Methods, devices, electronic equipment, and storage media for determining the pump flow rate of a blood pump.

Abstract

This application discloses a method, apparatus, electronic device, and storage medium for determining the pumping flow rate of a blood pump. The method includes: acquiring a first correspondence between the absolute value of a first current difference and a first pumping flow rate value at different rotational speeds when the blood pump is in an in vitro testing simulation environment; acquiring a first reference current value for each current cycle at each rotational speed when the blood pump is in an actual human body environment of the test subject; for each current cycle at each rotational speed, subtracting the first reference current value from the current value at each moment within the current cycle to obtain at least one second absolute current difference value; searching within the first correspondence for each second absolute current difference value corresponding to each current cycle at each rotational speed to obtain each second pumping flow rate value corresponding to each second absolute current difference value; and determining a target pumping flow rate value based on each second pumping flow rate value at each current cycle for each rotational speed. This achieves the effect of accurately determining the pumping flow rate of the blood pump.

Description

Technical Field

[0001] This application relates to the field of information processing, specifically to a method, apparatus, electronic device, and storage medium for determining the pumping flow rate of a blood pump. Background Technology

[0002] Short-term hemodynamic support is an effective treatment for cardiovascular and related complications. It provides hemodynamic support for a short period to promote rapid recovery of cardiac and other vital tissue and organ function. The effectiveness of short-term hemodynamic support is mainly reflected in the increase in aortic pressure and cardiac output. Cardiac output under short-term hemodynamic support is primarily determined by the patient's own cardiac output and the pumping flow rate of the short-term hemodynamic support. Therefore, accurately calibrating these two important effectiveness indicators is crucial.

[0003] Currently, pump flow rate is mainly calculated based on the relationship between the pump's current and the blood flow rate pumped by the catheter, while the patient's own cardiac output is calculated based on the pump flow rate. The applicant discovered that differences in the motors and catheters of different blood pumps cause variations in the pump's current, making it impossible to accurately represent the true pump flow rate based on the pump's current. Summary of the Invention

[0004] The purpose of this application is to provide a method, apparatus, electronic device, and storage medium for determining the pumping flow rate of a blood pump, so as to achieve the effect of accurately determining the pumping flow rate of the blood pump.

[0005] The technical solution of this application is as follows:

[0006] Firstly, a method for determining the pumping flow rate of a blood pump is provided, the method comprising:

[0007] The first correspondence between the absolute value of the first current difference and the first pump blood flow value is obtained when the blood pump is in an in vitro test simulation environment at different speeds.

[0008] The first reference current value of each current cycle is obtained when the blood pump is in the actual human body environment of the test subject, at each rotation speed.

[0009] For each current cycle in each rotational speed, the difference between the first reference current value and the current value at different times within the current cycle is calculated to obtain at least one absolute value of the second current difference.

[0010] For each current cycle in each rotational speed, at least one absolute value of the second current difference is searched in the first correspondence to obtain at least one second pump blood flow value corresponding to at least one absolute value of the second current difference;

[0011] For each rotational speed, the target pump blood flow value is determined based on at least one second pump blood flow value under each current cycle.

[0012] Secondly, a device for determining the pumping flow rate of a blood pump is provided, the device comprising:

[0013] The first acquisition module is used to acquire the first correspondence between the absolute value of the first current difference and the blood flow value of the first pump when the blood pump is in an in vitro test simulation environment at different speeds.

[0014] The second acquisition module is used to acquire the first reference current value of each current cycle during the operation of the blood pump at each rotation speed in the actual human body environment of the test object.

[0015] The first determining module is used to calculate the difference between the first reference current value and the current value at different times within the current cycle for each current cycle in each rotational speed, so as to obtain at least one absolute value of the second current difference.

[0016] The second determining module is used to search in the first correspondence for at least one absolute value of the second current difference corresponding to each current cycle in each rotation speed, and to obtain at least one second pump blood flow value corresponding to at least one absolute value of the second current difference.

[0017] The third determining module is used to determine the target pump blood flow value for each rotational speed based on at least one second pump blood flow value under each current cycle. Thirdly, embodiments of this application provide an electronic device including a processor, a memory, and a program or instructions stored in the memory and executable on the processor. When the program or instructions are executed by the processor, they implement the steps of the pump blood flow determination and positioning method for any of the blood pumps described in embodiments of this application.

[0018] Fourthly, embodiments of this application provide a readable storage medium storing a program or instructions, which, when executed by a processor, implement the steps of the method for determining and locating the blood flow rate of a blood pump as described in any embodiment of this application.

