Blood viscosity detection method, device and equipment

Abstract

The application provides a blood viscosity detection method, device and equipment. The blood viscosity detection method comprises the following steps: inputting a replacement fluid to a vein pipeline through a hard pipeline at a first flow rate, and determining a first inlet and outlet pressure difference of the hard pipeline; determining the viscosity of the replacement fluid according to the pipeline attribute of the hard pipeline, the first flow rate and the first inlet and outlet pressure difference; if the difference between the viscosity of the replacement fluid and the viscosity of water is within a first preset range, then determining a viscosity coefficient according to the viscosity of water, the first flow rate and the first inlet and outlet pressure difference; performing dialysis on blood, and determining the second flow rate of the blood in the hard pipeline after dialysis and the second inlet and outlet pressure difference of the hard pipeline in real time; and determining the real-time viscosity of the blood during dialysis according to the viscosity coefficient, the second flow rate and the second inlet and outlet pressure difference. The application solves the problem that the blood viscosity cannot be detected during hemodialysis treatment in the prior art.

Description

TECHNICAL FIELD

[0001] The utility model relates to blood purification technical field, specifically, relate to a blood purification equipment and storage medium. BACKGROUND

[0002] Blood purification equipment leads human body blood to outside, then filters specific molecular substance in blood, and then returns purified blood to human body. Blood purification treatment mode can be divided into hemodialysis, hemofiltration, hemodialysis filtration, blood perfusion, plasma replacement, immunoadsorption, peritoneal dialysis and other treatment modes according to blood purification principle. Different blood purification treatment modes are suitable for different clinical symptoms, for example: various cardiovascular instability, hypercatabolism or acute and chronic renal failure with brain water, multiple organ dysfunction syndrome, acute respiratory distress syndrome, crush syndrome, acute necrotizing pancreatitis, chronic heart failure, hepatic encephalopathy, drug and poison poisoning and various diseases rescue.

[0003] Blood purification treatment needs to rely on blood purification equipment to execute, taking hemodialysis treatment mode as an example, the blood of patient and dialysate of standard ion concentration are introduced into dialyzer simultaneously, dialysate and blood are on both sides of hollow fiber membrane, utilize the diffusion, convection, ultrafiltration of hollow fiber membrane, remove the excess water in patient's body with proper speed, reach the purpose of correcting water electrolyte and acid-base balance. In the hemodialysis treatment process through blood purification equipment, in order to ensure the safety of patient in the hemodialysis treatment process, need to monitor the hemodynamic parameter in the hemodialysis treatment process in real time, to effectively inhibit the complications such as hypertension, severe dehydration caused vascular atrophy produced in dialysis process. Therefore, the monitoring process of hemodynamic parameter as the essential function of blood purification equipment, has extremely great influence on the safety of patient's hemodialysis treatment.

[0004] Blood viscosity is a physical value representing flow resistance generated by the flow of blood in a pipeline. As one of the hemodynamic parameters, blood viscosity is an important indicator reflecting the flow properties of blood. When the blood viscosity increases during extracorporeal blood circulation, it can cause problems such as blood clotting and thrombosis, and cause cardiovascular-related complications. When the blood viscosity decreases during extracorporeal blood circulation, the dehydration efficiency of the patient's blood through the dialyzer is poor, reducing the patient's hemodialysis efficiency. In the prior art, when the blood viscosity of a patient is measured, the blood viscosity of the patient cannot be detected in real time during hemodialysis. Only after hemodialysis or before hemodialysis, the blood of the patient is extracted, and the blood routine or blood viscosity of the patient is tested. During the test, a viscosity tester and a blood instrument are used to test the blood viscosity of the patient. However, this blood viscosity measurement method has a certain lag, cannot ensure the safety of the patient's hemodialysis treatment, and reduces the practical value and reliability of the blood viscosity measurement process. SUMMARY

[0005] The present application aims to solve the problem that the blood viscosity cannot be detected during hemodialysis treatment in the prior art.

[0006] To solve the above problems, the first aspect of the present application provides a blood viscosity detection method, comprising:

[0007] determining the first inlet and outlet pressure difference of the hard pipeline by inputting the replacement fluid into the venous pipeline at a first flow rate through the hard pipeline;

[0008] determining the viscosity of the replacement fluid according to the pipeline attribute of the hard pipeline, the first flow rate and the first inlet and outlet pressure difference, wherein the pipeline attribute of the hard pipeline includes the length of the hard pipeline and the pipe diameter of the hard pipeline;

[0009] if the difference between the viscosity of the replacement fluid and the viscosity of water is within a first preset range, determining the viscosity coefficient according to the viscosity of water, the first flow rate and the first inlet and outlet pressure difference;

[0010] dialyzing blood, and determining the second flow rate of the blood in the hard pipeline after dialysis and the second inlet and outlet pressure difference of the hard pipeline in real time;

[0011] determining the real-time viscosity of the blood during dialysis according to the viscosity coefficient, the second flow rate and the second inlet and outlet pressure difference.

[0012] The second aspect of the present application provides a blood purification device, comprising:

[0013] The first pressure detection module is configured to input the replacement fluid to the venous pipeline through the hard pipeline at a first flow rate, and determine a first inlet-outlet pressure difference of the hard pipeline.

[0014] The first viscosity detection module is configured to determine the viscosity of the replacement fluid according to a pipeline attribute of the hard pipeline, the first flow rate, and the first inlet-outlet pressure difference, wherein the pipeline attribute of the hard pipeline includes a length of the hard pipeline and a pipe diameter of the hard pipeline.

[0015] The viscosity coefficient module is configured to determine that a difference between the viscosity of the replacement fluid and a viscosity of water is within a first preset range, and obtain a viscosity coefficient according to the viscosity of water, the first flow rate, and the first inlet-outlet pressure difference.

[0016] The second pressure detection module is configured to perform dialysis on the blood, and determine a second flow rate of the blood in the hard pipeline after dialysis and a second inlet-outlet pressure difference of the hard pipeline in real time.

[0017] The second viscosity detection module is configured to determine a real-time viscosity of the blood during dialysis according to the viscosity coefficient, the second flow rate, and the second inlet-outlet pressure difference.

[0018] The third aspect of the present application provides an electronic device, which comprises a memory, a processor, and a computer program stored in the memory, and the processor executes the computer program to implement the steps of the method of any one of the first aspect.

[0019] The fourth aspect of the present application provides a blood purification device, which comprises a pressure sensor, a hard pipeline, a venous pipeline, a dialyzer, and an electronic device as described in the third aspect, an input end of the venous pipeline is connected to a blood output end of the dialyzer, an output end of the venous pipeline is connected to a human venous blood vessel, the hard pipeline is installed on the venous pipeline, the pressure sensor is electrically connected to the electronic device, and the pressure sensor is configured to determine an inlet-outlet pressure difference of the hard pipeline.

[0020] The blood viscosity detection method, the blood purification device, the electronic equipment and the blood purification equipment provided by the present application utilize the operation steps in the hemodialysis process, first perform self-checking to exclude the fault state of each component of the blood purification equipment itself in the blood viscosity detection process, reduce the error caused by the components of the blood purification equipment itself in the blood viscosity detection process, improve the detection accuracy of the blood viscosity, then obtain the viscosity coefficient necessary in the blood viscosity detection process in advance according to the viscosity of water, the first flow and the first inlet and outlet pressure difference, so as to provide a data basis for the calculation process of the blood viscosity in the later stage, and the blood viscosity of the patient in the dialysis can be calculated in real time when the patient is hemodialyzed, and the actual dehydration effect of the dialyzer is accurately judged according to the blood viscosity in the dialysis, thereby ensuring the safety and efficiency of the patient in the hemodialysis process and preventing the patient from appearing in a fault state in the hemodialysis process; the blood viscosity detection and the hemodialysis process are perfectly combined, the viscosity detection is effectively integrated into the hemodialysis process, the blood viscosity of the patient can be detected and monitored in real time in the blood treatment stage, has strong practical operability and convenience, and overcomes the problem that the blood viscosity of the patient cannot be detected in the hemodialysis process in the prior art, resulting in low safety of the hemodialysis treatment of the patient; in addition, the blood is not needed to be separately collected and contacted in the blood purification stage to perform chemical treatment on the blood to obtain the blood viscosity, the contactless detection of the blood viscosity is realized, the blood in the pipeline is prevented from being polluted, the safety and anti-interference of the blood viscosity detection of the patient are greatly ensured, and the application range and practical value of the blood viscosity detection method are improved. BRIEF DESCRIPTION OF DRAWINGS

[0021] Figure 1 It is a first structure schematic view of the blood purification equipment provided in the embodiment of the present application.

[0022] Figure 2 It is a second structure schematic view of the blood purification equipment provided in the embodiment of the present application.

[0023] Figure 3 It is a flow schematic view of the blood viscosity detection method provided in the embodiment of the present application.

[0024] Figure 4 It is a relationship curve diagram of the real-time viscosity of blood and the dehydration amount in dialysis provided in the embodiment of the present application.

[0025] Figure 5 It is a relationship curve diagram of the blood viscosity before dialysis and the target dehydration amount provided in the embodiment of the present application.

[0026] Figure 6 It is a structure schematic view of the display screen provided in the embodiment of the present application.

