Cardiac suction recognition apparatus and recognition method, and ventricular assist system

Abstract

The present invention relates to a cardiac suction recognition apparatus and recognition method, and a ventricular assist system. The apparatus comprises a sampling module, used for sampling operation data of a ventricular assist device within a preset sampling duration to obtain sampled data; a data conversion module, used for performing data conversion on the sampled data to obtain frequency domain data; a calculation module, used for determining a first amplitude in the frequency domain data, the first amplitude corresponding to a maximum amplitude within a preset interval of the frequency domain data; and a judgment module, used for generating a cardiac suction judgment result according to whether the first amplitude is greater than a preset threshold value. According to the present invention, the state of the heart can be monitored in real time only by means of the operation condition of the device, while the presence of suction phenomena can be promptly judged.

Description

Cardiac pumping identification device, identification method and ventricular assist system Technical Field

[0001] The present invention relates to medical equipment for cardiac surgery and a control method, and in particular to a cardiac pumping identification device, an identification method and a ventricular assist system. Background Art

[0002] A percutaneous ventricular assist device (pVAD) is a small blood pump that is inserted percutaneously into the ventricle. The blood pump drains blood into the arterial system, partially or completely replacing the heart's pumping function and maintaining blood circulation in the human body.

[0003] pVAD devices can be used in clinical scenarios such as acute myocardial infarction treatment, high-risk PCI surgery protection, and short-term postoperative cardiac support, helping to improve the rescue survival rate of related indications.

[0004] If the pVAD device provides too much blood during operation, it can cause all the blood in the heart to be pumped into the aorta, leading to cardiac aspiration. Prolonged cardiac aspiration can be life-threatening. During pVAD operation, existing technology and equipment often cannot determine whether the heart is aspirating simply by looking at the device's operating status, while medical methods such as ultrasound cannot confirm aspiration within a short period of time.

[0005] Based on the above reasons, how to determine whether the patient has cardiac aspiration based on the operation of the pVAD device has become a technical problem that urgently needs to be solved.

[0006] Summary of the Invention

[0007] In view of this, embodiments of the present invention provide a cardiac aspiration recognition device, a recognition method, a ventricular assist system, an electronic device, and a readable medium to solve the problems existing in the prior art.

[0008] The present invention adopts the following technical solutions:

[0009] In a first aspect, an embodiment of the present invention provides a cardiac aspiration recognition device, comprising:

[0010] A sampling module is used to sample the operating data of the ventricular assist device within a preset sampling time to obtain sampling data;

[0011] A data conversion module, configured to perform data conversion on the sampled data to obtain frequency domain data;

[0012] a calculation module, configured to determine a first amplitude in the frequency domain data, where the first amplitude corresponds to a maximum amplitude within a preset interval of the frequency domain data;

[0013] The judgment module is configured to generate a cardiac aspiration judgment result according to whether the first amplitude is greater than a preset threshold.

[0014] In a second aspect, an embodiment of the present invention provides a cardiac aspiration recognition method, comprising:

[0015] Sampling the operating data of the ventricular assist device within a preset sampling time to obtain sampling data;

[0016] Performing data conversion on the sampled data to obtain frequency domain data;

[0017] Determining a first amplitude in the frequency domain data, where the first amplitude corresponds to a maximum amplitude within a preset interval of the frequency domain data;

[0018] A cardiac aspiration determination result is generated according to whether the first amplitude is greater than a preset threshold.

[0019] In a third aspect, an embodiment of the present invention provides a ventricular assist system, comprising a drive motor and a cardiac aspiration recognition device as described in any one of the above items, wherein the cardiac aspiration recognition device comprises a sampling module, a data conversion module, a calculation module, and a judgment module;

[0020] The sampling module is used to sample the operating data of the driving motor within a preset sampling time to obtain sampling data;

[0021] The data conversion module is used to perform data conversion on the sampled data to obtain frequency domain data;

[0022] The calculation module is used to determine a first amplitude in the frequency domain data, where the first amplitude corresponds to a maximum amplitude within a preset interval of the frequency domain data;

[0023] The judgment module is used to generate a cardiac aspiration judgment result according to whether the first amplitude is greater than a preset threshold.

[0024] In a fourth aspect, an embodiment of the present invention provides an electronic device, including:

[0025] one or more processors;

[0026] a memory for storing one or more programs;

[0027] When the one or more programs are executed by the one or more processors, the one or more processors implement the cardiac aspiration recognition method as described above.

[0028] In a fifth aspect, an embodiment of the present invention provides a readable storage medium, on which a ventricular assist system control program is stored. When the control program is executed by a processor, the cardiac aspiration recognition method as described above can be implemented.

[0029] One embodiment of the above invention has the following advantages or beneficial effects:

[0030] The present invention mainly provides a cardiac pumping recognition device, which can record the operating data of the ventricular assist device and sample the operating data of the ventricular assist device based on preset rules. The sampled time domain information can be subjected to fast Fourier transform to obtain the frequency domain information of the driving motor of the ventricular assist device during operation. The maximum amplitude and the corresponding characteristic frequency can be determined from the results of the frequency domain information. By judging whether the characteristic frequency deviates from the normal heart rate, it can be determined whether the patient's heart rate is within the normal heart rate range. If it is not within the normal range, it will be directly judged as an abnormal detection situation, and the speed will be directly reduced to the lowest gear, and an alarm will be issued to remind the doctor to detect the patient's physical condition. In addition, the device can also preset the frequency domain signal A first amplitude is calculated within the area, and the first amplitude is the maximum amplitude within the preset interval. A cardiac aspiration judgment result is generated based on whether the first amplitude is greater than a preset threshold and the comparison result. Furthermore, the device can also send a speed reduction instruction to the ventricular assist device when the cardiac aspiration judgment result indicates that aspiration has occurred, and at the same time send an execution instruction for repeating the operation to repeatedly execute the above steps until the judgment result indicates that there is no aspiration phenomenon. When the cardiac aspiration judgment result indicates that no aspiration has occurred, the execution instruction for repeating the operation is sent to repeatedly execute the above steps. When the speed of the drive motor of the ventricular assist device drops to a critical value and the cardiac aspiration judgment result indicates that aspiration has occurred, a speed reduction instruction is sent to the ventricular assist device.

[0031] Compared with the existing technology, the technical solution of the present invention does not require the use of other medical means such as ultrasound to determine whether the heart is experiencing aspiration. It can monitor the state of the heart in real time simply through the operation of the equipment, and promptly determine whether aspiration is occurring, providing a reference basis for doctors so that they can take timely treatment measures.