[0019] The technical solutions provided by the embodiments of this application bring at least the following beneficial effects:

[0020] The information processing method provided in this application embodiment obtains a first correspondence between the absolute value of a first current difference and the first pump blood flow value at different rotation speeds in an in vitro test simulation environment; obtains a first reference current value for each current cycle during the operation of the blood pump at each rotation speed in the actual human body environment of the test object; for each current cycle in each rotation speed, the first reference current value is subtracted from the current value at different times within the current cycle to obtain at least one second absolute current difference value; for each current cycle in each rotation speed, the at least one second absolute current difference value is searched in the first correspondence to obtain at least one second pump blood flow value corresponding to the at least one second absolute current difference value; for each rotation speed, based on the at least one second pump blood flow value in each current cycle, the target pump blood flow value is determined. In this way, the pump blood flow value of the blood pump is effectively characterized by the difference in current changes. Compared with the method of directly using current to characterize the pump blood flow value of the blood pump, the use of current difference can effectively reduce the error caused by the difference between different blood pump catheters, and achieve the effect of accurately determining the pump blood flow of the blood pump.

[0021] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Attached Figure Description

[0022] The accompanying drawings, which are incorporated in and form part of this specification, illustrate embodiments consistent with this application and, together with the description, serve to explain the principles of this application, and do not constitute an undue limitation of this application.

[0023] Figure 1 This is a schematic diagram of a method for determining the pumping blood flow rate of a blood pump, provided in an exemplary embodiment of this application. Figure 1 ;

[0024] Figure 2 This is a second correspondence diagram between the pressure difference at different rotational speeds and the second current value at each pressure difference, according to an exemplary embodiment of this application.

[0025] Figure 3 This is a third correspondence diagram between different pressure differences at different rotation speeds and the blood flow values ​​of the first pump at each pressure difference, according to an exemplary embodiment of this application.

[0026] Figure 4 This is a diagram showing the correspondence between the absolute values ​​of the pressure differences at different rotational speeds and the first current differences at each pressure difference, according to an exemplary embodiment of this application.

[0027] Figure 5 This is a graph showing the correspondence between the absolute value of the first current difference at different rotational speeds and the blood flow rate of the first pump, according to an exemplary embodiment of this application.

[0028] Figure 6 This is a current change curve within a cardiac cycle at a certain rotation speed, according to an exemplary embodiment of this application.

[0029] Figure 7 This is a graph showing the blood flow values ​​of the second pump during a certain current cycle at a certain rotational speed, according to an exemplary embodiment of this application.

[0030] Figure 8 This is a correction curve of the absolute value of the first current difference at a rotational speed n1 according to an exemplary embodiment of this application;

[0031] Figure 9 This is a correction curve of the absolute value of the first current difference at a rotational speed n2 according to an exemplary embodiment of this application;

[0032] Figure 10 This is a correction curve of the absolute value of the first current difference at a rotational speed n3 according to an exemplary embodiment of this application;

[0033] Figure 11 This is a structural block diagram of a blood pump blood flow determination device provided in an exemplary embodiment of this application;

[0034] Figure 12 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. Detailed Implementation

[0035] To enable those skilled in the art to better understand the technical solutions of this application, the technical solutions in the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. It should be understood that the specific embodiments described herein are merely intended to explain this application and not to limit it. For those skilled in the art, this application can be implemented without some of these specific details. The following description of the embodiments is merely to provide a better understanding of this application by illustrating examples.

[0036] It should be noted that the terms "first," "second," etc., used in the specification, claims, and accompanying drawings of this application are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of this application described herein can be implemented in orders other than those illustrated or described herein. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with this application. Rather, they are merely examples consistent with some aspects of this application as detailed in the appended claims.

[0037] To facilitate understanding of the technical solution of this application, the background of the embodiments of this application will be introduced first:

[0038] With a constant supply voltage to the blood pump motor, the current value reflects the motor's output power; the higher the current, the more work the motor performs. In an external blood pump motor system, the motor's external work includes the frictional work of overcoming the rotation of the external driven shaft rotor, the frictional work of the flexible drive shaft relative to the constraint layer, the frictional work of the internal bearing rotation, the rotational drive work of the impeller, drive shaft, and bearings, and the pumping work of the impeller on the blood. The absolute value of the motor current reflects the combined effect of these factors, not just the pumping work of the impeller on the blood. With other factors remaining constant, the higher the blood flow rate, the more work the impeller performs on the blood, and the higher the current value. However, catheters are not identical, and variations in tolerances between components can cause differences in the required frictional work. Therefore, different catheter bending states will also result in different frictional work of the drive shaft relative to the constraint layer. Thus, the pumping flow rate cannot be determined directly by correlating the impeller's work on the blood with the motor current value.

