Method and apparatus for detecting suction intensity of blood pump, device, and blood pump

Abstract

Disclosed are a method and an apparatus for detecting a suction intensity of a blood pump, a device, and a blood pump, belonging to the technical field of artificial hearts. The detection method comprises: in a first stage of operation after a blood pump is introduced into a heart of a target subject, determining a first ventricular diastolic pressure corresponding to the target subject (310), wherein the first stage refers to a stage in which the blood pump operates at a first support level, and a valve of the heart can be opened and closed at the first support level; in a second stage of operation of the blood pump, acquiring ventricular pressure data corresponding to the target subject (320), wherein the second stage refers to a stage in which the blood pump operates at a second support level, the second support level is higher than or equal to the first support level, the ventricular pressure data is data that is predicted on the basis of a prediction relationship, and the prediction relationship is determined on the basis of data obtained when the valve is in a normal open / closed state; and on the basis of the first ventricular diastolic pressure and the ventricular pressure data, determining suction intensity information of the blood pump (330), wherein the suction intensity information is positively correlated with a probability of an abnormal cardiac event, and the abnormal event comprises a continuous valve closing event and / or a suction event.

Description

Methods, devices, equipment, and blood pumps for detecting blood pump suction strength.

[0001] Cross-references to related applications

[0002] This patent application claims priority to Chinese Patent Application No. 202510065455.X, filed on January 15, 2025, entitled “Method, Apparatus, Device and Blood Pump for Detecting Blood Pump Suction Intensity”, the entire contents of which are incorporated herein by reference. Technical Field

[0003] This disclosure relates to the field of artificial heart technology, and in particular to a method, apparatus, equipment and blood pump for detecting the suction strength of a blood pump. Background Technology

[0004] Blood pump devices are used to provide mechanical circulatory support for patients. An interventional blood pump is a percutaneously implanted device. Its pump head is inserted percutaneously into the heart via a peripheral blood vessel. As the blades in the pump head rotate, they draw blood from the ventricles of the heart towards the aorta, thus providing ventricular assist function. During operation, if the pump rotates at excessive speed, it may cause heart valves, such as the aortic valve, to stop opening, posing a risk of aspiration.

[0005] In related technologies, a pressure sensor is installed at the pump head of the blood pump device. The electronic equipment in the blood pump device determines whether the heart valve is continuously closed or whether an abnormal event such as aspiration has occurred based on the pressure signal collected by the pressure sensor at the pump head, and then issues an alarm to instruct relevant personnel to handle the situation.

[0006] However, the above alerts are generated after the aforementioned abnormal events have occurred, and therefore cannot effectively prevent the occurrence of abnormal events. Summary of the Invention

[0007] According to one or more embodiments of this disclosure, a method for detecting the suction strength of a blood pump is provided. The method includes: determining a first ventricular diastolic pressure corresponding to the target object during a first stage of operation after the blood pump is inserted into the heart of a target object; wherein, the first stage refers to the stage in which the blood pump operates at a first support level, and the heart valves are able to open and close at the first support level; acquiring ventricular pressure data corresponding to the target object during a second stage of operation of the blood pump, wherein the second stage refers to the stage in which the blood pump operates at a second support level, the second support level being higher than or equal to the first support level, and the ventricular pressure data being data predicted based on a prediction relationship, the prediction relationship being determined based on data obtained when the valves are in a normal opening and closing state; and determining the suction strength information of the blood pump based on the first ventricular diastolic pressure and the ventricular pressure data, wherein the suction strength information is positively correlated with the probability of an abnormal event occurring in the heart, the abnormal event including a valve persistent closure event and / or aspiration event.

[0008] According to one or more embodiments of this disclosure, a blood pump suction intensity detection device is provided. The device includes: a first pressure determination module, used to determine a first ventricular diastolic pressure corresponding to the target object during a first stage of operation after the blood pump is inserted into the heart of a target object; wherein, the first stage refers to the stage in which the blood pump operates at a first support level, and the heart valves are able to open and close at the first support level; a second pressure determination module, used to acquire ventricular pressure data corresponding to the target object during a second stage of operation of the blood pump, wherein the second stage refers to the stage in which the blood pump operates at a second support level, the second support level being higher than or equal to the first support level, and the ventricular pressure data being data predicted based on a prediction relationship, the prediction relationship being determined based on data obtained when the valves are in a normal opening and closing state; and a suction intensity determination module, used to determine the blood pump suction intensity information based on the first ventricular diastolic pressure and the ventricular pressure data, wherein the suction intensity information is positively correlated with the probability of an abnormal event occurring in the heart, the abnormal event including a valve persistent closure event and / or aspiration event.

[0009] According to one or more embodiments of the present disclosure, an electronic device is provided, the electronic device including a processor and a memory, the memory storing at least one instruction, at least one program, code set or instruction set, the at least one instruction, at least one program, code set or instruction set being loaded and executed by the processor to implement the above-described method for detecting the suction strength of a blood pump.

[0010] According to one or more embodiments of the present disclosure, a blood pump device is provided, the blood pump device including a processor and a memory, the memory storing at least one instruction, at least one program, code set or instruction set, the at least one instruction, at least one program, code set or instruction set being loaded and executed by the processor to implement the above-described method for detecting the suction strength of the blood pump.

[0011] According to one or more embodiments of the present disclosure, a computer-readable storage medium is provided, which stores at least one instruction, at least one program, code set or instruction set, wherein the at least one instruction, at least one program, code set or instruction set is loaded and executed by a processor to implement the above-described method for detecting the suction strength of a blood pump.

[0012] According to one or more embodiments of this disclosure, a computer program product is provided, comprising computer instructions stored in a computer-readable storage medium. A processor of a computer device reads the computer instructions from the computer-readable storage medium and executes the computer instructions, causing the computer device to perform the aforementioned method for detecting the suction strength of a blood pump. Attached Figure Description

[0013] To more clearly illustrate the technical solutions in the embodiments of this disclosure, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of this disclosure. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0014] Figure 1 is a schematic diagram of a blood pump device provided in an embodiment of this disclosure;

[0015] Figure 2 illustrates a schematic diagram of a connection between an interventional pump and a fluid pipeline.

[0016] Figure 3 is a flowchart 1 of a method for detecting the suction strength of a blood pump according to an embodiment of this disclosure;

[0017] Figure 4 is a flowchart 2 of a method for detecting the suction strength of a blood pump according to another embodiment of this disclosure;

[0018] Figure 5 illustrates a theoretical schematic diagram of a cardiac pressure curve under normal aortic valve opening and closing conditions.

[0019] Figure 6 illustrates a schematic diagram of a differential pressure prediction data curve;

[0020] Figure 7 illustrates a schematic diagram of the pressure curve corrected according to the correction factor;

[0021] Figure 8 illustrates a theoretical schematic diagram of the cardiac pressure curve when the valve is normally closed.