[0032] The further effects of the above-mentioned non-conventional optional manner will be described below in conjunction with specific embodiments. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for describing the embodiments, which constitute a part of the present invention. The exemplary embodiments of the present invention and their descriptions are provided to explain the present invention and do not constitute an undue limitation of the present invention. In the drawings:

[0034] FIG1 is a block diagram of a cardiac aspiration recognition device according to an embodiment of the present invention;

[0035] FIG2 is a diagram of original operating data of a ventricular assist device under normal conditions provided by one embodiment of the present invention;

[0036] FIG3 is a diagram of original operating data of a ventricular assist device under suction provided by one embodiment of the present invention;

[0037] FIG4 is a spectrum diagram of FIG2 after FFT;

[0038] FIG5 is a spectrum diagram of FIG3 after FFT;

[0039] FIG6 is a flow chart of a cardiac aspiration recognition method provided by one embodiment of the present invention;

[0040] FIG7 is a structural block diagram of an electronic device provided by one embodiment of the present invention;

[0041] FIG8 is a diagram of original operating data of a ventricular assist device provided by one embodiment of the present invention;

[0042] Figure 9 is an enlarged view of point A in Figure 8;

[0043] Figure 10 is an enlarged view of point B in Figure 8;

[0044] FIG11 is an enlarged view of point C in FIG8 ;

[0045] FIG12 is a flow chart of a cardiac aspiration recognition method provided by one embodiment of the present invention. DETAILED DESCRIPTION

[0046] The following description of exemplary embodiments of the present invention is made in conjunction with the accompanying drawings, in which various details of the embodiments of the present invention are included to facilitate understanding. These details should be considered as merely exemplary. Therefore, it should be appreciated by those skilled in the art that various changes and modifications may be made to the embodiments described herein without departing from the scope and spirit of the present invention. Similarly, for the sake of clarity and conciseness, descriptions of well-known functions and structures are omitted in the following description.

[0047] A percutaneous ventricular assist device (pVAD) (hereinafter referred to as a VAD) is a crucial instrument in the transitional phase of treatment and transplantation for patients with severe heart failure. In a preferred embodiment, the VAD can be a catheter pump, which is percutaneously inserted into the ventricle to increase blood flow, enhance blood perfusion, and reduce myocardial oxygen consumption, thereby helping acute heart failure patients improve their cardiac pumping function in the short term. However, when the VAD is in too high a gear, the amount of blood it provides is too high, which can easily cause aspiration and ventricular collapse. Prolonged aspiration can be life-threatening to the patient. However, existing VADs cannot promptly detect whether aspiration is occurring within the heart, nor can they downshift to improve aspiration.

[0048] In view of the above-mentioned deficiencies, an embodiment of the present invention provides a cardiac aspiration recognition device, as shown in FIG1 . The cardiac aspiration recognition device 100 includes a sampling module 120, a data conversion module 130, a calculation module 140, and a judgment module 150. The cardiac aspiration recognition device 100 is applied to a ventricular assist device, and can record its operating status, determine whether the heart has aspiration according to the operating status, and intervene in time when aspiration occurs. By feedback-adjusting the gear position of the ventricular assist device, the cardiac aspiration phenomenon can be improved.

[0049] In one embodiment of the present invention, the data sampled by the sampling module 120 is derived from operating data of a ventricular assist device, and the operating data includes speed data and / or current data of a driving motor in the ventricular assist device.

[0050] In one embodiment of the present invention, a pre-processing module 110 is further included. The pre-processing module 110 is capable of eliminating interference data in the operating data and / or sampling data. The interference data includes DC components in the operating data and abnormal data points that seriously deviate from normal values, etc., so as to remove the DC components and abnormal data in the waveform, eliminate the DC offset, and retain only the AC component, so that the recorded amplitude range is adjusted to the center position, thereby more clearly observing and calculating the working status and periodic characteristics of the drive motor. The data finally obtained is regarded as the operating data of the drive motor.

[0051] In one embodiment of the present invention, the operating data of the driving motor of the ventricular assist device can be measured by a speed sensor and then sent to the preprocessing module 110, or the speed can be calculated by measuring the magnitude of the power supply voltage and / or current of the driving motor and its changing frequency and sent to the preprocessing module 110, or the driving signal of the driving motor can be sampled by a feedback control system, controller, etc. and sent to the preprocessing module 110.

[0052] 2 and 3 , there are shown original operation data diagrams of the ventricular assist device under normal conditions and original operation data diagrams of the ventricular assist device under suction conditions, respectively.

[0053] In one embodiment of the present invention, the sampling module 120 is configured to sample the operating data of the ventricular assist device within a preset sampling time period to obtain sampled data.

[0054] In one embodiment of the present invention, the sampling module 120 can continuously sample k points at a preset frequency within a preset sampling time, where the preset frequency is 5Hz to 50Hz, and k is an integer power of 2, such as 256, 512, 1024, 2048, 4096, etc.

[0055] Those skilled in the art know that the operating cycle of the drive motor is positively correlated with the cycle of the heart rhythm (pumping period and congestion period). The normal heart rate of a person is 55 to 120 beats / minute. Taking 60 beats / minute as an example, the corresponding frequency is 1Hz. Taking 100 beats / minute as an example, the corresponding frequency is 1.67Hz. In order to ensure the accuracy of the sampling results, the preset frequency is adjusted to at least twice the frequency corresponding to the heart rate. The larger the sampling frequency, the more accurate the final calculation result. Therefore, the sampling preset frequency is set to 5Hz to 50Hz.

[0056] In one embodiment of the present invention, k is taken as an integer power of 2 in order to enable efficient calculation when performing a fast Fourier transform (FFT). FFT can convert a time domain signal into a frequency domain signal, thereby facilitating spectrum analysis and detecting cardiac pumping conditions.

[0057] If the heart is pumping, a fluctuation in the maximum cardiac flow rate is likely to occur every certain number of heartbeats, and the preset sampling duration is determined based on this relationship. For example, if the maximum cardiac flow rate fluctuation occurs every 5 to 10 heartbeats, the preset sampling duration should at least cover this time interval. In one embodiment of the present invention, the preset sampling duration is k / f, a<k / f<b, where a and b are both empirical constants determined by the aforementioned relationship. Preferably, a has a value range of 5 to 20, and b has a value range of 20 to 60, more preferably, a=20, b=30. If the lower limit a is too small, pumping may not be detected; if the upper limit b is too high, the detection time interval may be too long, and pumping may not be detected in time. If pumping occurs for a long time, it will have a negative impact on the human body.