[0039] To address the aforementioned issues, this application provides a method for determining the pumping flow rate of a blood pump. This method involves: acquiring a first correspondence between the absolute value of a first current difference and a first pumping flow rate value at different rotational speeds when the blood pump is in an in vitro testing simulation environment; acquiring a first reference current value for each current cycle during operation at each rotational speed when the blood pump is in the actual human body environment of the test subject; subtracting the first reference current value from the current value at different times within each current cycle for each rotational speed to obtain at least one second absolute current difference value; searching within the first correspondence for the at least one second absolute current difference value corresponding to each current cycle at each rotational speed to obtain at least one second pumping flow rate value corresponding to the at least one second absolute current difference value; and determining a target pumping flow rate value based on the at least one second absolute current difference value for each rotational speed and each current cycle. Thus, by effectively characterizing the pumping flow rate value of the blood pump through the difference in current changes, compared to directly using current to characterize the pumping flow rate value, the use of current differences can effectively reduce the errors caused by differences between different blood pump catheters, achieving the effect of accurately determining the pumping flow rate of the blood pump.

[0040] The method for determining the blood flow rate of a blood pump provided in this application will be described in detail below with reference to the accompanying drawings, through specific embodiments and application scenarios.

[0041] Figure 1 This is a flowchart illustrating a method for determining the pumping blood flow rate of a blood pump according to an embodiment of this application. Figure 1 As shown, the method for determining the pump blood flow rate of a blood pump provided in this application embodiment may include steps 110-150.

[0042] Step 110: Obtain the first correspondence between the absolute value of the first current difference and the first pump blood flow value under different rotation speeds in an in vitro test simulation environment.

[0043] Step 120: Obtain the first reference current value for each current cycle during the operation of the blood pump at each rotation speed in the actual human body environment of the test subject.

[0044] Step 130: For each current cycle in each rotational speed, subtract the first reference current value from the current value at different times within the current cycle to obtain at least one absolute value of the second current difference.

[0045] Step 140: For each current cycle in each rotational speed, at least one absolute value of the second current difference is searched in the first correspondence to obtain at least one second pump blood flow value corresponding to at least one absolute value of the second current difference.

[0046] Step 150: For each rotational speed, determine the target pump blood flow value based on at least one second pump blood flow value under each current cycle.

[0047] In the embodiments of this application, a first correspondence is obtained between the absolute value of the first current difference and the first pump blood flow value at different rotation speeds in an in vitro test simulation environment; a first reference current value is obtained for each current cycle during the operation of the blood pump at each rotation speed in the actual human body environment of the test object; for each current cycle in each rotation speed, the difference between the first reference current value and the current value at different times within the current cycle is calculated to obtain at least one second absolute current difference value; for each current cycle in each rotation speed, the at least one second absolute current difference value is searched in the first correspondence to obtain at least one second pump blood flow value corresponding to the at least one second absolute current difference value; for each rotation speed, the target pump blood flow value is determined based on the at least one second pump blood flow value under each current cycle. In this way, the pump blood flow value of the blood pump is effectively characterized by the difference in current change. Compared with the method of directly using current to characterize the pump blood flow value of the blood pump, the use of current difference can effectively reduce the error caused by the difference between different blood pump catheters, and achieve the effect of accurately determining the pump blood flow of the blood pump.

[0048] The method for determining the pumping blood flow rate of the blood pump provided in the embodiments of this application will be described in detail below.

[0049] First, step 110 is introduced, which obtains the first correspondence between the absolute value of the first current difference and the first pump blood flow value under different rotation speeds in an in vitro test simulation environment.

[0050] Among them, the blood pump is a device that provides hemodynamic support to the patient.

[0051] In some embodiments of this application, the in vitro testing simulation environment can be an environment that simulates the human body in vitro, and the in vitro testing simulation environment is as close as possible to the environment inside the human body.

[0052] In one example, the fluid in the in vitro testing simulation environment can be selected to have a consistency equal to or close to that of blood, and a temperature equal to the blood temperature of the test subject (i.e., a human body, such as a patient), between 36 and 37°C. The fluid in the in vitro testing simulation environment can be a mixture of water and glycerol with a viscosity equal to that of blood, in a ratio ranging from 45% to 55%.

[0053] In some embodiments of this application, the absolute value of the first flow difference can be the absolute value of the difference between the current value at zero pressure difference and the current values ​​at other pressure differences, based on the different rotation speeds obtained, in an in vitro test simulation environment when the blood pump catheter is in a straight tube state.

[0054] The first pump blood flow value can be the pump blood flow value under different speeds and pressure differences.

[0055] The first correspondence can be the first correspondence between the absolute value of the first current difference and the first pump blood flow value.

[0056] In some embodiments of this application, in order to further accurately determine the target pump blood flow rate value of the blood pump, before step 110, the above-mentioned method for determining the pump blood flow rate of the blood pump may further include:

[0057] In an in vitro testing simulation environment, the second correspondence between the pressure difference and the second current value, and the third correspondence between the pressure difference and the blood flow rate of the first pump are obtained at different speeds of the blood pump.

[0058] For each rotational speed, the second current value corresponding to zero differential pressure is used as the second reference current value;

[0059] For each rotational speed, based on the second correspondence, the second current value under each pressure difference at each rotational speed is obtained, and the difference between the second reference current value and the second current value under each pressure difference at each rotational speed is obtained to obtain the absolute value of the first current difference under each pressure difference.

