Monitoring system and device for a ventricular assist device

Abstract

The embodiment of the application provides a kind of ventricular assist device monitoring system and device, it is related to medical instrument technical field, above-mentioned system includes ventricular assist device and monitoring device, the monitoring device executes following monitoring method: the current rotating speed of ventricular assist device is obtained rotating speed signal, and the first pressure signal of the left ventricular pressure of patient heart is determined;Based on the rotating speed signal and first pressure signal, the target correlation value of the degree of correlation between current rotating speed and left ventricular pressure is calculated;Based on the deviation between the target correlation value and preset reference value, the target support state of the ventricular assist device is determined.The scheme provided in the embodiment can realize the real-time continuous accurate monitoring of the support state of ventricular assist device.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical devices, in particular to a monitoring system and device for a ventricular assist device. BACKGROUND

[0002] A ventricular assist device is a device for providing support or assistance to a patient suffering from a heart-related disease, such as a heart failure patient, for assisting the heart to pump blood to other parts of the body. The ventricular assist device is in a dynamic running state in the heart and needs to be monitored in real time. SUMMARY

[0003] The purpose of the embodiments of the present application is to provide a monitoring system and device for a ventricular assist device to realize real-time continuous and accurate monitoring of the dynamic running state of the ventricular assist device. The specific technical solutions are as follows:

[0004] In a first aspect, the embodiments of the present application provide a monitoring system for a ventricular assist device, the system comprising a ventricular assist device and a monitoring device, the ventricular assist device being implanted in a patient's heart by a percutaneous intervention method to assist the patient's heart to pump blood, and the monitoring device being used to monitor the support state of the ventricular assist device, and the monitoring device performing the following monitoring method:

[0005] obtaining a rotation speed signal of a current rotation speed of the ventricular assist device and determining a first pressure signal of a left ventricular pressure of the patient's heart;

[0006] calculating a target correlation value representing the degree of correlation between the current rotation speed and the left ventricular pressure based on the rotation speed signal and the first pressure signal;

[0007] determining a target support state of the ventricular assist device based on the deviation between the target correlation value and a preset reference value, wherein the target support state is a full support state, a partial support state or a non-support state.

[0008] In one embodiment of the present application, the above-mentioned calculation of the target correlation value representing the degree of correlation between the current rotation speed and the left ventricular pressure based on the rotation speed signal and the first pressure signal comprises:

[0009] obtaining a second pressure signal of an aortic pressure of the patient's heart;

[0010] calculating a target interference value representing the interference of the aortic pressure on the correlation between the rotation speed signal and the first pressure signal based on the degree of correlation between the first pressure signal, the second pressure signal and the rotation speed signal;

[0011] Based on the target interference value, a signal correlation degree between the rotation speed signal and the first pressure signal excluding the aortic pressure interference is calculated as a target correlation value representing a correlation degree between the current rotation speed and the left ventricular pressure.

[0012] In one embodiment of the present application, the above-mentioned calculation of the target interference value representing the aortic pressure interference on the correlation between the rotation speed signal and the first pressure signal includes:

[0013] Based on the first self-power spectrum and the first cross-power spectrum of the second pressure signal, a correlation degree between the current rotation speed and the aortic pressure is calculated as a first interference value, wherein the first cross-power spectrum is a cross-power spectrum between the rotation speed signal and the second pressure signal;

[0014] Based on the first self-power spectrum and the second cross-power spectrum, a correlation degree between the left ventricular pressure and the aortic pressure is calculated as a second interference value, wherein the second cross-power spectrum is a cross-power spectrum between the first pressure signal and the second pressure signal;

[0015] Based on the first self-power spectrum, the first cross-power spectrum and the second cross-power spectrum, a correlation degree between the aortic pressure, the left ventricular pressure and the rotation speed is calculated as a third interference value;

[0016] The first interference value, the second interference value and the third interference value are determined as the target interference value representing the aortic pressure interference on the correlation between the rotation speed signal and the first pressure signal.

[0017] In one embodiment of the present application, the above-mentioned calculation of the target correlation value representing the correlation degree between the current rotation speed and the left ventricular pressure based on the target interference value includes:

[0018] A first difference value between the second self-power spectrum of the rotation speed signal and the first interference value is calculated;

[0019] A second difference value between the third self-power spectrum of the first pressure signal and the second interference value is calculated;

[0020] A third difference value between the third cross-power spectrum and the third interference value is calculated, wherein the third cross-power spectrum is a cross-power spectrum between the rotation speed signal and the first pressure signal;

[0021] Based on the first difference value, the second difference value and the third difference value, a partial coherence value between the rotation speed signal and the first pressure signal is calculated;

[0022] Based on the partial coherence value, the target correlation value representing the correlation degree between the current rotation speed and the left ventricular pressure is calculated.

[0023] In one embodiment of the present application, the first pressure signal of the left ventricular pressure of the patient's heart is determined by:

[0024] obtaining a current motor current of the ventricular assist device as a current signal;

[0025] estimating a pressure difference based on the current signal and the rotational speed signal, using a preset fitting coefficient, wherein the pressure difference is a pressure difference between the left ventricular pressure and the aortic pressure, and the preset fitting coefficient is a coefficient fitted by using historical clinical data;

[0026] determining the first pressure signal of the left ventricular pressure of the patient's heart based on the pressure difference and a second pressure signal of the aortic pressure.

