Pump blood flow estimation method and device of ventricular catheter pump

Abstract

The embodiment of the invention provides a pump blood flow estimation method and device of a ventricular catheter pump, relates to the technical field of artificial heart, and is applied to electronic medical equipment in a ventricular assist system, the ventricular assist system further comprises the ventricular catheter pump with a foldable impeller, and the electronic medical equipment is connected with the ventricular catheter pump. The method comprises the steps that the current operation parameter value of a motor in the ventricular catheter pump is obtained, and the impeller diameter variable quantity of an impeller in the ventricular catheter pump is obtained; and estimating the target pump blood flow of the ventricular catheter pump based on the motor operation parameter value and the impeller diameter variation. By applying the scheme provided by the embodiment, accurate estimation of the pump blood flow can be realized.

Description

Technical Field

[0001] The present application relates to the field of artificial heart technology, and in particular to a method and device for estimating the blood flow of a ventricular catheter pump. Background Art

[0002] The ventricular catheter pump is an intravascular miniature axial flow pump that supports the patient's blood circulation system. One of the core components of the ventricular catheter pump is the impeller. The high-speed rotation of the impeller can transfer blood from the blood inlet to the blood outlet, thereby realizing the ventricular catheter pump's auxiliary heart pumping function.

[0003] In order to better adapt to the complex environment in the heart of a living organism, the size of the ventricular catheter pump is required to be as small as possible, and the ventricular catheter pump with a foldable impeller can well meet this requirement. During the implantation process of the ventricular catheter pump with a foldable impeller, the impeller is in a contracted state, with a small size, and can be safely inserted into the heart through blood vessels; after implantation in the patient's body, the impeller is in an open state to achieve the function of assisting the heart to pump blood.

[0004] The blood pumping flow of a ventricular catheter pump can characterize the current working performance of the ventricular catheter pump, so an accurate blood pumping flow estimation scheme is urgently needed. Summary of the invention

[0005] The purpose of the embodiment of the present application is to provide a method and device for estimating the blood flow of a ventricular catheter pump, so as to achieve accurate estimation of the blood flow. The specific technical solution is as follows: In a first aspect, an embodiment of the present application provides a method for estimating the blood flow of a ventricular catheter pump, which is applied to an electronic medical device in a ventricular assist system, wherein the ventricular assist system further includes a ventricular catheter pump with a foldable impeller, and the electronic medical device is connected to the ventricular catheter pump, and the method includes: Obtaining current operating parameter values ​​of the motor in the ventricular catheter pump, and obtaining a change in the impeller diameter of the impeller in the ventricular catheter pump; The target blood flow rate of the ventricular catheter pump is estimated based on the motor operating parameter value and the impeller diameter change.

[0006] In one embodiment of the present application, the motor operating parameter value includes the current motor speed and the current motor power, and the target pumping blood flow rate of the ventricular catheter pump is estimated based on the motor operating parameter value and the impeller diameter change, including: Using a first preset linear coefficient, determining a first pump blood flow rate corresponding to the current motor power; Determine a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and use a second preset linear coefficient to determine a second pump blood flow corresponding to the target correlation value; A target pumping blood flow rate of the ventricular catheter pump is determined based on the first pumping blood flow rate and the second pumping blood flow rate.

[0007] In one embodiment of the present application, before determining the target pump blood flow rate of the ventricular catheter pump based on the first pump blood flow rate and the second pump blood flow rate, the method further includes: Acquire the current pressure difference between the blood inlet pressure and the bleeding outlet pressure of the ventricular catheter pump; Determining a target pumping blood flow rate of the ventricular catheter pump based on the first pumping blood flow rate and the second pumping blood flow rate comprises: Calculating the sum of the first pump blood flow rate and the second pump blood flow rate, and using the calculated sum as a reference pump blood flow rate; Determining a deviation amount of a reference pump blood flow rate based on the current pressure difference and the current motor speed; The reference blood pumping flow rate is adjusted according to the deviation, and the adjusted flow rate is determined as the target blood pumping flow rate of the ventricular catheter pump.

[0008] In one embodiment of the present application, the above-mentioned calculation of the deviation of the reference pump blood flow rate based on the current pressure difference and the current motor speed includes: Determine the flow deviation ratio corresponding to the current pressure difference and the current motor speed; Based on the reference pump blood flow rate and the flow deviation ratio, the deviation amount of the reference pump blood flow rate is calculated.

[0009] In one embodiment of the present application, the above-mentioned determination of the flow deviation ratio corresponding to the current pressure difference and the current motor speed includes: The flow deviation ratio is calculated according to the following expression: ; in, is the flow deviation ratio, is the current pressure difference, is the first preset nonlinear coefficient, is the second preset nonlinear coefficient, and N is the current motor speed.

