Dialysis device, method for measuring coagulation status of dialyzer and monitoring system

Abstract

The present application discloses a dialysis device, a method for determining the coagulation status of a dialyzer, and a monitoring system. The dialyzer coagulation status monitoring system is applied to a dialyzer connected with a dialyzer circuit and a blood circuit, wherein the dialyzer circuit is provided with a dialyzer inlet pressure sensor and a dialyzer outlet pressure sensor, and the blood circuit is provided with a blood chamber inlet pressure sensor and a blood chamber outlet pressure sensor, and further includes a control system, which is used to determine the coagulation status of a dialyzer according to the formula (P BI +P BO ) / 2‑(P DI +P DO ) / 2 calculates the transmembrane pressure, P BI is the pressure at the blood chamber entrance, P BO is the pressure at the blood chamber outlet, P DI is the pressure at the dialysate inlet, P DO is the pressure at the dialysate outlet; the flux at different times is calculated based on the transmembrane pressure, and the flux is equal to the dehydration rate of the dialyzer divided by the transmembrane pressure; it is also used to calculate the flux attenuation rate based on the flux at different times, and the flux attenuation rate = (1-flux at a certain moment / flux at the initial moment) × 100%.

Description

Technical Field

[0001] The present invention relates to the technical field of medical equipment, and in particular to a dialysis device, a method for measuring the coagulation status of a dialyzer, and a monitoring system. Background Art

[0002] We know that hemodialysis requires blood to be drawn out of the body, passed through a dialysis device, and then returned to the body. At this time, the blood is circulating outside the body, and prothrombin generation and fibrin deposition are likely to occur, which can easily cause blood coagulation. Therefore, the patient must be systemically heparinized before dialysis or the dialyzer must be pre-flushed with anticoagulants. Even during the dialysis process, additional heparin may be added to reduce the coagulation of the dialyzer, and heparin treatment should be added during the dialysis process.

[0003] In the past, ordinary heparin needed to be administered using a heparin pump. Now, with the development of low-molecular-weight heparin, the use of heparin can reduce the coagulation state. When the patient's heart function is good, increasing the hemodialysis flow rate can also slow down the coagulation state. Therefore, attention should be paid to anticoagulation during hemodialysis to ensure smooth dialysis.

[0004] Due to the differences in blood conditions of different renal dialysis patients, dialysis patients often experience blood coagulation in the dialysis membrane and blockage of the dialysis membrane channel during clinical treatment. For dialysis membrane developers, it is impossible to quantitatively determine the anticoagulation status of the dialyzer during development and can only be confirmed through clinical trials, which undoubtedly increases the risk of clinical trials and the development and registration cycle of new products.

[0005] The existing methods for evaluating dialyzer coagulation are highly subjective and arbitrary, and can only be used as qualitative judgments with poor reference value. They are also unable to systematically analyze and predict the coagulation and blockage status inside the dialyzer. Summary of the invention

[0006] The purpose of the present invention is to provide a method for measuring the coagulation status of a dialysis device and a dialyzer and a monitoring system, which can calculate the value of flux attenuation and then make a comprehensive evaluation of the coagulation status of the dialyzer to guide the developers of the hemodialysis machine to effectively adjust the performance of the product.

[0007] To achieve the above-mentioned purpose, the present application provides a dialyzer coagulation status monitoring system, which is applied to a dialyzer connected with a dialysate circuit and a blood circuit, and the dialyzer is provided with a dialysate inlet, a dialysate outlet, a blood chamber inlet and a blood chamber outlet;

[0008] The dialysate circuit is provided with a dialysate inlet pressure sensor for detecting the pressure of the dialysate inlet and a dialysate outlet pressure sensor for detecting the pressure of the dialysate outlet, and the blood circuit is provided with a blood chamber inlet pressure sensor for detecting the pressure of the blood chamber inlet and a blood chamber outlet pressure sensor for detecting the pressure of the blood chamber outlet.