[0027] In a second aspect, the embodiments of the present application provide a monitoring device of a ventricular assist device, which is applied to a monitoring system of the ventricular assist device, the monitoring system of the ventricular assist device further comprising a ventricular assist device, the ventricular assist device being implanted in a patient's heart by a percutaneous intervention method to assist the patient's heart in pumping blood, and the device comprising:

[0028] a signal determination module configured to obtain a rotational speed signal of a current rotational speed of the ventricular assist device and determine a first pressure signal of a left ventricular pressure of the patient's heart;

[0029] a parameter calculation module configured to calculate a target correlation value representing a degree of correlation between the current rotational speed and the left ventricular pressure based on the rotational speed signal and the first pressure signal;

[0030] a state monitoring module configured to determine a target support state of the ventricular assist device based on a deviation between the target correlation value and a preset reference value, wherein the target support state is a full support state, a partial support state or a non-support state.

[0031] In one embodiment of the present application, the parameter calculation module comprises:

[0032] a signal acquisition sub-module configured to obtain a second pressure signal of an aortic pressure of the patient's heart;

[0033] a first parameter calculation sub-module configured to calculate a target interference value representing aortic pressure interference on a correlation between the rotational speed signal and the first pressure signal based on a degree of correlation between the first pressure signal, the second pressure signal and the rotational speed signal;

[0034] a second parameter calculation sub-module configured to calculate a signal correlation between the rotational speed signal and the first pressure signal excluding the aortic pressure interference as a target correlation value representing a degree of correlation between the current rotational speed and the left ventricular pressure based on the target interference value.

[0035] In one embodiment of the present application, the first parameter calculation submodule comprises:

[0036] The first parameter calculation unit is configured to calculate a correlation degree between the current rotation speed and the aortic pressure based on the first self-power spectrum and the first cross-power spectrum of the second pressure signal, as a first interference value, wherein the first cross-power spectrum is a cross-power spectrum between the rotation speed signal and the second pressure signal.

[0037] The second parameter calculation unit is configured to calculate a correlation degree between the left ventricular pressure and the aortic pressure based on the first self-power spectrum and the second cross-power spectrum, as a second interference value, wherein the second cross-power spectrum is a cross-power spectrum between the first pressure signal and the second pressure signal.

[0038] The third parameter calculation unit is configured to calculate a correlation degree between the aortic pressure, the left ventricular pressure and the rotation speed based on the first self-power spectrum, the first cross-power spectrum and the second cross-power spectrum, as a third interference value.

[0039] The target parameter calculation unit is configured to determine the first interference value, the second interference value and the third interference value as a target interference value representing the aortic pressure interference on the correlation between the rotation speed signal and the first pressure signal.

[0040] In one embodiment of the present application, the second parameter calculation submodule is specifically configured to calculate a first difference value between the second self-power spectrum of the rotation speed signal and the first interference value; calculate a second difference value between the third self-power spectrum of the first pressure signal and the second interference value; calculate a third difference value between the third cross-power spectrum and the third interference value, wherein the third cross-power spectrum is a cross-power spectrum between the rotation speed signal and the first pressure signal; calculate a partial coherence value between the rotation speed signal and the first pressure signal based on the first difference value, the second difference value and the third difference value; and calculate a target correlation value representing a correlation degree between the current rotation speed and the left ventricular pressure based on the partial coherence value.

[0041] In one embodiment of the present application, the signal determination module is specifically configured to acquire a current motor current signal of the ventricular assist device; estimate a pressure difference based on the current signal, the rotation speed signal and a preset fitting coefficient, wherein the pressure difference is a pressure difference between the left ventricular pressure and the aortic pressure, and the preset fitting coefficient is a coefficient fitted by using historical clinical data; and determine a first pressure signal of the left ventricular pressure of the patient's heart based on the pressure difference and a second pressure signal of the aortic pressure.

[0042] In a third aspect, an electronic medical device is provided, comprising 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.

[0043] The memory is configured to store a computer program.

[0044] The processor is configured to execute the program stored in the memory, so as to implement the monitoring method performed by the monitoring device in the monitoring system of the ventricular assist device according to the first aspect.

[0045] In a fourth aspect, a computer readable storage medium is provided, and the computer readable storage medium stores a computer program. The computer program is executed by a processor to implement the monitoring method performed by the monitoring device in the monitoring system of the ventricular assist device according to the first aspect.

[0046] As can be seen from the above, the monitoring system provided by the embodiments of the present application can accurately determine the real-time support state of the ventricular assist device to the heart of the patient by using the target correlation value, so as to realize real-time and continuous accurate monitoring of the current support state of the ventricular assist device.

[0047] Of course, implementing any product or method of the present application does not necessarily require all the advantages described above. BRIEF DESCRIPTION OF DRAWINGS

[0048] In order to more clearly illustrate the technical solutions of the embodiments of the present application or the prior art, the drawings needed in the embodiments or the prior art description will be briefly introduced. Obviously, the drawings in the following description are only some embodiments of the present application, and other embodiments can also be obtained by those skilled in the art based on these drawings.