[0060] For each rotational speed, based on the absolute value of the first current difference and the third correspondence, a first correspondence between the absolute value of the first current difference and the blood flow value of the first pump is obtained at each rotational speed.

[0061] The second current value can be the current value of the blood pump under various pressure differences in the blood pump catheter when the blood pump is in an in vitro test simulation environment.

[0062] The second correspondence can be the correspondence between the pressure difference and the second current value at different speeds of the blood pump when the blood pump is in an in vitro test simulation environment.

[0063] The third correspondence can be the correspondence between the pressure difference and the first pump blood flow value at different speeds of the blood pump in an in vitro test simulation environment.

[0064] The second reference current value can be the current value of the blood pump catheter under zero differential pressure in an in vitro test simulation environment.

[0065] In some embodiments of this application, the pressure difference can be the pressure difference between the heart and other organs in a normal human body, and this pressure difference has a certain range, typically within 0-14 kPa. In some embodiments of this application, the pressure difference between the suction end and the discharge end of the blood pump's pumping conduit can be adjusted to the pressure difference between the heart and other organs in a normal human body, thereby allowing the determination of the current value and pumping flow rate under different pressure differences using the blood pump.

[0066] In one example, in an in vitro testing simulation environment, the blood pump can be operated at different speeds to obtain the second current value and the first pump blood flow value under each pressure difference at different speeds. Then, the second current values ​​under each pressure difference at different speeds can be fitted to obtain a second correspondence (e.g., ...). Figure 2 The blood flow values ​​of the first pump under different pressure differences at different speeds were fitted to obtain a third correspondence (e.g., Figure 3 ).

[0067] exist Figure 2 and Figure 3 In the diagram, n1, n2, and n3 represent different rotational speeds.

[0068] Continuing with the example above, after determining the second and third correspondences, the current value at zero differential pressure at each speed can be obtained and used as the second reference current value. For example, for speed n1, the current value I0 at zero differential pressure at that speed is obtained and used as the second reference current value. Then, based on the current values ​​at each differential pressure in the second correspondence, the current values ​​I and I0 at each differential pressure at speed n1 are subtracted, and the absolute value of the difference is taken to obtain the absolute value of the first current difference corresponding to each differential pressure (e.g., ...). Figure 4 Then, based on the absolute value of the first current difference and the third correspondence, the correspondence between the absolute value of the first current difference and the blood flow rate of the first pump can be obtained (e.g., Figure 5 ).

[0069] In the embodiments of this application, by placing the blood pump in an in vitro testing simulation environment, a second correspondence between the pressure difference and the second current value, and a third correspondence between the pressure difference and the first pump blood flow value are obtained at different speeds of the blood pump. For each speed, the second current value corresponding to zero pressure difference is used as the second reference current value. For each speed, based on the second correspondence, the second current value under each pressure difference at each speed is obtained, and the difference between the second reference current value and the second current value under each pressure difference at each speed is obtained to obtain the absolute value of the first current difference under each pressure difference. For each speed, based on the absolute value of the first current difference and the third correspondence, a first correspondence between the absolute value of the first current difference and the first pump blood flow value at that speed can be obtained. In this way, the first correspondence between the absolute value of the first current difference and the first pump blood flow value at each speed can be accurately obtained, so that the accurate pump blood flow value can be obtained based on the accurate first correspondence.

[0070] Then, step 120 is introduced: obtaining the first reference current value of each current cycle during the operation of the blood pump in the actual human body environment of the test object at each rotation speed.

[0071] The object being tested can be an object that is tested using a blood pump, such as an object in which the blood pump is placed inside the body of another object.

[0072] The current period can be the period of the current.

[0073] In some embodiments of this application, the human heart has a cardiac cycle; correspondingly, after a blood pump is placed in the human body, the current of the blood pump also has a cycle as the human heart beats periodically, such as... Figure 6 The figure shows the current variation curve within a certain cardiac cycle at a certain rotational speed. Within each current cycle, the current follows the... Figure 6 The curve shown changes in a regular pattern.

[0074] The first reference current value can be the reference current value in each current cycle during the operation of the blood pump at each speed in the actual human body environment of the test object.

[0075] In some embodiments of this application, in order to further accurately determine the pumping flow rate of the blood pump, step 120 may specifically include:

[0076] Obtain the first current value of each current cycle during the operation of the blood pump at each speed;

[0077] For each current cycle, the largest first current value in the current cycle is determined as the first reference current value of the current cycle.

[0078] The first current value can be the current value of the blood pump in each current cycle during its operation at each speed, i.e., as shown below. Figure 6 The current value shown.