[0010] In a second aspect, an embodiment of the present application provides a device for estimating the blood flow of a ventricular catheter pump, which is applied to an electronic medical device in a ventricular assist system, wherein the ventricular assist system further includes a ventricular catheter pump with a foldable impeller, and the electronic medical device is connected to the ventricular catheter pump, and the device includes: A parameter acquisition module, used to acquire the current operating parameter value of the motor in the ventricular catheter pump, and to acquire the change in the impeller diameter of the impeller in the ventricular catheter pump; The flow estimation module is used to estimate the target pumping blood flow of the ventricular catheter pump based on the motor operating parameter value and the change in impeller diameter.

[0011] In one embodiment of the present application, the motor operating parameter value includes the current motor speed and the current motor power, and the flow estimation module includes: A first flow determination submodule, configured to determine a first pump blood flow corresponding to the current motor power by using a first preset linear coefficient; A second flow determination submodule is used to determine a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and to determine a second pump blood flow corresponding to the target correlation value using a second preset linear coefficient; The target flow determination submodule is used to determine a target pumping blood flow of the ventricular catheter pump based on the first pumping blood flow and the second pumping blood flow.

[0012] In one embodiment of the present application, the above-mentioned flow estimation module further includes a pressure difference acquisition submodule, wherein: The pressure difference acquisition submodule is used to acquire the current pressure difference between the blood inlet pressure and the bleeding outlet pressure of the ventricular catheter pump before the target flow determination submodule; The target flow determination submodule includes: a flow calculation unit, used for calculating the sum of the first pump blood flow and the second pump blood flow, and using the calculated sum as a reference pump blood flow; a deviation calculation unit, used to determine a deviation amount of a reference pump blood flow rate based on the current pressure difference and the current motor speed; The flow rate adjustment unit is used to adjust the reference blood pumping flow rate according to the deviation amount, and determine the adjusted flow rate as the target blood pumping flow rate of the ventricular catheter pump.

[0013] In one embodiment of the present application, the above-mentioned deviation calculation unit is specifically used to determine the flow deviation ratio corresponding to the current pressure difference and the current motor speed; based on the baseline pump blood flow and the flow deviation ratio, calculate the deviation amount of the baseline pump blood flow.

[0014] In one embodiment of the present application, the above-mentioned deviation calculation unit is specifically used to calculate the flow deviation ratio according to the following expression: ; in, is the flow deviation ratio, is the current pressure difference, is the first preset nonlinear coefficient, is the second preset nonlinear coefficient, and N is the current motor speed.

[0015] In a third aspect, an embodiment of the present application provides a ventricular catheter pump system, comprising a ventricular catheter pump with a foldable impeller and an electronic medical device, wherein the ventricular catheter pump is connected to the electronic medical device, and the electronic medical device is used to execute the method steps described in the first aspect when controlling the operation of the ventricular catheter pump.

[0016] In a fourth aspect, an embodiment of the present application provides an electronic medical device, including a processor, a communication interface, a memory, and a communication bus, wherein the processor, the communication interface, and the memory communicate with each other via the communication bus; Memory, used to store computer programs; The processor is used to implement the method steps described in the first aspect when executing the program stored in the memory.

[0017] In a fifth aspect, an embodiment of the present application provides a computer-readable storage medium, wherein the computer-readable storage medium stores a computer program, and when the computer program is executed by a processor, the method steps described in the first aspect are implemented.

[0018] From the above, it can be seen that the blood pumping flow rate is estimated by the scheme provided in the embodiment of the present application. Since the target blood pumping flow rate is estimated based on the motor operating parameter value and the impeller diameter change, the motor operating parameter value represents the current operating information of the motor, and the impeller diameter change represents the geometric characteristic change information of the foldable impeller. Therefore, the estimated target blood pumping flow rate, in addition to considering the motor operating parameters, more importantly, considers the geometric characteristic change information of the foldable impeller. The geometric characteristic change of the foldable impeller affects the blood pumping flow rate, so that the target blood pumping flow rate is close to the actual blood pumping flow rate, thereby improving the accuracy of the blood pumping flow estimation.

[0019] Of course, implementing any product or method of the present application does not necessarily require achieving all of the advantages described above at the same time. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application, and for ordinary technicians in this field, other embodiments can also be obtained based on these drawings.

[0021] Figure 1a A schematic structural diagram of a ventricular catheter pump system provided in an embodiment of the present application; Figure 1b A schematic structural diagram of a ventricular catheter pump with a foldable impeller provided in an embodiment of the present application; Figure 2A schematic flow chart of a first method for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application; Figure 3 A schematic flow chart of a second method for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application; Figure 4 A schematic flow chart of a third method for estimating the blood flow rate of a ventricular catheter pump provided in this embodiment; Figure 5 A schematic structural diagram of a first device for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application; Figure 6 A schematic diagram of the structure of a second device for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application; Figure 7 A schematic diagram of the structure of a third device for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application; Figure 8 A schematic diagram of the structure of an electronic medical device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0022] The following will be combined with the drawings in the embodiments of the present application to clearly and completely describe the technical solutions in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field based on the present application belong to the scope of protection of the present application.