[0049] Figure 1a A structural schematic diagram of a ventricular assist device monitoring system provided by the embodiments of the present application;

[0050] Figure 1b A structural schematic diagram of a ventricular assist device provided by the embodiments of the present application;

[0051] Figure 2 A flowchart of a first ventricular assist device monitoring method provided by the embodiments of the present application;

[0052] Figure 3 A flowchart of a second ventricular assist device monitoring method provided in an embodiment of the present application;

[0053] Figure 4 A flowchart of a third ventricular assist device monitoring method provided in an embodiment of the present application;

[0054] Figure 5 A schematic structural diagram of a monitoring device for a first ventricular assist device provided in an embodiment of the present application;

[0055] Figure 6 A schematic structural diagram of a second ventricular assist device monitoring device provided in an embodiment of the present application;

[0056] Figure 7 A schematic structural diagram of a monitoring device for a third ventricular assist device provided in an embodiment of the present application;

[0057] Figure 8 A schematic structural diagram of an electronic medical device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0058] The following will be combined with the drawings in the embodiments of this application to clearly and completely describe the technical solutions in the embodiments of this application. Obviously, the embodiments described are only part of the embodiments of this application, not all of the embodiments. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field based on this application are within the scope of protection of this application.

[0059] Before introducing the embodiments of the present application, first, Figure 1a , the monitoring system of the ventricular assist device provided in the embodiment of the present application is described.

[0060] The monitoring system for a ventricular assist device includes a monitoring device 11 and a ventricular assist device 12. The ventricular assist device 12 is implanted percutaneously into the patient's heart to assist the patient's heart in pumping blood. The monitoring device 11 is used to monitor the operating status of the ventricular assist device 12.

[0061] The ventricular assist device 12 is in a dynamic state while operating in the heart. Specifically, the support state of the ventricular assist device includes three types: full support state, partial support state, and non-support state.

[0062] Among them, the full support state means that the ventricular assist device replaces the heart to be responsible for the complete pumping function, the partial support state means that the ventricular assist device replaces the heart to be responsible for part of the pumping function, and the non-support state means that the ventricular assist device is not responsible for the pumping function.

[0063] The support state of the ventricular assist device is in dynamic change, and real-time monitoring of the support state can achieve more effective ventricular assist device control. Therefore, there is an urgent need for a monitoring scheme for real-time monitoring of the support state of the ventricular assist device.

[0064] The ventricular assist device can be a left ventricular assist device. The ventricular assist device is described taking the left ventricular assist device as an example. Referring to Figure 1b , Figure 1b A structural schematic diagram of the left ventricular assist device is shown.

[0065] Figure 1b The ventricular assist device shown is a left ventricular catheter pump, which is used to pump blood from the left ventricle into the aorta across the aortic valve 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., which is not limited.

[0066] The left ventricular catheter pump includes a motor 101, an impeller 102, a blood outlet 103, and a blood inlet 104. The motor 101 rotates at high speed to drive the impeller 102 to rotate, generating suction to pump blood from the blood inlet 104 into the blood outlet 103. The blood inlet 104 is located in the left ventricle of the patient, and the blood outlet 103 is located in the aorta of the patient, achieving the purpose of assisting the patient's heart in pumping blood.

[0067] The following describes the monitoring scheme executed by the monitoring device.

[0068] Referring to Figure 2 , Figure 2 A flowchart of a first monitoring method provided by an embodiment of the present application is shown, and the method includes the following steps S201-S203.

[0069] Step S201: Obtain a rotation speed signal of a current rotation speed of the ventricular assist device, and determine a first pressure signal of the left ventricular pressure of the patient's heart.

[0070] The rotation speed signal can be monitored by a rotation speed monitor.

[0071] The first pressure signal can be monitored by a pressure sensor.

[0072] The first pressure signal can also be calculated in real time. Based on this, in an embodiment of the present application, a current current signal of the motor current of the ventricular assist device can be obtained; based on the current signal and the rotation speed signal, a pressure difference is estimated using a preset fitting coefficient; and based on the pressure difference and a pressure signal of the aortic pressure, the first pressure signal of the left ventricular pressure of the patient's heart is determined.

[0073] The preset fitting coefficient is a coefficient fitted using historical clinical data.

[0074] The pressure difference is a pressure difference between the left ventricular pressure and the aortic pressure. One embodiment of estimating the pressure difference is: according to a fitting formula containing preset fitting coefficients, taking the current signal and the rotation speed signal as variables of the fitting formula, calculating a calculation result of the fitting formula as the pressure difference.

[0075] After the pressure difference is estimated, a difference between the pressure signal of the aortic pressure and the pressure difference can be calculated as a first pressure signal.

[0076] Step S202: based on the rotation speed signal and the first pressure signal, a target correlation value representing a correlation degree between the current rotation speed and the left ventricular pressure is calculated.

[0077] The target correlation value represents the correlation degree between the current rotation speed and the left ventricular pressure. When the target correlation value is high, it indicates that the correlation degree is higher, and when the target correlation value is lower, it indicates that the correlation degree is lower.

[0078] One embodiment of calculating the target correlation value is: using partial coherence analysis to perform correlation analysis on the rotation speed signal and the first pressure signal, and determining the calculated partial coherence value as the target correlation value.

[0079] Other embodiments of calculating the target correlation value can be referred to in the subsequent Figure 3 The corresponding embodiments will not be described in detail here.

[0080] Step S203: based on a deviation between the target correlation value and a preset reference value, a target support state of the ventricular assist device is determined.

[0081] The target support state is a full support state, a partial support state or a non-support state. The specific meaning of each state has been specifically described before this embodiment and will not be repeated here.

[0082] The preset reference value can be a reference value corresponding to the full support state preset in advance. In this case, when the target correlation value is farther away from the preset reference value, it indicates that the ventricular assist device is less likely to be in the full support state, and vice versa. Based on this, one embodiment of determining the target support state is: when the deviation is less than a first preset threshold, it is determined as the full support state; when the deviation is between the first preset threshold and a second preset threshold, it is determined as the partial support state; and when the deviation is greater than the second preset threshold, it is determined as the non-support state.