[0022] Figure 9 illustrates a schematic diagram of a curve for determining the suction strength of a blood pump;

[0023] Figure 10 illustrates a schematic diagram of a pressure curve that is corrected twice based on suction strength.

[0024] Figure 11 is a block diagram of a blood pump suction strength detection device provided in an embodiment of the present disclosure. Detailed Implementation

[0025] To make the objectives, technical solutions, and advantages of this disclosure clearer, embodiments of this disclosure will be further described in detail below with reference to the accompanying drawings. Exemplary embodiments will be described in detail here, examples of which are illustrated in the accompanying drawings. When the following description refers to the drawings, unless otherwise indicated, the same numbers in different drawings represent the same or similar elements. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with this disclosure. Rather, they are merely examples of apparatuses and methods consistent with some aspects of this disclosure as detailed in the appended claims.

[0026] The terminology used in this disclosure is for the purpose of describing particular embodiments only and is not intended to be limiting of the disclosure. The singular forms “a,” “the,” and “the” as used in this disclosure and the appended claims are also intended to include the plural forms unless the context clearly indicates otherwise. It should also be understood that the term “and / or” as used herein refers to and includes any and all possible combinations of one or more of the associated listed items.

[0027] It should be understood that although the terms first, second, third, etc., may be used in this disclosure to describe various information, such information should not be limited to these terms. These terms are only used to distinguish information of the same type from one another.

[0028] Before introducing the method embodiments provided in this disclosure, a brief introduction will be given to the relevant technical background, related terms or nouns that may be involved in the method embodiments of this disclosure, so as to facilitate the understanding of those skilled in the art.

[0029] A blood pump device is a circulatory auxiliary device that replaces the function of the ventricles, including but not limited to external blood pump devices, interventional blood pump devices, and implantable blood pump devices.

[0030] An interventional blood pump device refers to a catheter-based pump used in medical settings to assist the heart in providing blood circulation. An interventional blood pump device includes an interventional blood pump (or simply interventional pump) and a control device used in conjunction with it, suitable for providing temporary ventricular circulatory support during relevant surgeries. Optionally, the interventional blood pump is a cardiac pump inserted into a living organism. Optionally, some or all components of the interventional blood pump are inserted into the living organism. In operation, the drive device in the control device drives the interventional pump to pump blood from the ventricles into the aorta, assisting the heart's pumping function and reducing the burden on the heart.

[0031] Figure 1 is a schematic diagram of a blood pump device provided in an embodiment of this disclosure. Referring to Figure 1, the blood pump device is an interventional blood pump device, including an interventional pump 10 and a control device 20, which are detachably connected to the interventional pump 10. The interventional pump 10 is a consumable component.

[0032] The control device 20 includes, but is not limited to, a console 21, a drive motor 22, and a flushing device 23. The console 21 is used at least to respond to human-machine interface operations and system control operations, allowing operators to monitor system status and patient physiological data, and adjust the speed of the blood pump according to the patient's needs to provide different levels of circulatory assistance, thereby temporarily maintaining blood circulation to the patient's vital organs and relieving the burden on the heart. The drive motor 22 is used at least to drive the interventional pump 10.

[0033] The interventional pump 10 includes a drive catheter handle 11, a drive catheter 12, a pump head 13, and a protective end 14. The pump head 13 includes, but is not limited to, an impeller, a support, and a membrane.

[0034] The interventional pump 10 can be percutaneously inserted into the heart through peripheral blood vessels. The pump head 13 is placed between the left ventricle and the aorta. The blood inlet of the pump head 13 is placed into the left ventricle, and the blood outlet of the pump head is placed into the aorta, thereby pumping blood from the left ventricle into the aorta to achieve ventricular assist function.

[0035] Since the interventional pump 10 needs to be inserted into the human body, it needs to be pre-charged before use and kept flushed during use to prevent air from entering the body through the gaps inside the interventional pump 10 and to prevent blood from stagnating in the gaps inside the interventional pump 10 and forming thrombi. Therefore, the interventional pump 10 can also be connected to a flushing line. The flushing device 23 is used to drive the flushing fluid in the flushing line to pre-charge, vent, and flush the gaps inside the interventional pump 10, thereby preventing blood from entering the drive catheter 12 and forming thrombi, and preventing air from entering the patient's body through the gaps inside the interventional pump and forming air embolisms. The flushing device 23 may include a peristaltic pump, which drives and squeezes the pump tube in the flushing line to pump the flushing fluid into the interventional pump 10, thereby preventing air bubbles from entering the drive catheter 12 of the interventional pump 10.

[0036] Optionally, the interventional pump system can monitor the patient's blood pressure. The interventional pump has an arterial pressure measurement channel that remains connected to a blood vessel. An arterial pressure sensor is installed in the arterial pressure measurement channel; when the channel is connected to the blood vessel fluid, the sensor can detect the patient's arterial pressure. Therefore, the interventional pump 10 can also be connected to an arterial pressure measurement line. The arterial pressure measurement line has a periodically open flushing valve; a pressure bag applies pressure to the fluid bag connected to the arterial pressure measurement line, driving fluid to flush the arterial pressure measurement pathway and prevent thrombosis.

[0037] As an example, see Figure 2, which exemplarily illustrates a schematic diagram of an interventional pump connected to a fluid line. The fluid line includes a flushing line and an arterial pressure monitoring line 40. The flushing line includes an infusion line 31, a circulation inlet line 32, and a circulation outlet line 33. The infusion line 31 can be driven and squeezed by the infusion pump 231 in the flushing device 23 (as shown in Figure 1), and the circulation inlet line 32 can be driven and squeezed by the circulation pump 232 in the flushing device 23.

[0038] After the drive catheter handle 11 is connected to the flushing pipeline, a flushing flow path is formed. Specifically, the flushing fluid inlet 111 of the drive catheter handle 11 is connected to the circulation inlet pipe 32 of the flushing pipeline, the flushing fluid outlet 112 of the drive catheter handle 11 is connected to the circulation outlet pipe 33 of the flushing pipeline, and the infusion pipe 31 of the flushing pipeline is connected to the fluid bag, forming the flushing flow path of the intervention pump 10. The infusion pump 231 drives the pump tube on the infusion pipe 31 to pump the flushing fluid in the fluid bag to the circulation inlet pipe 32, thereby driving the flushing fluid to enter the drive catheter handle 11 through the flushing fluid inlet 111. After the flushing fluid enters the drive catheter handle 11, part of it enters the drive catheter 12 through the flushing fluid chamber and is discharged to the human body from the pump head 13; the other part enters the coupling cooling chamber and flows back into the flushing pipeline from the flushing fluid outlet 112. The circulating pump 232 is used to drive the flushing fluid to circulate between the circulating inlet pipe 32, the drive guide handle 11, and the circulating outlet pipe 33 to cool the flushing fluid and prevent the high temperature generated by the coupled rotation between the drive motor 22 (as shown in Figure 1) and the intervention pump 10 (as shown in Figure 1) from causing the flushing fluid to reach a high temperature. At the same time, the circulating flushing fluid has a cooling effect on the coupled rotor.

