Monitoring system and device for ventricular auxiliary equipment

Abstract

The embodiment of the invention provides a monitoring system and device of a ventricular assist device, and relates to the technical field of medical instruments.The system comprises the ventricular assist device and a monitoring device.The monitoring device executes the following monitoring method that a rotating speed signal of the current rotating speed of the ventricular assist device is obtained, and determine a first pressure signal of the left ventricular pressure of the patient's heart; based on the rotating speed signal and the first pressure signal, a target correlation value representing the correlation degree between the current rotating speed and the left ventricular pressure is calculated; and determining a target support state of the ventricular assist device based on a deviation between the target correlation value and a preset reference value. By applying the scheme provided by the embodiment, the support state of the ventricular assist device can be continuously and accurately monitored in real time.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and particularly to a monitoring system and device for a ventricular assist device. Background Art

[0002] A ventricular assist device is a device that provides support or assistance to patients with heart-related diseases, such as heart failure patients, and is used to assist the heart in pumping blood to other parts of the body. The ventricular assist device is in a dynamic operating state within the heart and requires real-time monitoring of its dynamic operating state. Summary of the Invention

[0003] The purpose of the embodiments of this application is to provide a monitoring system and device for a ventricular assist device to achieve real-time, continuous, and accurate monitoring of the dynamic operating state of the ventricular assist device. The specific technical solutions are as follows: In a first aspect, the embodiments of this application provide a monitoring system for a ventricular assist device. The system includes a ventricular assist device and a monitoring device. The ventricular assist device is implanted into the patient's heart through a percutaneous intervention method to assist the patient's heart in pumping blood. The monitoring device is used to monitor the support state of the ventricular assist device, and the monitoring device executes the following monitoring method: Obtain a rotation speed signal of the current rotation speed of the ventricular assist device and determine a first pressure signal of the left ventricular pressure of the patient's heart; Based on the rotation speed signal and the first pressure signal, calculate a target correlation value representing the degree of correlation between the current rotation speed and the left ventricular pressure; Based on the deviation between the target correlation value and a preset reference value, determine the target support state of the ventricular assist device, where the target support state is a full support state, a partial support state, or a non-support state.

[0004] In an embodiment of this 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 includes: Obtain a second pressure signal of the aortic pressure of the patient's heart; Based on the correlation degrees among the first pressure signal, the second pressure signal, and the rotation speed signal, calculate 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 target interference value, calculate the signal correlation degree 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.

[0005] In one embodiment of the present application, calculating a target interference value characterizing the interference of the aortic pressure 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 includes: Calculating the correlation between the current rotational speed and the aortic pressure based on the first auto-power spectrum and the first cross-power spectrum of the second pressure signal as a first interference value, where the first cross-power spectrum is the cross-power spectrum between the rotational speed signal and the second pressure signal; Calculating the correlation between the left ventricular pressure and the aortic pressure based on the first auto-power spectrum and the second cross-power spectrum as a second interference value, where the second cross-power spectrum is the cross-power spectrum between the first pressure signal and the second pressure signal; Calculating the correlation between the aortic pressure, the left ventricular pressure and the rotational speed based on the first auto-power spectrum, the first cross-power spectrum and the second cross-power spectrum as a third interference value; Determining the first interference value, the second interference value and the third interference value as the target interference value characterizing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal.

[0006] In one embodiment of the present application, calculating a signal correlation between the rotational speed signal and the first pressure signal excluding the interference of the aortic pressure based on the target interference value as a target correlation value characterizing the correlation between the current rotational speed and the left ventricular pressure includes: Calculating a first difference between the second auto-power spectrum of the rotational speed signal and the first interference value; Calculating a second difference between the third auto-power spectrum of the first pressure signal and the second interference value; Calculating a third difference between the third cross-power spectrum and the third interference value, where the third cross-power spectrum is the 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; Calculating a target correlation value characterizing the correlation between the current rotational speed and the left ventricular pressure based on the partial coherence value.

[0007] In one embodiment of the present application, the first pressure signal for determining the left ventricular pressure of the patient's heart includes: Obtaining a current signal of the current motor current of the ventricular assist device; Estimating a pressure difference based on the current signal and the rotational speed signal using a preset fitting coefficient, where 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; Determine a first pressure signal of the left ventricular pressure of the patient's heart based on the second pressure signal of the pressure difference and the aortic pressure.