[0083] The preset reference value can also be a reference value corresponding to each support state, such as a reference value corresponding to the full support state, a reference value corresponding to the partial support state, and a reference value corresponding to the non-support state. Based on this, one embodiment of determining the target support state is to determine the support state corresponding to the deviation less than the third preset threshold as the target support state. For example, if the deviation between the preset reference value corresponding to the full support state and the target correlation value is less than the third preset threshold, and the deviations of the other two support states are greater than the third preset threshold, the target support state is determined as the full support state.

[0084] As can be seen from the above, by applying the monitoring system provided by the embodiment, since the target correlation value represents the correlation degree between the current rotating speed and the left ventricular pressure, the current rotating speed reflects the real-time running state of the ventricular assist device, and the left ventricular pressure reflects the real-time physiological state of the patient's heart, and since the patient's heart is in real-time change with the running of the ventricular assist device, that is, there is a correlation between the running of the ventricular assist device and the change of the patient's heart, therefore, by using the above target correlation value, the real-time support state of the ventricular assist device to the patient's heart can be accurately determined, so as to realize real-time and continuous accurate monitoring of the current support state of the ventricular assist device.

[0085] In the foregoing Figure 2 In the corresponding embodiment step S202, in addition to the above-mentioned calculation method, the target correlation value can also be calculated by steps S302-S304. Based on this, referring to Figure 3 , Figure 3 The flowchart of the second monitoring method provided by the embodiment of the application. The above method comprises steps S301-S305.

[0086] Step S301: obtaining a rotating speed signal of the current rotating speed of the ventricular assist device, and determining a first pressure signal of the left ventricular pressure of the patient's heart.

[0087] The step S301 is the same as the step S201, and will not be repeated here.

[0088] Step S302: obtaining a second pressure signal of the aortic pressure of the patient's heart.

[0089] The second pressure signal represents the current aortic pressure information of the patient's heart. The second pressure signal can be detected by a pressure sensor.

[0090] Step S303: calculating a target interference value representing the interference of the aortic pressure on the correlation between the rotating speed signal and the first pressure signal based on the correlation between the first pressure signal, the second pressure signal, and the rotating speed signal.

[0091] The target interference value represents an interference value of the aortic pressure affecting the correlation between the rotation speed signal and the first pressure signal.

[0092] From a large amount of clinical data, by reasoning, simulation, and verification, it is found that the aortic pressure is related to the rotation speed of the ventricular assist device and the left ventricular pressure, the heart and the ventricular assist device have interaction, the interaction has strong hysteresis and nonlinearity, the aortic pressure has different degrees of influence on the rotation speed signal and the left ventricular pressure signal, therefore, the correlation between the three types of signals can be used to accurately calculate the interference information corresponding to the aortic pressure.

[0093] One embodiment of calculating the target interference value is that the rotation speed signal, the first pressure signal, and the second pressure signal are input into a pre-trained interference prediction model to obtain an interference value output by the interference prediction model as the target interference value.

[0094] The interference prediction model is a model for predicting the interference value caused by the aortic pressure, which is obtained by pre-training a large number of sample rotation speed signals, sample left ventricular pressure signals, and sample aortic pressure signals as training samples, and using actual interference values as training benchmarks to train an initial neural network model.

[0095] Since the interference prediction model learns the characteristic relationship between the rotation speed signal, the left ventricular pressure signal, the aortic pressure signal, and the interference value by using a large number of training samples, the target interference value can be accurately predicted by using the interference prediction model.

[0096] Other embodiments of calculating the target interference value can be referred to in the subsequent Figure 4 The corresponding embodiments are not described in detail here.

[0097] Step S304: Based on the target interference value, a signal correlation between the rotation speed signal and the first pressure signal excluding the interference of the aortic pressure is calculated as a target correlation value representing the correlation degree between the current rotation speed and the left ventricular pressure.

[0098] Since the calculated signal correlation excludes the interference of the aortic pressure on the rotation speed signal and the first pressure signal, the signal correlation between the two types of signals excluding the interference is closer to the actual correlation, thereby improving the accuracy of the target correlation value.

[0099] One embodiment of calculating the target correlation value is that an initial correlation between the rotation speed signal and the first pressure signal is calculated, a difference between the initial correlation and the target interference value is calculated, and the calculated difference is determined as the target correlation value.

[0100] Other embodiments of calculating the target correlation value can be referred to in the subsequent Figure 4 The corresponding embodiments are not described in detail here.

[0101] Step S305: determining the target support state of the ventricular assist device based on the deviation between the target correlation value and the preset reference value.

[0102] The target support state is full support state, partial support state or non-support state.

[0103] The step S305 is the same as the step S203, and will not be repeated here.

[0104] As can be seen from the above, in the embodiment, since the calculated signal correlation degree excludes the interference of the aortic pressure, the calculated signal correlation degree is closer to the actual correlation degree, the accuracy of the target correlation value is improved, and the monitoring accuracy of the support state of the ventricular assist device is further improved.

[0105] In the foregoing Figure 3 In the step S303 of the corresponding embodiment, in addition to the mentioned manner of determining the target interference value, it can also be implemented according to the following steps S403-S406. Based on this, see Figure 4 , Figure 4 The flowchart of a third monitoring method provided by the embodiment of the application.