[0039] After the drive catheter handle 11 is connected to the arterial pressure measurement tubing 40, an arterial pressure measurement flow path is formed. Specifically, the pressure measurement inlet 113 of the drive catheter handle 11 is connected to the arterial pressure measurement tubing 40, and the pressure measurement outlet 114 of the drive catheter handle 11 is connected to the pressure measurement interface 51 of the interventional sheath 50. The interventional sheath 50, after being percutaneously inserted into the blood vessel, provides a pathway for the interventional pump 10 to be placed into the heart, and the interventional sheath 50 remains in the patient's blood vessel until the interventional pump 10 is removed. The fluid in the fluid bag connected to the arterial pressure measurement tubing 40 fills the entire arterial pressure measurement channel in the arterial pressure measurement tubing 40 and the interventional pump 10, and connects to the gap 53 between the interventional sheath 50 and the drive catheter 12, thereby maintaining communication with the blood in the blood vessel. Thus, the arterial pressure sensor 115 in the interventional pump can detect the patient's arterial pressure. The aforementioned arterial pressure sensor 115 is located outside the patient's body.

[0040] Please refer to Figure 3, which shows a flowchart of a method for detecting the suction strength of a blood pump according to an embodiment of this disclosure. This method can be applied to electronic devices, which are those capable of data calculation and processing. For example, the executing entity for each step can be related electronic equipment in the blood pump device shown in Figure 1, such as the control console 21, the flushing device 23, etc. The method may include the following steps (310-330).

[0041] Step 310, the first stage of operation after the blood pump is inserted into the heart of the target subject, determines the first ventricular diastolic pressure corresponding to the target subject.

[0042] The first stage refers to the stage where the blood pump operates at a first support level, under which the heart valves can open and close. The support level of the blood pump may depend on the target rotational speed, target flow rate, or target pressure of the blood pump, and this embodiment does not limit this.

[0043] Optionally, the first stage mentioned above can be the stage where the blood pump is in calibration operation.

[0044] The aforementioned first ventricular diastolic pressure refers to the ventricular diastolic pressure when the blood pump assists the ventricle at the first level of support.

[0045] The aforementioned diastolic pressure can be the pressure data in diastole identified from ventricular pressure data detected by sensors, or the pressure data in diastole identified from ventricular pressure data predicted based on relevant signals from the blood pump.

[0046] In some embodiments, the blood pump described above is an interventional pump (catheter pump), and the portion of the interventional pump that is inserted into the ventricle distal to the ventricle may be equipped with a pressure sensor to detect ventricular pressure data.

[0047] In some embodiments, the portion of the interventional pump that is inserted into the ventricle is not equipped with a pressure sensor. In this case, ventricular pressure data can be predicted based on the correlation between the relevant operating signal data of the blood pump and the ventricular pressure data.

[0048] To ensure the valves can open and close during the heartbeat cycle, the aforementioned first support level is relatively low, allowing for the determination of ventricular diastolic pressure under normal valve opening and closing conditions. Optionally, the first support level is the lowest support level within the operating range of the blood pump.

[0049] Step 320: In the second stage of blood pump operation, acquire the ventricular pressure data corresponding to the target object.

[0050] The second stage refers to the stage where the blood pump operates at a second support level, which is higher than or equal to the first support level. For example, the target rotational speed or target flow rate corresponding to the second stage is higher than the target rotational speed or target flow rate corresponding to the first stage.

[0051] Step 330: Determine the suction strength information of the blood pump based on the first ventricular diastolic pressure and ventricular pressure data.

[0052] Among them, the suction intensity information is positively correlated with the probability of abnormal cardiac events, including valvular closure events and / or aspiration events.

[0053] The ventricular pressure data determined in the second stage above are based on data predicted by a predictive relationship, which is determined based on data obtained when the valves are in a normal opening and closing state.

[0054] For some blood pumps, the pump head does not have a pressure sensor, making it difficult to directly detect ventricular pressure. However, ventricular pressure data can be predicted using predictive relationships, such as the blood pump's operating signal data, the target's arterial pressure data, and other operating data obtainable by the blood pump device. To determine the predictive relationship between these other operating data and ventricular pressure, multiple experiments can be conducted to establish the predictive relationship based on the experimental data. However, the inventors of this disclosure have found that the above experiments are usually conducted under the premise of normal valve opening and closing. Therefore, the predictive relationship can only accurately predict ventricular pressure when the valve is in a normal opening and closing state. In the second stage, the second support level of the blood pump is set according to actual needs and may be equal to the first support level (for example, the first support level is the lowest support level within the working range, and the support level in the second stage is also set to the lowest support level). The second support level may also be higher than the first support level, requiring normal or high-flow ventricular assist for the target. In the second stage, it is difficult to determine whether the valve is in a normal opening and closing state. If the valve stops opening during the heartbeat cycle, the predicted ventricular pressure data in the second stage mentioned above may be affected by the continued closure of the valve, potentially leading to abnormal ventricular pressure readings. Typically, when the valve is continuously closed, systolic ventricular pressure drops significantly, while diastolic ventricular pressure is less affected; diastolic pressure remains almost constant regardless of whether the valve is continuously closed or normally open. In the prediction relationship, considering the relative ease of obtaining arterial pressure, the assumption that the ventricular pressure during systolic opening is approximately equal to the arterial pressure is a crucial reference feature. Therefore, the predicted ventricular pressure during systole is often assumed to be equal to the arterial pressure. Thus, when the valve stops opening, even if the actual systolic pressure is lower than the arterial pressure, the device will still increase the ventricular pressure signal to make it equal, resulting in a predicted systolic pressure higher than the actual systolic pressure. Under this prediction relationship, the predicted systolic pressure is almost equal to the arterial pressure, conforming to normal patterns, making it difficult to detect valvular abnormalities by judging the difference between systolic and arterial pressure (because the difference is eliminated by fitting). However, the inventors of this disclosure further discovered that although ventricular diastolic pressure is less affected by the continuous closure of the valve in practice, it is more affected by the continuous closure of the valve in predictive relationships. This is because once the valve stops opening, the ventricular pressure signal will be excessively increased, and the ventricular diastolic pressure will also be excessively increased, causing the ventricular diastolic pressure, which should be kept at a low level, to be pulled up to an abnormal level.