[0008] In a second aspect, an embodiment of the present application provides a monitoring device for a ventricular assist device. The device is applied to a monitoring system of the ventricular assist device. The monitoring system of the ventricular assist device further includes a ventricular assist device. The ventricular assist device is implanted into the patient's heart through a percutaneous intervention method to assist the patient's heart in pumping blood. The device includes: A signal determination module, configured to obtain a rotational speed signal of the current rotational speed of the ventricular assist device and determine a first pressure signal of the left ventricular pressure of the patient's heart; A parameter calculation module, configured to calculate a target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure based on the rotational speed signal and the first pressure signal; A status monitoring module, configured to determine a target support status of the ventricular assist device based on a deviation between the target correlation value and a preset reference value, where the target support status is a full support status, a partial support status, or a non-support status.

[0009] In an embodiment of the present application, the above parameter calculation module includes: A signal acquisition sub-module, configured to acquire a second pressure signal of the aortic pressure of the patient's heart; A first parameter calculation sub-module, configured to calculate a target interference value characterizing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal based on the correlation degrees among the first pressure signal, the second pressure signal, and the rotational speed signal; A second parameter calculation sub-module, configured to calculate, based on the target interference value, a signal correlation degree between the rotational speed signal and the first pressure signal excluding the interference of the aortic pressure as a target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure.

[0010] In an embodiment of the present application, the above first parameter calculation sub-module includes: A first parameter calculation unit, configured to calculate a correlation degree between the current rotational speed and the aortic pressure based on a first auto-power spectrum and a first cross-power spectrum of the second pressure signal as a first interference value, where 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 a correlation degree between the left ventricular pressure and the aortic pressure based on the first auto-power spectrum and a second cross-power spectrum 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; A third parameter calculation unit, configured to calculate a correlation degree between the aortic pressure, the left ventricular pressure and the rotational speed based on the first auto-power spectrum, the first cross-power spectrum, and the second cross-power spectrum, as a third interference value; A target parameter calculation unit, configured to determine the first interference value, the second interference value, and the third interference value as target interference values characterizing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal.

[0011] In an embodiment of the present application, the above-mentioned second parameter calculation sub-module is specifically configured to calculate a first difference between the second auto-power spectrum of the rotational speed signal and the first interference value; calculate a second difference between the third auto-power spectrum of the first pressure signal and the second interference value; calculate a third difference between the third cross-power spectrum and the third interference value, where the third cross-power spectrum is the cross-power spectrum between the rotational speed signal and the first pressure signal; calculate 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; and calculate a target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure based on the partial coherence value.

[0012] In an embodiment of the present application, the above-mentioned 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 rotational speed signal using a preset fitting coefficient, where 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; 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.

[0013] In a third aspect, an embodiment of the present application provides an electronic medical device, including a processor, a communication interface, a memory, and a communication bus, where the processor, the communication interface, and the memory complete communication with each other through the communication bus; The memory is used to store a computer program; The processor is configured to implement the monitoring method performed by the monitoring device in the monitoring system of the ventricular assist device described in the first aspect when executing the program stored in the memory.

[0014] In a fourth aspect, an embodiment of the present application provides a computer-readable storage medium, in which a computer program is stored, and when the computer program is executed by a processor, the monitoring method performed by the monitoring device in the monitoring system of the ventricular assist device described in the first aspect is implemented.

[0015] As can be seen from the above, when applying the monitoring system provided in the embodiments of the present application, since the target correlation value characterizes the correlation degree between the current rotation speed and the left ventricular pressure, the current rotation speed reflects the real-time operation condition of the ventricular assist device, and the left ventricular pressure reflects the real-time physiological condition of the patient's heart. Also, as the ventricular assist device operates, the patient's heart is in a state of real-time change. That is to say, there is a correlation between the operation of the ventricular assist device and the change of the patient's heart. Therefore, by using the above-mentioned target correlation value, the real-time support state of the ventricular assist device for the patient's heart can be accurately determined to achieve real-time, continuous, and accurate monitoring of the current support state of the ventricular assist device.

[0016] Of course, when implementing any product or method of the present application, it is not necessarily required to simultaneously achieve all the above-mentioned advantages. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the following will briefly introduce the drawings required for use in the description of the embodiments or the prior art. Obviously, the following drawings are only some embodiments of the present application, and those of ordinary skill in the art can also obtain other embodiments based on these drawings.

[0018] Figure 1a It is a schematic structural diagram of a monitoring system for a ventricular assist device provided in an embodiment of the present application; Figure 1b It is a schematic structural diagram of a ventricular assist device provided in an embodiment of the present application; Figure 2 It is a schematic flowchart of a first monitoring method for a ventricular assist device provided in an embodiment of the present application; Figure 3 It is a schematic flowchart of a second monitoring method for a ventricular assist device provided in an embodiment of the present application; Figure 4 It is a schematic flowchart of a third monitoring method for a ventricular assist device provided in an embodiment of the present application; Figure 5 It is a schematic structural diagram of a first monitoring device for a ventricular assist device provided in an embodiment of the present application; Figure 6 It is a schematic structural diagram of a second monitoring device for a ventricular assist device provided in an embodiment of the present application; Figure 7 It is a schematic structural diagram of a third monitoring device for a ventricular assist device provided in an embodiment of the present application; Figure 8 It is a schematic structural diagram of an electronic medical device provided in an embodiment of the present application. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0019] Next, with reference to the accompanying drawings in the embodiments of the present application, the technical solutions in the embodiments of the present application will be described clearly and completely. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art based on the present application belong to the scope of protection of the present application.