[0027] Figure 7A first change curve of real-time viscosity of blood over time provided in an embodiment of the present application;

[0028] Figure 8 A schematic diagram of a display screen displaying a second change curve and a third change curve provided in an embodiment of the present application;

[0029] Figure 9 A third structural schematic diagram of a blood purification device provided in an embodiment of the present application.

[0030] Figure 10 A structural schematic diagram of an electronic device provided in an embodiment of the present application.

[0031] Legend of reference signs:

[0032] 1-arterial line; 2-venous line; 3-dialyzer; 4-blood break; 5-venous pot; 6-dialysate pump; 7-dialysate bag; 8-first weight sensor; 9-first heater; 10-first flow interruption detector; 11-filter pump; 12-waste bag; 13-second weight sensor; 14-blood leakage detector; 15-substitution fluid pump; 16-substitution fluid bag; 17-third weight sensor; 18-second heater; 19-second flow interruption detector; 20-previous substitution; 21-later substitution; 22-heparin pump; 23-bubble detector; 24-blood detector; 25-blood flow meter; 26-display screen; 27-first pressure sensor; 28-second pressure sensor; 29-rigid line. DETAILED DESCRIPTION

[0033] The technical solutions of the present application and how the technical solutions of the present application solve the above technical problems will be described in detail below with specific embodiments. The following specific embodiments can be combined with each other, and the same or similar concepts or processes can not be described again in some embodiments. The embodiments of the present application will be described below with reference to the accompanying drawings.

[0034] It should be noted that examples of embodiments of the present application are shown in the accompanying drawings, wherein the same or similar reference numerals represent the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present application and cannot be interpreted as a limitation of the present application.

[0035] Those skilled in the art will understand that, unless explicitly stated otherwise, the singular forms “a,” “an,” and “the” used herein may also include the plural forms. It should be further understood that the term “comprising” as used in the specification of this application means the presence of features, integers, steps, operations, elements, and / or components, but does not exclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and / or groups thereof. It should be understood that when we say an element is “connected” or “coupled” to another element, it can be directly connected or coupled to the other element, or there may be intermediate elements. Furthermore, “connected” or “coupled” as used herein can include wireless connections or wireless coupling. The term “and / or” as used herein includes all or any units and all combinations of one or more associated listed items.

[0036] See Figure 1 , Figure 1 This is a schematic diagram of the structure of one embodiment of the blood purification device in this application. Figure 1 This is a basic structural diagram of a blood purification treatment device. (Combined with...) Figure 1 As shown, the blood purification device includes: an arterial line 1, a venous line 2, a dialyzer 3, a blood pump 4, a venous reservoir 5, a dialysate pump 6, a dialysis bag 7, a first weight sensor 8, a first heater 9, a first flow interruption detector 10, a filtration pump 11, a waste fluid bag 12, a second weight sensor 13, a blood leakage detector 14, a replacement fluid pump 15, a replacement bag 16, a third weight sensor 17, a second heater 18, a second flow interruption detector 19, a pre-replacement unit 20, a post-replacement unit 21, a heparin pump 22, a bubble detector 23, and a blood detector 24. The input end of the arterial line 1 is connected to the patient's blood. The system connects to the arterial blood vessels. The output end of the arterial line 1 is connected to the blood input end of the dialyzer 3, and the input end of the venous line 2 is connected to the blood output end of the dialyzer 3. The output end of the venous line 2 is connected to the human vein, forming a blood circulation loop. The dialyzer 3 has a hollow fiber membrane inside, and blood and dialysate are distributed on both sides of the hollow fiber membrane. The dialysate and blood exchange substances on both sides of the hollow fiber membrane. The venous line 2 returns the purified blood to the human vein. The waste fluid generated during the hemodialysis process is input into and stored in the waste fluid bag 12, thus completing the hemodialysis treatment process.

[0037] To facilitate real-time monitoring of blood viscosity during hemodialysis treatment, this embodiment... Figure 1 Based on this, improvements were made to the blood purification equipment, resulting in... Figure 2 The diagram shows the structure of a blood purification device. (Combined with...) Figure 2As shown, the blood purification device also includes: a first pressure sensor 27, a second pressure sensor 28, and a rigid tubing 29. The rigid tubing 29 is disposed on the venous tubing 2, and the first pressure sensor 27 and the second pressure sensor 28 are respectively disposed at both ends of the rigid tubing 29. Specifically, the venous tubing 2 includes a first venous tubing 2a, a second venous tubing 2b, and a third venous tubing 2c. The first end of the first venous tubing 2a is connected to the blood output end of the dialyzer 3, and the second end of the first venous tubing 2a is connected to the venous reservoir 5. The inlet connection is made of the second vein 2b, the first end of which is connected to the outlet of the vein pot 5, the second end of which is connected to the input end of the rigid tube 29, and the output end of the rigid tube 29 is connected to the third vein 2c. The first pressure sensor 27 is located at the connection between the second vein 2b and the rigid tube 29, and the second pressure sensor 28 is located at the connection between the rigid tube 29 and the third vein 2c. The first pressure sensor 27 and the second pressure sensor 28 are used to measure the pressure difference between the inlet and outlet of the rigid tube 29.

[0038] In this embodiment, a rigid conduit 29 is provided on the venous conduit 2. Compared with other conduits (including arterial conduit 1, first venous conduit 2a, second venous conduit 2b and third venous conduit 2c), the rigid conduit 29 has a greater rigidity. For example, the rigid conduit 29 typically has a rigidity of 45 to 65. The rigid conduit 29 can prevent excessive liquid pressure from causing elastic deformation of the conduit and fluctuations in the liquid flow rate within the conduit. Liquid can be smoothly transmitted through the rigid conduit 29 to ensure the accuracy of blood viscosity detection.

[0039] See Figure 3 , Figure 3 This is a schematic flowchart of the blood viscosity detection method provided in the embodiments of this application. Combined with... Figure 3 As shown, a first aspect of this application provides a blood viscosity detection method, comprising:

[0040] Step S31: Through rigid tubing 29, introduce replacement fluid into venous tubing 2 at a first flow rate, and determine the first inlet and outlet pressure difference of rigid tubing 29.

[0041] Before starting the blood purification equipment, it is necessary to install the tubing, that is, to install the blood purification equipment according to the structural diagram (e.g., Figure 2The blood purification device is connected to the pipeline to ensure that the blood purification device is in a normal physical connection state. When the blood purification device is connected to the pipeline, the blood purification device can be pre-flushed. The pre-flushing stage is an essential step in the operation of the blood purification device. After the pre-flushing stage, impurities remaining in the pipeline (including the arterial pipeline 1, the venous pipeline 2, and the rigid pipeline 29), the dialyzer 3, and the venous jug 5 can be prevented from mixing into the patient's blood during hemodialysis, thereby affecting the safety of subsequent blood treatment. The following will be described in combination with Figure 2 During the pre-flushing stage, one end of the arterial pipeline 1 is connected to the replacement fluid, and the replacement fluid flows through the arterial pipeline 1, the dialyzer 3, the first venous pipeline 2a, the venous jug 5, the second venous pipeline 2b, the rigid pipeline 29, and the third venous pipeline 2c in sequence. The replacement fluid is used to flush the pipeline, the dialyzer 3, and the venous jug 5. The flushed replacement fluid becomes waste fluid, and one end of the third venous pipeline 2c outputs the waste fluid to the waste fluid bag, which stores the waste fluid.

[0042] Specifically, the first flow rate can be determined by detecting the flow rate of the replacement fluid in the third venous pipeline 2c. A blood flow meter 25 can be arranged on the third venous pipeline 2c to detect the flow rate of the replacement fluid in the third venous pipeline 2c.

[0043] When the replacement fluid flows through the rigid pipeline 29, the first inlet pressure of the rigid pipeline 29 is detected by the first pressure sensor 27, and the first outlet pressure of the rigid pipeline 29 is detected by the second pressure sensor 28. The first inlet and outlet pressure difference of the rigid pipeline 29 is | first inlet pressure - first outlet pressure |.

[0044] Step S32, according to the pipeline attribute of the rigid pipeline 29, the first flow rate, and the first inlet and outlet pressure difference, the viscosity of the replacement fluid is determined, wherein the pipeline attribute of the rigid pipeline 29 includes the length of the rigid pipeline 29 and the pipe diameter of the rigid pipeline 29.

[0045] In actual use, the pipeline attribute of the rigid pipeline 29 may not completely match the nameplate data of the rigid pipeline 29, and the pipeline attribute of the rigid pipeline 29 may be adjusted according to the actual situation, for example, the length of the rigid pipeline 29 is adjusted. Therefore, in order to improve the detection accuracy of the blood viscosity, the length and the pipe diameter of the rigid pipeline 29 need to be determined before the viscosity of the replacement fluid is determined. Specifically, the length and the pipe diameter of the rigid pipeline 29 can be detected by a conventional detection method, for example, by a light source detection method.