[0023] The embodiment of the present application provides a solution for estimating the blood flow rate of a ventricular catheter pump. Here, the concept of blood flow rate needs to be emphasized first.

[0024] During the process of the ventricular catheter pump assisting the patient's heart in pumping blood, the total blood output of the heart is composed of two parts. One part is the blood flow pumped by the heart's own function, which is called the natural cardiac output; the other part is the blood flow pumped by the ventricular catheter pump's own function, which is the blood pumping flow referred to in this application.

[0025] See also Figure 1a , Figure 1a is a structural diagram of a ventricular catheter pump system. The ventricular catheter pump system includes a ventricular catheter pump 11 with a foldable impeller and an electronic medical device 12 . The electronic medical device 12 is connected to the ventricular catheter pump 11 .

[0026] After the ventricular catheter pump 11 is implanted in the human heart, the electronic medical device 12 controls the operation of the ventricular catheter pump 11 to assist the heart in pumping blood. In the process of controlling the operation of the ventricular catheter pump 11, the electronic medical device 12 at least performs the steps of the method for estimating the blood flow rate of the ventricular catheter pump provided in the embodiment of the present application.

[0027] Figure 1b A schematic diagram of the structure of a ventricular catheter pump with a foldable impeller. Figure 1b The ventricular catheter pump shown is a left ventricular catheter pump.

[0028] The left ventricular catheter pump is placed across the aortic valve to pump the left ventricular blood into the aorta to assist the heart in pumping blood. Of course, in addition to the left ventricular catheter pump, the ventricular catheter pump of the present application can also be a right ventricular catheter pump, a biventricular catheter pump, etc., without limitation.

[0029] The main components of the left ventricular catheter pump include a blood inlet, a foldable impeller, a bleeding port and a motor, wherein except for the motor, the other components are all located in the patient's body.

[0030] The motor is connected to the impeller through a flexible driving shaft to drive the impeller to rotate.

[0031] The foldable impeller is in a contracted state before being implanted into a biological body, and this contracted state can ensure that the size of the ventricular catheter pump is small; after reaching the left ventricle of the heart, the foldable impeller is in an open state, and the impeller rotates to pump the blood in the left ventricle through the blood inlet to the bleeding outlet of the aorta until it reaches the aorta, thereby assisting the heart in pumping blood.

[0032] The execution subject of the embodiment of the present application is an electronic medical device. The electronic medical device can achieve high-precision estimation of the pumping blood flow of a ventricular catheter pump by executing the pumping blood flow estimation method provided in the embodiment of the present application.

[0033] The following describes the solution provided in the embodiments of the present application.

[0034] See also Figure 2 , Figure 2 A flowchart of a first method for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application is applied to electronic medical equipment. The method includes the following steps S201-S202.

[0035] Step S201: obtaining the current operating parameter value of the motor in the ventricular catheter pump, and obtaining the change in the impeller diameter of the impeller in the ventricular catheter pump.

[0036] The current operating parameter value represents the current operating condition of the motor in the ventricular catheter pump. The current operating parameter value includes the current motor current, the current motor voltage, etc. In one embodiment of the present application, the motor operating parameter value includes the current motor speed and the current motor power.

[0037] The foldable impeller of the ventricular catheter pump is elastic. When the impeller rotates, it is affected by various complex factors such as the blood environment and the pump operation time, and the geometric shape of the impeller changes accordingly. The change in the impeller diameter represents the change characteristics of the geometric shape of the impeller.

[0038] The above-mentioned current operating parameter values ​​and the change in impeller diameter may be obtained by reading from a data storage device or by acquiring in real time.

[0039] Regardless of which acquisition method is used, the above-mentioned parameter information needs to be obtained. Specifically, the current operating parameter value can be obtained by real-time collection and processing of the corresponding sensors, such as using a Hall sensor to collect the current motor speed, using an ammeter to collect the current motor current, using a voltmeter to collect the current motor voltage, using the current motor current and the current motor voltage to calculate the current motor power, etc., and using motion sensors and other detections to obtain the change in impeller diameter.

[0040] Step S202: estimating the target blood flow rate of the ventricular catheter pump based on the motor operating parameter value and the change in the impeller diameter.

[0041] The target blood pumping flow rate represents the current blood pumping flow rate information of the ventricular catheter pump.

[0042] One implementation method for estimating the target blood pumping flow rate is: inputting the motor operating parameter value and the impeller diameter change into a pre-trained blood pumping flow rate estimation model, and obtaining the blood pumping flow rate output by the blood pumping flow rate estimation model as the target blood pumping flow rate of the ventricular catheter pump.