[0058] In one embodiment of the present invention, the data conversion module 130 is used to perform data conversion on the sampled data to obtain frequency domain data.

[0059] In one embodiment of the present invention, data conversion includes performing a fast Fourier transform (FFT) on the sampled time domain data to obtain frequency domain data. In the obtained spectrum, the vertical axis is amplitude and the horizontal axis is frequency.

[0060] In an embodiment of the present invention, the calculation module 140 is configured to calculate a first amplitude in the frequency-domain data, and the first amplitude corresponds to the maximum value of the amplitudes within a preset interval of the frequency-domain data.

[0061] In an embodiment of the present invention, the calculation module 140 is capable of determining the maximum amplitude and the corresponding characteristic frequency in the frequency-domain data, and determining a preset interval.

[0062] Specifically, in the entire spectrogram, the position where the maximum amplitude A0 appears is the characteristic frequency f0, and f0 corresponds to the heart rate of the patient. Based on the value of f0, a preset interval can be determined. The preset interval is a certain frequency interval before f0, and the amplitudes within this interval have local maximum values, which are positioned as the first amplitude.

[0063] In an embodiment of the present invention, the preset interval is 0 to n*f0, where n is an empirical constant. Preferably, 0.25 < n < 0.75. Due to the fluctuations of the heart rate and measurement errors, one or more small peaks may appear on both sides of the characteristic frequency f0 corresponding to the maximum amplitude A0. Therefore, the upper limit in this value range is used to reduce the influence of heart rate fluctuations on the data, and the lower limit of the value range is used to confirm the situation of the cardiac suction waveform.

[0064] Referring to FIGS. 4 and 5, the unit of the abscissa in both figures is times / minute. The regions marked by the two boxes are the maximum amplitudes in the normal state and the suction state of the heart respectively, and the region marked by the circular frame in FIG. 5 is the first amplitude in the cardiac suction state.

[0065] In an embodiment of the present invention, the judgment module 150 is configured to judge whether the characteristic frequency f0 deviates from the normal heart rate and generate a judgment result.

[0066] Specifically, if the characteristic frequency f0 is not within the normal heart rate range (55 to 120 beats / minute), it will be judged as an abnormal detection situation.

[0067] In an embodiment of the present invention, the judgment module 150 is configured to determine a preset threshold, and the preset threshold is determined based on the maximum amplitude A0; a cardiac suction judgment result is generated by judging whether the first amplitude is greater than the preset threshold.

[0068] In an embodiment of the present invention, the preset threshold is m*A0, where m is an empirical constant. Preferably, 0.05 < m < 0.25. The upper limit of 0.25 depends on the empirical data of the suction situation, and the lower limit of 0.05 depends on the 5% threshold confirmation of the error in digital signal processing.

[0069] In one embodiment of the present invention, a control module 160 is further included. If the first amplitude is greater than a preset threshold, the judgment module 150 determines that the heart has pumped, generates a judgment result indicating that the heart has pumped, and sends the judgment result to the control module 160. If the first amplitude is less than the preset threshold, it is determined that the heart has not pumped, and a judgment result indicating that the heart has not pumped is generated and sent to the control module 160.

[0070] In one embodiment of the present invention, the control module 160 is configured to generate a control instruction based on the judgment result and send the control instruction to the ventricular assist device. The control instruction includes a speed reduction instruction and / or a repeat operation instruction.

[0071] In one embodiment of the present invention, the rotation speed of the driving motor is divided into a plurality of gears, each gear corresponding to a certain motor speed, so the motor speed can be directly adjusted by adjusting the gear.

[0072] In one embodiment of the present invention, the speed reduction instruction is used to reduce the gear of the drive motor in the ventricular assist device to achieve speed adjustment, and the repeat operation instruction is used to enable the preprocessing module 110, the sampling module 120, the data module 130, the calculation module 140 and the judgment module 150 to perform their respective operations in sequence to achieve the next round of recognition and judgment of cardiac pumping.

[0073] In one embodiment of the present invention, an alarm module 170 is further included. The alarm module 170 is configured to trigger an alarm when the characteristic frequency deviates from the normal heart rate or when the cardiac aspiration determination result indicates the presence of cardiac aspiration.

[0074] In one embodiment of the present invention, when the characteristic frequency deviates from the normal heart rate, the judgment module 150 sends the judgment result to the control module 160, and the control module 160 generates a deceleration instruction based on the judgment result to control the ventricular assist device to directly downshift to the lowest gear.

[0075] In one embodiment of the present invention, the control module 160 also sends a trigger instruction to the alarm module 170 at the same time, and the alarm module 170 prompts the doctor to check the patient's physical condition as soon as possible.

[0076] In one embodiment of the present invention, when the judgment result of the judgment module 150 indicates that there is a cardiac aspiration phenomenon, the control module 160 generates and sends a deceleration instruction based on the judgment result to control the ventricular assist device to downshift step by step. Each time it downshifts a gear, the control module 160 simultaneously generates and sends a repeat operation instruction to the preprocessing module 110 or the sampling module 120, so that it re-collects the operating status of the drive motor in the ventricular assist device and re-determines whether the heart has aspirated. If the aspiration condition still exists, the deceleration instruction is generated again, and the repeat operation instruction is generated and sent to the preprocessing module 110 or the sampling module 120 again to collect the operating status again until the judgment result of the judgment module 150 indicates that the heart has not aspirated.

[0077] In one embodiment of the present invention, the control module 160 also sends a trigger instruction to the alarm module 170 each time it generates a deceleration instruction or the last time it generates a deceleration instruction. The alarm module 170 prompts the doctor to check the patient's physical condition as soon as possible.

[0078] In one embodiment of the present invention, when the control module 160 continuously generates deceleration instructions, causing the ventricular assist device to downshift step by step, and the suction condition is still not relieved when it is finally downshifted to the preset critical gear, the control module 160 sends a trigger instruction to the alarm module 170 to prompt the doctor to take other medical measures.

[0079] In one embodiment of the present invention, the critical gear is greater than or equal to the lowest gear, and the lowest gear is the gear that maintains the patient's basic physiological blood volume.

[0080] In one embodiment of the present invention, when the judgment module 150 makes an initial judgment indicating that there is no pumping phenomenon in the heart, the control module 160 only generates a repeat operation instruction and sends it to the preprocessing module 110 or the sampling module 120, so that it re-collects the operating status of the drive motor in the ventricular assist device and re-judges whether the heart is pumping.