[0020] Before introducing the embodiments of the present application, first, in combination with Figure 1a , the monitoring system of the ventricular assist device provided by the embodiments of the present application will be described.

[0021] The monitoring system of the ventricular assist device includes a monitoring device 11 and a ventricular assist device 12. Among them, the ventricular assist device 12 is implanted into the patient's heart through a percutaneous intervention method to assist the patient's heart in pumping blood; the monitoring device 11 is used to monitor the operating state of the ventricular assist device 12.

[0022] The ventricular assist device 12 operates dynamically inside the heart. Specifically, the support states of the ventricular assist device include three types: full support state, partial support state, and non-support state.

[0023] 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.

[0024] The support state of the ventricular assist device is dynamically changing. Real-time monitoring of the above support state can achieve more effective control of the ventricular assist device. Therefore, there is an urgent need for a monitoring solution for real-time monitoring of the support state of the ventricular assist device.

[0025] The above ventricular assist device may be a left ventricular assist device. Taking the left ventricular assist device as an example, the above ventricular assist device will be described. Refer to Figure 1b , Figure 1b which shows a schematic structural diagram of the left ventricular assist device.

[0026] Figure 1b The shown ventricular assist device is a left ventricular catheter pump, and the left ventricular catheter pump is used to cross 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 may also be a right ventricular catheter pump, a biventricular catheter pump, etc., and no limitation is made thereto.

[0027] The left ventricular catheter pump includes a motor 101, an impeller 102, a blood outlet 103, and a blood inlet 104. The high-speed rotation of the motor 101 drives 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 patient's left ventricle, and the blood outlet 103 is located in the patient's aorta, realizing the auxiliary pumping of the patient's heart.

[0028] The following describes the monitoring scheme implemented by the monitoring device.

[0029] See Figure 2 , Figure 2 which is a schematic flowchart of the first monitoring method provided by the embodiment of the present application. The above method includes the following steps S201-S203.

[0030] Step S201: Obtain the rotational speed signal of the current rotational speed of the ventricular assist device and determine the first pressure signal of the left ventricular pressure of the patient's heart.

[0031] The above rotational speed signal can be monitored by a rotational speed monitor.

[0032] The above first pressure signal can be monitored by a pressure sensor.

[0033] The above first pressure signal can also be calculated in real time. Based on this, in an embodiment of the present application, the current motor current signal of the ventricular assist device can be obtained; based on the current signal and the rotational speed signal, using a preset fitting coefficient, the pressure difference is estimated; based on the pressure difference and the pressure signal of the aortic pressure, the first pressure signal of the left ventricular pressure of the patient's heart is determined.

[0034] The above preset fitting coefficient is a coefficient obtained by fitting historical clinical data.

[0035] The above pressure difference is the pressure difference between the left ventricular pressure and the aortic pressure. One implementation of estimating the pressure difference: According to the fitting formula including the preset fitting coefficient, taking the current signal and the rotational speed signal as the variables of the above fitting formula, calculating the calculation result of the fitting formula as the pressure difference.

[0036] After estimating the pressure difference, the difference between the pressure signal of the aortic pressure and the pressure difference can be calculated as the first pressure signal.

[0037] Step S202: Based on the rotational speed signal and the first pressure signal, calculate the target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure.

[0038] The above target correlation value characterizes the correlation degree between the current rotational speed and the left ventricular pressure. When the target correlation value is high, it indicates a higher correlation degree; when the target correlation value is low, it indicates a lower correlation degree.

[0039] One implementation of calculating the target correlation value is as follows: using partial coherence analysis, perform correlation analysis on the rotational speed signal and the first pressure signal, and determine the calculated partial coherence value as the target correlation value.

[0040] For other implementations of calculating the target correlation value, reference can be made to the subsequent Figure 3 corresponding embodiments, which will not be elaborated here.

[0041] Step S203: Based on the deviation between the target correlation value and the preset reference value, determine the target support state of the ventricular assist device.

[0042] Wherein, the above target support state is a full support state, a partial support state or a non - support state. The specific meanings of each of the above states have been specifically described before this embodiment and will not be repeated here.