[0079] In some embodiments of this application, during a cardiac cycle, the pressure in the aorta and the left ventricle is approximately the same when the aortic valve opens. At this time, the pressure difference between the suction end and the outflow end of the blood pump's pumping catheter is approximately 0. At this time, the blood flow rate is at its maximum, the motor does its maximum work, and the current is at its maximum. Therefore, the maximum first current value in each current cycle can be determined as the reference current value (i.e., the first reference current value) for that current cycle.

[0080] In the embodiments of this application, by obtaining the first current value of each current cycle during the operation of the blood pump at each speed, and for each current cycle, the largest first current value in that current cycle is determined as the first reference current value of that current cycle. In this way, based on the first reference current value, the absolute value of the second current difference can be accurately determined to obtain the accurate target pump blood flow value.

[0081] In some embodiments of this application, after the blood pump is placed in the human body, if the blood pump is placed in the correct position, the current during the operation of the blood pump will change periodically. Only when the current during the operation of the blood pump changes periodically can the first reference current value of each current cycle be obtained. Therefore, before step 120, it is necessary to determine that the current during the operation of the blood pump changes periodically.

[0082] Therefore, prior to step 120, the method for determining the pump flow rate of the blood pump mentioned above may further include:

[0083] Based on the cardiac cycle of the subject at each rotational speed, the current cycle of the blood pump at each rotational speed is determined;

[0084] For each rotational speed, the current cycle at that speed is compared with the predicted current cycle corresponding to the cardiac cycle.

[0085] Based on the comparison results, it was determined whether the current value at each rotational speed underwent periodic changes.

[0086] Specifically, for each rotational speed, the predicted current cycle can be the current cycle predicted using a preset algorithm based on the cardiac cycle at that rotational speed.

[0087] In some embodiments of this application, the cardiac cycle of the detection object at each rotation speed can be obtained. Based on the cardiac cycle, the current cycle of the blood pump at each rotation speed can be obtained by measurement. The current cycle is compared with the predicted current cycle. If the comparison results are consistent, it is determined that the current value at each rotation speed has changed periodically. If the comparison results are inconsistent, it indicates that the blood pump is not placed correctly and needs to be repositioned.

[0088] Correspondingly, step 120 can be specifically described as follows: when it is determined that the current value changes periodically at each rotation speed, the first reference current value of each current cycle is obtained when the blood pump is in the actual human body environment of the test object and during the operation at each rotation speed.

[0089] In some embodiments of this application, if the blood pump current data is abnormal for a long time, i.e., there is no periodic change, an alarm message can be generated to indicate that the blood pump is not placed in the correct position and needs to be repositioned.

[0090] In the embodiments of this application, by acquiring the cardiac cycle of the detection object at each rotation speed, and based on the cardiac cycle, the current cycle of the blood pump at each rotation speed can be obtained by measurement, and the current cycle is compared with the predicted current cycle. Based on the comparison result, it is determined whether the current value at each rotation speed has undergone periodic changes, thus ensuring that the blood pump can work normally.

[0091] Then, step 130 is introduced: for each current cycle in each rotational speed, the difference between the first reference current value and the current value at different times in the current cycle is calculated to obtain at least one absolute value of the second current difference.

[0092] The absolute value of the second current difference can be the absolute value obtained by subtracting the first reference current value in each current cycle of each rotational speed from the current value at different times in that current cycle and taking the difference.

[0093] In one example, for a certain current cycle at rotational speed n1, the maximum current value I1 within that current cycle is obtained, and this maximum current value I1 is determined as the first reference current value. Then, the difference between I1 and the current value at each moment within that current cycle is taken as the absolute value, and multiple absolute values ​​of the second current difference corresponding to that current cycle at rotational speed n1 can be obtained.

[0094] Then, step 140 is introduced: for each current cycle in each rotation speed, at least one absolute value of the second current difference is searched in the first correspondence to obtain at least one second pump blood flow value corresponding to at least one absolute value of the second current difference.

[0095] The second pump blood flow value can be the pump blood flow value that corresponds to the absolute value of the second current difference found in the first correspondence.

[0096] In some embodiments of this application, since the first correspondence contains a correspondence between the absolute value of the first current difference and the first pump blood flow value at each rotational speed (i.e. Figure 5Once the absolute value of the second current difference for each current cycle in each rotational speed is obtained, for example, after obtaining the absolute value of the second current difference for a certain current cycle in rotational speed n1, the first correspondence (i.e. Figure 5 The pump blood flow value corresponding to the absolute value of each second current difference is found in the [reference to a specific unit, likely a typo, should be inserted here]. This value is then determined as the second pump blood flow value for that current cycle within rotational speed n1. This process yields the [specific result / details]. Figure 7 The graph shows the blood flow rate of the second pump during a certain current cycle at a certain speed.

[0097] In some embodiments of this application, in order to ensure that the absolute value of the second current difference is within Figure 5 To improve the accuracy of the search, after step 120, the method for determining the pump flow rate of the blood pump mentioned above may further include:

[0098] The first reference current value is calibrated as the second reference current value.