[0043] Other implementations of estimating target pump blood flow can be found in the following Figure 3 The corresponding embodiments are not described in detail here.

[0044] From the above, it can be seen that the blood pumping flow rate is estimated by the scheme provided in this embodiment. Since the target blood pumping flow rate is estimated based on the motor operating parameter value and the impeller diameter change, the motor operating parameter value represents the current operating information of the motor, and the impeller diameter change represents the geometric characteristic change information of the foldable impeller. Therefore, the estimated target blood pumping flow rate, in addition to considering the motor operating parameters, more importantly, considers the geometric characteristic change information of the foldable impeller. The geometric characteristic change of the foldable impeller affects the blood pumping flow rate, so that the target blood pumping flow rate taken into consideration is close to the actual blood pumping flow rate, thereby improving the accuracy of the blood pumping flow rate estimation.

[0045] In the aforementioned Figure 2In the corresponding embodiment, when the motor operating parameter value includes the current motor speed and the current motor power, the aforementioned step S202 can be implemented according to the following steps S302-S304. Figure 3 , Figure 3 This is a flow chart of a second method for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application. The method includes the following steps S301-S304.

[0046] Step S301: obtaining the current operating parameter value of the motor in the ventricular catheter pump, and obtaining the change in the impeller diameter of the impeller in the ventricular catheter pump.

[0047] The motor operating parameter values ​​include the current motor speed and the current motor power.

[0048] Step S302: using a first preset linear coefficient to determine a first pump blood flow rate corresponding to the current motor power.

[0049] The first blood pumping flow rate is a representation of the blood pumping flow rate contributed by the current motor power, that is, the blood pumping flow rate reflected from the perspective of the current motor power situation.

[0050] The first preset linear coefficient represents the linear relationship between the motor power and the pump blood flow rate, and the first preset linear coefficient is determined in advance under a simulation test environment.

[0051] An implementation method of determining the first pumping blood flow rate is: calculating the product between the first linear coefficient and the current motor power, and determining the calculated product as the first pumping blood flow rate.

[0052] Step S303: determining a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and using a second preset linear coefficient to determine a second pump blood flow corresponding to the target correlation value.

[0053] The above target correlation value is used to characterize the correlation between the current motor speed and the impeller diameter change. Any calculation method for determining the correlation between parameters in the prior art can be used to calculate the target correlation value between the current motor speed and the impeller diameter change.

[0054] The second preset linear coefficient represents the linear relationship between the correlation degree and the pump blood flow rate, and the correlation degree is the correlation relationship between the motor speed and the impeller diameter change. The second preset linear coefficient is determined in advance in a simulation test environment.

[0055] One implementation method of determining the second blood pumping flow rate is: calculating the product between the first preset flow coefficient and the above-mentioned associated value, and using the calculated product as the first blood pumping flow rate.

[0056] Step S304: Determine a target blood pumping flow rate of the ventricular catheter pump based on the first blood pumping flow rate and the second blood pumping flow rate.

[0057] One implementation of determining the target blood pumping flow rate is: calculating the sum of the first blood pumping flow rate and the second blood pumping flow rate, and determining the calculated sum as the target blood pumping flow rate.

[0058] Other implementations for determining the target pump blood flow rate can be found in the following Figure 4 The corresponding embodiments are not described in detail here.

[0059] In this embodiment, the target blood flow of the ventricular catheter pump is determined based on the first blood flow and the second blood flow, wherein the first blood flow is determined based on the current motor power, and the second blood flow is determined based on the correlation between the current motor speed and the change in impeller diameter. On the one hand, the motor power directly affects the blood flow, and the accuracy of the first blood flow determined based on the current motor power is relatively high. On the other hand, the correlation between the motor speed and the impeller change also affects the blood flow, and the accuracy of the second blood flow determined based on the above correlation is also relatively high. Therefore, combining the above two aspects, the accuracy of the target blood flow determined based on the first blood flow and the second blood flow is further improved.

[0060] In the aforementioned Figure 4 In the corresponding embodiment, the target pump blood flow rate can be implemented by adopting the above-mentioned implementation method, or by adopting the following S405-S407. Figure 4 , Figure 4 This is a flow chart of a third method for estimating the blood flow rate of a ventricular catheter pump provided in this embodiment. The method includes the following steps S401-S407.

[0061] Step S401: obtaining the current operating parameter value of the motor in the ventricular catheter pump, and obtaining the change in the impeller diameter of the impeller in the ventricular catheter pump.

[0062] The motor operating parameter values ​​include the current motor speed and the current motor power.

[0063] Step S402: using a first preset linear coefficient to determine a first pump blood flow rate corresponding to the current motor power.

[0064] Step S403: determining a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and using a second preset linear coefficient to determine a second pump blood flow corresponding to the target correlation value.

[0065] The above steps S401-S403 are the same as the above steps S301-S303, and will not be repeated here.