[0055] Therefore, in the technical solution provided by this disclosure, the ventricular diastolic pressure, which is greatly affected by the valve state in the prediction relationship, is used as the judgment object. First, the first ventricular diastolic pressure is determined in the first stage when the valve can open and close normally. Then, the ventricular pressure data predicted in the second stage is compared with the first ventricular diastolic pressure to determine the blood pump suction strength information that can characterize the probability of abnormal events such as aspiration and continuous valve closure. This makes it easier for users to quickly judge whether the blood pump support level is too high and improves the safety of the blood pump.

[0056] The reason why the suction intensity information is ultimately determined rather than a direct judgment of the valve status is that the movement within the heart is complex and there are individual differences. A slight abnormal increase in ventricular diastolic pressure cannot be absolutely considered as the occurrence of a sustained valvular closure event or aspiration event. However, an increase in the blood pump support level will cause an increase in ventricular diastolic pressure in the above-mentioned predictive relationship. Therefore, the inventors of this disclosure believe that by determining the suction intensity information that can characterize the probability of the occurrence of abnormal events, more information can be conveyed to the surgeon. The surgeon can further judge whether a sustained valvular closure event, aspiration event or other abnormal events have occurred based on the intensity information. The surgeon can also adjust the blood pump support level in a timely manner based on the intensity information to effectively prevent the occurrence of the above-mentioned abnormal events.

[0057] Optionally, step 303 may include: determining the second ventricular diastolic pressure corresponding to the diastolic phase in the ventricular pressure data; and determining the suction intensity information based on the difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure.

[0058] As mentioned earlier, if the valves stop opening, the ventricular pressure signal will be elevated, and the diastolic pressure will also be correspondingly elevated, causing the diastolic pressure, which should be at a low or normal level, to rise to an abnormal level. Therefore, by comparing the difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure in the predicted ventricular pressure data, the aforementioned suction strength information can be accurately determined. The greater the suction strength of the blood pump, the greater the difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure.

[0059] The aforementioned difference information can be the difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure. The difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure is determined as the suction strength information.

[0060] The suction strength is determined directly by the difference between the diastolic pressure of the second ventricle and the diastolic pressure of the first ventricle, which improves the detection efficiency of suction strength and simplifies the quantification process of suction strength.

[0061] In one possible implementation, after determining the suction strength information, suction event prevention information and / or suction event alarm information can be issued based on the suction strength information.

[0062] Since the suction intensity information described above can characterize the probability of an aspiration event, aspiration event prevention message can be issued once the suction intensity reaches a certain value, such as exceeding a first threshold, to remind the surgeon to prevent an aspiration event from occurring. It should be noted that this aspiration event prevention message can be a preventative reminder issued before an aspiration event occurs. Furthermore, if the suction intensity rises to a relatively high value, such as exceeding a second threshold, an aspiration event alarm message can be issued to remind the surgeon that an aspiration event has occurred within the heart.

[0063] In one possible implementation, after determining the suction strength information, the blood pump support level information can also be determined based on the suction strength information; and a prompt message corresponding to the support level information can be issued.

[0064] The suction strength of a blood pump is positively correlated with its support level. If the pump's support level, such as the set speed or flow rate, is too high, it will cause excessive suction on the blood in the ventricles, potentially unloading the left ventricular pressure and preventing the valves from opening. Conversely, if the suction strength is detected, the pump's support level can be determined based on that strength; there is a direct correlation between the two.

[0065] In one example, the aforementioned support level information could be a warning message indicating that the blood pump support level is too high. For instance, if the suction intensity exceeds a third threshold, a warning message indicating that the blood pump support level is too high would be issued to promptly notify the surgeon.

[0066] In one possible implementation, after determining the suction strength information, the opening and closing state of the valve can also be determined based on the suction strength information, and indication information corresponding to the opening and closing state of the valve can be issued.

[0067] For example, if the suction intensity exceeds a fourth threshold, an indication is issued that the valve is in a normally closed state. By indicating the valve's opening and closing state through suction intensity, embodiments of this disclosure can predict the occurrence of a sustained valve closure event before it occurs and alert or remind the operator, thereby improving the safety of blood pump use.

[0068] If the valve is detected to be continuously closed, the differential pressure prediction data needs to be recalibrated. This is because the actual differential pressure between the blood pump inlet and outlet changes after the valve is continuously closed, which may cause errors in the differential pressure prediction data. In order to make the differential pressure prediction data more accurate, the differential pressure data corresponding to the pump head is corrected based on the suction intensity information when the valve is detected to be continuously closed, so as to obtain the second differential pressure correction data.

[0069] As mentioned earlier, when the valve is normally closed, the predicted ventricular pressure data will be shifted upwards compared to the actual ventricular pressure data, with the upward shift amount being similar to the suction strength described above. This is equivalent to the predicted differential pressure data being shifted downwards. The actual systolic differential pressure is larger, but it is shifted downwards in the prediction relationship by a certain amount, i.e., the correction factor described below. Therefore, when the valve is detected to be normally closed, the abnormally shifted differential pressure data can be corrected according to the suction strength, thereby obtaining the correct differential pressure data.

[0070] Furthermore, after correcting the differential pressure prediction data, the flow rate data corresponding to the blood pump can be predicted based on the second differential pressure correction data, thereby improving the accuracy of flow rate detection.

[0071] There is a conversion relationship between differential pressure data and the flow rate of the interventional pump. When the valve is normally closed, the differential pressure prediction data is corrected by the suction intensity to obtain a relatively accurate second differential pressure correction data. Based on the relatively accurate second differential pressure correction data and the above conversion relationship, the flow rate of the interventional pump can be determined more accurately when the valve is normally closed.

[0072] The above is a description of the method for detecting blood pump suction intensity provided in the embodiments of this disclosure, which involves the prediction of ventricular pressure data, and will be described in detail below.

[0073] Figure 4 illustrates a flowchart 2 of a method for detecting the suction strength of a blood pump according to another embodiment of this disclosure. Optionally, determining the first ventricular diastolic pressure corresponding to the target object in step 310 may include the following steps (311-313).

[0074] Step 311: Obtain arterial pressure data, blood pump operation signal data, and at least one reference factor for the target object.

[0075] Among them, at least one reference factor characterizes the reference differential pressure or reference ventricular pressure corresponding to the pump head.

[0076] Step 312: Determine ventricular pressure correction data based on at least one reference factor, running signal data, and arterial pressure data.

[0077] In one possible implementation, the operating signal data can be converted to obtain differential pressure prediction data corresponding to the pump head; the differential pressure prediction data can be corrected based on a reference differential pressure to obtain differential pressure correction data; and ventricular pressure correction data can be determined based on arterial pressure data and differential pressure correction data. At least one reference factor is used to characterize the reference differential pressure corresponding to the pump head.

[0078] In the first stage, first operating signal data is acquired. This first operating signal data includes the operating signal data collected during the first stage when the blood pump device is in calibration operation. The operating signal data collected during this stage can be used as sample data to determine the calibration factor.