[0081] In one embodiment of the present invention, when the speed of the drive motor drops to a critical speed and the cardiac pumping determination result indicates the presence of cardiac pumping, the control module 160 generates a speed reduction instruction to cause the ventricular assist device to downshift again.

[0082] As shown in FIG6 , an embodiment of the present invention provides a cardiac aspiration recognition method, including:

[0083] Step 210: sampling the operating data of the ventricular assist device within a preset sampling time to obtain sampled data.

[0084] In one embodiment of the present invention, before step 210, the method further includes:

[0085] Step 200: Acquire operating data of the ventricular assist device, the operating data including speed data and / or current data of a drive motor in the ventricular assist device, remove interference data from the operating data, and obtain the operating data.

[0086] In one embodiment of the present invention, step 210 further specifically includes the following steps:

[0087] Continuously sample k points at a preset frequency within a preset sampling time. The preset frequency is 5Hz to 50Hz, and k is an integer power of 2, such as 256, 512, 1024, 2048, 4096, etc.

[0088] Step 220: Perform data conversion on the sampled data to obtain frequency domain data.

[0089] In one embodiment of the present invention, step 220 further specifically includes the following steps:

[0090] The sampled time domain data is subjected to a fast Fourier transform (FFT) to obtain frequency domain data. In the obtained spectrum diagram, the vertical axis is the amplitude and the horizontal axis is the frequency.

[0091] Step 230: Determine a first amplitude in the frequency domain data, where the first amplitude corresponds to a maximum amplitude within a preset interval of the frequency domain data.

[0092] In one embodiment of the present invention, step 230 further specifically includes the following steps:

[0093] Locate the maximum amplitude and the corresponding characteristic frequency in the frequency domain data and determine the preset interval. In the entire spectrum, the position where the maximum amplitude A0 appears is the characteristic frequency f0, which corresponds to the patient's heart rate. The preset interval is calculated based on the value of f0. The preset interval is 0 to n*f0, where n is an empirical constant, preferably 0.25 <n<0.75。

[0094] Step 240: Generate a cardiac aspiration determination result based on whether the first amplitude is greater than a preset threshold.

[0095] In one embodiment of the present invention, step 240 further specifically includes the following steps:

[0096] A preset threshold is determined based on the maximum amplitude A0, and the first amplitude is compared to see whether it is greater than the preset threshold. Based on the comparison result, it is determined whether the heart is experiencing aspiration, and a cardiac aspiration determination result is generated. The preset threshold is m*A0, where m is an empirical constant, preferably 0.05<m<0.25.

[0097] In one embodiment of the present invention, if the first amplitude is greater than a preset threshold, it is determined that the heart has pumped, and a judgment result of pumping is generated; if the first amplitude is less than the preset threshold, it is determined that the heart has not pumped, and a judgment result of not pumping is generated.

[0098] In one embodiment of the present invention, step 240 further includes comparing whether the characteristic frequency deviates from the normal heart rate. If the characteristic frequency is not within the normal heart rate range (55-120 beats / minute), it is determined to be an abnormal detection situation.

[0099] Step 250: Generate a control instruction based on the judgment result, and send the control instruction to the ventricular assist device.

[0100] In one embodiment of the present invention, the control instruction includes a speed reduction instruction and / or a repeat operation instruction.

[0101] In one embodiment of the present invention, step 250 further specifically includes the following steps:

[0102] When the characteristic frequency deviates from the normal heart rate, a deceleration command is generated and sent to the ventricular assist device, causing it to downshift directly to the lowest gear. At the same time, a trigger alarm is sent, prompting the doctor to check the patient's physical condition as soon as possible.

[0103] When the judgment result indicates that there is cardiac aspiration, a speed reduction instruction is generated and sent to the ventricular assist device, causing it to downshift step by step. Each time it downshifts, a repeated operation instruction is generated and sent to re-collect the operating status of the drive motor in the ventricular assist device and re-judge whether the heart has aspirated. If the aspiration condition still exists, a speed reduction instruction is generated again and sent to the ventricular assist device, and a repeated execution control instruction is generated and sent again to collect the operating status again until the judgment result indicates that the heart has not aspirated.

[0104] Each time a downshift instruction is sent or when a downshift instruction is sent for the last time, a trigger alarm is also sent simultaneously to prompt the doctor to check the patient's physical condition as soon as possible.

[0105] When a deceleration command is continuously sent to the ventricular assist device to cause it to downshift step by step, and the suction condition is still not relieved when it finally downshifts to the preset critical gear, an additional alarm is triggered to prompt the doctor to take other medical measures.

[0106] When the first judgment result indicates that there is no pumping phenomenon in the heart, only a repeat operation instruction is generated and sent to re-collect the operation status of the drive motor in the ventricular assist device and re-judge whether the heart has pumped.

[0107] When the speed of the drive motor drops to a critical speed and the cardiac aspiration determination result indicates the presence of cardiac aspiration, a deceleration command is generated and sent, causing the ventricular assist device to downshift again. An embodiment of the present invention provides a ventricular assist system comprising the aforementioned ventricular assist device and the aforementioned cardiac aspiration identification device 100, wherein the ventricular assist device comprises a catheter pump, and the cardiac aspiration identification device 100 comprises a sampling module 120, a data conversion module 130, a calculation module 140, and a determination module 150. In one embodiment of the present invention, the cardiac aspiration identification device 100 further comprises a preprocessing module 110, which is configured to eliminate interference data from operating data or sampled data, wherein the interference data comprises a DC component in the operating data, to obtain operating data containing only an AC component.

[0108] In one embodiment of the present invention, the sampling module 120 is configured to sample the operating data of the drive motor within a preset sampling time period to obtain sampled data.

[0109] In one embodiment of the present invention, the data conversion module 130 is used to perform data conversion on the sampled data to obtain frequency domain data.

[0110] In one embodiment of the present invention, the calculation module 140 is configured to determine a first amplitude in the frequency domain data, where the first amplitude corresponds to a maximum amplitude within a preset interval of the frequency domain data.

[0111] In one embodiment of the present invention, the determination module 150 is configured to generate a cardiac aspiration determination result based on whether the first amplitude is greater than a preset threshold.

[0112] In one embodiment of the present invention, the control module 160 is configured to generate a control instruction based on the judgment result and send the control instruction to the ventricular assist device. The control instruction includes a speed reduction instruction and / or a repeat operation instruction.