[0009] It also includes a control system connected to a dialysate inlet pressure sensor, a dialysate outlet pressure sensor, a blood chamber inlet pressure sensor, and a blood chamber outlet pressure sensor.

[0010] The control system is used to calculate the transmembrane pressure TMP according to the pressure of the dialysate inlet, the pressure of the dialysate outlet, the pressure of the blood chamber inlet and the pressure of the blood chamber outlet, wherein TMP=(P BI +P BO ) / 2-(P DI +P DO ) / 2,P BI is the pressure at the blood chamber entrance, P BO is the pressure at the blood chamber outlet, P DI is the pressure at the dialysate inlet, P DO is the pressure at the dialysate outlet, and the unit of transmembrane pressure TMP is kPa;

[0011] The control system is also used to calculate the flux at different times according to the transmembrane pressure. The flux is equal to the dehydration rate of the dialyzer divided by the transmembrane pressure TMP. The unit of the dehydration rate is L / h, and the unit of the flux is L / (h·kPa);

[0012] The control system is used to calculate the flux attenuation rate η according to the flux at different moments, wherein the flux attenuation rate η=(1-flux at a certain moment / flux at an initial moment)×100%.

[0013] Optionally, a host computer connected to the control system is also included, and the host computer is used to output curves of transmembrane pressure and flux attenuation rate changing with time.

[0014] The present application also discloses a dialysis device, including a dialyzer connected with a dialysate circuit and a blood circuit, and also including the above-mentioned dialyzer coagulation status monitoring system.

[0015] Optionally, the dialysate circuit comprises:

[0016] A degassing chamber, which is used to degas the liquid inside;

[0017] At least two dialysate containers for containing different dialysates, the outlets of all dialysate containers being connected to the outlet of the degassing chamber;

[0018] The mixing chamber is arranged at the connection point between the outlet of the dialysate container and the outlet of the degassing chamber, and the outlet of the mixing chamber is connected with the dialysate inlet.

[0019] Optionally, the dialysate outlet is connected to a heat exchanger for exchanging heat of the dialysate via a waste liquid pipeline, and the heat exchanger is connected to the waste liquid outlet so that the dialysate after heat exchange is discharged from the waste liquid outlet.

[0020] Optionally, a conductivity sensor for detecting the concentration of the dialysate is provided between the dialysate inlet and the mixing chamber, and a passage for draining out unqualified dialysate is provided between the conductivity sensor and the waste liquid pipeline.

[0021] Optionally, a disinfectant container is connected between the dialysate outlet and the heat exchanger, and the waste liquid pipeline is cleaned by the disinfectant in the disinfectant container.

[0022] Optionally, the heat exchanger is connected to the degassing chamber so that the injection water enters the degassing chamber through the heat exchanger.

[0023] The present application also discloses a method for determining the coagulation status of a dialyzer, comprising:

[0024] Obtain pressure values ​​at the dialysate inlet, dialysate outlet, blood chamber inlet and blood chamber outlet of the dialyzer;

[0025] According to the pressure values ​​of the above four and the formula (P BI +P BO ) / 2-(P DI +P DO ) / 2 to calculate the transmembrane pressure, P BI is the pressure at the blood chamber entrance, P BO is the pressure at the blood chamber outlet, P DI is the pressure at the dialysate inlet, P DO is the pressure of the dialysate outlet, and the unit of transmembrane pressure is kPa;

[0026] The flux at different times is calculated according to the transmembrane pressure, where the flux is equal to the dehydration rate of the dialyzer divided by the transmembrane pressure, the unit of the dehydration rate is L / h, and the unit of the flux is L / (h·kPa);

[0027] The flux attenuation rate η is calculated based on the flux at different times, where the flux attenuation rate η=(1-flux at a certain time / flux at the initial time)×100%.