[0043] The above preset reference value can be a reference value corresponding to the full support state set in advance. In this case, the farther the target correlation value is from the preset reference value, the lower the possibility that the ventricular assist device is in the full support state; conversely, the higher. Based on this, one implementation of determining the target support state is: when the above deviation is less than the first preset threshold, it is determined as the full support state; when the above deviation is between the first preset threshold and the second preset threshold, it is determined as the partial support state; when the above deviation is greater than the second preset threshold, it is determined as the non - support state.

[0044] The above preset reference value can also be the reference values corresponding to each support state, such as the reference value corresponding to the full support state, the reference value corresponding to the partial support state, and the reference value corresponding to the non - support state. Based on this, one implementation of determining the target support state is: 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 partial coherence value is less than the third preset threshold, while the other two support states are greater than the third preset threshold, then the target support state is determined as the full support state.

[0045] As can be seen from the above, by applying the monitoring system provided in this embodiment, since the target correlation value represents the correlation degree between the current rotational speed and the left ventricular pressure, the current rotational speed reflects the real - time operation of the ventricular assist device, and the left ventricular pressure reflects the real - time physiological condition of the patient's heart, and also because as the ventricular assist device operates, the patient's heart is changing in real time, that is to say, there is an association relationship between the operation of the ventricular assist device and the change of the patient's heart. Therefore, using the above target correlation value, the real - time support state of the ventricular assist device for the patient's heart can be accurately determined to achieve real - time, continuous and accurate monitoring of the current support state of the ventricular assist device.

[0046] In the foregoing Figure 2In the corresponding embodiment step S202, the target correlation value can be calculated by the aforementioned method, or can be implemented by the following steps S302-S304. Figure 3 , Figure 3 The flowchart of the second monitoring method provided in the embodiment of the present application includes the following steps S301-S305.

[0047] Step S301: Acquire a speed signal of the current speed of the ventricular assist device, and determine a first pressure signal of the left ventricular pressure of the patient's heart.

[0048] The above step S301 is the same as the above step S201 and will not be described again.

[0049] Step S302: Acquire a second pressure signal of the aortic pressure of the patient's heart.

[0050] 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.

[0051] Step S303: 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 is calculated.

[0052] The target interference value indicates the interference value of the aortic pressure affecting the correlation between the rotation speed signal and the first pressure signal.

[0053] Through reasoning, simulation and verification from a large amount of clinical data, it is found that 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 are interactive, and this 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 above three types of signals can be used to accurately calculate the interference information corresponding to the above aortic pressure.

[0054] One implementation method for calculating the target interference value is: inputting the rotation speed signal, the first pressure signal and the second pressure signal into a pre-trained interference prediction model to obtain the interference value output by the interference prediction model as the target interference value.

[0055] The above-mentioned interference prediction model is: a large number of sample speed signals, sample left ventricular pressure signals, and sample aortic pressure signals are used as training samples in advance, and the actual interference value is used as the training benchmark to train the initial neural network model to obtain a model for predicting the interference value caused by aortic pressure.

[0056] Since the interference prediction model has learned the characteristic relationship between the rotational speed signal, the left ventricular pressure signal, the aortic pressure signal, and the interference value using a large number of training samples, the target interference value can be accurately predicted using the above interference prediction model.

[0057] Other implementation manners for calculating the target interference value can be referred to the subsequent Figure 4 corresponding embodiments, which will not be elaborated herein.

[0058] Step S304: Based on the target interference value, calculate the signal correlation between the rotational speed signal and the first pressure signal excluding the aortic pressure interference, and use it as the target correlation value representing the correlation degree between the current rotational speed and the left ventricular pressure.

[0059] Since the calculated signal correlation excludes the interference of the aortic pressure on the rotational speed signal and the first pressure signal, the signal correlation between the two types of signals excluding the above interference is closer to the actual correlation, thereby improving the accuracy of the target correlation value.

[0060] One implementation manner for calculating the target correlation value is: calculate the initial correlation between the rotational speed signal and the first pressure signal, calculate the difference between the initial correlation and the target interference value, and determine the calculated difference as the target correlation value.

[0061] Other implementation manners for calculating the target correlation value can be referred to the subsequent Figure 4 corresponding embodiments, which will not be elaborated herein.

[0062] Step S305: Based on the deviation between the target correlation value and the preset reference value, determine the target support state of the ventricular assist device.

[0063] Wherein, the above target support state is a full support state, a partial support state, or a non-support state.

[0064] The above step S305 is the same as the foregoing step S203, and will not be elaborated herein.

[0065] As can be seen from the above, in this embodiment, since the calculated signal correlation excludes the interference of the aortic pressure, the calculated signal correlation is closer to the actual correlation, improving the accuracy of the target correlation value and further improving the monitoring accuracy of the support state of the ventricular assist device.