[0046] After the pipeline attribute of the rigid pipeline 29, the first flow rate, and the first inlet and outlet pressure difference are determined, the viscosity of the replacement fluid can be calculated by the following formula:

[0047]

[0048] Wherein, C1 represents the viscosity of the displacement liquid, the unit is Pa.S; R represents the pipe diameter of the hard pipeline, the unit is m; L represents the length of the hard pipeline, the unit is m; ΔP1 represents the first inlet and outlet pressure difference, the unit is Pa; Q1 represents the first flow, the unit is m 3 / s.

[0049] Step S33, if the difference between the viscosity of the displacement liquid and the viscosity of water is in the first preset range, then the viscosity coefficient is obtained according to the viscosity of water, the first flow and the first inlet and outlet pressure difference.

[0050] Specifically, after determining the viscosity of the displacement liquid, the viscosity of the displacement liquid and the viscosity of water are compared, if the absolute value of the difference between the viscosity of the displacement liquid and the viscosity of water is less than the first preset range, then the information for prompting the determination of the viscosity coefficient is output; if the absolute value of the difference between the viscosity of the displacement liquid and the viscosity of water is greater than or equal to the first preset range, then the information for prompting the fault is output.

[0051] Wherein, the viscosity of water is usually a constant value, and there is no concentration problem of water, and those skilled in the art can refer to relevant technical documents to determine the viscosity of water, for example: the viscosity of water is 100 m 3 / s. And the displacement liquid is usually water for injection, and under normal circumstances, the viscosity of the displacement liquid is approximately equal to the viscosity of water, that is, |the viscosity of the displacement liquid-the viscosity of water|<the first preset range; when the absolute value of the difference between the viscosity of the displacement liquid and the viscosity of water detected by the embodiment is greater than or equal to the first preset range, it indicates that the viscosity of the displacement liquid detected by the embodiment has a large error, and the information for prompting the fault can prompt the user to check each part of the blood purification equipment (including: blood flow meter, first pressure sensor, dialyzer, blood pump, etc.), so as to troubleshoot the fault state of the blood purification equipment. And after troubleshooting the fault of the blood purification equipment, steps S31 and S32 also need to be re-executed until the absolute value of the difference between the viscosity of the displacement liquid and the viscosity of water detected by the embodiment is less than the first preset range.

[0052] It should be noted that the first preset range is not further limited in the embodiment, and those skilled in the art can set it according to the actual situation, for example: the first preset range is 5 m 3 / s, if the viscosity of water is 100 m 3 / s, the viscosity of the displacement liquid is 90 m 3 / s, then |90 m 3 / s-100 m 3 / s|=10 m 3 / s≥5 m 3 / s, output information for prompting a fault; if the viscosity of the replacement fluid is 102m 3 / s, 102m 3 / s-100m 3 / s|=2m 3 / s<5m 3 / s, output information for prompting determination of the viscosity coefficient, and continue to perform subsequent operations.

[0053] After receiving the information for determining the viscosity coefficient, the viscosity coefficient is calculated by the following formula:

[0054]

[0055] wherein μ represents the viscosity coefficient; M1 represents the viscosity of water, in units of Pa.s; ΔP1 represents the first inlet and outlet pressure difference, in units of Pa; Q1 represents the first flow rate, in units of m 3 / s.

[0056] The viscosity coefficient represents a coefficient of the blood purification device itself, and the viscosity coefficient only has a correlation with the pipeline structure characteristics of the blood purification device itself. According to the viscosity of water, the first flow rate, and the first inlet and outlet pressure difference, the viscosity coefficient can be obtained. The viscosity coefficient is a specific parameter in the blood viscosity detection process. By using the operation steps in the hemodialysis process, the viscosity system parameters necessary in the blood viscosity detection process are obtained in advance, so as to provide a data basis for the calculation of the blood viscosity in the later period. When the patient is subjected to hemodialysis, not only is the blood viscosity detection step simplified, but the blood viscosity can also be calculated more accurately.

[0057] In this embodiment, the viscosity of the replacement fluid is first determined, and then it is determined whether the difference between the viscosity of the replacement fluid and the viscosity of water is in the first preset range. If it is determined that the difference between the viscosity of the replacement fluid and the viscosity of water is in the first preset range, the viscosity coefficient is obtained according to the viscosity of water, the first flow rate, and the first inlet and outlet pressure difference. This not only avoids the difference between the parameter tolerance of the hard pipeline and the actual value of the hard pipeline, which leads to the calculation error of the blood viscosity, but also allows the fault state of each component in the blood purification device to be checked in advance. This not only reduces the error caused by the components of the blood purification device in the blood viscosity detection process, improves the detection accuracy of the blood viscosity, but also avoids invalid operations caused by the fault state of the blood purification device, and improves the detection efficiency of the blood viscosity.

[0058] In step S34, the blood is subjected to dialysis, and the second flow rate of the blood in the hard pipeline 29 after dialysis and the second inlet and outlet pressure difference of the hard pipeline 29 are determined in real time.

[0059] Specifically, after the blood purification device sequentially passes through the pre-flushing stage and the blood introduction stage, the blood purification device enters the blood purification stage. In the blood purification stage, the dialyzer 3 is connected to the blood and the dialysate at the same time, and the blood and the dialysate exchange substances on both sides of the hollow fiber membrane to complete the hemodialysis. The blood purification stage usually lasts for 12 to 24 hours to achieve a good hemodialysis effect.

[0060] The second flow rate represents the dialyzed blood flow rate output by the rigid pipeline 29. According to the second flow rate, the dialyzed blood flow rate output by the rigid pipeline 29 can be determined. During the hemodialysis process, the dialyzed blood flow rate in the third venous pipeline 2c can be detected by the blood flow meter 25 to determine the second flow rate, for example, the second flow rate is 10 ml / min.

[0061] When the blood flows through the rigid pipeline 29, the second inlet pressure of the rigid pipeline 29 is detected by the first pressure sensor 27, and the second outlet pressure of the rigid pipeline 29 is detected by the second pressure sensor 28. The second inlet and outlet pressure difference of the rigid pipeline 29 is | second inlet pressure-second outlet pressure |.

[0062] In this embodiment, the second flow rate of the dialyzed blood in the rigid pipeline 29 and the second inlet and outlet pressure difference of the rigid pipeline 29 are determined in real time. The second flow rate of the dialyzed blood in the rigid pipeline 29 and the second inlet and outlet pressure difference of the rigid pipeline 29 can be determined every preset period. Those skilled in the art can set the preset period in advance according to the actual situation, for example, the preset period is 10 s, and then the second flow rate of the dialyzed blood in the rigid pipeline 29 and the second inlet and outlet pressure difference of the rigid pipeline 29 are detected every 10 s.

[0063] In step S35, the real-time viscosity of the blood during dialysis is determined according to the viscosity coefficient, the second flow rate, and the second inlet and outlet pressure difference.

[0064] After the viscosity coefficient, the second flow rate, and the second inlet and outlet pressure difference are determined, the real-time viscosity of the blood during dialysis can be calculated by the following formula:

[0065]

[0066] Wherein, C2 represents the real-time viscosity of the blood during dialysis, and the unit is Pa.S; μ represents the viscosity coefficient; ΔP2 represents the second inlet and outlet pressure difference, and the unit is Pa; Q2 represents the second flow rate, and the unit is ml / min. 3 / s.

[0067] The real-time viscosity of blood in dialysis represents the blood viscosity in the blood purification stage. In this embodiment, the second flow rate of blood after dialysis in the rigid pipeline 29 and the second pressure difference between the inlet and outlet of the rigid pipeline 29 are determined in real time, so that the real-time viscosity of blood in dialysis can be obtained, thereby obtaining the change amount of blood viscosity of the patient in the blood purification stage, and judging the actual dehydration effect of the dialyzer 3.

[0068] Specifically, there is a corresponding relationship between the blood viscosity of the patient and the dehydration amount of the patient. After repeated tests by those skilled in the art, a curve as shown in Figure 4 is obtained. Figure 4 The curve is the relationship curve between the real-time viscosity of blood in dialysis and the dehydration amount. After obtaining the real-time viscosity of blood in dialysis, the actual dehydration amount of the patient in the blood purification stage can be directly obtained according to the real-time viscosity of blood in dialysis, and in combination with Figure 4 When the real-time viscosity of blood is larger, the actual dehydration amount of the patient is smaller, the water removed from the blood of the patient by the dialyzer 3 is smaller, and the actual dehydration effect of the dialyzer 3 is lower. When the real-time viscosity of blood is smaller, the actual dehydration amount of the patient is larger, the water removed from the blood of the patient by the dialyzer 3 is larger, and the actual dehydration effect of the dialyzer 3 is higher. Therefore, the actual dehydration effect of the dialyzer 3 can be accurately judged according to the real-time viscosity of blood in this embodiment, so that the user can monitor the hemodialysis state of the patient in real time, and the safety of hemodialysis of the patient is improved.