[0106] Step S401: acquiring a rotation speed signal of a current rotation speed of the ventricular assist device, and determining a first pressure signal of the left ventricular pressure of the patient's heart.

[0107] Step S402: acquiring a second pressure signal of the aortic pressure of the patient's heart.

[0108] The steps S401-S402 are the same as the steps S301-S302, and will not be repeated here.

[0109] Step S403: calculating the correlation degree between the current rotation speed and the aortic pressure based on the first self-power spectrum and the first cross-power spectrum of the second pressure signal, as a first interference value.

[0110] The first cross-power spectrum is the cross-power spectrum between the rotation speed signal and the second pressure signal.

[0111] One embodiment of calculating the first interference value is: calculating the square of the absolute value of the first cross-power spectrum as the numerator, taking the first self-power spectrum as the denominator, and calculating the ratio between the numerator and the denominator as the first interference value.

[0112] Step S404: calculating the correlation degree between the left ventricular pressure and the aortic pressure based on the first self-power spectrum and the second cross-power spectrum, as a second interference value.

[0113] The second cross power spectrum is a cross power spectrum between the first pressure signal and the second pressure signal.

[0114] One implementation of calculating the second interference value is to calculate a square of an absolute value of the second cross power spectrum as a numerator, calculate the first auto power spectrum as a denominator, and calculate a ratio between the numerator and the denominator as the second interference value.

[0115] Step S405: Based on the first auto power spectrum, the first cross power spectrum, and the second cross power spectrum, a correlation between the aortic pressure, the left ventricular pressure, and the rotation speed is calculated as a third interference value.

[0116] One implementation of calculating the third interference value is to calculate a square of an absolute value of a product between the first cross power spectrum and the second cross power spectrum as a numerator, calculate the first auto power spectrum as a denominator, and calculate a ratio between the numerator and the denominator as the third interference value.

[0117] Step S406: The first interference value, the second interference value, and the third interference value are determined as target interference values representing aortic pressure interference on a correlation between the rotation speed signal and the first pressure signal.

[0118] The target interference values include the first interference value, the second interference value, and the third interference value.

[0119] Step S407: Based on the target interference values, a signal correlation between the rotation speed signal and the first pressure signal excluding aortic pressure interference is calculated as a target correlation value representing a correlation degree between a current rotation speed and the left ventricular pressure.

[0120] When the target interference values include the first interference value, the second interference value, and the third interference value, one implementation of calculating the target correlation value is to calculate a first difference between a second auto power spectrum of the rotation speed signal and the first interference value, calculate a second difference between a third auto power spectrum of the first pressure signal and the second interference value, calculate a third difference between a third cross power spectrum and the third interference value, calculate a partial coherence value between the rotation speed signal and the first pressure signal based on the first difference, the second difference, and the third difference, and calculate the target correlation value representing the correlation degree between the current rotation speed and the left ventricular pressure based on the partial coherence value.

[0121] The third cross power spectrum is a cross power spectrum between the rotation speed signal and the first pressure signal.

[0122] One implementation of calculating the partial coherence value is to calculate a square of an absolute value of the third difference as a numerator, calculate a product between the first difference and the second difference as a denominator, and calculate a ratio between the numerator and the denominator to obtain the partial coherence value.

[0123] After the partial coherence value is calculated, a mean value of the partial coherence value in a preset frequency band can be calculated, and the calculated mean value is taken as the target correlation value.

[0124] Step S408: determining a target support state of the ventricular assist device based on a deviation between the target correlation value and a preset reference value.

[0125] The target support state is a full support state, a partial support state or a non-support state.

[0126] As can be seen from the above, the first interference value, the second interference value and the third interference value are all taken as the target interference value, and the first interference value reflects the interference degree of the aortic pressure on the rotation speed, the second interference value reflects the interference degree of the aortic pressure on the left ventricular pressure, and the third interference value reflects the interference degree of the aortic pressure on the relationship between the rotation speed and the left ventricular pressure. It can be seen that the above three types of interference values comprehensively contain various interference situations of the aortic pressure, thereby improving the accuracy of the target interference value and further improving the accuracy of the ventricular assist device monitoring.

[0127] Corresponding to the above-mentioned ventricular assist device monitoring system, an embodiment of the present application also provides a ventricular assist device monitoring device.

[0128] Referring to Figure 5 , Figure 5 A first ventricular assist device monitoring device provided by an embodiment of the present application is shown in a structural schematic diagram, and the device is applied to a ventricular assist device monitoring system. The ventricular assist device monitoring system also includes a ventricular assist device, and the ventricular assist device is implanted in a patient's heart through a percutaneous intervention manner to assist the patient's heart in pumping blood. The device includes:

[0129] A signal determination module 501 is configured to acquire a rotation speed signal of a current rotation speed of the ventricular assist device and determine a first pressure signal of a left ventricular pressure of the patient's heart.

[0130] A parameter calculation module 502 is configured to calculate a target correlation value representing a correlation degree between the current rotation speed and the left ventricular pressure based on the rotation speed signal and the first pressure signal.

[0131] A state monitoring module 503 is configured to determine a target support state of the ventricular assist device based on a deviation between the target correlation value and a preset reference value, and the target support state is a full support state, a partial support state or a non-support state.