[0066] In the foregoing Figure 3 corresponding embodiment of step S303, in addition to the method mentioned above for determining the target interference value, it can also be implemented according to the following steps S403 - S406. Based on this, refer to Figure 4 , Figure 4 which is the flowchart of the third monitoring method provided by the embodiments of the present application.

[0067] Step S401: Obtain the rotational speed signal of the current rotational speed of the ventricular assist device, and determine the first pressure signal of the left ventricular pressure of the patient's heart.

[0068] Step S402: Obtain the second pressure signal of the aortic pressure of the patient's heart.

[0069] The above steps S401 - S402 are the same as the foregoing steps S301 - S302, and will not be elaborated here.

[0070] Step S403: Calculate the correlation between the current rotational speed and the aortic pressure based on the first auto - power spectrum and the first cross - power spectrum of the second pressure signal, and use it as the first interference value.

[0071] Wherein, the above - mentioned first cross - power spectrum is the cross - power spectrum between the rotational speed signal and the second pressure signal.

[0072] One implementation of calculating the first interference value is: calculate the square of the absolute value of the first cross - power spectrum as the numerator, use the first auto - power spectrum as the denominator, and calculate the ratio between the above - mentioned numerator and denominator as the first interference value.

[0073] Step S404: Calculate the correlation between the left ventricular pressure and the aortic pressure based on the first auto - power spectrum and the second cross - power spectrum, and use it as the second interference value.

[0074] Wherein, the above - mentioned second cross - power spectrum is the cross - power spectrum between the first pressure signal and the second pressure signal.

[0075] One implementation of calculating the second interference value is: calculate the square of the absolute value of the second cross - power spectrum as the numerator, use the first auto - power spectrum as the denominator, and calculate the ratio between the above - mentioned numerator and denominator as the second interference value.

[0076] Step S405: Calculate the correlation between the aortic pressure, the left ventricular pressure and the rotational speed based on the first auto - power spectrum, the first cross - power spectrum and the second cross - power spectrum, and use it as the third interference value.

[0077] One implementation of calculating the third interference value is: calculate the square of the absolute value of the product of the first cross - power spectrum and the second cross - power spectrum as the numerator, use the first auto - power spectrum as the denominator, and calculate the ratio between the above - mentioned numerator and denominator as the third interference value.

[0078] Step S406: Determine the first interference value, the second interference value and the third interference value as the target interference values characterizing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal.

[0079] The target interference values include the first interference value, the second interference value and the third interference value.

[0080] Step S407: Based on the target interference value, calculate the signal correlation between the rotational speed signal and the first pressure signal after excluding the aortic pressure interference, and use it as the target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure.

[0081] When the target interference value includes the first interference value, the second interference value, and the third interference value, one implementation of calculating the target correlation value is as follows: Calculate the first difference between the second auto-power spectrum of the rotational speed signal and the first interference value; calculate the second difference between the third auto-power 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; based on the first difference, the second difference, and the third difference, calculate the partial coherence value between the rotational speed signal and the first pressure signal, and based on the partial coherence value, calculate the target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure.

[0082] The above-mentioned third cross-power spectrum is the cross-power spectrum between the rotational speed signal and the first pressure signal.

[0083] One implementation of calculating the partial coherence value is as follows: Calculate the square of the absolute value of the third difference as the numerator, calculate the product between the first difference and the second difference as the denominator, and calculate the ratio between the above numerator and denominator to obtain the partial coherence value.

[0084] After calculating the partial coherence value, the mean value of the partial coherence value in the preset frequency band can be calculated, and the calculated mean value is used as the target correlation value.

[0085] Step S408: Based on the deviation between the target correlation value and the preset reference value, determine the target support state of the ventricular assist device.

[0086] Wherein, the above-mentioned target support state is the full support state, the partial support state, or the non-support state.

[0087] As can be seen from the above, taking the first interference value, the second interference value, and the third interference value as the target interference values, and the first interference value reflects the interference degree of the aortic pressure on the rotational 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 rotational speed and the left ventricular pressure. It can be seen that the above three types of interference values comprehensively cover various interference situations of the aortic pressure, thereby improving the accuracy of the target interference value and further improving the monitoring accuracy of the ventricular assist device.

[0088] Corresponding to the above monitoring system of the ventricular assist device, an embodiment of the present application further provides a monitoring device for the ventricular assist device.

[0089] See Figure 5 , Figure 5The structural schematic diagram of the first monitoring device provided by the embodiment of the present application, the device is applied to the monitoring system of the ventricular assist device, the monitoring system of the ventricular assist device further includes a ventricular assist device, the ventricular assist device is implanted into the patient's heart through a percutaneous intervention method to assist the patient's heart in pumping blood, and the device includes: A signal determination module 501, configured to obtain a rotational speed signal of the current rotational speed of the ventricular assist device and determine a first pressure signal of the left ventricular pressure of the patient's heart; A parameter calculation module 502, configured to calculate a target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure based on the rotational speed signal and the first pressure signal; A state monitoring module 503, configured to determine the 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.