[0066] Step S404: obtaining the current pressure difference between the blood inlet pressure and the blood outlet pressure of the ventricular catheter pump.

[0067] After the ventricular catheter pump is implanted in the human body, the blood inlet and the bleeding outlet are located in different heart areas. For example, for the left ventricular catheter pump, the blood inlet is in the left ventricle of the heart and the bleeding outlet is in the aorta of the heart. There is a pressure difference between the blood inlet and the bleeding outlet. The blood overcomes the pressure difference and is transmitted from the blood inlet of the left ventricle to the bleeding outlet of the aorta. The current pressure difference reflects the pressure difference information between the blood inlet pressure and the bleeding outlet pressure.

[0068] The above-mentioned current pressure difference can be determined by a pressure sensor, such as integrating a pressure sensor at the blood inlet to obtain the blood inlet pressure, integrating a pressure sensor at the bleeding outlet to obtain the bleeding outlet pressure, and calculating the pressure difference between the blood inlet pressure and the bleeding outlet pressure as the current pressure difference.

[0069] Step S405: Calculate the sum of the first blood pumping flow rate and the second blood pumping flow rate, and use the calculated sum as the reference blood pumping flow rate.

[0070] Step S406: Determine the deviation of the reference pump blood flow rate based on the current pressure difference and the current motor speed.

[0071] Due to the blood environment, dynamic changes in patient status and the operating time of the ventricular catheter pump, there is a deviation between the blood flow estimated by the motor operating parameters and the impeller change characteristics and the actual blood flow. Based on this, the deviation of the blood flow is calculated using the current pressure difference and the current motor speed, so as to accurately correct the baseline blood flow and improve the accuracy of the blood flow estimation.

[0072] The first implementation method for determining the deviation of the baseline pump blood flow is: determine the standard pressure difference corresponding to the current motor speed, calculate the pressure difference deviation between the standard pressure difference and the current pressure difference, and determine the flow deviation corresponding to the pressure difference deviation as the deviation of the baseline pump blood flow.

[0073] In this embodiment, the correspondence between the motor speed and the pressure difference can be preset, and each correspondence represents the pressure difference value that should be reached under the motor speed. According to the above correspondence, the pressure difference corresponding to the current motor speed is determined as the standard pressure difference.

[0074] After determining the standard pressure difference, the difference between the standard pressure difference and the current pressure difference is calculated as the pressure difference deviation; after obtaining the pressure difference deviation, the flow deviation corresponding to the pressure difference deviation is determined according to the preset correspondence between the pressure difference deviation and the flow deviation, as the deviation of the benchmark blood pump flow.

[0075] The second implementation method for determining the deviation of the reference blood pump flow is: determining the flow deviation ratio corresponding to the current pressure difference and the current motor speed; and calculating the deviation of the reference blood pump flow based on the reference blood pump flow and the flow deviation ratio.

[0076] The above flow deviation ratio represents the proportional relationship between the deviation flow and the baseline pump blood flow.

[0077] The first implementation method for determining the flow deviation ratio is: presetting the corresponding relationship between the pressure difference, the motor speed and the flow deviation ratio, and determining the flow deviation ratio corresponding to the current pressure difference and the current motor speed according to the above corresponding relationship.

[0078] The second implementation method for determining the flow deviation ratio is: calculating the flow deviation ratio according to the following expression: ; in, is the flow deviation ratio, is the current pressure difference, is the first preset nonlinear coefficient, is the second preset nonlinear coefficient, and N is the current motor speed.

[0079] In one embodiment of the present application, the first preset nonlinear coefficient is obtained by fitting the linear relationship between blood viscosity and impeller design parameters under a simulated test environment. The second preset nonlinear coefficient represents the compensation proportional coefficient of the rotation speed to the pressure difference.

[0080] In one embodiment of the present application, the first preset linear coefficient, the second preset linear coefficient, the first preset nonlinear coefficient, and the second preset nonlinear coefficient are obtained by training the supervised model under a simulated test environment using different rotation speeds, pressure differences, powers, and blood viscosities, and using the actual blood flow of the ventricular catheter pump as training samples of the supervised model. In addition, during the operation of the ventricular catheter pump, the above coefficients can also be optimized in real time using the existing parameter optimization method using the real-time collected data.

[0081] After calculating the flow deviation ratio, the product of the baseline pump blood flow and the flow deviation ratio is calculated, and the calculated value is determined as the deviation amount of the baseline pump blood flow.

[0082] Step S407: adjusting the reference blood pumping flow rate according to the deviation, and determining the adjusted flow rate as the target blood pumping flow rate of the ventricular catheter pump.

[0083] One implementation of adjusting the reference blood pumping flow rate is: calculating the difference between the reference blood pumping flow rate and the deviation amount, and determining the calculated interpolation value as the final blood pumping flow rate.