[0113] In one embodiment of the present invention, the cardiac aspiration recognition device 100 further includes an alarm module 170, which is configured to trigger an alarm when the characteristic frequency deviates from the normal heart rate or when the judgment result indicates the presence of cardiac aspiration.

[0114] In one embodiment of the present invention, all modules of the cardiac aspiration recognition device 100 except the alarm module 170 are integrated into the host main control board, and the alarm module 170 is located in the host computer; the operating status is transmitted to the host main control board through the catheter pump, and the host main control board records the operating status data and sends a downshift / speed reduction instruction to the driver board of the catheter pump, and sends an alarm to the host computer, displaying a warning to notify the doctor.

[0115] As shown in FIG7 , in one embodiment of the present invention, an electronic device is further provided. The electronic device includes at least one processor 320 and a memory 310. The memory 310 is used to store one or more programs. When the one or more programs are executed by the processor 320, the processor 320 can implement the cardiac aspiration recognition method as described above.

[0116] In one embodiment of the present invention, a readable storage medium is further provided, on which a control program based on a ventricular assist system is stored. When the control program is executed by a processor, the above steps 210 to 250 can be implemented.

[0117] It should be noted that the cardiac pumping recognition method provided in the above embodiment and the embodiment of the ventricular assist system have the same concept. The specific implementation process is detailed in the device embodiment and will not be repeated here.

[0118] Those skilled in the art will understand that all or part of the steps to implement the above embodiments may be accomplished by hardware, or by a program to instruct the relevant hardware, and the program may be stored in a computer-readable storage medium, which may be a read-only memory, a disk, or an optical disk, etc.

[0119] In another embodiment of the present invention, a cardiac aspiration identification device is provided. The cardiac aspiration identification device 100 includes a sampling module 120, a data conversion module 130, a calculation module 140, a judgment module 150, and an alarm module 170. The aforementioned cardiac aspiration identification device 100 is applied to a ventricular assist device, can record its operating status, determine whether the heart has aspiration based on the operating status, and intervene in time when aspiration occurs, thereby improving the cardiac aspiration phenomenon by feedback adjustment of the gear position of the ventricular assist device.

[0120] In one embodiment of the present invention, the data sampled by the sampling module 120 is derived from operating data of a ventricular assist device, and the operating data includes speed data and / or current data of a driving motor in the ventricular assist device.

[0121] In one embodiment of the present invention, a pre-processing module 110 is further included. The pre-processing module 110 is capable of eliminating interference data in the operating data and / or sampling data. The interference data includes DC components in the operating data and abnormal data points that seriously deviate from normal values, etc., so as to remove the DC components and abnormal data in the waveform, eliminate the DC offset, and retain only the AC component, so that the recorded amplitude range is adjusted to the center position, thereby more clearly observing and calculating the working status and periodic characteristics of the drive motor. The data finally obtained is regarded as the operating data of the drive motor.

[0122] In one embodiment of the present invention, the operating data of the driving motor of the ventricular assist device can be measured by a speed sensor and then sent to the preprocessing module 110, or the speed can be calculated by measuring the magnitude of the power supply voltage and / or current of the driving motor and its changing frequency and sent to the preprocessing module 110, or the driving signal of the driving motor can be sampled by a feedback control system, controller, etc. and sent to the preprocessing module 110.

[0123] In one embodiment of the present invention, the judgment module 150 is configured to determine the difference between the maximum and minimum values ​​of the operating data within a preset time period, and compare the difference with a preset difference threshold. When the difference is less than the preset difference threshold, a severe puff judgment result is generated.

[0124] In one embodiment of the present invention, the operating data includes the speed data and / or current data of the driving motor in the ventricular assist device. In this embodiment, taking the speed as an example, referring to Figures 8 to 11, Figure 8 fully shows the original operating data diagram of the ventricular assist device in normal state, suction state and severe suction state, among which Figure 9 is the original operating data diagram of the ventricular assist device under normal conditions, Figure 10 is the original operating data diagram of the ventricular assist device under suction state, and Figure 11 is the original operating data diagram of the ventricular assist device under severe suction state.

[0125] Based on Figures 10 and 11, it can be seen that in the suction state, the difference between the maximum and minimum values ​​of the operating data of the ventricular assist device is large; in the severe suction state, the difference between the maximum and minimum values ​​of the operating data of the ventricular assist device is small.

[0126] In order to determine whether severe aspiration has occurred through the operating data of the ventricular assist device before sampling, so that the doctor can intervene in time, the preset time period determined by the judgment module 150 is configured to be 10s-40s, and more preferably 15s-30s; if the recording time is too short, multiple heart cycles cannot be displayed, and recording errors may occur. If the recording time is too long, severe aspiration may not be detected in time, and the best time for intervention may be missed.

[0127] In one embodiment of the present invention, taking the rotational speed as an example, the preset difference threshold is 500-800, and more preferably 600. If the difference threshold is too small, the random fluctuation during the operation of the motor may lead to inaccurate judgment. If the difference threshold is too large, it is impossible to distinguish between puffing and severe puffing.

[0128] In one embodiment of the present invention, when a severe suction state is determined to have occurred, the alarm module 170 is triggered to sound an alarm, indicating that it may be necessary to determine the position of the ventricular assist device by other means (such as X-ray, etc.), or to use ultrasound to determine the patient's heart condition.

[0129] In one embodiment of the present invention, if the judgment module 150 determines that the patient has not experienced severe aspiration, the sampling module 120 samples the operating data of the ventricular assist device within a preset sampling time to obtain sampling data, which is preferably used for the judgment of aspiration as shown in Figure 10.

[0130] In one embodiment of the present invention, the sampling module 120 can continuously sample k points at a preset frequency within a preset sampling time, where the preset frequency is 5Hz to 50Hz, and k is an integer power of 2, such as 256, 512, 1024, 2048, 4096, etc.

[0131] Those skilled in the art know that the operating cycle of the drive motor is positively correlated with the cycle of the heart rhythm (pumping period and congestion period). The normal heart rate of a person is 55 to 120 beats / minute. Taking 60 beats / minute as an example, the corresponding frequency is 1Hz. Taking 100 beats / minute as an example, the corresponding frequency is 1.67Hz. In order to ensure the accuracy of the sampling results, the preset frequency is adjusted to at least twice the frequency corresponding to the heart rate. The larger the sampling frequency, the more accurate the final calculation result. Therefore, the sampling preset frequency is set to 5Hz to 50Hz.