[0090] As can be seen from the above, by applying the monitoring system provided in this embodiment, since the target correlation value characterizes the correlation degree between the current rotational speed and the left ventricular pressure, the current rotational speed reflects the real-time operation condition of the ventricular assist device, and the left ventricular pressure reflects the real-time physiological condition of the patient's heart. Also, as the ventricular assist device operates, the patient's heart is changing in real time, that is to say, there is a correlation relationship between the operation 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 for the patient's heart can be accurately determined to realize real-time continuous and accurate monitoring of the current support state of the ventricular assist device.

[0091] See Figure 6 , Figure 6 The structural schematic diagram of the second monitoring device provided by the embodiment of the present application, the above device includes: A signal determination module 601, configured to obtain a rotational speed signal of the current rotational speed of the ventricular assist device and determine a first pressure signal of the left ventricular pressure of the patient's heart; A signal acquisition sub-module 602, configured to obtain a second pressure signal of the aortic pressure of the patient's heart; A first parameter calculation sub-module 603, configured to calculate a target interference value characterizing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal based on the correlation degrees among the first pressure signal, the second pressure signal and the rotational speed signal; A second parameter calculation sub-module 604, configured to calculate the signal correlation degree between the rotational speed signal and the first pressure signal excluding the aortic pressure interference based on the target interference value as the target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure.

[0092] A status monitoring module 605 is configured to determine a target support status of the ventricular assist device based on a deviation between the target correlation value and a preset reference value, where the target support status is a full support status, a partial support status, or a non-support status.

[0093] As can be seen from the above, in this embodiment, since the calculated signal correlation excludes the interference of the aortic pressure, the calculated signal correlation is closer to the actual correlation, improving the accuracy of the target correlation value and further improving the monitoring accuracy of the support status of the ventricular assist device.

[0094] See Figure 7 , Figure 7 FIG. is a schematic structural diagram of a monitoring device for a third ventricular assist device provided by an embodiment of the present application. The above device includes: A signal determination module 701 is configured to obtain a rotational speed signal of the current rotational speed of the ventricular assist device and determine a first pressure signal of the left ventricular pressure of the patient's heart; A signal acquisition sub-module 702 is configured to obtain a second pressure signal of the aortic pressure of the patient's heart; A first parameter calculation unit 703 is configured to calculate a correlation between the current rotational speed and the aortic pressure based on a first auto-power spectrum and a first cross-power spectrum of the second pressure signal as a first interference value, where 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 704 is configured to calculate a correlation between the left ventricular pressure and the aortic pressure based on the first auto-power spectrum and a second cross-power spectrum 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; A third parameter calculation unit 705 is configured to calculate a correlation between the aortic pressure, the left ventricular pressure, and the rotational speed based on the first auto-power spectrum, the first cross-power spectrum, and the second cross-power spectrum as a third interference value; A 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 characterizing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal.

[0095] A second parameter calculation sub-module 707 is configured to calculate a signal correlation between the rotational speed signal and the first pressure signal excluding the interference of the aortic pressure based on the target interference value as a target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure.

[0096] A status monitoring module 708 is configured to determine a target support status of the ventricular assist device based on a deviation between the target correlation value and a preset reference value, where the target support status is a full support status, a partial support status, or a non-support status.

[0097] As can be seen from the above, taking the first interference value, the second interference value, and the third interference value as the target interference values, where the first interference value reflects the interference degree of the aortic pressure on the rotational 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 rotational speed and the left ventricular pressure. It can be seen that the above three types of interference values comprehensively cover various interference situations of the aortic pressure, thereby improving the accuracy of the target interference value and further improving the accuracy of the monitoring of the ventricular assist device.

[0098] In one embodiment of the present application, the second parameter calculation sub-module is specifically configured to calculate a first difference between the second auto-power spectrum of the rotational speed signal and the first interference value; calculate a second difference between the third auto-power spectrum of the first pressure signal and the second interference value; calculate a third difference between the third cross-power spectrum and the third interference value, where the third cross-power spectrum is the cross-power spectrum between the rotational speed signal and the first pressure signal; calculate the 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; calculate the target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure based on the partial coherence value.

[0099] In one embodiment of the present application, the signal determination module is specifically configured to obtain the current motor current signal of the ventricular assist device; estimate the pressure difference based on the current signal and the rotational speed signal using a preset fitting coefficient, where 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; determine the first pressure signal of the left ventricular pressure of the patient's heart based on the pressure difference and the second pressure signal of the aortic pressure.