[0084] Corresponding to the above-mentioned method for estimating the blood flow rate of a ventricular catheter pump, an embodiment of the present application further provides a device for estimating the blood flow rate of a ventricular catheter pump.

[0085] See also Figure 5 , Figure 5 A schematic diagram of the structure of a first ventricular catheter pump blood flow estimation device provided in an embodiment of the present application. An electronic medical device applied to a ventricular assist system, wherein the ventricular assist system further includes a ventricular catheter pump with a foldable impeller, the electronic medical device is connected to the ventricular catheter pump, and the device includes: The parameter acquisition module 501 is used to acquire the current operating parameter value of the motor in the ventricular catheter pump and acquire the change in the impeller diameter of the impeller in the ventricular catheter pump; The flow estimation module 502 is used to estimate the target pumping blood flow of the ventricular catheter pump based on the motor operating parameter value and the impeller diameter change.

[0086] From the above, it can be seen that the blood pumping flow rate is estimated by the scheme provided in this embodiment. Since the target blood pumping flow rate is estimated based on the motor operating parameter value and the impeller diameter change, the motor operating parameter value represents the current operating information of the motor, and the impeller diameter change represents the geometric characteristic change information of the foldable impeller. Therefore, the estimated target blood pumping flow rate, in addition to considering the motor operating parameters, more importantly, considers the geometric characteristic change information of the foldable impeller. The geometric characteristic change of the foldable impeller affects the blood pumping flow rate, so that the target blood pumping flow rate taken into consideration is close to the actual blood pumping flow rate, thereby improving the accuracy of the blood pumping flow rate estimation.

[0087] See also Figure 6 , Figure 6 A schematic structural diagram of a second device for estimating blood flow rate of a ventricular catheter pump provided in an embodiment of the present application.

[0088] The parameter acquisition module 601 is used to acquire the current operating parameter value of the motor in the ventricular catheter pump and acquire the change in the impeller diameter of the impeller in the ventricular catheter pump; The above motor operating parameter values ​​include the current motor speed and the current motor power.

[0089] A first flow determination submodule 602, configured to determine a first pump blood flow corresponding to the current motor power by using a first preset linear coefficient; The second flow determination submodule 603 is used to determine a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and to determine a second pump blood flow corresponding to the target correlation value using a second preset linear coefficient; The target flow determination submodule 604 is used to determine a target pumping blood flow of the ventricular catheter pump based on the first pumping blood flow and the second pumping blood flow.

[0090] In this embodiment, the target blood flow rate of the ventricular catheter pump is determined based on the first blood flow rate and the second blood flow rate, wherein the first blood flow rate is determined based on the current motor power, and the second blood flow rate is determined based on the correlation between the current motor speed and the change in impeller diameter. On the one hand, the motor power directly affects the blood flow rate, and the accuracy of the first blood flow rate determined based on the current motor power is relatively high. On the other hand, the correlation between the motor speed and the impeller change also affects the blood flow rate, and the accuracy of the second blood flow rate determined based on the above correlation is also relatively high. Therefore, combining the above two aspects, the accuracy of the determined target blood flow rate is further improved.

[0091] See also Figure 7 , Figure 7 A schematic structural diagram of a third device for estimating the blood flow rate of a ventricular catheter pump provided in an embodiment of the present application.

[0092] The parameter acquisition module 701 is used to acquire the current operating parameter value of the motor in the ventricular catheter pump and acquire the change in the impeller diameter of the impeller in the ventricular catheter pump; The above motor operating parameter values ​​include the current motor speed and the current motor power.

[0093] A first flow determination submodule 702, configured to determine a first pump blood flow corresponding to the current motor power by using a first preset linear coefficient; The second flow determination submodule 703 is used to determine a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and to determine a second pump blood flow corresponding to the target correlation value using a second preset linear coefficient; The pressure difference acquisition submodule 704 is used to acquire the current pressure difference between the blood inlet pressure and the bleeding outlet pressure of the ventricular catheter pump before the target flow determination submodule; A flow calculation unit 705, configured to calculate the sum of the first pump blood flow rate and the second pump blood flow rate, and use the calculated sum as a reference pump blood flow rate; a deviation calculation unit 706, configured to determine a deviation of a reference pump blood flow rate based on the current pressure difference and the current motor speed; The flow rate adjustment unit 707 is used to adjust the reference blood pumping flow rate according to the deviation, and determine the adjusted flow rate as the target blood pumping flow rate of the ventricular catheter pump.

[0094] The deviation of the blood pumping flow is calculated by using the current pressure difference and the current motor speed, so as to accurately correct the reference blood pumping flow and improve the accuracy of the blood pumping flow estimation.

[0095] In one embodiment of the present application, the above-mentioned deviation calculation unit 706 is specifically used to determine the flow deviation ratio corresponding to the current pressure difference and the current motor speed; based on the baseline pump blood flow and the flow deviation ratio, calculate the deviation amount of the baseline pump blood flow.