[0069] The blood viscosity detection method provided in the embodiments of the present application utilizes the operation steps in the hemodialysis process to first perform self-checking to exclude the fault states of various components of the blood purification device itself in the blood viscosity detection process, reduce errors caused by the components of the blood purification device itself in the blood viscosity detection process, and improve the detection accuracy of the blood viscosity. Then, according to the viscosity of water, the first flow rate, and the first inlet and outlet pressure difference, the viscosity coefficient necessary in the blood viscosity detection process is obtained in advance, so as to provide a data basis for the calculation process of the blood viscosity in the later stage. When the patient is performing hemodialysis, the blood viscosity of the patient during dialysis can be calculated in real time, and the actual dehydration effect of the dialyzer can be accurately judged according to the blood viscosity during dialysis, thereby ensuring the safety and efficiency of the patient during the hemodialysis process and preventing the patient from being in a fault state during the hemodialysis process. The embodiments of the present application perfectly combine blood viscosity detection and the hemodialysis process, effectively integrate the viscosity detection into the hemodialysis process, and can detect and monitor the blood viscosity of the patient in real time in the blood treatment stage. The embodiments of the present application have strong practical operability and convenience, overcome the problem that the blood viscosity of the patient cannot be detected during the hemodialysis process in the prior art, and the safety of the hemodialysis treatment of the patient is low. In addition, the embodiments of the present application do not need to separately collect and contact blood in the blood purification stage to perform chemical treatment on the blood to obtain the blood viscosity, realize contactless detection of the blood viscosity, prevent the blood in the pipeline from being polluted, greatly guarantee the safety and anti-interference of the blood viscosity detection of the patient, and also improve the application range and practical value of the blood viscosity detection method in the embodiments of the present application.

[0070] On the basis of the above-mentioned embodiments, after determining the real-time viscosity of blood during dialysis in step S35, the method further comprises:

[0071] detecting the liquid level of the venous jug 5 and determining whether the liquid level of the venous jug 5 is greater than a preset liquid level, and if the liquid level of the venous jug 5 is greater than the preset liquid level, determining the actual dehydration effect of the dialyzer 3 according to the real-time viscosity of blood.

[0072] Specifically, the venous jug 5 plays a role of buffering the blood flow rate in the pipeline and removing the air bubbles in the blood, the first venous pipeline 2a outputs the dialyzed blood to the venous jug 5, the dialyzed blood is accumulated in the venous jug 5, and the liquid level of the venous jug 5 refers to the liquid level height of the blood in the venous jug 5. During the blood purification stage, when the blood in the first venous pipeline 2a in the blood purification device is in a normal flow state, the liquid level of the venous jug 5 is greater than the preset liquid level. Only when the blood is in the normal flow state, the actual dehydration effect of the dialyzer 3 is judged according to the real-time viscosity of the blood, so as to evaluate the blood dialysis efficiency of the patient. When the liquid level of the venous jug 5 is less than or equal to the preset liquid level, it indicates that the liquid level of the venous jug 5 is too low, and air bubble failure is prone to occur in the second venous pipeline 2b and the third venous pipeline 2c, resulting in blood purification failure. At this time, it is meaningless to judge the actual dehydration effect of the dialyzer 3 according to the real-time viscosity of the blood, and it is also difficult to accurately judge the actual dehydration effect of the dialyzer 3 according to the real-time viscosity of the blood. Therefore, it is not necessary to judge the actual dehydration effect of the dialyzer 3 according to the real-time viscosity of the blood. Before judging the actual dehydration effect of the dialyzer 3, the embodiment judges whether the liquid level of the venous jug 5 is in a normal state in advance, which can eliminate the judgment error of the actual dehydration effect of the dialyzer 3 caused by the liquid level failure of the venous jug 5, and greatly improves the judgment accuracy of the actual dehydration effect of the dialyzer 3.

[0073] In the embodiment, the preset liquid level represents the lowest safe liquid level of the venous jug 5 during the blood purification stage. Only when the liquid level of the venous jug 5 is greater than the preset liquid level, the blood in the blood purification device is in a normal flow state. The specific value of the preset liquid level can be obtained by technicians in the art according to multiple clinical experiences. For example, the preset liquid level is 1 / 3 of the highest liquid level of the venous jug 5 that can accommodate blood.

[0074] In order to better output the prompt operation and facilitate the user to judge the blood dialysis effect, the blood purification device further comprises a display screen 26, Figure 6 The structure diagram of the display screen is shown in FIG. 6. On the basis of the above embodiment, the step S35 further comprises:

[0075] The first change curve of the real-time viscosity of the blood with time during dialysis is drawn, and the first change curve of the real-time viscosity of the blood with time is displayed on the display screen 26.

[0076] Specifically, in the blood purification stage, the blood viscosity of the patient is detected in real time, and the user can view the real-time viscosity of the blood of the patient on the display screen 26 in real time, so that the user can know the real-time viscosity of the blood of the patient in the dialysis in real time, and through the first change curve of the real-time viscosity of the blood with time, the user can timely obtain the change of the blood viscosity of the patient with time in the blood purification stage, so as to judge the treatment effect of the hemodialysis of the patient in the blood purification stage, and ensure the safety of the hemodialysis of the patient. Exemplarily, Figure 7 the first change curve of the real-time viscosity of the blood with time, and the second change curve and the third change curve displayed on the display screen are combined Figure 7 It can be seen that in the normal state of the blood purification stage, the real-time viscosity of the blood slowly increases with time, and if the change trend of the first change curve on the display screen 26 changes sharply, it means that the real-time viscosity detection process of the blood or the hemodialysis process of the patient has a problem, and the user can know that the real-time viscosity of the blood is abnormal by seeing the first change curve on the display screen 26, so as to find out the reason for the abnormality of the real-time viscosity of the blood in time.

[0077] On the basis of the above embodiment, step S34 further comprises:

[0078] The second change curve of the second inlet pressure with time and the third change curve of the second outlet pressure with time are drawn, and the second change curve and the third change curve are displayed on the display screen 26.

[0079] Specifically, in the blood purification stage, the blood inlet pressure change curve of the hard pipeline 29, i.e. the second change curve, and the blood outlet pressure change curve of the hard pipeline 29, i.e. the third change curve, are drawn respectively, the user can see the second change curve and the third change curve on the display screen 26 at the same time, and compare the blood inlet pressure of the hard pipeline 29 with the blood outlet pressure of the hard pipeline 29 to judge whether the blood pressure change amount in the hard pipeline 29 is in a normal state; Exemplarily, Figure 8 the second change curve and the third change curve displayed on the display screen are combined Figure 8It can be seen that, in the blood purification stage in the normal state, the changes of the second change curve and the third change curve are both gentle, and the change trends of the second change curve and the third change curve are also approximately the same, and the difference between the second inlet pressure and the second outlet pressure will remain stable; the user can judge whether the blood pressure in the hard pipeline 29 fails according to the fluctuation of the second change curve and the third change curve, for example: when the second change curve appears a sharp fluctuation in a certain time period, the user sees the sharp fluctuation phenomenon of the second change curve on the display screen 26, and then it is known that the blood pressure in the hard pipeline 29 fails, so that the failure state of the blood pressure in the hard pipeline 29 can be handled in time.

[0080] On the basis of the above embodiment, step S34 further comprises:

[0081] It is judged whether the change amount of the second flow with time is greater than a preset change amount, and if the change amount of the second flow with time is greater than the preset change amount, a flow fluctuation prompt information is output.

[0082] Specifically, the change amount of the second flow with time refers to the difference between the maximum value of the second flow and the minimum value of the second flow in the process of detecting the blood flow of the third venous pipeline 2c. Generally, when the liquid flow in the pipeline changes too much, it will cause a greater fluctuation in the process of detecting the liquid pressure in the pipeline, and the process of detecting the liquid pressure in the pipeline is prone to error, for example: the pressure detection value of the pipeline is too large or too small. In order to reduce the liquid pressure detection error caused by the change amount of the blood flow, it can be judged whether the change amount of the second flow with time is greater than a preset change amount, and when it is judged that the change amount of the second flow with time is greater than the preset change amount, it indicates that the change amplitude of the blood flow in the hard pipeline 29 is too large, and the user is prompted through the flow fluctuation prompt information to pay attention to the blood flow fluctuation failure in the hard pipeline 29 in time, so as to prevent the change amount of the blood flow in the hard pipeline 29 from causing interference to the blood viscosity detection process and avoid a larger error in the blood viscosity detection process.

[0083] In the embodiment, the skilled person in the art can set the preset change amount in advance according to clinical experience, for example: the preset change amount is 4 ml / min, and exemplarily: if the change amount of the second flow with time (5 ml / min) > the preset change amount (4 ml / min), a sound prompt information such as "the change amplitude of the blood flow in the pipeline is too large" is output to remind the user to pay attention to the abnormal state of the change amount of the blood flow in the hard pipeline 29.

[0084] On the basis of the above embodiment, before the blood is dialyzed in step S34, it further comprises:

[0085] The blood is input to the venous line 2 through the hard line 29 at a third flow rate, and a third inlet-outlet pressure difference of the hard line 29 is determined;

[0086] The blood viscosity before dialysis is determined according to the viscosity coefficient, the third flow rate and the third inlet-outlet pressure difference.

[0087] Specifically, after the blood purification device goes through the pre-flushing stage, the blood purification device enters the blood drawing stage, and then enters the blood purification stage. In the blood drawing stage, one end of the arterial line 1 is connected to the patient's artery, and the arterial line 1 is connected to the blood, and the blood flows through the arterial line 1, the dialyzer 3, the first venous line 2a, the venous jug 5, the second venous line 2b, the hard line 29 and the third venous line 2c in sequence. The blood drawing stage is the initial stage of the dialyzer 3 contacting the blood. The blood detector 24 detects whether there is blood in the third venous line 2c by using the principle of photosensing. When the blood detector 24 detects that there is blood in the third venous line 2c, it means that the blood drawing is successful.