[0100] Corresponding to the above monitoring system of the ventricular assist device, an embodiment of the present application provides an electronic medical device. Refer to Figure 8 , Figure 8 is a schematic structural diagram of an electronic medical device provided by an embodiment of the present application. The above electronic medical device includes a processor 801, a communication interface 802, a memory 803, and a communication bus 804. Among them, the processor 801, the communication interface 802, and the memory 803 communicate with each other through the communication bus 804; The memory 803 is used to store a computer program; When the processor 801 is configured to execute the program stored on the memory 803, it implements the steps of the foregoing monitoring method of the ventricular assist device.

[0101] The communication bus mentioned in the above controller can be a Peripheral Component Interconnect (PCI) bus, an Extended Industry Standard Architecture (EISA) bus, etc. This communication bus can be divided into an address bus, a data bus, a control bus, etc. For the sake of convenience in representation, only a thick line is used in the figure, but it does not mean that there is only one bus or one type of bus.

[0102] The communication interface is used for communication between the above controller and other devices.

[0103] The memory can include a Random Access Memory (RAM), or 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 far from the aforementioned processor.

[0104] 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.

[0105] In another embodiment provided by the present application, there is also provided a computer-readable storage medium, in which a computer program is stored, and when the computer program is executed by a processor, the monitoring method steps of the foregoing ventricular assist device are implemented.

[0106] In another embodiment provided by the present application, there is also provided a computer program product containing instructions, which when running on a computer, causes the computer to implement the monitoring method steps of the foregoing ventricular assist device when executed.

[0107] 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 processes or functions described in the embodiments of the present application are generated in whole or in part. The computer can be a general-purpose computer, a special-purpose computer, a computer network, or other programmable devices. The computer instructions can be stored in a computer-readable storage medium, or transmitted from one computer-readable storage medium to another. For example, the computer instructions can be transmitted from one website, computer, server, or data center to another website, computer, server, or data center by wire (such as coaxial cable, optical fiber, digital subscriber line (DSL)) or wireless (such as infrared, wireless, microwave, etc.). The computer-readable storage medium can be any available medium that can be accessed by a computer or a data storage device such as a server or a data center that includes one or more integrated available media. The available medium can be a magnetic medium (such as a floppy disk, a hard disk, a magnetic tape), an optical medium (such as a DVD), or a semiconductor medium (such as a solid state disk (SSD)).

[0108] It should be noted that, in this document, relational terms such as first and second are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any actual relationship or order between these entities or operations. Moreover, the term "comprising", "including" or any other variation thereof is intended to cover non-exclusive inclusion, so that a process, method, article or device comprising a series of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such process, method, article or device. Without further limitation, an element defined by the statement "comprising one..." does not exclude the presence of additional identical elements in the process, method, article or device comprising the element.

[0109] Each embodiment in this specification is described in a related manner. The same or similar parts among the embodiments can be referred to each other, and the differences between each embodiment and other embodiments are emphasized. 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 description of the method embodiments.

[0110] The above are only the preferred embodiments of the present application and are not intended to limit the protection scope of the present application. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principle of the present application are all included in the protection scope of the present 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 into the patient's heart through a percutaneous intervention method to assist the patient's heart in pumping blood. The monitoring device is used to monitor the support status of the ventricular assist device, and the monitoring device performs the following monitoring method: Obtain a rotational speed signal of the current rotational speed of the ventricular assist device and determine a first pressure signal of the left ventricular pressure of the patient's heart; Based on the rotational speed signal and the first pressure signal, calculate a target correlation value representing the degree of correlation between the current rotational speed and the left ventricular pressure; Based on the deviation between the target correlation value and a preset reference value, determine the target support status of the ventricular assist device, where the target support status is a full support status, a partial support status, or a non-support status.

2. The system according to claim 1, wherein The calculating, based on the rotational speed signal and the first pressure signal, a target correlation value representing the degree of correlation between the current rotational speed and the left ventricular pressure includes: Obtain a second pressure signal of the aortic pressure of the patient's heart; Based on the correlation degrees among the first pressure signal, the second pressure signal, and the rotational speed signal, calculate a target interference value representing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal; Based on the target interference value, calculate the signal correlation degree between the rotational 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 rotational speed and the left ventricular pressure.