[0028] With respect to the above-mentioned background technology, the dialyzer coagulation status monitoring system provided by the present application is applied to a dialyzer connected with a dialysate circuit and a blood circuit, the dialyzer is provided with a dialysate inlet, a dialysate outlet, a blood chamber inlet and a blood chamber outlet, the dialysate circuit is provided with a dialysate inlet pressure sensor for detecting the pressure of the dialysate inlet and a dialysate outlet pressure sensor for detecting the pressure of the dialysate outlet, the blood circuit is provided with a blood chamber inlet pressure sensor for detecting the pressure of the blood chamber inlet and a blood chamber outlet pressure sensor for detecting the pressure of the blood chamber outlet, and also includes a blood chamber inlet pressure sensor connected to the dialysate inlet pressure sensor, the dialysate outlet pressure sensor, the blood chamber inlet pressure sensor and the blood chamber outlet pressure sensor The control system is used to calculate the transmembrane pressure according to the pressure of the dialysate inlet, the pressure of the dialysate outlet, the pressure of the blood chamber inlet and the pressure of the blood chamber outlet. The transmembrane pressure = (pressure of the blood chamber inlet + pressure of the blood chamber outlet) / 2-(pressure of the dialysate inlet + pressure of the dialysate outlet) / 2, and the unit of the transmembrane pressure is kPa. The control system is also used to calculate the flux at different times according to the transmembrane pressure. The flux = dehydration speed of the dialyzer / transmembrane pressure. The unit of the dehydration speed is L / h, and the unit of the flux is L / (h·kPa); the control system is used to calculate the flux attenuation rate according to the flux at different times. The flux attenuation rate = (1-flux at a certain moment / flux at an initial moment) × 100%.

[0029] The applicant has found through a large number of experimental verifications and data analysis that when the dialyzer is coagulated and blocked, the transmembrane pressure rises sharply and the flux decays significantly. According to this principle, monitoring the attenuation of the dialyzer flux can timely reflect the coagulation state of the dialyzer during the entire treatment process. The dialyzer coagulation status monitoring system set up in this way can monitor and analyze the flux decay state of the dialysis membrane in real time, and calculate the value of the flux decay through the above calculation method, so as to comprehensively evaluate the coagulation state of the dialyzer, so as to guide the hemodialyzer developers to effectively adjust the performance of the product.

[0030] The dialyzer coagulation status determination method and dialysis device provided in the present application have the above-mentioned beneficial effects, which will not be elaborated in this article. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on the provided drawings without paying creative work.

[0032] Figure 1 This is a schematic diagram of a dialysis device provided in an embodiment of the present invention. DETAILED DESCRIPTION

[0033] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0034] In order to enable those skilled in the art to better understand the scheme of the present invention, the present invention is further described in detail below in conjunction with the accompanying drawings and specific implementation methods.

[0035] The dialyzer coagulation status monitoring system provided in the present application is applied to a dialyzer 25 connected with a dialysate circuit and a blood circuit. Figure 1 The top of the dialyzer 25 is the blood chamber outlet, the bottom of the dialyzer 25 is the blood chamber inlet, the upper left side of the dialyzer 25 is the dialysate inlet, and the lower left side of the dialyzer 25 is the dialysate outlet.

[0036] The dialysate circuit is connected to the dialysate inlet and the dialysate outlet of the dialyzer 25 , and the blood circuit is connected to the blood chamber inlet and the blood chamber outlet of the dialyzer 25 .

[0037] The dialysate circuit is provided with a dialysate inlet pressure sensor 24 and a dialysate outlet pressure sensor 26. The dialysate inlet pressure sensor 24 is used to detect the pressure of the dialysate inlet, and the dialysate outlet pressure sensor 26 is used to detect the pressure of the dialysate outlet.