[0132] As can be seen from the above, by using the monitoring system provided in the embodiment, since the target correlation value represents the correlation degree between the current rotating speed and the left ventricular pressure, the current rotating speed reflects the real-time running state of the ventricular assist device, and the left ventricular pressure reflects the real-time physiological state of the patient's heart, and since the patient's heart is in real-time change along with the running of the ventricular assist device, that is, there is a correlation between the running of the ventricular assist device and the change of the patient's heart, therefore, by using the above target correlation value, the real-time support state of the ventricular assist device to the patient's heart can be accurately determined, so as to realize real-time and continuous accurate monitoring of the current support state of the ventricular assist device.

[0133] Referring to Figure 6 , Figure 6 The second ventricular assist device monitoring device provided in the embodiment of the application is shown in the structural schematic diagram, and the device comprises:

[0134] The signal determination module 601 is configured to acquire a rotating speed signal of a current rotating speed of a ventricular assist device and determine a first pressure signal of a left ventricular pressure of a patient's heart.

[0135] The signal acquisition sub-module 602 is configured to acquire a second pressure signal of an aortic pressure of the patient's heart.

[0136] The first parameter calculation sub-module 603 is configured to calculate, based on the correlation degree between the first pressure signal, the second pressure signal and the rotating speed signal, a target interference value representing the interference of the aortic pressure to the correlation between the rotating speed signal and the first pressure signal.

[0137] The second parameter calculation sub-module 604 is configured to calculate, based on the target interference value, the signal correlation degree between the rotating speed signal and the first pressure signal excluding the interference of the aortic pressure, as a target correlation value representing the correlation degree between the current rotating speed and the left ventricular pressure.

[0138] The state monitoring module 605 is configured to determine, based on the deviation between the target correlation value and a preset reference value, a target support state of the ventricular assist device, wherein the target support state is a full support state, a partial support state or a non-support state.

[0139] As can be seen from the above, in the embodiment, since the calculated signal correlation degree excludes the interference of the aortic pressure, the calculated signal correlation degree is closer to the actual correlation degree, the accuracy of the target correlation value is improved, and the monitoring accuracy of the support state of the ventricular assist device is further improved.

[0140] Referring to Figure 7 , Figure 7 The third ventricular assist device monitoring device provided in the embodiment of the application is shown in the structural schematic diagram, and the device comprises:

[0141] The signal determination module 701 is configured to acquire a rotation speed signal of a current rotation speed of a ventricular assist device, and determine a first pressure signal of a left ventricular pressure of a patient's heart;

[0142] The signal acquisition sub-module 702 is configured to acquire a second pressure signal of an aortic pressure of the patient's heart;

[0143] The first parameter calculation unit 703 is configured to calculate, based on a first self-power spectrum of the second pressure signal and a first cross-power spectrum, a correlation degree between the current rotation speed and the aortic pressure as a first interference value, where the first cross-power spectrum is a cross-power spectrum between the rotation speed signal and the second pressure signal;

[0144] The second parameter calculation unit 704 is configured to calculate, based on the first self-power spectrum and a second cross-power spectrum, a correlation degree between the left ventricular pressure and the aortic pressure as a second interference value, where the second cross-power spectrum is a cross-power spectrum between the first pressure signal and the second pressure signal;

[0145] The third parameter calculation unit 705 is configured to calculate, based on the first self-power spectrum, the first cross-power spectrum and the second cross-power spectrum, a correlation degree between the aortic pressure, the left ventricular pressure and the rotation speed as a third interference value;

[0146] The target parameter calculation unit 706 is configured to determine the first interference value, the second interference value and the third interference value as a target interference value representing aortic pressure interference on a correlation between the rotation speed signal and the first pressure signal.

[0147] The second parameter calculation sub-module 707 is configured to calculate, based on the target interference value, a signal correlation degree between the rotation speed signal and the first pressure signal excluding aortic pressure interference as a target correlation value representing a correlation degree between the current rotation speed and the left ventricular pressure.

[0148] The state monitoring module 708 is configured to determine a target support state of the ventricular assist device based on a deviation between the target correlation value and a preset reference value, where the target support state is a full support state, a partial support state or a non-support state.

[0149] As can be seen from the above, the first interference value, the second interference value and the third interference value are all taken as the target interference value, the first interference value reflects aortic pressure interference on the rotation speed, the second interference value reflects aortic pressure interference on the left ventricular pressure, and the third interference value reflects aortic pressure interference on a relationship between the rotation speed and the left ventricular pressure. It can be seen that the above three types of interference values comprehensively contain various interference situations of the aortic pressure, thereby improving the accuracy of the target interference value and further improving the accuracy of the ventricular assist device monitoring.

[0150] In one embodiment of the present application, the second parameter calculation submodule is specifically configured to calculate a first difference value between a second self-power spectrum of the rotation speed signal and a first interference value; calculate a second difference value between a third self-power spectrum of the first pressure signal and a second interference value; calculate a third difference value between a third cross-power spectrum and a third interference value, wherein the third cross-power spectrum is a cross-power spectrum between the rotation speed signal and the first pressure signal; calculate a partial coherence value between the rotation speed signal and the first pressure signal based on the first difference value, the second difference value, and the third difference value; and calculate a target correlation value representing a degree of correlation between the current rotation speed and the left ventricular pressure based on the partial coherence value.

[0151] In one embodiment of the present application, the signal determination module is specifically configured to obtain a current motor current signal of the ventricular assist device; estimate a pressure difference based on the current signal and the rotation speed signal, wherein the pressure difference is a pressure difference between the left ventricular pressure and the aortic pressure, and the preset fitting coefficient is a coefficient fitted by using historical clinical data; and determine the first pressure signal of the left ventricular pressure of the patient's heart based on the pressure difference and a second pressure signal of the aortic pressure.

