light intensity of the mixed simulated liquid in the storage component 1 and transmits it to the controller 9 to be automatically converted into the size and quantity distribution of the silicon balls in the simulated liquid in the initial state.

[0086] Control the first pump 4 and the second pump 5 to operate according to the preset parameters through the controller 9. When the pressure sensor 7 detects that the pressure does not change within 2 minutes, the controller 9 automatically controls the detection component 8 to perform light scattering measurement and converts and records the size and quantity distribution of the silicon balls in the fully filled state at this time.

[0087] Specifically, for this dialysis appliance membrane pore size testing device, the light scattering method is adopted. The light scattering method refers to a method of irradiating particles with a laser, analyzing the light intensity fluctuations of the scattered light, and then calculating the particle size and quantity. After the silica sol simulated liquid enters the storage component 1, the size and quantity of the silicon balls in it can be tested through light scattering and used as the size and quantity distribution of the silicon balls in the simulated liquid in the initial state, denoted as 100%, as Figures 4 - 6 shown by the middle line a. Subsequently, entering the test cycle, some silicon balls in the simulated liquid will fill into the membrane pore spaces of the dialysis appliance 6, resulting in a decrease in the quantity of silicon balls of different sizes; when the pressure in the pressure sensor 7 shows stable and unchanged, it means that the silicon balls have filled the membrane pore spaces of the dialysis appliance 6. Measure and record the size and quantity distribution of the silicon balls in the simulated liquid in the fully filled state at this time, and denote it as the size and quantity distribution of the silicon balls after testing, as Figures 4 - 6 shown by the middle line b; the difference in the size and quantity changes of the silicon balls between the initial state and after testing is caused by the silicon balls filling in the membrane pore spaces of the dialysis appliance 6. Therefore, the difference between the two can be used as the membrane pore size distribution of the dialysis appliance 6, as Figures 4 - 6 shown by the middle line c. Three different dialysis appliances 6 were measured using this device, and the data as shown in Figures 4 - 6 were obtained. Through three data graphs, the membrane pore size distribution of each dialysis appliance 6 can be clearly obtained.

[0088] The above has introduced in detail the dialysis appliance membrane pore size testing device provided by the present utility model. Specific examples are used in this article to elaborate on the principle and implementation manner of the present utility model. The description of the above embodiments is only used to help understand the method and its core idea of the present utility model. It should be noted that for those of ordinary skill in the art, without departing from the principle of the present utility model, several improvements and modifications can still be made to the present utility model, and these improvements and modifications also fall within the protection scope of the present utility model.

Claims

1. A dialysis apparatus membrane pore size testing device, the dialysis apparatus (6) comprising a housing and a hollow fiber membrane located in the housing, the inner cavity of the hollow fiber membrane forming a blood chamber (66), and a dialysate chamber (65) formed between the hollow fiber membrane and the housing; characterized in that: include: A storage component (1) for containing purified water or simulated liquid; A main pipeline (21) for the purified water or the simulated liquid to flow, both ends of the main pipeline (21) are placed in the storage component (1), the blood chamber inlet (61) and the blood chamber outlet (62) of the blood chamber (66) are connected to the main pipeline (21), the purified water or the simulated liquid can flow through the inner cavity of the hollow fiber membrane, and after partially passing through the membrane pores of the hollow fiber membrane, enter the dialysate chamber (65), and part of the silicon balls in the simulated liquid are filled in the membrane pores; A branch pipe (22), one end of which is mounted on the housing and communicates with the dialysate chamber (65), and the other end of which is placed in the storage component (1); A first pump (4) connected to the main pipeline (21) and used to control the flow rate of the blood chamber inlet (61) of the dialysis apparatus (6); a second pump (5), connected to the branch pipeline (22), for controlling the ultrafiltration flow rate to drive the purified water or the simulated liquid to pass through the side wall of the hollow fiber membrane; A detection component (8) for irradiating the simulated liquid in the storage component (1) and collecting the light scattering intensity of the simulated liquid in an initial state and a fully filled state; A controller (9), the controller (9) being connected to both the first pump (4) and the second pump (5) and being used to control the flow rates of the first pump (4) and the second pump (5); the controller (9) being also connected to the detection component (8) and calculating the pore size distribution of the hollow fiber membrane based on the light scattering intensity of the simulated liquid in an initial state and a fully filled state.

2. The dialysis apparatus membrane pore size testing device according to claim 1, characterized in that: Also includes: A pressure sensor (7) for detecting a pressure difference between the blood chamber (66) and the dialysate chamber (65); The controller (9) is connected to the pressure sensor (7), and the controller (9) is also used to determine whether the simulated liquid in the storage component (1) is in a fully filled state based on the pressure difference.

3. The dialysis apparatus membrane pore size testing device according to claim 2, characterized in that: The branch line (22) is connected to the dialysate chamber inlet (63) of the dialysate chamber (65), and the pressure sensor (7) is installed between the dialysate chamber inlet (63) and the blood chamber outlet (62).

4. The dialysis equipment membrane pore size testing device according to claim 1, characterized in that: It also comprises a simulated liquid storage barrel (10), the simulated liquid storage barrel (10) being connected to the storage component (1) via a liquid injection pipeline (23), the simulated liquid storage barrel (10) being used to store simulated liquid and to add the simulated liquid into the storage component (1).

5. The dialysis apparatus membrane pore size testing device according to claim 4, characterized in that: The injection pipeline (23) is provided with a simulated liquid valve, and the simulated liquid valve is connected to the controller (9). The controller (9) is also used to control the opening and closing of the simulated liquid valve to control the storage liquid in the simulated liquid storage barrel (10) to flow into the storage component (1).

6. The dialysis apparatus membrane pore size testing device according to claim 5, characterized in that: The height of the simulated liquid storage barrel (10) is higher than the height of the storage component (1), and a drainage port (11) is provided at the bottom of the side of the storage component (1), and the drainage port (11) can be opened or closed.

7. The dialysis equipment membrane pore size testing device according to claim 1, characterized in that: The first pump (4) and the second pump (5) are both peristaltic pumps.

8. The dialysis equipment membrane pore size testing device according to claim 1, characterized in that: The dialysis apparatus (6) is a dialyzer or a hemofilter.

9. The dialysis equipment membrane pore size testing device according to claim 1, characterized in that: The simulated liquid is a silica sol simulated liquid, and the simulated liquid contains a plurality of silica balls, and the diameter of the silica balls is 1-15 nm.

10. The dialysis equipment membrane pore size testing device according to any one of claims 1 to 9, characterized in that: The detection component (8) comprises: A light scattering component, used for irradiating the simulated liquid in the storage component (1); A light sensor is used to collect the light scattering intensity of the simulated liquid in real time, the light sensor is connected to the controller (9) and sends the light scattering intensity to the controller (9).

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