[0038] The blood circuit is provided with a blood chamber inlet pressure sensor 46 and a blood chamber outlet pressure sensor 47. The blood chamber inlet pressure sensor 46 is used to detect the pressure at the blood chamber inlet, and the blood chamber outlet pressure sensor 47 is used to detect the pressure at the blood chamber outlet.

[0039] There are many specific configurations for other locations in the dialysate circuit and the blood circuit, and only one preferred implementation is given below.

[0040] The dialyzer coagulation status monitoring system of the present invention also includes a control system, which can be specifically a PLC, etc. The control system is connected to the dialysate inlet pressure sensor 24, the dialysate outlet pressure sensor 26, the blood chamber inlet pressure sensor 46 and the blood chamber outlet pressure sensor 47. The control system can also use the formula The transmembrane pressure is calculated, and the change of transmembrane pressure is used to characterize the change of dialyzer flux attenuation.

[0041] Among them, P BI is the pressure at the blood chamber entrance, P BOis the pressure at the blood chamber outlet, P DI is the pressure at the dialysate inlet, P DO It is the pressure at the dialysate outlet, that is, transmembrane pressure TMP = (pressure at the blood chamber inlet + pressure at the blood chamber outlet) / 2 - (pressure at the dialysate inlet + pressure at the dialysate outlet) / 2. The unit of transmembrane pressure is kPa.

[0042] The flux is then calculated using the control system;

[0043]

[0044] In the above formula, J i is the flux at a certain moment, in L / (h·kPa), Q F is the dehydration rate of the dialyzer, in L / h, TMP is the transmembrane pressure of the patient at a certain moment, in kPa; Q F It can be determined by setting the parameters of the dialyzer;

[0045] Finally, the control system is used to calculate the flux attenuation rate η: flux attenuation rate = (1-the rate of change of flux at different times) × 100%. Among them, the most preferred is:

[0046]

[0047] Where J0 is the flux at the initial moment, and the unit is L / (h·kPa).

[0048] That is, the flux attenuation rate is preferably compared with the initial flux. Obviously, the flux attenuation rate η = (1-the flux at the i-th moment / the flux at the initial moment) × 100%.

[0049] When the test is completed, the control system can also upload the test result data to the host computer database system, and the host computer will output the change curves of transmembrane pressure and flux attenuation rate during the entire experiment for analysis, that is, the host computer can output the curves of transmembrane pressure and flux attenuation rate changing with time.

[0050] The dialyzer coagulation status monitoring system involved in this article is suitable for the dialyzer design stage rather than the treatment process; that is, in the process of designing the dialyzer, animal blood is used in the blood circuit to test the flux attenuation rate, so that the working status of the dialyzer can be clearly and intuitively determined in order to optimize and improve its structure.

[0051] The dialysis device described in this article includes a dialyzer 25 connected to a dialysate circuit and a blood circuit. The schematic diagram of the dialysis device is shown in the attached manual. Figure 1 shown.

[0052] Further, the dialysate circuit comprises:

[0053] A degassing chamber 8, which is used to degas the liquid inside;

[0054] At least two dialysate containers for containing different dialysates, the outlets of all dialysate containers being connected to the outlet of the degassing chamber 8;

[0055] The mixing chamber is arranged at the connection point between the outlet of the dialysate container and the outlet of the degassing chamber 8, and the outlet of the mixing chamber is connected to the dialysate inlet.

[0056] Instructions attached Figure 1 Two dialysate containers are shown, namely a first dialysate container 19 and a second dialysate container 14 , wherein the first dialysate container 19 and the second dialysate container 14 contain dialysates of different components, which should be mixed on site for use.