[0079] The first operating signal data is converted to obtain the differential pressure prediction data corresponding to the pump head. Specifically, after obtaining the first operating signal data, it can be directly converted into differential pressure prediction data according to the above conversion relationship. The differential pressure prediction data here is the prediction data obtained directly from the above operating signal data sample.

[0080] Identify feature points in the differential pressure prediction data that are associated with one or more scenarios. These scenarios are related to pressure waveform characteristics and time; therefore, these feature points can be determined by identifying differential pressure waveform characteristics or performing timestamp matching. For example, if we need to identify feature points under aortic valve open conditions, we need to determine the differential pressure waveform characteristics at the pump head under these conditions. When the aortic valve is open, the left ventricle is connected to the aorta, so the left ventricular pressure and aortic pressure are essentially the same, which can also be considered a pressure waveform feature. Furthermore, the fact that the left ventricular pressure and aortic pressure are essentially the same also means that the actual differential pressure at the pump head is approximately 0, which can be the aforementioned reference differential pressure. The reference differential pressure is the actual differential pressure at the pump head when the valve is open, which is approximately 0.

[0081] By comparing the predicted pressure difference and the reference pressure difference corresponding to this feature point, a correction factor that characterizes the pressure difference offset error can be determined. Based on this correction factor, the pressure difference prediction data curve is shifted to align the predicted pressure difference corresponding to this feature point with the reference pressure difference, thus obtaining the pressure difference correction data. Then, based on the arterial pressure data and the pressure difference correction data, accurate ventricular pressure correction data can be obtained, thereby determining the first ventricular diastolic pressure.

[0082] In another possible implementation, the operating signal data can also be converted and processed to obtain the differential pressure prediction data corresponding to the pump head; however, unlike the previous implementation, here the ventricular pressure prediction data can be determined first based on the arterial pressure data and the differential pressure prediction data. Then, the ventricular pressure prediction data is corrected based on the reference ventricular pressure to obtain the corrected ventricular pressure data.

[0083] The aforementioned reference ventricular pressure can be the actual ventricular pressure corresponding to the aforementioned feature point. For example, when the aortic valve is open, the ventricular pressure equals the arterial pressure. Therefore, the aforementioned reference ventricular pressure can be the arterial pressure when the aortic valve is open, i.e., the systolic arterial pressure. When correcting the predicted ventricular pressure data, a feature point when the aortic valve is open can be found, such as the maximum value in the predicted ventricular pressure data. Then, by comparing the predicted ventricular pressure corresponding to this point with the arterial pressure detected at the same time, a correction factor that can characterize the ventricular pressure offset error can be determined. By aligning the predicted ventricular pressure corresponding to this point with the arterial pressure detected at the same time, the corrected ventricular pressure data can be obtained, thereby determining the first ventricular diastolic pressure.

[0084] Step 313: Identify the data in diastole from the ventricular pressure correction data to obtain the first ventricular diastolic pressure.

[0085] Accordingly, as shown in Figure 4, step 320 above may include the following steps (321-323).

[0086] Step 321: In the second stage of blood pump operation, acquire arterial pressure data of the target object, blood pump operation signal data, and at least one correction factor.

[0087] Wherein, at least one correction factor characterizes at least one of the differential pressure offset error corresponding to the pump head and the ventricular pressure offset error; the correction factor is determined under a first stage, the first stage including one or more situations in which the actual differential pressure corresponding to the pump head or the actual ventricular pressure can be determined, measured or estimated. One or more situations include, but are not limited to, situations in which the blood pump operates at a first support level, and the heart valves are able to open and close under the first support level.

[0088] Step 322: Convert and process the operating signal data to obtain the differential pressure prediction data corresponding to the pump head.

[0089] The conversion process between the operating signal data and the differential pressure prediction data in the second stage is similar to that in the first stage, and will not be repeated here.

[0090] Step 323: Determine ventricular pressure data based on differential pressure prediction data, arterial pressure data, and at least one correction factor.

[0091] In one possible implementation, at least one correction factor can be applied to offset the differential pressure prediction data to obtain differential pressure corrected data; and the difference between the arterial pressure data and the differential pressure corrected data can be determined as ventricular pressure data.

[0092] As mentioned above, in the first stage, a correction factor can be obtained to correct the original conversion relationship. In some examples, this correction factor represents the differential pressure offset error corresponding to the pump head. By using this correction factor to perform offset correction on the differential pressure prediction data, differential pressure correction data can be obtained. Then, the difference between the arterial pressure data and the differential pressure correction data can be used as the predicted ventricular pressure data.

[0093] In another possible implementation, ventricular pressure prediction data can be determined first and then corrected. Specifically, the difference between arterial pressure data and pressure gradient prediction data can be determined as ventricular pressure prediction data; ventricular systolic pressure prediction data corresponding to the systolic phase can be identified from the ventricular pressure prediction data, and arterial systolic pressure data corresponding to the systolic phase can be identified from the arterial pressure data; the pressure gradient offset between the ventricular systolic pressure prediction data and the arterial systolic pressure data can be corrected to a target pressure gradient indicated by at least one correction factor to obtain ventricular pressure data.

[0094] If the correction factor determined in the first stage is a correction factor characterizing the ventricular pressure offset error, then the difference between the arterial pressure data and the pressure difference prediction data can be used to obtain preliminary predicted ventricular pressure data. Then, the ventricular pressure prediction data can be offset corrected according to the correction factor. Specifically, this can involve shifting the curve of the ventricular pressure prediction data upwards or downwards, thereby keeping the error between the systolic ventricular pressure prediction data (ventricular systolic pressure prediction data) and the arterial systolic pressure data within the target pressure difference range. This yields corrected ventricular pressure data, which is then used to determine the difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure, i.e., the suction intensity.

[0095] In an exemplary embodiment, in order to determine the correction factor, the first stage further includes the following steps: acquiring the blood pump's operating signal data and at least one reference factor, wherein the at least one reference factor characterizes the reference differential pressure corresponding to the pump head under one or more conditions; performing conversion processing on the operating signal data sample to obtain differential pressure prediction data corresponding to the pump head; determining feature points in the differential pressure prediction data that are associated with one or more conditions; and determining the correction factor based on the predicted differential pressure corresponding to the feature points and at least one reference factor.

[0096] One or more of these situations include the aortic valve opening during the cardiac cycle, in which case the left ventricular pressure and the aortic pressure are essentially the same. This means that during the phase when the aortic valve remains open, if either the left ventricular pressure or the aortic pressure is known, the other can also be known to be estimated as the same pressure as the former, or the net pressure corresponding to the pump head can be known to be estimated as 0.