[0096] In one embodiment of the present application, the deviation calculation unit 706 is specifically used to calculate the flow deviation ratio according to the following expression: ; in, is the flow deviation ratio, is the current pressure difference, is the first preset nonlinear coefficient, is the second preset nonlinear coefficient, and N is the current motor speed.

[0097] Corresponding to the above-mentioned estimation of the blood flow of the ventricular catheter pump, the present application embodiment provides an electronic medical device, see Figure 8 , Figure 8 A schematic diagram of the structure of an electronic medical device provided in an embodiment of the present application, wherein the electronic medical device includes a processor 801, a communication interface 802, a memory 803 and a communication bus 804, wherein the processor 801, the communication interface 802, and the memory 803 communicate with each other via the communication bus 804; Memory 803, used for storing computer programs; The processor 801 is used to implement the steps of the method for estimating the pumping blood flow of the ventricular catheter pump when executing the program stored in the memory 803.

[0098] The communication bus mentioned in the above controller can be a Peripheral Component Interconnect (PCI) bus or an Extended Industry Standard Architecture (EISA) bus, etc. The communication bus can be divided into an address bus, a data bus, a control bus, etc. For ease of representation, only one thick line is used in the figure, but it does not mean that there is only one bus or one type of bus.

[0099] The communication interface is used for communication between the above controller and other devices.

[0100] The memory may include a random access memory (RAM) or a non-volatile memory (NVM), such as at least one disk memory. Optionally, the memory may also be at least one storage device located away from the aforementioned processor.

[0101] The above-mentioned processor can be a general-purpose processor, including a central processing unit (CPU), a network processor (NP), etc.; it can also be a digital signal processor (DSP), an application specific integrated circuit (ASIC), a field programmable gate array (FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components.

[0102] In another embodiment provided in the present application, a computer-readable storage medium is provided, in which a computer program is stored. When the computer program is executed by a processor, the method for estimating the blood flow of the ventricular catheter pump provided in the embodiment of the present application is implemented.

[0103] In another embodiment provided in the present application, a computer program product including instructions is also provided, which, when executed on a computer, enables the computer to implement the above-mentioned method for estimating the blood flow of the ventricular catheter pump provided in the embodiment of the present application.

[0104] From the above, it can be seen that the blood pumping flow rate is estimated by the scheme provided in this embodiment. Since the target blood pumping flow rate is estimated based on the motor operating parameter value and the impeller diameter change, the motor operating parameter value represents the current operating information of the motor, and the impeller diameter change represents the geometric characteristic change information of the foldable impeller. Therefore, the estimated target blood pumping flow rate, in addition to considering the motor operating parameters, more importantly, considers the geometric characteristic change information of the foldable impeller. The geometric characteristic change of the foldable impeller affects the blood pumping flow rate, so that the target blood pumping flow rate taken into consideration is close to the actual blood pumping flow rate, thereby improving the accuracy of the blood pumping flow rate estimation.

[0105] In the above embodiments, it can be implemented in whole or in part by software, hardware, firmware or any combination thereof. When implemented using software, it can be implemented in whole or in part in the form of a computer program product. The computer program product includes one or more computer instructions. When the computer program instructions are loaded and executed on a computer, the process or function described in the embodiment of the present application is generated in whole or in part. The computer may be a general-purpose computer, a special-purpose computer, a computer network, or other programmable device. The computer instructions may be stored in a computer-readable storage medium, or transmitted from one computer-readable storage medium to another computer-readable storage medium. For example, the computer instructions may be transmitted from a website site, a computer, a server or a data center by wired (e.g., coaxial cable, optical fiber, digital subscriber line (DSL)) or wireless (e.g., infrared, wireless, microwave, etc.) mode to another website site, computer, server or data center. The computer-readable storage medium may be any available medium that a computer can access or a data storage device such as a server or a data center that includes one or more available media integrated. The available medium may be a magnetic medium (e.g., a floppy disk, a hard disk, a tape), an optical medium (e.g., a DVD), or a semiconductor medium (e.g., a solid-state drive Solid State Disk (SSD)), etc.

[0106] It should be noted that, in this article, relational terms such as first and second, etc. are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Moreover, the terms "include", "comprise" or any other variants thereof are intended to cover non-exclusive inclusion, so that a process, method, article or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In the absence of further restrictions, the elements defined by the sentence "comprise a ..." do not exclude the existence of other identical elements in the process, method, article or device including the elements.

[0107] Each embodiment in this specification is described in a related manner, and the same or similar parts between the embodiments can be referred to each other, and each embodiment focuses on the differences from other embodiments. In particular, for the device, ventricular catheter pump system, electronic medical device, and computer-readable storage medium embodiments, since they are basically similar to the method embodiments, the description is relatively simple, and the relevant parts can be referred to the partial description of the method embodiments.