[0088] The third flow rate represents the blood flow rate input from the hard line 29 to the third venous line 2c, and the blood flow rate input to the third venous line 2c can be determined according to the third flow rate. During the dialysis of the blood, the blood flow rate of the third venous line 2c can be detected by the blood flow meter 25 to determine the third flow rate.

[0089] When the blood flows through the hard line 29, the third inlet pressure of the hard line 29 is detected by the first pressure sensor 27, and the third outlet pressure of the hard line 29 is detected by the second pressure sensor 28. The third inlet-outlet pressure difference of the hard line 29 = | third inlet pressure - third outlet pressure |.

[0090] After the viscosity coefficient, the third flow rate and the third inlet-outlet pressure difference are determined, the blood viscosity before dialysis can be calculated by the following formula:

[0091]

[0092] Wherein, C3 represents the blood viscosity before dialysis, the unit is Pa.S; μ represents the viscosity coefficient; ΔP3 represents the third inlet-outlet pressure difference, the unit is Pa; Q3 represents the third flow rate, the unit is m 3 / s.

[0093] In the blood introduction stage, the patient's blood has not been formally hemodialyzed, therefore, the blood viscosity before dialysis represents the blood viscosity of the patient before hemodialysis, according to the blood viscosity before dialysis, the content of excess water in the blood can be calculated, and according to the blood viscosity before dialysis, the target dehydration amount of the dialyzer 3 can be obtained. The target dehydration amount of the dialyzer 3 represents the most ideal theoretical dehydration amount of the patient in the blood purification stage, when the dehydration amount of the dialyzer 3 is exactly equal to the target dehydration amount, then the patient achieves the best hemodialysis treatment effect. There is a corresponding relationship between the blood viscosity before dialysis and the target dehydration amount of the dialyzer, after many experiments by the skilled in the art, the curve shown in Figure 5 is obtained, Figure 5 which is the relationship curve of the blood viscosity before dialysis and the target dehydration amount. After obtaining the blood viscosity before dialysis, according to the relationship curve in Figure 5 , the corresponding target dehydration amount of the dialyzer can be directly obtained.

[0094] It should be noted that the relationship curve between the blood viscosity before dialysis and the target dehydration amount is affected by multiple factors, for example: the model of the dialyzer, the physical condition of the patient, etc. The skilled in the art can set the relationship curve between the blood viscosity before dialysis and the target dehydration amount in advance according to clinical experience.

[0095] On the basis of the above embodiment, the blood viscosity detection method further comprises:

[0096] determining whether the dialyzer 3 needs to stop dialysis according to the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis; if it is determined that the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis is in the second preset range, stopping the hemodialysis; if it is determined that the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis is not in the second preset range, the hemodialysis does not need to be stopped.

[0097] wherein, the real-time blood viscosity during dialysis represents the actual blood viscosity of the patient in the blood purification stage, the blood viscosity before dialysis represents the blood viscosity of the patient before the dialyzer 3 starts hemodialysis, and the difference between the real-time blood viscosity during dialysis and the blood viscosity before dialysis represents the change amount of the blood viscosity of the patient after hemodialysis.

[0098] If the difference between the blood viscosity before dialysis and the real-time viscosity of the blood during dialysis is within the second preset range, and the patient's blood has undergone hemodialysis through dialyzer 3, the actual blood viscosity has rapidly decreased due to the amount of water removed by dialyzer 3, and the hemodialysis effect has achieved the expected therapeutic effect, then dialyzer 3 needs to stop hemodialysis. If the difference between the blood viscosity before dialysis and the real-time viscosity of the blood during dialysis is not within the second preset range, and the actual amount of water removed by dialyzer 3 has not reached the user's expected amount of water removal, then hemodialysis needs to continue, and dialyzer 3 does not need to stop hemodialysis. Therefore, in this embodiment, the need to stop hemodialysis can be determined based on the second preset range, which improves the efficiency of hemodialysis for patients and prevents problems such as excessive water loss or excessive fluid replacement during hemodialysis, leading to low blood concentration and deformed blood cell morphology, thus improving the safety of patients during hemodialysis.

[0099] The second preset range is: |Real-time viscosity of blood during dialysis - Viscosity of blood before dialysis| ≥ preset viscosity error range, wherein the preset viscosity error range is determined in advance by those skilled in the art based on multiple clinical trials, specifically, the preset viscosity error range is 20m. 3 / s. For example: the predialysis blood viscosity obtained during the blood draw phase is 90m. 3 / s, after 12 hours of hemodialysis, the real-time viscosity of the dialyzed blood obtained during the blood purification phase is: 110m. 3 / s, |Real-time viscosity of blood during dialysis - Viscosity of blood before dialysis| = |110m 3 / s-90m 3 / s|=20m 3 If the viscosity per second ( / s) is greater than or equal to the preset viscosity error range, it means that after 12 hours of hemodialysis, the actual amount of water removed from the patient's blood has been controlled within the user's expected amount. At this point, dialyzer 3 needs to stop hemodialysis. The blood viscosity obtained before dialysis during the blood draw stage is: 90 mg / L. 3 / s, after 12 hours of hemodialysis, the real-time viscosity of the dialyzed blood obtained during the blood purification phase is: 100m. 3 / s, |Real-time viscosity of blood during dialysis - Viscosity of blood before dialysis| = |110m 3 / s-90m 3 / s|=10m 3 If / s < preset viscosity error range, it means that the actual amount of water removed from the patient's blood after 12 hours of hemodialysis has not reached the user's expected amount of water removal. In this case, the user needs to continue hemodialysis until the preset viscosity error range is met.

[0100] It should be noted that the real-time viscosity of blood in dialysis is a real-time detection value, that is, the real-time viscosity of blood in dialysis is determined every interval preset period in the embodiment, therefore, the real-time viscosity of blood in dialysis is real-time change (usually the real-time viscosity of blood in dialysis gradually rises with the dialysis time), and whether the dialyzer 3 needs to stop dialysis is determined according to the real-time viscosity of blood in dialysis.

[0101] On the basis of the above embodiment, the blood viscosity detection method further comprises:

[0102] Before dialysis of the blood, a first temperature of the blood in the venous pipeline is acquired;

[0103] When the blood is dialyzed, a second temperature of the blood in the venous pipeline is acquired;

[0104] If the difference between the first temperature and the second temperature is in a preset temperature range, the blood dialysis is stopped according to that the difference between the blood viscosity before dialysis and the real-time viscosity of blood in dialysis is in a second preset range.

[0105] Specifically, a temperature sensor can be arranged on the third venous pipeline 2c, the temperature of the blood in the third venous pipeline 2c is detected by the temperature sensor, so as to obtain the first temperature and the second temperature. The temperature of the liquid has a great influence on the viscosity of the liquid in the pipeline, when the temperature of the liquid in the pipeline changes, the viscosity of the liquid in the pipeline will also change accordingly, by detecting the first temperature of the blood in the venous pipeline 2 before blood dialysis and the second temperature of the blood in the venous pipeline 2 during blood dialysis respectively, and according to whether the difference between the first temperature and the second temperature is in a preset temperature range, the interference of the temperature change amount of the blood on the blood viscosity detection process can be excluded, which is beneficial to improve the accuracy of the blood viscosity detection.

[0106] The first temperature represents the temperature at the blood viscosity before dialysis, and the second temperature represents the temperature at the real-time viscosity of blood in dialysis. If the absolute value of the difference between the first temperature and the second temperature is less than a preset temperature difference, the difference between the first temperature and the second temperature is in a preset temperature range; if the absolute value of the difference between the first temperature and the second temperature is greater than or equal to the preset temperature difference, the difference between the first temperature and the second temperature is not in the preset temperature range. The preset temperature difference represents the allowable temperature change error of the blood of the patient in the blood dialysis process, the specific value of the preset temperature difference is not limited in the embodiment of the application, and the person skilled in the art can set it according to the clinical treatment experience, for example: the preset temperature difference is 2℃.

[0107] When the difference between the first temperature and the second temperature is not in the preset temperature range, it indicates that the temperature difference in both the blood drawing stage and the blood purification stage is too large, and the large temperature difference will cause detection error of the blood viscosity. According to the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis, the actual dehydration amount of the patient in the blood purification stage cannot be accurately obtained. Therefore, the embodiment timely detects the difference between the first temperature and the second temperature. Only when the difference between the first temperature and the second temperature is in the preset temperature range, it indicates that the blood viscosity before dialysis and the real-time blood viscosity during dialysis are detected under the same temperature condition. Therefore, whether the dialyzer 3 needs to be stopped for blood dialysis can be determined according to the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis, so as to avoid the error caused by the temperature change to the blood viscosity detection process and the blood dialysis judgment process, and improve the accuracy of the blood viscosity detection.