[0132] In one embodiment of the present invention, k is taken as an integer power of 2 in order to enable efficient calculation when performing a fast Fourier transform (FFT). FFT can convert a time domain signal into a frequency domain signal, thereby facilitating spectrum analysis and detecting cardiac pumping conditions.

[0133] If the heart experiences aspiration as shown in Figure 10, a fluctuation in the maximum cardiac flow rate is likely to occur every certain number of heartbeats. The preset sampling duration is determined based on this relationship. For example, if a fluctuation in the maximum cardiac flow rate occurs every 5 to 10 heartbeats, the preset sampling duration should at least cover this time interval. In one embodiment of the present invention, the preset sampling duration is k / f, where a < k / f < b, where a and b are empirical constants determined by the aforementioned relationship. Preferably, a ranges from 5 to 20, and b ranges from 20 to 60, more preferably, a = 20 and b = 30. If the lower limit a is too small, aspiration may not be detected. If the upper limit b is too high, the detection interval may be too long, preventing timely detection of aspiration. Prolonged aspiration can negatively impact the human body.

[0134] In one embodiment of the present invention, the data conversion module 130 is used to perform data conversion on the sampled data to obtain frequency domain data.

[0135] In one embodiment of the present invention, data conversion includes performing a fast Fourier transform (FFT) on the sampled time domain data to obtain frequency domain data. In the obtained spectrum, the vertical axis is amplitude and the horizontal axis is frequency.

[0136] In one embodiment of the present invention, the calculation module 140 is configured to calculate a first amplitude in the frequency-domain data, and the first amplitude corresponds to the maximum value of the amplitudes within a preset interval of the frequency-domain data.

[0137] In one embodiment of the present invention, the calculation module 140 is capable of determining the maximum amplitude and the corresponding characteristic frequency in the frequency-domain data, and determining a preset interval.

[0138] Specifically, in the entire spectrogram, the position where the maximum amplitude A0 appears is the characteristic frequency f0, and f0 corresponds to the heart rate of the patient. Based on the value of f0, a preset interval can be determined. The preset interval is a certain frequency interval before f0, and the amplitudes within this interval have local maximum values, which are positioned as the first amplitude.

[0139] In one embodiment of the present invention, the preset interval is 0 to n*f0, where n is an empirical constant. Preferably, 0.25 < n < 0.75. Due to the fluctuations of the heart rate and measurement errors, one or more small peaks may appear on both sides of the characteristic frequency f0 corresponding to the maximum amplitude A0. Therefore, the upper limit in this value range is used to reduce the influence of heart rate fluctuations on the data, and the lower limit of the value range is used to confirm the situation of the cardiac aspiration waveform.

[0140] Referring to FIGS. 4 and 5, the unit of the abscissa in both figures is times per minute. The regions marked by the two boxes are the maximum amplitudes in the normal state and the aspiration state of the heart respectively, and the region marked by the circular frame in FIG. 5 is the first amplitude in the cardiac aspiration state.

[0141] In one embodiment of the present invention, the judgment module 150 is configured to judge whether the characteristic frequency f0 deviates from the normal heart rate and generate a judgment result.

[0142] Specifically, if the characteristic frequency f0 is not within the normal heart rate range (55 to 120 beats per minute), it will be judged as an abnormal detection situation.

[0143] In one embodiment of the present invention, the judgment module 150 is configured to determine a preset threshold, and the preset threshold is determined based on the maximum amplitude A0; a cardiac aspiration judgment result is generated by judging whether the first amplitude is greater than the preset threshold.

[0144] In one embodiment of the present invention, the preset threshold is m*A0, where m is an empirical constant. Preferably, 0.05 < m < 0.25. The upper limit 0.25 depends on the empirical data of the aspiration situation, and the lower limit 0.05 depends on the 5% threshold confirmation of the error in digital signal processing.

[0145] In one embodiment of the present invention, the judgment module 150 performs the judgment logic for severe puffing shown in FIG. 11 before the judgment logic for normal puffing shown in FIG. Because the judgment logic for severe puffing consumes less computing power, performing the judgment for it first can avoid wasting computing power, which is particularly beneficial for embedded software.

[0146] In one embodiment of the present invention, a control module 160 is further included. If the first amplitude is greater than a preset threshold, the judgment module 150 determines that the heart has experienced aspiration as shown in FIG10 , generates a judgment result indicating aspiration, and sends the judgment result to the control module 160. If the first amplitude is less than the preset threshold, it is determined that the heart has not experienced aspiration, and a judgment result indicating no aspiration is generated and sent to the control module 160.

[0147] In one embodiment of the present invention, the control module 160 is configured to generate a control instruction based on the judgment result and send the control instruction to the ventricular assist device. The control instruction includes a speed reduction instruction and / or a repeat operation instruction.

[0148] In one embodiment of the present invention, the rotation speed of the driving motor is divided into a plurality of gears, each gear corresponding to a certain motor speed, so the motor speed can be directly adjusted by adjusting the gear.

[0149] In one embodiment of the present invention, the speed reduction instruction is used to reduce the gear of the drive motor in the ventricular assist device to achieve speed adjustment, and the repeat operation instruction is used to enable the preprocessing module 110, the sampling module 120, the data module 130, the calculation module 140 and the judgment module 150 to perform their respective operations in sequence to achieve the next round of recognition and judgment of cardiac pumping.

[0150] In one embodiment of the present invention, the alarm module 170 is further configured to trigger an alarm when the characteristic frequency deviates from the normal heart rate, or when the cardiac aspiration determination result indicates the presence of cardiac aspiration.

[0151] In one embodiment of the present invention, when the characteristic frequency deviates from the normal heart rate, the judgment module 150 sends the judgment result to the control module 160, and the control module 160 generates a deceleration instruction based on the judgment result to control the ventricular assist device to directly downshift to the lowest gear.

[0152] In one embodiment of the present invention, the control module 160 also sends a trigger instruction to the alarm module 170 at the same time, and the alarm module 170 prompts the doctor to check the patient's physical condition as soon as possible.

[0153] In one embodiment of the present invention, when the judgment result of the judgment module 150 indicates that there is a cardiac aspiration phenomenon, the control module 160 generates and sends a deceleration instruction based on the judgment result to control the ventricular assist device to downshift step by step. Each time it downshifts a gear, the control module 160 simultaneously generates and sends a repeat operation instruction to the preprocessing module 110 or the sampling module 120, so that it re-collects the operating status of the drive motor in the ventricular assist device and re-determines whether the heart has aspirated. If the aspiration condition still exists, the deceleration instruction is generated again, and the repeat operation instruction is generated and sent to the preprocessing module 110 or the sampling module 120 again to collect the operating status again until the judgment result of the judgment module 150 indicates that the heart has not aspirated.