[0057] The outlet of the degassing chamber 8 is connected to the water inlet of the pump body 11, and the water outlet of the pump body 11 is connected to the inlet of the second mixing chamber 15. The second dialysate container 14 can pass through the second filter 13 and then be connected to the inlet of the second mixing chamber 15 through the second plunger pump 12. The outlet of the second mixing chamber 15 passes through the first conductivity sensor 16 and then is connected to the inlet of the first mixing chamber 20. The first dialysate container 19 passes through the first filter 18 and then is connected to the inlet of the first mixing chamber 20 through the first plunger pump 17. The outlet of the first mixing chamber 20 is connected to the dialysate inlet of the dialyzer 25 through the conductivity sensor 21, the first solenoid valve 22, and the second solenoid valve 23. A dialysate inlet pressure sensor 24 is connected between the second solenoid valve 23 and the dialyzer 25.

[0058] The dialysate outlet is connected to the heat exchanger 4 via the waste liquid pipeline, and the heat exchanger 4 is connected to the waste liquid outlet, so that the dialysate after heat exchange is discharged from the waste liquid outlet. A passage for leading out unqualified dialysate can also be provided between the conductivity sensor 21 and the waste liquid pipeline.

[0059] The first solenoid valve 22 and the second solenoid valve 23 are connected to the inlet of the third solenoid valve 28, the outlet of the third solenoid valve 28 is connected to the fourth solenoid valve 27 and the blood leakage detection sensor 30, the dialysate outlet of the dialyzer 25 is connected to the inlet of the flow pump 31 through the fourth solenoid valve 27 and the blood leakage detection sensor 30, a dialysate outlet pressure sensor 26 is connected between the dialyzer 25 and the fourth solenoid valve 27, a pressure sensor 29 is connected between the fourth solenoid valve 27 and the blood leakage detection sensor 30, the first disinfectant container 34 is connected to the blood leakage detection sensor 30 and the flow pump 31 through the first filter 33 and the solenoid valve 1 32, the second disinfectant container 37 is connected to the blood leakage detection sensor 30 and the flow pump 31 through the second filter 36 and the solenoid valve 2 35, the flow pump 31 is connected to the inlet of the heat exchanger 4 through the solenoid valve 38, and the outlet of the heat exchanger 4 is connected to the waste liquid outlet through the solenoid valve 4 40.

[0060] For the dialysate circuit, it can also include a pressure reducing valve 1 and a solenoid valve 6 2. The injected water is connected to the water inlet of the heat exchanger 4 through the pressure reducing valve 1 and the solenoid valve 6 2, and then enters the water inlet of the degassing chamber 8 through the heater 5 and the flow limiter 6. A first pressure sensor 3 is connected between the solenoid valve 6 2 and the heat exchanger 4. The solenoid valve 6 2 and the heat exchanger 4 are connected to the waste liquid outlet through the solenoid valve 7 39 and the solenoid valve 4 40. The degassing chamber 8 has three outlets, one of which is connected to the one-way valve 9, and the one-way valve 9 is connected to the heat exchanger 4 and the heater 5. The other outlet of the degassing chamber 8 is connected to the solenoid valve 8 10, and the outlet of the solenoid valve 8 10 is connected to the waste liquid pipeline.

[0061] When the test is completed, the pipeline between the dialysate inlet and the dialysate outlet of the dialyzer 25 can be short-circuited, the disinfection program can be started, the first filter 33, the solenoid valve 2 35, the solenoid valve 7 39 can be automatically opened, the solenoid valve 4 40 can be closed, and an appropriate amount of disinfectant can be inhaled. The conductivity of the disinfectant can be detected by the first conductivity sensor 16 and the conductivity sensor 21 to determine the concentration of the disinfectant. After the disinfectant circulates and flushes in the pipeline for a period of time, the solenoid valve 6 2 and the solenoid valve 4 40 can be opened again, the solenoid valve 7 39 can be closed, and the disinfectant can be cleaned with pure water.