[0099] In some embodiments of this application, after determining the first reference current value, the first reference current value can be calibrated as the second reference current value, that is, I1 = I0.

[0100] In some embodiments of this application, after determining the second reference current value, the flow rate value corresponding to the second reference current value can be used as the maximum flow rate value Qmax of the current cycle. When displaying the target blood flow rate value later, the maximum flow rate value Qmax can also be displayed.

[0101] Correspondingly, step 130 can specifically include:

[0102] For each current cycle at each rotational speed, the difference between the second reference current value and the current value at each moment within the current cycle is calculated to obtain at least one absolute value of the second current difference.

[0103] In some embodiments of this application, after the first reference current value is calibrated as the second reference current value, for each current cycle in each rotational speed, the difference between the second reference current value and the current value at each moment in the current cycle can be calculated to obtain at least one absolute value of the second current difference.

[0104] In some embodiments of this application, for each current cycle in each rotational speed, after obtaining the absolute value of each second current difference in that current cycle, the pump blood flow value corresponding to the largest absolute value of the second current difference can be determined as the minimum flow value Qmin of that current cycle. When displaying the target pump blood flow value later, the minimum flow value Qmin can also be displayed.

[0105] In the embodiments of this application, the first reference current value is calibrated as the second reference current value. By selecting the same reference current value, the absolute values ​​of the differences obtained (the first absolute value and the second absolute value) are based on the same reference current value, ensuring that subsequent... Figure 5 When searching, the pump blood flow value corresponding to the absolute value of the difference obtained based on the same reference current value can be found, thus obtaining an accurate pump blood flow value.

[0106] Finally, step 150 is introduced: for each rotational speed, the target pump blood flow value is determined based on at least one second pump blood flow value under each current cycle.

[0107] The target blood flow rate value can be the blood flow rate value obtained at each rotation speed, which is the flow rate value used to characterize the blood pump's pumping capacity.

[0108] In some embodiments of this application, in order to accurately determine the target pump blood flow value, step 150 may specifically include:

[0109] For each current cycle in each rotational speed, the blood flow value of at least one second pump under the current cycle is integrated to obtain the blood flow value of the first total pump under the current cycle.

[0110] For each current cycle at each rotational speed, the average pump blood flow value under the current cycle is determined based on the first total pump blood flow value and the current cycle value.

[0111] For each rotational speed, the average pump blood flow value under each current cycle is summed to obtain the second total pump blood flow value under each rotational speed;

[0112] For each rotational speed, the average value of the second master pump blood flow is calculated to obtain the target pump blood flow value at that rotational speed.

[0113] Specifically, for each current cycle at each rotational speed, the first total pump blood flow value can be obtained by integrating at least one second pump blood flow value under that current cycle.

[0114] The current cycle value can be the duration of each current cycle. For example, if a current cycle is 10 seconds, then the current cycle value is 10 seconds.

[0115] For each current cycle at each rotational speed, the average pump blood flow value can be obtained by averaging the first total pump blood flow value under that current cycle.

[0116] For each rotational speed, the second total pump blood flow value can be obtained by summing the average pump blood flow values ​​of each current cycle at that rotational speed.

[0117] In one example, such as Figure 7 This is a graph showing the blood flow rate of the second pump during a specific current cycle at a given rotational speed n1. Figure 7 The first total pump blood flow value under that current cycle is obtained by integrating the blood flow values ​​of each second pump in the current cycle. Then, the first total pump blood flow value is divided by the current cycle value to obtain the average pump blood flow value under that current cycle. The average pump blood flow values ​​of each current cycle under that speed n1 are summed to obtain the second total pump blood flow value under that speed n1. The target pump blood flow value under that speed n1 is obtained by averaging the second total pump blood flow values ​​under that speed n1.

[0118] In some embodiments of this application, the curve of the pump blood flow rate within one current cycle can be obtained by fitting the correspondence between the absolute value of the second current difference and the second pump blood flow rate. The fitting method can include polynomial fitting, trigonometric function fitting, exponential function fitting and logarithmic function fitting, or a combination thereof.

[0119] In the embodiments of this application, the determined target pump blood flow value can help clinicians determine how much blood flow the blood pump should provide to the subject and when the blood pump can be withdrawn.

[0120] In some embodiments of this application, after obtaining the target pump blood flow value at each rotational speed, the cardiac output value at that rotational speed can be determined based on the target pump blood flow value at each rotational speed.

[0121] In some embodiments of this application, in order to accurately determine the recovery function of the target object, after step 150, the method for determining the pump flow rate of the blood pump mentioned above may further include:

[0122] For each rotational speed, the cardiac output value at that rotational speed is determined based on the target pump blood flow value at that rotational speed.

[0123] Among them, cardiac output can be a value used to characterize the heart's recovery function in the tested subject.