[0154] In one embodiment of the present invention, the control module 160 also sends a trigger instruction to the alarm module 170 each time it generates a deceleration instruction or the last time it generates a deceleration instruction. The alarm module 170 prompts the doctor to check the patient's physical condition as soon as possible.

[0155] In one embodiment of the present invention, when the control module 160 continuously generates deceleration instructions, causing the ventricular assist device to downshift step by step, and the suction condition is still not relieved when it is finally downshifted to the preset critical gear, the control module 160 sends a trigger instruction to the alarm module 170 to prompt the doctor to take other medical measures.

[0156] In one embodiment of the present invention, the critical gear is greater than or equal to the lowest gear, and the lowest gear is the gear that maintains the patient's basic physiological blood volume.

[0157] In one embodiment of the present invention, when the judgment module 150 makes an initial judgment indicating that there is no pumping phenomenon in the heart, the control module 160 only generates a repeat operation instruction and sends it to the preprocessing module 110 or the sampling module 120, so that it re-collects the operating status of the drive motor in the ventricular assist device and re-judges whether the heart is pumping.

[0158] In one embodiment of the present invention, when the speed of the drive motor drops to a critical speed and the cardiac pumping determination result indicates the presence of cardiac pumping, the control module 160 generates a speed reduction instruction to cause the ventricular assist device to downshift again.

[0159] As shown in FIG12 , an embodiment of the present invention provides a cardiac aspiration recognition method, including:

[0160] Step 200: Acquire operating data of the ventricular assist device, the operating data including speed data and / or current data of a drive motor in the ventricular assist device, remove interference data from the operating data, and obtain the operating data.

[0161] Step 201 : determining the difference between the maximum and minimum values ​​of the operating data within a preset time period, and comparing the difference with a preset difference threshold. When the difference is less than the preset difference threshold, a severe puffing determination result is generated.

[0162] Figures 10 and 11 show that in the aspirating state, the difference between the maximum and minimum values ​​of the VAD's operating data is large; in the severe aspirating state, the difference between the maximum and minimum values ​​is small. To determine whether severe aspirating has occurred based on the VAD's operating data before sampling, facilitating timely physician intervention, the preset time period for severe aspirating determination is set to 10s-40s, preferably 15s-30s. If the recording time is too short, multiple cardiac cycles cannot be displayed, potentially leading to recording errors. If the recording time is too long, severe aspirating may not be detected in a timely manner, missing the optimal time for intervention.

[0163] In one embodiment of the present invention, taking the rotational speed as an example, the preset difference threshold is 500-800, and more preferably 600. If the difference threshold is too small, the random fluctuation during the operation of the motor may lead to inaccurate judgment. If the difference threshold is too large, it is impossible to distinguish between puffing and severe puffing.

[0164] In one embodiment of the present invention, when a severe aspiration state is determined to have occurred, an alarm is triggered, indicating that it may be necessary to determine the position of the ventricular assist device by other means (such as X-rays, etc.), or to use ultrasound to determine the patient's heart condition.

[0165] In one embodiment of the present invention, if it is determined that the patient does not have severe aspiration, the process proceeds to step S210 .

[0166] Step 210: sampling the operating data of the ventricular assist device within a preset sampling time to obtain sampled data.

[0167] In one embodiment of the present invention, step 210 further specifically includes the following steps:

[0168] Continuously sample k points at a preset frequency within a preset sampling time. The preset frequency is 5Hz to 50Hz, and k is an integer power of 2, such as 256, 512, 1024, 2048, 4096, etc.

[0169] Step 220: Perform data conversion on the sampled data to obtain frequency domain data.

[0170] In one embodiment of the present invention, step 220 further specifically includes the following steps:

[0171] The sampled time domain data is subjected to a fast Fourier transform (FFT) to obtain frequency domain data. In the obtained spectrum diagram, the vertical axis is the amplitude and the horizontal axis is the frequency.

[0172] Step 230: Determine a first amplitude in the frequency domain data, where the first amplitude corresponds to a maximum amplitude within a preset interval of the frequency domain data.

[0173] In one embodiment of the present invention, step 230 further specifically includes the following steps:

[0174] Locate the maximum amplitude and the corresponding characteristic frequency in the frequency domain data and determine the preset interval. In the entire spectrum, the position where the maximum amplitude A0 appears is the characteristic frequency f0, which corresponds to the patient's heart rate. The preset interval is calculated based on the value of f0. The preset interval is 0 to n*f0, where n is an empirical constant, preferably 0.25 <n<0.75。

[0175] Step 240: Generate a cardiac aspiration determination result based on whether the first amplitude is greater than a preset threshold.

[0176] In one embodiment of the present invention, step 240 further specifically includes the following steps:

[0177] A preset threshold is determined based on the maximum amplitude A0, and the first amplitude is compared to see whether it is greater than the preset threshold. Based on the comparison result, it is determined whether the heart is experiencing aspiration, and a cardiac aspiration determination result is generated. The preset threshold is m*A0, where m is an empirical constant, preferably 0.05<m<0.25.

[0178] In one embodiment of the present invention, if the first amplitude is greater than a preset threshold, it is determined that the heart has pumped, and a judgment result of pumping is generated; if the first amplitude is less than the preset threshold, it is determined that the heart has not pumped, and a judgment result of not pumping is generated.

[0179] In one embodiment of the present invention, step 240 further includes comparing whether the characteristic frequency deviates from the normal heart rate. If the characteristic frequency is not within the normal heart rate range (55-120 beats / minute), it is determined to be an abnormal detection situation.

[0180] Specifically, since the judgment logic of severe puff consumes less computing power, the severe puff judgment step is configured before the normal puff judgment step to avoid wasting computing power, which has a more positive significance for embedded software.

[0181] Step 250: Generate a control instruction based on the judgment result, and send the control instruction to the ventricular assist device.

[0182] In one embodiment of the present invention, the control instruction includes a speed reduction instruction and / or a repeat operation instruction.

[0183] In one embodiment of the present invention, step 250 further specifically includes the following steps:

[0184] When the characteristic frequency deviates from the normal heart rate, a deceleration command is generated and sent to the ventricular assist device, causing it to downshift directly to the lowest gear. At the same time, a trigger alarm is sent, prompting the doctor to check the patient's physical condition as soon as possible.