[0097] The process of determining suction intensity is briefly explained below with reference to the graphs to facilitate understanding by those skilled in the art. Please refer to Figure 5, which exemplarily illustrates a theoretical schematic diagram of cardiac pressure curves under normal aortic valve opening and closing conditions. This includes aortic pressure curve 51, left ventricular pressure curve 52, and pressure differential curve 53. It can be seen that during the aortic valve opening phase, aortic pressure curve 51 and left ventricular pressure curve 52 are very close; therefore, pressure differential curve 53 also approaches 0 during the aortic valve opening phase.

[0098] Please refer to Figure 6, which exemplarily illustrates a curve diagram of differential pressure prediction data. In the first stage, the pump head differential pressure can be predicted based on the conversion relationship between operating signal data and differential pressure data, resulting in differential pressure prediction data curve 61. The left ventricular pressure prediction curve 62 can be determined based on differential pressure prediction data curve 61 and aortic pressure curve 51. However, since the conversion relationship is determined based on historical or experimental data, during the actual operation of the interventional pump, the predicted differential pressure prediction data curve 61 has a differential pressure offset error 63 compared to the correct differential pressure curve 53 in Figure 5. Correspondingly, the left ventricular pressure prediction curve 62 has a ventricular pressure offset error 64 compared to the left ventricular pressure curve 52 in Figure 5, or it can be understood that the left ventricular pressure prediction curve 62 and the aortic pressure curve 51 have a ventricular pressure offset error 64, since theoretically they should be quite close.

[0099] After determining the differential pressure offset error 63 and / or ventricular pressure offset error 64 in the first stage, in the second stage, the differential pressure offset error 63 and / or ventricular pressure offset error 64 can be used as correction factors. In subsequent operation, these correction factors can be used to offset and correct the differential pressure prediction data curve 61 and / or the left ventricular pressure prediction curve 62, resulting in a differential pressure correction data curve and a corrected left ventricular pressure curve. Figure 7 exemplifies the curve diagram of pressure curve correction based on the correction factors. Specifically, shifting the differential pressure prediction data curve 61 upwards by the distance indicated by the differential pressure offset error 63 yields the differential pressure correction data curve 71; or shifting the left ventricular pressure prediction curve 62 downwards by the distance indicated by the ventricular pressure offset error 64 yields the ventricular pressure correction curve 72. Thus, after correction by the correction factors, the differential pressure correction data curve 71 is closer to the differential pressure curve 53 shown in Figure 5, and the ventricular pressure correction curve 72 is closer to the left ventricular pressure curve 52 shown in Figure 5, thereby obtaining more accurate left ventricular pressure and pump head differential pressure.

[0100] However, if the blood pump support level is too high in the second stage, causing the valve to close, the data curve corrected by the aforementioned correction factor will deviate from the true value at this time. Please refer to Figure 8, which exemplarily shows a theoretical schematic diagram of the cardiac pressure curve when the valve is normally closed. As shown in Figure 8, since the aortic valve is not open during systole and is normally closed, the left ventricular pressure curve 81 and the aortic pressure curve 51 are no longer close during systole, but rather there is a certain pressure difference 83 between them. Correspondingly, the pressure difference curve 82 is no longer close to 0 during systole, but has a certain pressure difference 83. Comparing Figure 8 and Figure 5, the left ventricular pressure curve 81 and the left ventricular pressure curve 52 are relatively close during diastole.

[0101] When the valves are normally closed, the reference relationships between the left ventricular pressure curve 81 and the aortic pressure curve 51 during systole are no longer equal. Therefore, the data calibration conditions for the valve-open state are no longer applicable to the valve-closed state. However, for the machine, predicting the differential pressure and / or left ventricular pressure according to the aforementioned correction factor offset when the valves are normally closed will result in prediction errors.

[0102] Figure 9 illustrates an exemplary curve for determining the suction strength of a blood pump. If the pressure difference prediction data curve is further offset according to the aforementioned correction factor, the pressure difference correction data curve 91 will shift downwards compared to the actual pressure difference curve 82, thus reducing the actual pressure difference 83 to a pressure difference 93. Correspondingly, the ventricular pressure correction curve 92 will shift upwards compared to the actual left ventricular pressure curve 81, and the difference between systolic ventricular pressure and aortic pressure will also be reduced to 93. This results in a difference 94 between the corrected ventricular pressure correction curve 92 and the actual left ventricular pressure curve 81 during diastole, i.e., the difference between the first ventricular diastolic pressure and the second ventricular diastolic pressure, which can be used to determine the suction strength of the blood pump.

[0103] Furthermore, as shown in Figure 10, which exemplarily illustrates a schematic diagram of secondary correction of the pressure curve based on suction intensity, after detecting the aforementioned suction intensity, i.e., after the aforementioned difference 94 appears, the ventricular pressure correction curve 92 can be offset based on the difference 94, for example, offset downward by the distance indicated by the difference 94, to obtain the secondary corrected ventricular pressure correction data curve 101. Alternatively, the differential pressure correction data curve 91 can be offset a second time based on the difference, for example, offset upward by the distance indicated by the difference 94, to obtain the second differential pressure correction data curve 102. In this way, under the normally closed valve state, secondary correction of the pump head differential pressure and left ventricular pressure is achieved through suction intensity, improving the accuracy of differential pressure and left ventricular pressure prediction. Moreover, the secondary corrected differential pressure can also be used to correct the flow rate, thereby obtaining a more accurate interventional pump flow rate.

[0104] The following are embodiments of the apparatus disclosed herein, which can be used to execute embodiments of the method disclosed herein. For details not disclosed in the apparatus embodiments of this disclosure, please refer to the embodiments of the method disclosed herein.

[0105] Please refer to Figure 11, which shows a block diagram of a blood pump suction strength detection device according to an embodiment of this disclosure. This device has the function of implementing the above-described blood pump suction strength detection method; the function can be implemented in hardware or by hardware executing corresponding software. This device can be a computer device or can be installed within a computer device. The device 1100 may include:

[0106] The first pressure determination module 1110 is used to determine the first ventricular diastolic pressure corresponding to the target object during the first stage of operation after the blood pump intervenes in the heart of the target object; wherein, the first stage refers to the stage in which the blood pump operates at the first support level, and the heart valves can open and close at the first support level.

[0107] The second pressure determination module 1120 is used to acquire ventricular pressure data corresponding to the target object in the second stage of blood pump operation. The second stage refers to the stage in which the blood pump operates at a second support level. The second support level is higher than or equal to the first support level. The ventricular pressure data is data predicted based on a prediction relationship. The prediction relationship is determined based on data obtained when the valve is in a normal opening and closing state.

[0108] The suction intensity determination module 1130 is used to determine the suction intensity information of the blood pump based on the first ventricular diastolic pressure and ventricular pressure data. The suction intensity information is positively correlated with the probability of abnormal cardiac events, including valve closure events and / or suction events.