[0108] If it is determined that the difference between the first temperature and the second temperature is not in the preset temperature range, that is, the absolute value of the difference between the first temperature and the second temperature is greater than or equal to the preset temperature difference, at this time, the blood drawing stage and the blood purification stage are in different temperature conditions, which indicates that the temperature of the patient's blood in the dialysis process has failed. When the temperature of the patient's blood in the dialysis process fails, it has no substantial meaning and no reference value to determine whether the dialyzer 3 needs to be stopped for blood dialysis according to the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis. Therefore, if it is determined that the difference between the first temperature and the second temperature is not in the preset temperature range, a prompt information is outputted, which is used to prompt the user that the blood temperature in the third venous line 2c has changed suddenly. When the user receives the prompt information, he will manually investigate the cause of the blood temperature failure in the line.

[0109] For example, if the first temperature is 36°C, the second temperature is 35°C, the preset temperature difference is 2°C, and the absolute value of the difference between the first temperature and the second temperature is 1°C, which is less than the preset temperature difference and is in the preset temperature range, whether the dialyzer 3 needs to be stopped for blood dialysis can be determined according to the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis. At this time, the error caused by the blood temperature change to the blood viscosity detection process and the judgment process is excluded.

[0110] On the basis of the above embodiment, before determining the blood viscosity before dialysis, the method further comprises:

[0111] determining the fourth flow rate of the blood input into the hard line 29, and if it is determined that the fourth flow rate is greater than the preset flow rate range, determining the blood viscosity before dialysis according to the viscosity coefficient, the third flow rate and the third inlet and outlet pressure difference.

[0112] Specifically, the fourth flow rate of blood input into the hard pipeline 29 represents the blood flow rate in the arterial pipeline 1, because the blood in the arterial pipeline 1 is directly drawn from the patient's body and has not been dialyzed by the dialyzer 3, it is not disturbed by the blood dialysis process. If the blood flow rate in the venous pipeline 2 is detected to determine whether the blood in the pipeline of the blood purification device is in a normal flow state, the blood flow rate in the venous pipeline 2 is easily disturbed by the blood dialysis process of the dialyzer 3, and it is difficult to accurately determine whether the blood in the pipeline of the blood purification device is in a normal flow state. Therefore, by detecting the blood flow rate in the arterial pipeline 1 to determine whether the blood in the pipeline of the blood purification device is in a normal flow state, the blood dialysis process of the dialyzer 3 can be avoided, and the accuracy of the determination can be improved.

[0113] In the process of determining the blood viscosity before dialysis, the blood viscosity before dialysis can be determined only according to the pressure difference between the inlet and outlet of the hard pipeline 29. The blood flow rate in the hard pipeline 29 has a very important influence on the detection accuracy of the pressure difference between the inlet and outlet of the hard pipeline 29. The preset flow rate range represents the minimum flow rate of the blood flowing in the arterial pipeline 1 of the blood purification device. Only when the blood flow rate of the arterial pipeline 1 is greater than the preset flow rate range, the blood in the pipeline of the blood purification device (including the arterial pipeline 1, the first venous pipeline 2a, the second venous pipeline 2b, the hard pipeline 29, and the third venous pipeline 2c) is in a normal flow state, and the blood viscosity before dialysis can be normally calculated. If the blood flow rate of the arterial pipeline 1 is less than or equal to the preset flow rate range, it indicates that the blood in the pipeline of the blood purification device is not in a normal flow state. In this case, the blood viscosity before dialysis detected is disturbed by the blood flow rate of the arterial pipeline 1, thereby affecting the accuracy of the real-time blood viscosity in the subsequent dialysis in the blood purification stage.

[0114] It should be noted that the preset flow rate range can be set according to clinical experience. For example, the preset flow rate range is 5 ml / min. Only when the fourth flow rate is greater than 5 ml / min, the blood in the arterial pipeline 1 is in a normal flow state, and the blood viscosity before dialysis can be calculated.

[0115] On the basis of the above embodiment, before determining the first pressure difference between the inlet and outlet of the hard pipeline 29 in step S31, the method further comprises:

[0116] determining the fourth pressure difference between the inlet and outlet of the hard pipeline 29 by inputting the replacement fluid into the venous pipeline 2 from the hard pipeline 29 at the fifth flow rate;

[0117] determining the fifth pressure difference between the inlet and outlet of the hard pipeline 29 by inputting the replacement fluid into the hard pipeline 29 from the venous pipeline 2 at the sixth flow rate;

[0118] If it is determined that the fourth inlet-outlet pressure difference is equal to the fifth inlet-outlet pressure difference, a safe operation prompt is output to prompt the user to continue to determine the first inlet-outlet pressure difference of the hard pipeline 29.

[0119] Preferably, the fifth flow rate is equal to the sixth flow rate.

[0120] Specifically, the displacement liquid can be sequentially input from the second venous pipeline 2b to the hard pipeline 29 and the third venous pipeline 2c at the fifth flow rate, at this time, the displacement liquid flows in the hard pipeline 29 in a forward direction, and the fourth inlet-outlet pressure difference represents the difference between the inlet pressure and the outlet pressure of the displacement liquid in the hard pipeline 29 when the displacement liquid flows in the forward direction; the displacement liquid can be sequentially input from the third venous pipeline 2c to the hard pipeline 29 and the second venous pipeline 2b at the sixth flow rate, at this time, the displacement liquid flows in the hard pipeline 29 in a reverse direction, and the fifth inlet-outlet pressure difference represents the difference between the inlet pressure and the outlet pressure of the displacement liquid in the hard pipeline 29 when the displacement liquid flows in the reverse direction. If the fourth inlet-outlet pressure difference is equal to the fifth inlet-outlet pressure difference, it indicates that the inlet-outlet pressure difference of the hard pipeline 29 is the same whether the displacement liquid flows in the forward direction or the reverse direction, at this time, the pressure detection process of the hard pipeline 29 is in a normal state, and a prompt information is output to prompt the user to execute the subsequent steps in the blood viscosity detection method; if the fourth inlet-outlet pressure difference is not equal to the fifth inlet-outlet pressure difference, it indicates that the inlet-outlet pressure difference of the hard pipeline 29 is different when the displacement liquid flows in the forward direction or the reverse direction, at this time, the pressure detection process of the hard pipeline 29 fails, and a fault prompt information is output to prompt the user that the pressure detection process of the hard pipeline 29 fails and needs to be handled in time, only after the pressure detection failure of the hard pipeline 29 is handled, the subsequent steps in the blood viscosity detection method can be continued to be executed. In the embodiment, before detecting the blood viscosity of the patient, whether the pressure detection process of the hard pipeline 29 fails is detected in advance by determining whether the fourth inlet-outlet pressure difference is equal to the fifth inlet-outlet pressure difference, so as to exclude the blood viscosity detection error caused by the error of the first pressure sensor 27 and the second pressure sensor 28 themselves when detecting the liquid pressure at both ends of the hard pipeline 29, and further improve the detection accuracy of the blood viscosity of the patient in the blood purification stage.

[0121] In the embodiment, the prompt information and the fault prompt information are acousto-optic signals, that is, sound prompt information can be output, or text prompt information can be displayed on the display screen to achieve the prompting effect.

[0122] On the basis of the above-mentioned embodiments, after it is determined that the difference between the viscosity of the displacement liquid and the viscosity of water is in the first preset range in step S33, the method further comprises:

[0123] Detect the pipe diameter of the second venous pipeline 2b, and determine whether the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is within a preset pipe diameter difference range; if the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is within the preset pipe diameter difference range, output a prompt information to prompt the user to continue detection; if the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is not within the preset pipe diameter difference range, output a fault prompt information.

[0124] Specifically, the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is within the preset pipe diameter difference range means that the absolute value of the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is less than the preset pipe diameter difference range; the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is not within the preset pipe diameter difference range means that the absolute value of the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is greater than or equal to the preset pipe diameter difference range. The preset pipe diameter difference range can be set by the clinician according to the clinical treatment experience, for example, the preset pipe diameter difference range is 2 cm, when the pipe diameter of the rigid pipeline 29 is 8 cm and the pipe diameter of the second venous pipeline 2b is 5 cm, then |the pipe diameter of the second venous pipeline- the pipe diameter of the rigid pipeline| = |5 cm-8 cm| = 3 cm≥2 cm, a fault prompt information is outputted, and the pipe diameter error prompt information can be timely sent to the user through the fault prompt information.

[0125] When the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is not within the preset pipe diameter difference range, it means that the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is too large, and there will be a large pressure difference between the second venous pipeline 2b and the rigid pipeline 29, for example, when the pipe diameter of the second venous pipeline 2b is larger than the pipe diameter of the rigid pipeline 29, under the same liquid flow condition, the liquid flow rate in the rigid pipeline 29 will be much larger than the liquid flow rate in the second venous pipeline 2b, and there will be a flow difference between the second venous pipeline 2b and the rigid pipeline 29, thereby causing a large error in the pressure detection process of the first pressure sensor 27, and the pressure detection value detected by the first pressure sensor 27 cannot truly reflect the liquid inlet pressure of the rigid pipeline 29. Therefore, when it is determined that the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is not within the preset pipe diameter difference range, a prompt information is sent to the user through the fault prompt information to prompt the user that the difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29 is too large, so that the user can focus on preventing the blood viscosity detection error caused by the too large difference between the pipe diameter of the second venous pipeline 2b and the pipe diameter of the rigid pipeline 29.