[0124] In some embodiments of this application, specifically for each rotational speed, the cardiac output value at that rotational speed is determined based on the target pump blood flow value at that rotational speed. This can be achieved in the following ways:

[0125] For each rotational speed, the vascular resistance of the test subject at the initial moment is determined based on the total cardiac output and mean aortic pressure of the test subject at the initial moment;

[0126] For each rotational speed, the total cardiac output of the test subject at each time point is determined based on the mean aortic pressure value of the test subject at each time point and the vascular resistance of the test subject at the initial time point.

[0127] For each rotational speed, the cardiac output value of the subject at each rotational speed is determined based on the total cardiac output value of the subject at each time point and the target pump blood flow value.

[0128] The initial moment can be the moment when the blood pump is placed inside the subject's body and begins to work.

[0129] In some embodiments of this application, the total cardiac output value of the detected object at each time point can be obtained by measurement using an external device, such as a Pulse Indicator Continuous Cardiac Output (PiCCO) monitoring device or a Swan-Ganz floating catheter. The mean aortic pressure value can also be obtained using an auxiliary pressure sensor.

[0130] In some embodiments of this application, the specific method of obtaining the total cardiac output and mean aortic pressure of the test subject at each time point is not limited in this application.

[0131] In some embodiments of this application, the vascular resistance of the test subject at the initial moment can be determined by detecting the total cardiac output and the mean aortic pressure at the initial moment, specifically according to the following formula (1):

[0132] CO = MAP / SVR (1)

[0133] Wherein, CO represents total cardiac output, MAP represents mean aortic pressure, and SVR represents vascular resistance.

[0134] The vascular resistance SVR0 of the test subject at the initial moment can be calculated according to the above formula (1).

[0135] In some embodiments of this application, since vascular resistance remains constant over a period of time (e.g., 8 hours), the total cardiac output of the object detected at time Ti over that period can be obtained based on the following formula (2):

[0136] COi=MAPTi / SVR0 (2)

[0137] The real-time COi of the detected object can be calculated using the above formula (2).

[0138] For each rotational speed, based on the total cardiac output of the test subject at each time point and the target pumping blood flow at that rotational speed, the cardiac output of the test subject at that rotational speed can be determined using the following formulas (3) and (4):

[0139] COi=Con+COC (3)

[0140] Wherein, Con represents the cardiac output value of the object being tested at a certain rotational speed, and COC represents the blood flow rate of the blood pump at that rotational speed. According to the above formula (3), the following formula (4) can be obtained:

[0141] Con = COi - COC (4)

[0142] The CO value (i.e. cardiac output value) of the test object at a certain rotational speed can be obtained by using the above formula (4).

[0143] In the embodiments of this application, for each rotational speed, the cardiac output value at that rotational speed is determined based on the target pump blood flow value at that rotational speed. In this way, the accurate cardiac output can be determined based on the accurate target pump blood flow value, and thus the degree of recovery of the heart of the test subject can be accurately known.

[0144] In some embodiments of this application, the target pump blood flow value determined above can be obtained based on the blood pump catheter being in a straight state or in a bent state. In actual application, the state of the blood pump catheter may differ from that in the in vitro testing simulation environment. This will lead to different current values ​​in actual application, i.e., abnormal current values, and consequently, different absolute values ​​of the current difference. Therefore, the first correspondence in the in vitro testing simulation environment cannot be used. However, if the state of the blood pump catheter does not change significantly in actual application compared to the in vitro testing simulation environment, the current value will not change much, and the target pump blood flow value can be determined based on the first correspondence in the in vitro testing simulation environment. Therefore, in actual application, a certain adjustment range is allowed for the absolute value of the first current difference in the in vitro testing simulation environment.

[0145] In some embodiments of this application, the blood pump catheter has two states: a first state and a second state.

[0146] In some embodiments of this application, the first state may be that the blood pump catheter is in a straight state, and the second state may be that the blood pump catheter is in a bent state.

[0147] When the blood pump catheter is in different states, correspondingly, in the in vitro testing simulation environment, for each rotational speed, obtaining the second current value under each pressure difference at each rotational speed can be done by obtaining the second current value under each pressure difference at each rotational speed under different states. Here, the second current value can include a first sub-current value and a second sub-current value. The first sub-current value can be the current value of the blood pump catheter in the first state at each rotational speed and under each pressure difference; the second sub-current value can be the current value of the blood pump catheter in the second state at each rotational speed and under each pressure difference.

[0148] In some embodiments of this application, in order to achieve a certain degree of correction of the absolute value of the first current difference, in step 110, after obtaining the absolute values ​​of the first current difference of the blood pump at each rotation speed and each pressure difference in the first state and the second state respectively, the method for determining the blood flow rate of the blood pump mentioned above may further include:

[0149] For each pressure difference at each rotational speed, the difference between the first sub-current value and the second sub-current value under the pressure difference is used to obtain the absolute value of the third current difference.