[0108] The above description is only a preferred embodiment of the present application and is not intended to limit the protection scope of the present application. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application are included in the protection scope of the present application.

Claims

1. A method for estimating the blood flow rate of a ventricular catheter pump, characterized in that: An electronic medical device used in a ventricular assist system, wherein the ventricular assist system further comprises a ventricular catheter pump with a foldable impeller, the electronic medical device being connected to the ventricular catheter pump, and the method comprising: Obtaining current operating parameter values ​​of the motor in the ventricular catheter pump, and obtaining a change in the impeller diameter of the impeller in the ventricular catheter pump; The target blood flow rate of the ventricular catheter pump is estimated based on the motor operating parameter value and the impeller diameter change.

2. The method according to claim 1, characterized in that: The motor operation parameter value includes a current motor speed and a current motor power. The estimating a target pump blood flow rate of the ventricular catheter pump based on the motor operation parameter value and the impeller diameter change includes: Using a first preset linear coefficient, determining a first pump blood flow rate corresponding to the current motor power; Determine a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and use a second preset linear coefficient to determine a second pump blood flow corresponding to the target correlation value; A target pumping blood flow rate of the ventricular catheter pump is determined based on the first pumping blood flow rate and the second pumping blood flow rate.

3. The method according to claim 2, characterized in that Before determining the target pumping blood flow rate of the ventricular catheter pump based on the first pumping blood flow rate and the second pumping blood flow rate, the method further includes: Acquire the current pressure difference between the blood inlet pressure and the bleeding outlet pressure of the ventricular catheter pump; The determining a target pumping blood flow rate of the ventricular catheter pump based on the first pumping blood flow rate and the second pumping blood flow rate comprises: Calculating the sum of the first pump blood flow rate and the second pump blood flow rate, and using the calculated sum as a reference pump blood flow rate; Determining a deviation amount of a reference pump blood flow rate based on the current pressure difference and the current motor speed; The reference blood pumping flow rate is adjusted according to the deviation, and the adjusted flow rate is determined as the target blood pumping flow rate of the ventricular catheter pump.

4. The method according to claim 3, characterized in that The step of calculating the deviation of the reference pump blood flow rate based on the current pressure difference and the current motor speed includes: Determine the flow deviation ratio corresponding to the current pressure difference and the current motor speed; Based on the reference pump blood flow rate and the flow deviation ratio, the deviation amount of the reference pump blood flow rate is calculated.

5. The method according to claim 4, characterized in that The determining of the flow deviation ratio corresponding to the current pressure difference and the current motor speed includes: The flow deviation ratio is calculated according to the following expression: ； in, is the flow deviation ratio, is the current pressure difference, is the first preset nonlinear coefficient, is the second preset nonlinear coefficient, and N is the current motor speed.

6. A device for estimating the blood flow rate of a ventricular catheter pump, characterized in that: An electronic medical device used in a ventricular assist system, wherein the ventricular assist system further comprises a ventricular catheter pump with a foldable impeller, the electronic medical device being connected to the ventricular catheter pump, the device comprising: A parameter acquisition module, used to acquire the current operating parameter value of the motor in the ventricular catheter pump, and to acquire the change in the impeller diameter of the impeller in the ventricular catheter pump; The flow estimation module is used to estimate the target pumping blood flow of the ventricular catheter pump based on the motor operating parameter value and the change in impeller diameter.

7. The device according to claim 6, characterized in that The motor operation parameter value includes the current motor speed and the current motor power. The flow estimation module includes: A first flow determination submodule, configured to determine a first pump blood flow corresponding to the current motor power by using a first preset linear coefficient; A second flow determination submodule is used to determine a target correlation value representing the correlation between the current motor speed and the impeller diameter change, and to determine a second pump blood flow corresponding to the target correlation value using a second preset linear coefficient; The target flow determination submodule is used to determine a target pumping blood flow of the ventricular catheter pump based on the first pumping blood flow and the second pumping blood flow.

8. A ventricular catheter pump system, characterized in that: The ventricular catheter pump system comprises a ventricular catheter pump with a foldable impeller and an electronic medical device, wherein the ventricular catheter pump is connected to the electronic medical device, and the electronic medical device is used to execute the method steps of any one of claims 1 to 5 when controlling the operation of the ventricular catheter pump.

9. An electronic medical device, characterized in that: It includes a processor, a communication interface, a memory and a communication bus, wherein the processor, the communication interface and the memory communicate with each other through the communication bus; Memory, used to store computer programs; A processor, for implementing the method steps described in any one of claims 1 to 5 when executing a program stored in a memory.

10. A computer-readable storage medium, characterized in that: The computer-readable storage medium stores a computer program, and when the computer program is executed by a processor, the method steps of any one of claims 1 to 5 are implemented.

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