[0152] Corresponding to the above-mentioned ventricular assist device monitoring system, an electronic medical device is provided in the embodiments of the present application, which is described with reference to Figure 8 , Figure 8 A structural schematic diagram of an electronic medical device provided in the embodiments of the present application is shown in the above-mentioned electronic medical device, which 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 complete mutual communication through the communication bus 804.

[0153] The memory 803 is used to store a computer program.

[0154] The processor 801 is used to execute the program stored in the memory 803, so as to realize the steps of the above-mentioned ventricular assist device monitoring method.

[0155] The communication bus mentioned by the above-mentioned 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 the convenience of representation, only one thick line is shown in the figure, but it does not mean that there is only one bus or one type of bus.

[0156] The communication interface is used for communication between the above-mentioned controller and other devices.

[0157] The memory can include a Random Access Memory (RAM) and can also include a Non-Volatile Memory (NVM), such as at least one disk memory. Optionally, the memory can also be at least one storage device located remotely from the aforementioned processor.

[0158] The aforementioned processor can be a general processor, including a Central Processing Unit (CPU), a Network Processor (NP), etc.; can also be a Digital Signal Processor (DSP), an Application Specific Integrated Circuit (ASIC), a Field-Programmable Gate Array (FPGA) or other programmable logic device, a discrete gate or transistor logic device, a discrete hardware component.

[0159] In yet another embodiment provided in the present application, a computer readable storage medium is also provided, and the computer readable storage medium stores a computer program, and the computer program is executed by a processor to implement the steps of the aforementioned monitoring method of the ventricular assist device.

[0160] In yet another embodiment provided in the present application, a computer program product containing instructions is also provided, and when the computer program product is run on a computer, the computer is caused to implement the steps of the aforementioned monitoring method of the ventricular assist device.

[0161] In the embodiments described above, all or some of the steps can be implemented by software, hardware or firmware, or any combination thereof. When implemented by software, all or some of the steps can be implemented in the form of one or more computer programs. The computer program can be stored in any computer readable medium, and loaded into the computer for execution. The computer readable medium includes computer storage media and communication media. The computer storage media includes any tangible or physical medium for storing or transmitting the program. The computer storage media can be a volatile (e.g., RAM) or non-volatile (e.g., ROM, disk, or CD) storage medium. The communication media typically include computer readable instructions, data structures, program modules or other data in a modulated data signal such as a carrier wave or other transport mechanism, and includes any information delivery media. The computer readable media does not include carrier waves or other transient signals.

[0162] It should be noted that, in the present document, the terms such as first and second are used only to differentiate one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Also, the terms "comprising", "containing", or any other variant thereof are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include those elements only, but can also include other elements not expressly listed, or other elements inherent in such process, method, article, or apparatus. Without more limitations, an element defined by the phrase "comprising a" does not exclude the existence of additional identical elements in the process, method, article, or apparatus that includes the element.

[0163] Each of the embodiments in the present specification is described in a related manner, and the same or similar parts between the embodiments can be referred to each other. Each embodiment focuses on the difference from other embodiments. In particular, for the device, 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 part of the method embodiment.

[0164] The above merely provides the preferred embodiments of the application, and not intended to limit the protection scope of the application. Any modification, equivalent replacement, improvement, and the like made within the principle and technical scope of the application shall fall into the protection scope of the application.

Claims

1. A monitoring system for a ventricular assist device, characterized in that: The system includes a ventricular assist device and a monitoring device. The ventricular assist device is implanted in the patient's heart through percutaneous intervention to assist the patient's heart in pumping blood. The monitoring device is used to monitor the support status of the ventricular assist device. The monitoring device performs the following monitoring method: obtaining a speed signal of a current speed of the ventricular assist device and determining a first pressure signal of a left ventricular pressure of the patient's heart; Calculating a target correlation value representing a degree of correlation between the current rotational speed and the left ventricular pressure based on the rotational speed signal and the first pressure signal; wherein the target correlation value reflects the interactivity between the heart and the ventricular assist device; determining a target support state of the ventricular assist device based on a deviation between the target correlation value and a preset reference value, wherein the target support state is a full support state, a partial support state, or a non-support state; The calculating, based on the rotation speed signal and the first pressure signal, a target correlation value representing the degree of correlation between the current rotation speed and the left ventricular pressure includes: obtaining a second pressure signal of an aortic pressure of the patient's heart; Calculating a target interference value representing aortic pressure interference on the correlation between the rotation speed signal and the first pressure signal based on correlations among the first pressure signal, the second pressure signal, and the rotation speed signal; calculating, based on the target interference value, a signal correlation between the rotation speed signal and the first pressure signal, excluding interference from the aortic pressure, as a target correlation value representing a degree of correlation between the current rotation speed and the left ventricular pressure; The calculating, based on the correlation between the first pressure signal, the second pressure signal, and the rotation speed signal, a target interference value representing the aortic pressure interference on the correlation between the rotation speed signal and the first pressure signal includes: calculating, based on a first autopower spectrum and a first cross-power spectrum of the second pressure signal, a correlation between the current rotational speed and the aortic pressure as a first interference value, wherein the first cross-power spectrum is a cross-power spectrum between the rotational speed signal and the second pressure signal; calculating, based on the first autopower spectrum and the second cross-power spectrum, a correlation between the left ventricular pressure and the aortic pressure as a second interference value, wherein the second cross-power spectrum is a cross-power spectrum between the first pressure signal and the second pressure signal; Calculating correlations among aortic pressure, left ventricular pressure, and rotational speed based on the first autopower spectrum, the first cross-power spectrum, and the second cross-power spectrum as a third interference value; The first interference value, the second interference value, and the third interference value are determined as target interference values ​​representing aortic pressure interference to the correlation between the rotation speed signal and the first pressure signal.