[0185] When the judgment result indicates that there is cardiac aspiration, a speed reduction instruction is generated and sent to the ventricular assist device, causing it to downshift step by step. Each time it downshifts, a repeated operation instruction is generated and sent to re-collect the operating status of the drive motor in the ventricular assist device and re-judge whether the heart has aspirated. If the aspiration condition still exists, a speed reduction instruction is generated again and sent to the ventricular assist device, and a repeated execution control instruction is generated and sent again to collect the operating status again until the judgment result indicates that the heart has not aspirated.

[0186] Each time a downshift instruction is sent or when a downshift instruction is sent for the last time, a trigger alarm is also sent simultaneously to prompt the doctor to check the patient's physical condition as soon as possible.

[0187] When a deceleration command is continuously sent to the ventricular assist device to cause it to downshift step by step, and the suction condition is still not relieved when it finally downshifts to the preset critical gear, an additional alarm is triggered to prompt the doctor to take other medical measures.

[0188] When the first judgment result indicates that there is no pumping phenomenon in the heart, only a repeat operation instruction is generated and sent to re-collect the operation status of the drive motor in the ventricular assist device and re-judge whether the heart has pumped.

[0189] When the speed of the driving motor drops to a critical speed and the cardiac aspiration determination result indicates the presence of cardiac aspiration, a speed reduction instruction is generated and sent, causing the ventricular assist device to downshift again.

[0190] The embodiments of the present invention are described above in conjunction with the accompanying drawings, but the present invention is not limited to the above-mentioned specific implementation methods. The above-mentioned specific implementation methods are merely illustrative and not restrictive. Under the guidance of the present invention, ordinary technicians in this field can also make many forms without departing from the scope of protection of the present invention and the claims, all of which are protected by the present invention.

Claims

1. A cardiac aspiration identification device, characterized in that: include: A sampling module, used for sampling the operation data of the ventricular assist device within a preset sampling time to obtain sampling data; A data conversion module, used for performing data conversion on the sampled data to obtain frequency domain data; A calculation module, configured to determine a first amplitude in the frequency domain data, wherein the first amplitude corresponds to a maximum amplitude in a preset interval of the frequency domain data; The judgment module is used to generate a cardiac aspiration judgment result according to whether the first amplitude is greater than a preset threshold.

2. The cardiac aspiration identification device according to claim 1, characterized in that: The operation data of the ventricular assist device includes speed data and / or current data of a driving motor in the ventricular assist device.

3. The cardiac aspiration identification device according to claim 2, characterized in that: Also includes: The preprocessing module is used to eliminate interference data in the operating data and / or sampling data, wherein the interference data includes a DC component in the operating data.

4. The cardiac aspiration identification device according to claim 1, characterized in that: The sampling module is used to continuously sample k points within the preset sampling time at a preset frequency, where the preset frequency is between 5 Hz and 50 Hz, and k is an integer power of 2.

5. The cardiac aspiration identification device according to claim 4, characterized in that: The sampling module is further used to determine the preset sampling duration according to the relationship between the heartbeat cycle and the maximum heart flow fluctuation cycle.

6. The cardiac aspiration identification device according to claim 1, characterized in that: The data conversion module is further used to perform fast Fourier transform on the sampled data to obtain frequency domain data.

7. The cardiac aspiration identification device according to claim 1, characterized in that: The calculation module is further used to determine the preset interval based on the characteristic frequency corresponding to the maximum amplitude in the frequency domain data.

8. The cardiac aspiration identification device according to claim 7, characterized in that: The judging module is further used to judge whether the characteristic frequency deviates from the normal heart rate; The judgment module is further used to determine the preset threshold, and the preset threshold is determined based on the maximum amplitude.

9. The cardiac aspiration identification device according to claim 8, characterized in that: Also includes: A control module is used to generate a control instruction according to the judgment result, and send the control instruction to the ventricular assist device, wherein the control instruction includes a speed reduction instruction and / or a repeat operation instruction.

10. The cardiac aspiration identification device according to claim 9, characterized in that: The control module is used to generate the speed reduction instruction when the characteristic frequency deviates from the normal heart rate; The control module is used to generate the speed reduction instruction and the repeat operation instruction when the cardiac aspiration determination result indicates the presence of cardiac aspiration phenomenon; The control module is used to generate the repeat operation instruction when the cardiac aspiration determination result indicates that there is no cardiac aspiration phenomenon; The control module is used to generate the speed reduction instruction when the speed of the driving motor of the ventricular assist device drops to a critical speed and the cardiac aspiration judgment result indicates the presence of cardiac aspiration.

11. The cardiac aspiration identification device according to claim 9, characterized in that: Also includes: The alarm module is used to trigger an alarm when the characteristic frequency deviates from the normal heart rate or the cardiac aspiration judgment result indicates the presence of cardiac aspiration.

12. The cardiac aspiration identification device according to claim 1, characterized in that: Also includes: The judgment module is further used to determine the difference between the maximum value and the minimum value of the operating data within a preset time period, and compare the difference with a preset difference threshold, and generate a severe suction judgment result when the difference is less than the preset difference threshold.

13. A method for identifying cardiac aspiration, characterized in that: include: Sampling the operating data of the ventricular assist device within a preset sampling time to obtain sampling data; Performing data conversion on the sampled data to obtain frequency domain data; Determine a first amplitude in the frequency domain data, the first amplitude corresponding to a maximum amplitude within a preset interval of the frequency domain data; A cardiac aspiration determination result is generated according to whether the first amplitude is greater than a preset threshold.

14. A ventricular assist system, characterized in that: It comprises a driving motor and a cardiac aspiration identification device as claimed in any one of claims 1 to 12, wherein the cardiac aspiration identification device comprises a sampling module, a data conversion module, a calculation module and a judgment module; The sampling module is used to sample the operation data of the drive motor within a preset sampling time to obtain sampling data; The data conversion module is used to perform data conversion on the sampled data to obtain frequency domain data; The calculation module is used to determine a first amplitude in the frequency domain data, where the first amplitude corresponds to a maximum amplitude in a preset interval of the frequency domain data; The judgment module is used to generate a cardiac aspiration judgment result according to whether the first amplitude is greater than a preset threshold.

15. An electronic device, characterized in that: include: one or more processors; A memory for storing one or more programs; When the one or more programs are executed by the one or more processors, the one or more processors implement the cardiac aspiration recognition method as claimed in claim 13.

16. A readable storage medium, characterized in that: The readable storage medium stores a ventricular assist system control program, and when the control program is executed by the processor, the cardiac aspiration recognition method as claimed in claim 13 can be implemented.

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