[0062] For the blood circuit, it may include a physiological saline container 41 that delivers physiological saline to a blood container 44 through a pump 42 and a solenoid valve 43. The blood container 44 is connected to the blood chamber inlet of the dialyzer 25 through a blood pump 45. A blood chamber inlet pressure sensor 46 is connected between the blood pump 45 and the dialyzer 25. The blood chamber outlet of the dialyzer 25 is connected to the blood container 44 through a pressure sensor 47. Among them, all the above-mentioned pressure sensors, solenoid valves and pumps are uniformly controlled by the control system, and the test result data is stored in the memory of the PLC. The water used in the equipment is pure water with a conductivity of less than 50μs / cm and a water temperature of 24-26°C.

[0063] The dialyzer coagulation status determination method described in the present application may refer to the description of the above-mentioned dialyzer coagulation status monitoring system and the dialysis device. The dialyzer coagulation status determination method may be applied to the above-mentioned dialysis device. The dialyzer coagulation status determination method includes:

[0064] Obtain pressure values ​​at the dialysate inlet, dialysate outlet, blood chamber inlet, and blood chamber outlet of the dialyzer 25;

[0065] The transmembrane pressure is calculated based on the pressure values ​​of the above four and the formula: transmembrane pressure = (pressure at the blood chamber inlet + pressure at the blood chamber outlet) / 2-(pressure at the dialysate inlet + pressure at the dialysate outlet) / 2. The unit of transmembrane pressure is kPa.

[0066] The flux at different times is calculated according to the transmembrane pressure, wherein the flux = the dehydration rate of the dialyzer 25 / the transmembrane pressure, the unit of the dehydration rate is L / h, and the unit of the flux is L / (h·kPa);

[0067] The flux attenuation rate is calculated based on the flux at different moments, wherein the flux attenuation rate = (1-the rate of change of the flux at different moments) × 100%; preferably, the flux attenuation rate = (1-the flux at the i-th moment / the flux at the initial moment) × 100%.

[0068] In conjunction with the above dialysis device, the method for determining the coagulation status of the dialyzer may specifically include the following steps, which may also be considered as a test process of the dialysis device:

[0069] (1) First, set the flow rate of the blood pump 45 to 200 ml / min, the flow rate of the pump body 11 to 500 ml / min, the flow rate of the flow pump 31 to 520 ml / min, and the flow rate of the plunger pump 42 to 20 ml / min.

[0070] (2) Setting the dialysate concentration ratio: for the dialysates containing different components in the first dialysate container 19 and the second dialysate container 14 , the ratio of the first dialysate: the second dialysate: water is 1:1.2:32.

[0071] (3) The instrument is started and begins to operate. The instrument automatically operates according to the set control process under the control system. The solenoid valve 43 opens the blood pump 45 and the plunger pump 42 operate at the set speed. The blood passes through the dialyzer and returns to the blood container 44, repeating the cycle.

[0072] (4) The solenoid valve 6 2 is automatically opened, and the pure water passes through the heat exchanger 4, the heater 5, and the flow restrictor 6 into the degassing pump 7, and then enters the degassing chamber 8 to separate the bubbles from the water.

[0073] (5) The degassed pure water enters the second mixing chamber 15 and the first mixing chamber 20 in turn under the conveyance of the pump body 11, and is fully mixed with the first dialysate and the second dialysate in the mixing chamber. The configured dialysate is detected by the conductivity sensor 21. The dialysate that meets the requirements enters the dialyzer 25 after passing through the first solenoid valve 22 and the second solenoid valve 23. The dialysate that does not meet the requirements enters the blood leakage detection sensor 30 through the third solenoid valve 28, and is discharged to the drain port after passing through the flow pump 31, the solenoid valve three 38, the heat exchanger 4 and the solenoid valve four 40.

[0074] (6) After the dialysate passes through the dialyzer 25, it goes through the fourth solenoid valve 27 to the blood leakage detection sensor 30. If there is blood leakage, the test is stopped and the dialyzer 25 is replaced and the test is restarted.