2. The system according to claim 1, wherein: The calculating, based on the target interference value, the signal correlation between the rotation speed signal and the first pressure signal excluding the interference of the aortic pressure as the target correlation value representing the degree of correlation between the current rotation speed and the left ventricular pressure includes: Calculating a first difference between a second autopower spectrum of the rotational speed signal and a first interference value; calculating a second difference between a third autopower spectrum of the first pressure signal and a second interference value; calculating a third difference between a third cross power spectrum and a third interference value, wherein the third cross power spectrum is a cross power spectrum between the rotational speed signal and the first pressure signal; Calculating a partial coherence value between the rotational speed signal and the first pressure signal based on the first difference, the second difference, and the third difference; A target correlation value representing the degree of correlation between the current rotation speed and the left ventricular pressure is calculated based on the partial coherence value.

3. The system according to claim 1 or 2, characterized in that The determining of a first pressure signal of a left ventricular pressure of a patient's heart comprises: obtaining a current signal of a current motor current of the ventricular assist device; Based on the current signal and the speed signal, a preset fitting coefficient is used to estimate the pressure difference, wherein the pressure difference is the pressure difference between the left ventricular pressure and the aortic pressure, and the preset fitting coefficient is a coefficient obtained by fitting historical clinical data; A first pressure signal of a left ventricular pressure of the patient's heart is determined based on the pressure difference and a second pressure signal of aortic pressure.

4. A monitoring device for a ventricular assist device, characterized in that: The device is applied to a monitoring system for a ventricular assist device, wherein the monitoring system also includes a ventricular assist device, which is implanted into a patient's heart via percutaneous intervention to assist the patient's heart in pumping blood. The device includes: a signal determination module, configured to obtain a speed signal of a current speed of the ventricular assist device and determine a first pressure signal of a left ventricular pressure of the patient's heart; a parameter calculation module, configured to calculate a target correlation value representing a degree of correlation between a current rotational speed and left ventricular pressure based on the rotational speed signal and the first pressure signal; wherein the target correlation value reflects interactivity between the heart and the ventricular assist device; a state monitoring module, configured to determine a target support state of the ventricular assist device based on a deviation between the target related value and a preset reference value, wherein the target support state is a full support state, a partial support state, or a non-support state; The parameter calculation module includes: a signal acquisition submodule, configured to acquire a second pressure signal of the aorta pressure of the patient's heart; a first parameter calculation submodule, configured to calculate a target interference value representing aortic pressure interference on the correlation between the rotational speed signal and the first pressure signal based on the correlation between the first pressure signal, the second pressure signal and the rotational speed signal; a second parameter calculation submodule, configured to calculate, based on the target interference value, a signal correlation between the rotational speed signal and the first pressure signal, excluding interference from aortic pressure, as a target correlation value representing a degree of correlation between the current rotational speed and left ventricular pressure; The first parameter calculation submodule includes: a first parameter calculation unit, configured to calculate, as a first interference value, a correlation between the current rotational speed and the aortic pressure based on a first autopower spectrum and a first cross-power spectrum of the second pressure signal, wherein the first cross-power spectrum is a cross-power spectrum between the rotational speed signal and the second pressure signal; a second parameter calculation unit, configured to calculate, as a second interference value, a correlation between the left ventricular pressure and the aortic pressure based on the first autopower spectrum and the second cross-power spectrum, wherein the second cross-power spectrum is a cross-power spectrum between the first pressure signal and the second pressure signal; a third parameter calculation unit, configured to calculate, based on the first autopower spectrum, the first cross-power spectrum, and the second cross-power spectrum, a correlation between the aortic pressure, the left ventricular pressure, and the rotational speed as a third interference value; The target parameter calculation unit is configured to determine the first interference value, the second interference value, and the third interference value as target interference values ​​representing the aortic pressure interference on the correlation between the rotational speed signal and the first pressure signal.

5. The device according to claim 4, characterized in that The second parameter calculation submodule is specifically used to calculate the first difference between the second autopower spectrum of the speed signal and the first interference value; calculate the second difference between the third autopower spectrum of the first pressure signal and the second interference value; calculate the third difference between the third cross-power spectrum and the third interference value, wherein the third cross-power spectrum is the cross-power spectrum between the speed signal and the first pressure signal; based on the first difference, the second difference and the third difference, calculate the partial coherence value between the speed signal and the first pressure signal; based on the partial coherence value, calculate the target correlation value that characterizes the degree of correlation between the current speed and the left ventricular pressure.

6. The device according to claim 4 or 5, characterized in that The signal determination module is specifically used to obtain the current signal of the current motor current of the ventricular assist device; based on the current signal and the speed signal, a preset fitting coefficient is used to estimate the pressure difference, wherein the pressure difference is the pressure difference between the left ventricular pressure and the aortic pressure, and the preset fitting coefficient is a coefficient obtained by fitting using historical clinical data; based on the pressure difference and the second pressure signal of the aortic pressure, a first pressure signal of the left ventricular pressure of the patient's heart is determined.

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