3. The system according to claim 2, wherein The calculating, based on the correlation degrees among the first pressure signal, the second pressure signal, and the rotational speed signal, a target interference value representing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal includes: Based on the first auto-power spectrum and the first cross-power spectrum of the second pressure signal, calculate the correlation degree between the current rotational speed and the aortic pressure as a first interference value, where the first cross-power spectrum is the cross-power spectrum between the rotational speed signal and the second pressure signal; Based on the first auto-power spectrum and the second cross-power spectrum, calculate the correlation degree between the left ventricular pressure and the aortic pressure as a second interference value, where the second cross-power spectrum is the cross-power spectrum between the first pressure signal and the second pressure signal; Based on the first auto-power spectrum, the first cross-power spectrum, and the second cross-power spectrum, calculate the correlation degree among the aortic pressure, the left ventricular pressure, and the rotational speed as a third interference value; Determine the first interference value, the second interference value, and the third interference value as the target interference value representing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal.

4. The system according to claim 3, characterized in that The calculating, based on the target interference value, the signal correlation degree between the rotational 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 rotational speed and the left ventricular pressure includes: Calculate a first difference between the second auto-power spectrum of the rotational speed signal and the first interference value; Calculate a second difference between the third auto-power spectrum of the first pressure signal and the second interference value; Calculate a third difference between the third cross-power spectrum and the third interference value, where the third cross-power spectrum is the cross-power spectrum between the rotational speed signal and the first pressure signal; Calculate the 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; Calculate a target correlation value representing the correlation degree between the current rotational speed and the left ventricular pressure based on the partial coherence value.

5. The system according to any one of claims 1-4, characterized in that, The first pressure signal for determining the left ventricular pressure of the patient's heart includes: Obtain a current signal of the current motor current of the ventricular assist device; Based on the current signal and the rotational speed signal, use a preset fitting coefficient to estimate the pressure difference, where 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; Based on the pressure difference and the second pressure signal of the aortic pressure, determine the first pressure signal of the left ventricular pressure of the patient's heart.

6. A monitoring device for a ventricular assist device, characterized in that, The device is applied to a monitoring system of a ventricular assist device, and the monitoring system of the ventricular assist device further includes a ventricular assist device. The ventricular assist device is implanted into the patient's heart through a percutaneous intervention method to assist the patient's heart in pumping blood. The device includes: A signal determination module, configured to obtain a rotational speed signal of the current rotational speed of the ventricular assist device and determine a first pressure signal of the left ventricular pressure of the patient's heart; A parameter calculation module, configured to calculate a target correlation value representing the correlation degree between the current rotational speed and the left ventricular pressure based on the rotational speed signal and the first pressure signal; 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, where the target support state is a full support state, a partial support state, or a non-support state.

7. The device according to claim 6, characterized in that, The parameter calculation module includes: A signal acquisition sub-module, configured to obtain a second pressure signal of the aortic pressure of the patient's heart; A first parameter calculation sub-module, configured to calculate a target interference value representing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal based on the correlation degrees among the first pressure signal, the second pressure signal, and the rotational speed signal; A second parameter calculation sub-module, configured to calculate the signal correlation degree between the rotational 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 rotational speed and the left ventricular pressure based on the target interference value.

8. The device according to claim 7, characterized in that, The first parameter calculation sub-module includes: A first parameter calculation unit, configured to calculate the correlation degree between the current rotational speed and the aortic pressure as a first interference value based on the first auto-power spectrum and the first cross-power spectrum of the second pressure signal, where the first cross-power spectrum is the cross-power spectrum between the rotational speed signal and the second pressure signal; A second parameter calculation unit, configured to calculate the correlation degree between the left ventricular pressure and the aortic pressure as a second interference value based on the first auto-power spectrum and the second cross-power spectrum, where the second cross-power spectrum is the cross-power spectrum between the first pressure signal and the second pressure signal; A third parameter calculation unit, configured to calculate the correlation degree among the aortic pressure, the left ventricular pressure, and the rotational speed as a third interference value based on the first auto-power spectrum, the first cross-power spectrum, and the second cross-power spectrum; A target parameter calculation unit for determining the first interference value, the second interference value, and the third interference value as target interference values characterizing the interference of the aortic pressure on the correlation between the rotational speed signal and the first pressure signal.

9. The device according to claim 8, wherein The second parameter calculation sub-module is specifically configured to calculate a first difference between the second auto-power spectrum of the rotational speed signal and the first interference value; calculate a second difference between the third auto-power spectrum of the first pressure signal and the second interference value; calculate a third difference between the third cross-power spectrum and the third interference value, where the third cross-power spectrum is the cross-power spectrum between the rotational speed signal and the first pressure signal; calculate the 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; calculate a target correlation value characterizing the correlation degree between the current rotational speed and the left ventricular pressure based on the partial coherence value.

10. The device according to any one of claims 6-9, characterized in that The signal determination module is specifically configured to obtain the current motor current signal of the ventricular assist device; estimate the pressure difference based on the current signal and the rotational speed signal using a preset fitting coefficient, where 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; determine the first pressure signal of the left ventricular pressure of the patient's heart based on the pressure difference and the second pressure signal of the aortic pressure.

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