[0075] (7) The dialysate after passing through the blood leakage detection sensor 30 is discharged to the waste liquid outlet by the flow pump 31 through the electromagnetic valve 3 38, the heat exchanger 4, the pipeline on the right side of the electromagnetic valve 7 39 and the electromagnetic valve 4 40. The heat exchanger 4 transfers the heat in the waste liquid to the pure water, and the energy is reused.

[0076] (8) The entire experiment lasted for nearly 4 hours, and four pressure sensors (dialysis fluid inlet pressure sensor 24, dialysate outlet pressure sensor 26, blood chamber inlet pressure sensor 46, and blood chamber outlet pressure sensor 47) monitored the pressure before and after the dialyzer blood chamber and the pressure before and after the dialyzer dialysate chamber in real time. A set of pressure data was recorded every 15 minutes.

[0077] (9) Using the formula The transmembrane pressure is calculated, and the change of transmembrane pressure is used to characterize the change of dialyzer flux attenuation.

[0078] Among them, P BI is the pressure at the blood chamber entrance, P BO is the pressure at the blood chamber outlet, P DI is the pressure at the dialysate inlet, P DO It is the pressure at the dialysate outlet, that is, transmembrane pressure TMP = (pressure at the blood chamber inlet + pressure at the blood chamber outlet) / 2 - (pressure at the dialysate inlet + pressure at the dialysate outlet) / 2. The unit of transmembrane pressure is kPa.

[0079] (10) Calculation of flux attenuation rate

[0080] Flux J:

[0081]

[0082] In the formula, J i is the flux at a certain moment, the unit is L / (h·kPa), Q Fis the dehydration rate of the dialyzer, the unit is L / h, TMP is the transmembrane pressure of the patient at a certain moment, the unit is kPa.

[0083] Flux decay rate η:

[0084]

[0085] Where J0 is the flux at the initial moment, L / (h·kPa).

[0086] (11) After the test is completed, the dialysate inlet and outlet pipes of the dialyzer 25 are short-circuited, the disinfection program is started, the solenoid valves 33, 35, and 39 are automatically opened, the solenoid valve 40 is closed, and an appropriate amount of disinfectant is sucked in. The conductivity of the disinfectant is detected by the conductivity sensor 16 and the conductivity sensor 21 to determine the concentration of the disinfectant. After the disinfectant is circulated and flushed in the pipe for a period of time, the solenoid valve 2 and the solenoid valve 40 are opened again, the solenoid valve 39 is closed, and the disinfectant is cleaned with pure water.

[0087] (12) After the test is completed, the control system uploads the test result data to the host computer database system, and the host computer outputs the change curve of the transmembrane pressure and flux attenuation rate during the entire experiment for analysis.

[0088] The applicant needs to point out that the method for determining the coagulation status of the dialyzer described in this article is not used in the treatment process, but is applicable to the design stage of the product; the blood container 44 contains animal blood to simulate the hemodialysis process, thereby testing the flux attenuation rate, so that the working state of the dialyzer can be clearly and intuitively determined, and the structure of the dialysis device can be optimized and improved.

[0089] This application innovatively introduces the concept of dialyzer flux attenuation in the field of dialysis, and develops a dialyzer coagulation status monitoring system and a dialysis device in combination with this indicator. The method of this application can quantitatively evaluate the membrane coagulation and blockage status of the dialyzer during use, making up for the deficiency of the original technology that relies on human subjective judgment of dialyzer coagulation, and can provide systematic analysis and prediction data for dialyzer developers when studying dialyzer coagulation.

[0090] It should be noted that, in this specification, relational terms such as first and second are merely used to distinguish one entity from other entities, but do not necessarily require or imply any actual relationship or order between these entities.

[0091] The above is a detailed introduction to the dialysis device, the method for determining the coagulation status of the dialyzer and the monitoring system provided by the present invention. Specific examples are used herein to illustrate the principles and implementation methods of the present invention. The description of the above embodiments is only used to help understand the method of the present invention and its core idea. It should be pointed out that for ordinary technicians in this technical field, without departing from the principle of the present invention, the present invention can also be improved and modified, and these improvements and modifications also fall within the scope of protection of the claims of the present invention.