[0126] In this embodiment, the difference between the viscosity of the replacement fluid and the viscosity of water is first determined to be within a first preset range to ensure that the viscosity detection of the replacement fluid in the rigid tubing 29 is in a normal state. Then, it is further determined whether the difference between the diameter of the second venous tubing 2b and the diameter of the rigid tubing 29 is within a preset diameter difference range to ensure that the pressure detection value detected by the first pressure sensor 27 can truly reflect the liquid inlet pressure of the rigid tubing 29, thereby improving the detection accuracy of the patient's blood viscosity during the blood purification stage and the reliability of the detection results.

[0127] Based on the above embodiments, step S33 further includes: if it is determined that the difference between the viscosity of the replacement fluid and the viscosity of water is not within a first preset range, then detect whether there are air bubbles in the venous tubing, or adjust the length of the rigid tubing 29 according to the viscosity of the replacement fluid.

[0128] Specifically, if the difference between the viscosity of the replacement fluid and the viscosity of water is not within the first preset range, it indicates that there is a large error in the viscosity detection process of the replacement fluid. It is necessary to further detect the specific reasons for the error in the viscosity of the replacement fluid, so as to eliminate these faults in time and facilitate the subsequent detection of blood viscosity.

[0129] The significant error in the viscosity measurement of the replacement fluid may be due to air bubble malfunction. Those skilled in the art can detect the presence of air bubbles in the replacement fluid within the third venous line 2c to determine the presence of air bubbles in the venous line 2. If air bubble malfunction is detected in the third venous line 2c, it indicates that the viscosity measurement error is caused by air bubble malfunction, and the user can promptly eliminate the air bubble malfunction to facilitate subsequent blood viscosity measurement. Specifically, the presence of air bubbles in the replacement fluid within the third venous line 2c can be detected using the following method: Ultrasonic testing is performed on the replacement fluid within the third venous line 2c, converting the non-electrical signals of air bubbles in the replacement fluid into electrical signals. For example, converting the non-electrical signals of air bubbles in the replacement fluid into voltage signals, and comparing the voltage, it is determined whether air bubble malfunction exists in the third venous line 2c. For instance, after ultrasonic testing of the air bubbles in the replacement fluid, if the detected voltage is greater than 5V, it is determined that the air bubbles in the replacement fluid within the third venous line 2c are in a malfunctioning state, indicating the presence of air bubble malfunction in the third venous line 2c.

[0130] The reason for causing large error in the viscosity detection process of the replacement liquid can also be that the length of the hard pipeline 29 is not appropriate. The skilled person in the art can adjust the length of the hard pipeline 29 so that the detected viscosity of the replacement liquid can be in a normal state, facilitating the subsequent continuous detection of the viscosity of the blood, and improving the detection efficiency of the blood viscosity. When adjusting the length of the hard pipeline 29, the inlet and outlet pressure difference of the hard pipeline 29 will be affected, thereby changing the viscosity of the replacement liquid in the hard pipeline 29. If it is determined that the difference between the viscosity of the replacement liquid and the viscosity of the water is not in the first preset range, the length of the hard pipeline 29 can be repeatedly adjusted until the difference between the viscosity of the replacement liquid and the viscosity of the water is in the first preset range.

[0131] The hard pipeline 29 in the embodiment is a telescopic hard pipe. The skilled person in the art can adjust the length of the hard pipeline 29 according to actual needs by using the telescopic hard pipe, for example, lengthening or shortening the hard pipeline 29. In the embodiment, the length of the hard pipeline 29 is adjusted by using the telescopic hard pipe, so that the detected viscosity of the replacement liquid is in a normal state, the operation process is simple and convenient, and the efficiency and accuracy of the blood viscosity detection are improved.

[0132] On the basis of the above-mentioned embodiments, the blood viscosity detection method further comprises:

[0133] The blood is dialyzed, and the color detection value of the dialyzed blood in the hard pipeline 29 is determined. If it is determined that the difference between the color detection value and the preset color detection value is greater than the preset color difference value range, information for prompting blood dialysis failure is output.

[0134] Specifically, the blood color in the third venous line 2c can be detected to determine the color detection value of the dialysis blood in the rigid line 29, and the blood in the third venous line 2c is the blood after hemodialysis. According to the principle of hemodialysis, the blood and the dialysate exchange substances in the dialyzer 3, and the blood color after hemodialysis can be used to evaluate the hemodialysis efficiency of the dialyzer 3 and the hemodialysis safety of the dialyzer 3. Generally, when the dialyzer 3 is in a normal hemodialysis state, the color of the blood after hemodialysis is also in a normal color range, and the preset color detection value represents the color value of the blood in the normal state. When the difference between the color detection value of the blood after hemodialysis and the preset color detection value is less than or equal to the preset color difference range, it indicates that the color of the blood after hemodialysis is in a normal color range. When the difference between the color detection value of the blood after hemodialysis and the preset color detection value is greater than the preset color difference range, it indicates that the color of the blood after hemodialysis is in an abnormal color range. For example, the normal blood color of the patient is dark red, and the blood color in the third venous line 2c becomes light red, indicating that the blood color after hemodialysis is in an abnormal color range. At this time, a prompt information can be output to prompt the user that the blood color after hemodialysis has a fault, and the user can find the specific reason for the abnormal blood color after hemodialysis in the blood purification stage according to the fault prompt information. Generally, the reason for the abnormal blood color after hemodialysis is that the dialyzer 3 has a membrane rupture fault.

[0135] The color detection value of the blood after hemodialysis, the preset color detection value, and the preset color difference range can all be represented by RGB values. For example, the RGB value of the preset color detection value is (225, 10, 30), the RGB value of the color detection value of the blood after hemodialysis is (200, 26, 41), and the RGB value of the preset color difference range is (32, 20, 19). The RGB value of the difference between the preset color detection value and the color detection value of the blood after hemodialysis is (25, 16, 11), which is within the range of the RGB value of the preset color difference range. This indicates that the blood color after hemodialysis is in a normal color range, and the patient's hemodialysis state is in a normal state.

[0136] The embodiment can detect the blood color in the third venous line 2c to determine the color detection value of the blood after hemodialysis in the rigid line 29, so as to determine whether the patient's hemodialysis state has a fault, thereby improving the monitoring performance and fault detection efficiency of the patient's hemodialysis state.

[0137] In this embodiment, the fault prompt information is an audible and visual signal, that is, audible prompt information can be sent, and text prompt information can be displayed on the display screen to achieve the prompt effect.

[0138] In combination Figure 9 As shown in the first aspect, the second aspect of the present application provides a blood purification device, comprising:

[0139] The first pressure detection module is configured to input the replacement fluid to the venous line 2 through the hard line 29 at a first flow rate, and determine a first inlet and outlet pressure difference of the hard line 29.

[0140] The first viscosity detection module is configured to determine the viscosity of the replacement fluid according to the pipe property of the hard line 29, the first flow rate, and the first inlet and outlet pressure difference.

[0141] The viscosity coefficient module is configured to determine that a difference between the viscosity of the replacement fluid and the viscosity of water is within a first preset range, and obtain a viscosity coefficient according to the viscosity of water, the first flow rate, and the first inlet and outlet pressure difference.

[0142] The second pressure detection module is configured to perform dialysis on the blood, and determine a second flow rate of the blood after dialysis in the hard line 29 and a second inlet and outlet pressure difference of the hard line 29 in real time.

[0143] The second viscosity detection module is configured to determine the real-time viscosity of the blood during dialysis according to the viscosity coefficient, the second flow rate, and the second inlet and outlet pressure difference.

[0144] Compared with the prior art, the technical effect of the blood purification device of the present application is the same as that of the blood viscosity detection method provided in the first aspect, which will not be repeated here.

[0145] The third aspect of the present application provides an electronic device, which comprises a memory, a processor, and a computer program stored in the memory. The processor executes the computer program to implement the steps of the method shown in the first aspect. For specific processes, please refer to the description of the method embodiments of the first aspect, which will not be repeated here. Figure 3

[0146] Compared with the prior art, the technical effect of the electronic device provided in the present application is the same as that of the blood viscosity detection method provided in the first aspect, which will not be repeated here.

[0147] In an optional embodiment, an electronic device is provided as shown in Figure 10 Figure 10 ​​The electronic device 100 shown includes a processor 101 and a memory 103. The processor 101 and the memory 103 are connected, for example, via a bus 102. Optionally, the electronic device 100 can also include a transceiver 104. It should be noted that the transceiver 104 is not limited to one in actual applications, and the structure of the electronic device 100 does not constitute a limitation on the embodiments of the present application.

[0148] The processor 101 can be a CPU (Central Processing Unit), a general-purpose processor, a DSP (Digital Signal Processor), an ASIC (Application Specific Integrated Circuit), an FPGA (Field Programmable Gate Array), or other programmable logic devices, transistor logic devices, hardware components, or any combination thereof. It can implement or execute various exemplary logical blocks, modules, and circuits described in combination with the disclosure of the present application. The processor 101 can also be a combination that implements a computing function, such as a combination of one or more microprocessors, a combination of a DSP and a microprocessor, and the like.