[0109] The technical solution provided in this disclosure uses ventricular diastolic pressure, which is greatly affected by valve status in the prediction relationship, as the judgment object. First, the first ventricular diastolic pressure is determined under the first stage where the valve can open and close normally. Then, the ventricular pressure data predicted in the second stage is compared with the first ventricular diastolic pressure to determine the blood pump suction strength information that can characterize the probability of abnormal events such as aspiration and continuous valve closure. This makes it easier for users to quickly judge whether the blood pump support level is too high and improves the safety of the blood pump.

[0110] It should be noted that the apparatus provided in the above embodiments is only illustrated by the division of the above functional modules when implementing its functions. In actual applications, the above functions can be assigned to different functional modules as needed, that is, the internal structure of the device can be divided into different functional modules to complete all or part of the functions described above. In addition, the apparatus and method embodiments provided in the above embodiments belong to the same concept, and the specific implementation process can be found in the method embodiments, which will not be repeated here.

[0111] This disclosure provides an electronic device in one embodiment. The electronic device can be a control console in a blood pump device, or a computer device within the flushing device of a blood pump device. The electronic device includes a processor and a memory. The memory stores at least one instruction, at least one program, a code set, or an instruction set. The processor loads and executes the at least one instruction, at least one program, code set, or instruction set to implement the blood pump suction strength detection method provided in the above embodiment. Specifically:

[0112] Typically, electronic devices include a processor and memory.

[0113] The processor may include one or more processing cores, such as a quad-core processor, an octa-core processor, etc. The processor may be implemented using at least one hardware form selected from DSP (Digital Signal Processing), FPGA (Field Programmable Gate Array), and PLA (Programmable Logic Array). The processor may also include a main processor and coprocessors. The main processor, also known as the CPU (Central Processing Unit), is used to process data in the wake-up state; the coprocessor is a low-power processor used to process data in the standby state. In some embodiments, the processor may integrate a GPU (Graphics Processing Unit), which is responsible for rendering and drawing the content required to be displayed on the screen. In some embodiments, the processor may also include an AI (Artificial Intelligence) processor, which is used to handle computational operations related to machine learning.

[0114] The memory may include one or more computer-readable storage media, which may be non-transitory. The memory may also include high-speed random access memory and non-volatile memory, such as one or more disk storage devices or flash memory devices. In some embodiments, the non-transitory computer-readable storage media in the memory is used to store at least one instruction, at least one program, code set, or instruction set, and is configured to be executed by one or more processors to implement the above-described method for detecting the suction strength of a blood pump.

[0115] In some embodiments, the electronic device may also optionally include: a peripheral device interface and at least one peripheral device. The processor, memory, and peripheral device interface can be connected via a bus or signal line. Each peripheral device can be connected to the peripheral device interface via a bus, signal line, or circuit board. Specifically, the peripheral device includes at least one of: radio frequency circuitry, a touch display screen, a camera assembly, an audio circuit, a positioning assembly, and a power supply.

[0116] Those skilled in the art will understand that the above structure does not constitute a limitation on the electronic device, and may include more or fewer components, or combine certain components, or adopt different component arrangements.

[0117] In some possible implementations, the method for detecting the blood pump suction strength described herein can be implemented in the software of an electronic device. Some hardware electronic device platforms particularly suitable for implementation include microcontrollers, FPGAs, operating system-based microprocessor platforms, or cloud computing platforms. The former allows for faster and more direct access to data, while the latter is more likely to utilize complex models. It can also be implemented in analog circuits.

[0118] In an exemplary embodiment, a blood pump device is also provided, which includes a processor and a memory. The memory stores at least one instruction, at least one program, code set, or instruction set. The processor loads and executes the at least one instruction, at least one program, code set, or instruction set to implement the above-described method for detecting the suction strength of the blood pump.

[0119] In an exemplary embodiment, a computer-readable storage medium is also provided, which stores at least one instruction, at least one program, code set, or instruction set, wherein the at least one instruction, at least one program, code set, or instruction set is executed by a processor to implement the above-described method for detecting the suction strength of a blood pump.

[0120] Optionally, the computer-readable storage medium may include: ROM (Read Only Memory), RAM (Random Access Memory), SSD (Solid State Drives), or optical disc, etc. The random access memory may include ReRAM (Resistance Random Access Memory) and DRAM (Dynamic Random Access Memory).

[0121] In an exemplary embodiment, a computer program product or computer program is also provided, which includes computer instructions stored in a computer-readable storage medium. A processor of a computer device reads the computer instructions from the computer-readable storage medium and executes the computer instructions, causing the computer device to perform the aforementioned method for detecting the blood pump suction strength.

[0122] It should be understood that "multiple" as used herein refers to two or more. "And / or" describes the relationship between related objects, indicating that three relationships can exist. For example, A and / or B can represent: A alone, A and B simultaneously, or B alone. The character " / " generally indicates that the preceding and following related objects are in an "or" relationship. Furthermore, the step numbers described herein are merely illustrative of one possible execution order. In some other embodiments, the steps may not be executed in numerical order, such as two steps with different numbers being executed simultaneously, or two steps with different numbers being executed in the reverse order of the illustration. This disclosure does not limit this.

[0123] Furthermore, in the specific embodiments of this disclosure, data such as user information are involved. When the above embodiments of this disclosure are applied to specific products or technologies, user permission or consent is required, and the collection, use and processing of related data must comply with the relevant laws, regulations and standards of the relevant countries and regions.

[0124] The above description is merely an exemplary embodiment of this disclosure and is not intended to limit this disclosure. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this disclosure should be included within the protection scope of this disclosure.

Claims

1. A method for detecting the suction strength of a blood pump, wherein, The method includes: In the first stage of operation after the blood pump intervenes in the heart of the target object, the first ventricular diastolic pressure corresponding to the target object is determined; wherein, the first stage refers to the stage in which the blood pump operates at a first support level, and the valves of the heart are able to open and close at the first support level; In the second phase of the blood pump's operation, ventricular pressure data corresponding to the target object is acquired. This second phase refers to the stage where the blood pump operates at a second support level, which is higher than or equal to the first support level. The ventricular pressure data is based on a predictive relationship determined using data obtained when the valves are in a normal opening and closing state. Based on the first ventricular diastolic pressure and the ventricular pressure data, the suction strength information of the blood pump is determined. The suction strength information is positively correlated with the probability of abnormal events occurring in the heart. The abnormal events include valve closure events and / or suction events.

2. The method according to claim 1, wherein, The blood pump includes a pump head, and determining the first ventricular diastolic pressure corresponding to the target object includes: Acquire arterial pressure data of the target object, operating signal data of the blood pump, and at least one reference factor, wherein the at least one reference factor characterizes the reference differential pressure or reference ventricular pressure corresponding to the pump head; Based on the at least one reference factor, the operating signal data, and the arterial pressure data, ventricular pressure correction data are determined; and The first ventricular diastolic pressure is obtained by identifying the data in the diastolic phase of the ventricular pressure correction data.