Claims

1. A dialyzer coagulation status monitoring system, applied to a dialyzer (25) connected with a dialysate circuit and a blood circuit, wherein the dialyzer (25) is provided with a dialysate inlet, a dialysate outlet, a blood chamber inlet and a blood chamber outlet, and characterized in that; The dialysate circuit is provided with a dialysate inlet pressure sensor (24) for detecting the pressure of the dialysate inlet and a dialysate outlet pressure sensor (26) for detecting the pressure of the dialysate outlet, and the blood circuit is provided with a blood chamber inlet pressure sensor (46) for detecting the pressure of the blood chamber inlet and a blood chamber outlet pressure sensor (47) for detecting the pressure of the blood chamber outlet. It also includes a control system connected to the dialysate inlet pressure sensor (24), the dialysate outlet pressure sensor (26), the blood chamber inlet pressure sensor (46) and the blood chamber outlet pressure sensor (47), The control system is used to calculate the transmembrane pressure TMP according to the pressure of the dialysate inlet, the pressure of the dialysate outlet, the pressure of the blood chamber inlet and the pressure of the blood chamber outlet, wherein TMP=(P BI +P BO ) / 2-(P DI +P DO ) / 2,P BI is the pressure at the blood chamber entrance, P BO is the pressure at the blood chamber outlet, P DI is the pressure at the dialysate inlet, P DO is the pressure at the dialysate outlet, and the unit of the transmembrane pressure TMP is kPa; The control system is also used to calculate the flux at different times according to the transmembrane pressure, the flux being equal to the dehydration rate of the dialyzer (25) divided by the transmembrane pressure TMP, the unit of the dehydration rate being L / h, and the unit of the flux being L / (h·kPa); The control system is used to calculate the flux attenuation rate η according to the flux at different moments, wherein the flux attenuation rate η=(1-flux at a certain moment / flux at an initial moment)×100%.

2. The dialyzer coagulation status monitoring system according to claim 1, characterized in that: It also includes a host computer connected to the control system, and the host computer is used to output curves of the transmembrane pressure and the flux attenuation rate changing with time.

3. A dialysis device, characterized in that: The dialyzer (25) includes the dialysate circuit and the blood circuit connected thereto, and also includes the dialyzer coagulation status monitoring system as described in claim 1 or 2 above.

4. The dialysis device according to claim 3, characterized in that The dialysate circuit comprises: A degassing chamber (8), which is used to degas the liquid inside; at least two dialysate containers for containing different dialysates, the outlets of all the dialysate containers being connected to the outlet of the degassing chamber (8); A mixing chamber is provided at the connection point between the outlet of the dialysate container and the outlet of the degassing chamber (8), and the outlet of the mixing chamber is connected to the dialysate inlet.

5. The dialysis device according to claim 4, characterized in that The dialysate outlet is connected to a heat exchanger (4) for exchanging the heat of the dialysate via a waste liquid pipeline, and the heat exchanger (4) is connected to the waste liquid outlet so that the dialysate that has undergone heat exchange is discharged from the waste liquid outlet.

6. The dialysis device according to claim 5, characterized in that A conductivity sensor (21) for detecting the concentration of the dialysate is also provided between the dialysate inlet and the mixing chamber, and a passage for conducting unqualified dialysate is also provided between the conductivity sensor (21) and the waste liquid pipeline.

7. The dialysis device according to claim 5, characterized in that A disinfectant container is also connected between the dialysate outlet and the heat exchanger (4), and the waste liquid pipeline is cleaned by the disinfectant in the disinfectant container.

8. The dialysis device according to claim 5, characterized in that The heat exchanger (4) and the degassing chamber (8) are in communication, so that the injected water enters the degassing chamber (8) through the heat exchanger (4).

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