[0149] The bus 102 can include a path for transmitting information between the above-mentioned components. The bus 102 can be a PCI (Peripheral Component Interconnect) bus or an EISA (Extended Industry Standard Architecture) bus, or the like. The bus 102 can be divided into an address bus, a data bus, a control bus, and the like. For ease of representation, Figure 10 Only one thick line is used in the middle, but it does not mean that there is only one bus or one type of bus.

[0150] The memory 103 can be a ROM (Read Only Memory) or other type of static storage device that can store static information and instructions, a RAM (Random Access Memory) or other type of dynamic storage device that can store information and instructions, an EEPROM (Electrically Erasable Programmable Read Only Memory), a CD-ROM (Compact Disc Read Only Memory) or other optical disk storage, a magnetic disk storage medium or other magnetic storage device, or any other medium that can be used to carry or store desired program code in the form of instructions or data structures and that can be accessed by a computer, but is not limited thereto.

[0151] The memory 103 is used to store application program codes for implementing the scheme of the present application, and is controlled to execute by the processor 101. The processor 101 is used to execute the application program codes stored in the memory 103 to realize the content shown in the foregoing method embodiments.

[0152] The fourth aspect of the embodiments of the present application provides a blood purification device, comprising: a pressure sensor, a hard pipeline, an arterial pipeline, a venous pipeline and a dialyzer, the input end of the arterial pipeline is connected with a human body arterial blood vessel, the output end of the arterial pipeline is connected with the blood input end of the dialyzer, the input end of the venous pipeline is connected with the blood output end of the dialyzer, the output end of the venous pipeline is connected with a human body venous blood vessel, forming a blood circulation loop, the hard pipeline is installed on the venous pipeline, the pressure sensor comprises a first pressure sensor and a second pressure sensor, the first pressure sensor is located at the connection between the first end of the hard pipeline and the venous pipeline, the second pressure sensor is located at the connection between the second end of the hard pipeline and the venous pipeline, and the first pressure sensor and the second pressure sensor are used to determine the pressure difference between the inlet and outlet of the hard pipeline.

[0153] The blood purification device further comprises the electronic device shown in the third aspect, and the electronic device is electrically connected with the memory, the first pressure sensor and the second pressure sensor through a bus.

[0154] Compared with the prior art, the technical effect of the blood purification device provided by the embodiments of the present application is the same as that of the blood viscosity detection method provided by the first aspect, which will not be described here.

[0155] It should be understood that although the steps in the flowcharts of the accompanying figures are shown sequentially as indicated by the arrows, these steps are not necessarily executed in the order indicated by the arrows. Unless explicitly stated herein, there is no strict order restriction on the execution of these steps, and they can be executed in other orders. Moreover, at least some steps in the flowcharts of the accompanying figures may include multiple sub-steps or multiple stages. These sub-steps or stages are not necessarily completed at the same time, but can be executed at different times, and their execution order is not necessarily sequential, but can be performed alternately or in turn with other steps or at least some of the sub-steps or stages of other steps.

[0156] While the disclosure is as stated above, its scope of protection is not limited thereto. Those skilled in the art can make various changes and modifications without departing from the spirit and scope of this disclosure, and all such changes and modifications will fall within the protection scope of this invention.

Claims

1. A method for detecting blood viscosity, characterized in that, include: Replacement fluid is introduced into the venous line through a rigid tubing at a first flow rate, and the first inlet and outlet pressure difference of the rigid tubing is determined. The viscosity of the displacement fluid is determined based on the pipe properties of the rigid pipe, the first flow rate, and the first inlet and outlet pressure difference, wherein the pipe properties of the rigid pipe include the length and diameter of the rigid pipe. If it is determined that the difference between the viscosity of the replacement fluid and the viscosity of water is within a first preset range, then the viscosity coefficient is determined based on the viscosity of water, the first flow rate, and the first inlet and outlet pressure difference. The blood is dialyzed, and the second flow rate of the dialyzed blood in the rigid tubing and the second inlet-outlet pressure difference of the rigid tubing are determined in real time. The real-time viscosity of blood during dialysis is determined based on the viscosity coefficient, the second flow rate, and the second inlet / outlet pressure difference. The viscosity coefficient is calculated using the following formula: in, M1 represents the viscosity coefficient; M1 represents the viscosity of water, in Pa·s. Q1 represents the first inlet and outlet pressure difference, in Pa; Q1 represents the first flow rate, in m³ / s. 3 / s; The real-time viscosity of blood during dialysis is calculated using the following formula: Where C2 represents the real-time viscosity of blood during dialysis, in Pa·s; Represents viscosity coefficient; Q2 represents the second inlet and outlet pressure difference, in Pa; Q2 represents the second flow rate, in m³ / s. 3 / s.

2. The blood viscosity detection method according to claim 1, characterized in that, Prior to the blood dialysis procedure, the following also includes: Blood is infused into the venous line through the rigid tubing at a third flow rate, and the third inlet and outlet pressure difference of the rigid tubing is determined. The blood viscosity before dialysis is determined based on the viscosity coefficient, the third flow rate, and the third inlet / outlet pressure difference.

3. The blood viscosity detection method according to claim 2, characterized in that, Also includes: If the difference between the blood viscosity before dialysis and the real-time blood viscosity during dialysis is within a second preset range, then hemodialysis is stopped.

4. The blood viscosity detection method according to claim 3, characterized in that, Also includes: Before dialysis, the first temperature of the blood in the venous tubing is obtained; During blood dialysis, the second temperature of the blood within the venous tubing is obtained; If the difference between the first temperature and the second temperature is determined to be within a preset temperature range, then hemodialysis is stopped based on the difference between the blood viscosity before dialysis and the real-time viscosity of the blood during dialysis being within the second preset range.

5. The blood viscosity detection method according to claim 2, characterized in that, Before determining the blood viscosity before dialysis, the method further includes: A fourth flow rate of blood input into the rigid tubing is determined. If the fourth flow rate is determined to be greater than a preset flow rate range, the blood viscosity before dialysis is determined based on the viscosity coefficient, the third flow rate, and the third inlet-outlet pressure difference.

6. The blood viscosity detection method according to claim 1, characterized in that, Before determining the first inlet and outlet pressure difference of the rigid pipeline, the following steps are also included: The replacement fluid is introduced from the rigid tubing into the venous tubing at a fifth flow rate, and the fourth inlet and outlet pressure difference of the rigid tubing is determined. The replacement fluid is introduced from the venous line to the rigid line at a sixth flow rate, and the fifth inlet and outlet pressure difference of the rigid line is determined. If the pressure difference between the fourth inlet and outlet is determined to be equal to the pressure difference between the fifth inlet and outlet, a safety operation prompt will be output.

7. The blood viscosity detection method according to claim 1, characterized in that, Also includes: If it is determined that the difference between the viscosity of the replacement fluid and the viscosity of water is not within the first preset range, then the presence of air bubbles in the intravenous tubing is detected, or the length of the rigid tubing is adjusted according to the viscosity of the replacement fluid.

8. A blood purification device, characterized in that, include: The first pressure detection module is used to input replacement fluid into the venous tubing through the rigid tubing at a first flow rate, and to determine the first inlet and outlet pressure difference of the rigid tubing. The first viscosity detection module is used to determine the viscosity of the displacement fluid based on the pipe properties of the rigid pipe, the first flow rate, and the first inlet and outlet pressure difference, wherein the pipe properties of the rigid pipe include the length of the rigid pipe and the diameter of the rigid pipe. The viscosity coefficient module is used to determine that the difference between the viscosity of the replacement fluid and the viscosity of water is within a first preset range, and to obtain the viscosity coefficient based on the viscosity of water, the first flow rate and the first inlet and outlet pressure difference. The second pressure detection module is used to perform dialysis on blood and determine the second flow rate of the dialyzed blood in the rigid tubing and the second inlet-outlet pressure difference of the rigid tubing in real time. The second viscosity detection module is used to determine the real-time viscosity of blood during dialysis based on the viscosity coefficient, the second flow rate, and the second inlet and outlet pressure difference. The viscosity coefficient module calculates the viscosity coefficient using the following formula: in, M1 represents the viscosity coefficient; M1 represents the viscosity of water, in Pa·s. Q1 represents the first inlet and outlet pressure difference, in Pa; Q1 represents the first flow rate, in m³ / s. 3 / s; The second viscosity detection module calculates the real-time viscosity of blood during dialysis using the following formula: Where C2 represents the real-time viscosity of blood during dialysis, in Pa·s; Represents viscosity coefficient; Q2 represents the second inlet and outlet pressure difference, in Pa; Q2 represents the second flow rate, in m³ / s. 3 / s.

9. An electronic device comprising a memory, a processor, and a computer program stored in the memory, characterized in that, The processor executes the computer program to implement the steps of the method according to any one of claims 1 to 7.

10. A blood purification device, characterized in that, include: The invention comprises a pressure sensor, a rigid tubing, a venous tubing, a dialyzer, and the electronic device of claim 9, wherein the input end of the venous tubing is connected to the blood output end of the dialyzer, the output end of the venous tubing is connected to a human venous vessel, the rigid tubing is installed on the venous tubing, the pressure sensor is electrically connected to the electronic device, and the pressure sensor is used to determine the inlet and outlet pressure difference of the rigid tubing.

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