3. The method according to claim 2, wherein, The determination of ventricular pressure correction data based on the at least one reference factor, the operating signal data, and the arterial pressure data includes: The operating signal data is converted and processed to obtain the differential pressure prediction data corresponding to the pump head; The differential pressure prediction data is corrected based on the reference differential pressure corresponding to the pump head to obtain the differential pressure correction data; and Based on the arterial pressure data and the differential pressure correction data, the ventricular pressure correction data is determined.

4. The method according to claim 2, wherein, The determination of ventricular pressure correction data based on the at least one reference factor, the operating signal data, and the arterial pressure data includes: The operating signal data is converted and processed to obtain the differential pressure prediction data corresponding to the pump head; Based on the arterial pressure data and the differential pressure prediction data, the ventricular pressure prediction data is determined; and The ventricular pressure prediction data is corrected based on the reference ventricular pressure to obtain the corrected ventricular pressure data.

5. The method according to claim 1, wherein, In the second stage of the blood pump operation, acquiring the ventricular pressure data corresponding to the target object includes: In the second stage of the blood pump operation, arterial pressure data of the target object, operating signal data of the blood pump, and at least one correction factor are acquired; wherein, the at least one correction factor characterizes at least one of the differential pressure offset error and ventricular pressure offset error corresponding to the pump head; the correction factor is determined in the first stage, which includes one or more cases where the actual differential pressure or actual ventricular pressure corresponding to the pump head can be determined, measured, or estimated. The operating signal data is converted and processed to obtain the differential pressure prediction data corresponding to the pump head; and The ventricular pressure data are determined based on the differential pressure prediction data, the arterial pressure data, and the at least one correction factor.

6. The method according to claim 5, wherein, The step of determining the ventricular pressure data based on the differential pressure prediction data, the arterial pressure data, and the at least one correction factor includes: The differential pressure prediction data is offset-corrected by applying the at least one correction factor to obtain differential pressure corrected data; and The difference between the arterial pressure data and the differential pressure correction data is determined as the ventricular pressure data.

7. The method according to claim 5, wherein, The step of determining the ventricular pressure data based on the differential pressure prediction data, the arterial pressure data, and the at least one correction factor includes: The difference between the arterial pressure data and the differential pressure prediction data is determined as the ventricular pressure prediction data; Identify the predicted ventricular systolic pressure data corresponding to the systolic phase from the predicted ventricular pressure data, and identify the arterial systolic pressure data corresponding to the systolic phase from the arterial pressure data; and The pressure difference offset between the predicted ventricular systolic pressure data and the arterial systolic pressure data is corrected to the target pressure difference indicated by the at least one correction factor to obtain the ventricular pressure data.

8. The method according to claim 5, wherein, The method further includes the following in the first stage after the blood pump is inserted into the target object: Acquire the operating signal data of the blood pump and at least one reference factor, wherein the at least one reference factor characterizes the reference differential pressure corresponding to the pump head under one or more conditions; The operating signal data samples are converted and processed to obtain the differential pressure prediction data corresponding to the pump head; Identify feature points in the differential pressure prediction data that are associated with one or more of the aforementioned conditions; and The correction factor is determined based on the predicted pressure difference corresponding to the feature point and the at least one reference factor.

9. The method according to claim 1, wherein, The step of determining the suction strength information of the blood pump based on the first ventricular diastolic pressure and the ventricular pressure data includes: Determine the second ventricular diastolic pressure corresponding to diastole in the ventricular pressure data; and The suction strength information is determined based on the difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure.

10. The method according to claim 9, wherein, The step of determining the suction intensity information based on the difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure includes: The difference between the second ventricular diastolic pressure and the first ventricular diastolic pressure is determined as the suction intensity information.

11. The method according to any one of claims 1 to 10, wherein, The method further includes: Based on the suction strength information, suction event prevention information and / or suction event alarm information are issued.

12. The method according to any one of claims 1 to 10, wherein, The method further includes: Based on the suction strength information, the support level information of the blood pump is determined; and Issue a prompt message corresponding to the support level information.

13. The method according to any one of claims 1 to 10, wherein, The method further includes: Based on the suction intensity information, the opening and closing state of the valve is determined; and It issues indication information corresponding to the opening and closing state of the valve.

14. The method according to any one of claims 1 to 10, wherein, The method further includes: When the valve is detected to be in a continuously closed state, the differential pressure data corresponding to the pump head is corrected based on the suction intensity information to obtain second differential pressure correction data.

15. The method according to claim 14, wherein, The method further includes: Based on the second differential pressure correction data, the flow rate data corresponding to the blood pump is predicted.

16. A device for detecting the suction strength of a blood pump, wherein, The device includes: The first pressure determination module is used to determine the first ventricular diastolic pressure corresponding to the target object during the first stage of operation after the blood pump intervenes in the heart of the target object; wherein, the first stage refers to the stage in which the blood pump operates at a first support level, and the valves of the heart are able to open and close at the first support level; A second pressure determination module is used to acquire ventricular pressure data corresponding to the target object during the second phase of the blood pump's operation. The second phase refers to the stage where the blood pump operates at a second support level, which is higher than or equal to the first support level. The ventricular pressure data is data predicted based on a prediction relationship, which is determined based on data obtained when the valve is in a normal opening and closing state. The suction intensity determination module is used to determine the suction intensity information of the blood pump based on the first ventricular diastolic pressure and the ventricular pressure data. The suction intensity information is positively correlated with the probability of an abnormal event occurring in the heart. The abnormal events include a valve closure event and / or aspiration events.

17. An electronic device, wherein, The control device includes a processor and a memory, wherein the memory stores at least one instruction, at least one program, a code set, or an instruction set, and the at least one instruction, the at least one program, the code set, or the instruction set is loaded and executed by the processor to implement the method for detecting the blood pump suction strength as described in any one of claims 1 to 15.

18. A blood pump device, wherein, The blood pump device includes a processor and a memory, wherein the memory stores at least one instruction, at least one program, code set, or instruction set, and the at least one instruction, the at least one program, the code set, or the instruction set is loaded and executed by the processor to implement the method for detecting the blood pump suction strength as described in any one of claims 1 to 15.

19. A computer-readable storage medium, wherein, The storage medium stores at least one instruction, at least one program, code set, or instruction set, wherein the at least one instruction, the at least one program, the code set, or instruction set is loaded and executed by a processor to implement the method for detecting the blood pump suction strength as described in any one of claims 1 to 15.

20. A computer program product, wherein, The computer program product includes computer instructions stored in a computer-readable storage medium. The processor of the computer device reads the computer instructions from a computer-readable storage medium, and the processor executes the computer instructions to cause the computer device to perform a method for detecting the suction strength of a blood pump as described in any one of claims 1 to 15.

Images