[0150] For each pressure difference at each rotational speed, the absolute value of the first current difference under the target state is corrected based on the absolute value of the third current difference.

[0151] For each rotational speed, the absolute value of the third current difference can be the absolute value obtained by subtracting the first sub-current value and the second sub-current value under each pressure difference at that rotational speed.

[0152] The target state can be either the first state or the second state.

[0153] In some embodiments of this application, the current values ​​(i.e., the first sub-current value and the second sub-current value) of the blood pump at various speeds and pressure differences can be obtained in the first state and the second state, respectively. Then, the current values ​​under each pressure difference in the two states are subtracted to obtain the absolute value of the third current difference. This absolute value of the third current difference can be used to correct the absolute value of the first current difference in the first state (or the second state). That is, the absolute value of the current difference in the bending state can be used to correct the absolute value of the current difference in the straight pipe state, or the absolute value of the current difference in the straight pipe state can be used to correct the absolute value of the current difference in the bending state.

[0154] In one example, we will use the absolute value of the current difference in the bent state to correct the absolute value of the current difference in the straight state. At a rotation speed n1, when the blood pump catheter is in the straight state, the current values ​​(i.e., the first sub-current values) under different pressure differences are 1, 2, 1, and 3, respectively. When the blood pump catheter is in the bent state, the current values ​​(i.e., the second sub-current values) under different pressure differences are 1.2, 1.8, 1.1, and 3.1, respectively. Then, we take the absolute value of the difference between the first and second sub-current values ​​under the corresponding pressure differences at the rotation speed n1 to obtain the absolute value of the third current difference, i.e., |1-1.2|=0.2, |2-1.8|=0.2, |1-1.1|=0.1, |3-3.1|=0.1, where 0.2, 0.2, 0.1, and 0.1 are the absolute values ​​of the third current difference.

[0155] In some embodiments of this application, the maximum value among the absolute values ​​of the third current difference may be used as the correction range of the absolute value of the first current difference.

[0156] Continuing with the example above, after determining 0.2, 0.2, 0.1, and 0.1 as the absolute values ​​of the third current value difference, the maximum value of 0.2 among 0.2, 0.2, 0.1, and 0.1, 0.2, can be used as the correction range for the absolute value of the first current value difference. That is, the absolute value of the first current value difference can fluctuate within the range of 0.2.

[0157] In one example, such as Figure 8 As shown, Figure 8 Middle curve 1 (i.e.) Figure 8 The curve corresponding to n1 shows the relationship between the absolute value of the first current difference and the first pump blood flow value when the blood pump catheter is in a straight tube state at rotation speed n1. Curve 2 (i.e. Figure 8 The curve corresponding to n11 is the curve formed by the maximum value of the correction range of the absolute value of the first current difference at speed n1. Correspondingly, Figure 9 Middle curve 1 (i.e.) Figure 9 The curve corresponding to n2 represents the relationship between the absolute value of the first current difference and the first pump blood flow value when the blood pump catheter is in a straight tube state at a rotation speed of n2. Curve 2 (i.e. Figure 9 The curve corresponding to n22 is the curve formed by the maximum value of the correction range of the absolute value of the first current difference at rotational speed n2. Figure 10 Middle curve 1 (i.e.) Figure 10 The curve corresponding to n3 shows the relationship between the absolute value of the first current difference and the first pump blood flow value when the blood pump catheter is in a straight tube state at rotation speed n3. Curve 2 (i.e. Figure 10 The curve corresponding to n33 is the curve formed by the maximum value of the correction range of the absolute value of the first current difference at speed n3.

[0158] In some embodiments of this application, the absolute value of the current difference under a certain bending state can be used to correct the absolute value of the current difference under another bending state. For example, the absolute value of the current difference under a bending degree of 5° can be used to correct the absolute value of the current difference under a bending degree of 8°.

[0159] In some embodiments of this application, if the current increment exceeds a predetermined limit (i.e., exceeds the correction range of the absolute value of the first current difference) due to changes in the degree of catheter bending or other circumstances, the data of that current cycle is discarded, and the target pump blood flow value is calculated again after the current cycle stabilizes.

[0160] In the embodiments of this application, after obtaining the first sub-current value of the blood pump at various speeds and pressure differences in a first state and the second sub-current value of the blood pump at various speeds and pressure differences in a second state, the difference between the first and second sub-current values ​​under each pressure difference at each speed is calculated to obtain the absolute value of the third current difference. The absolute value of the first current difference in the target state is then corrected based on this third current difference. This correction of the absolute value of the first current difference ensures that in the actual application of the blood pump catheter, as long as its state is within the correction range compared to the simulated in vitro testing environment, the second pump blood flow value can be directly found based on the first correspondence. This guarantees the efficiency of determining the target pump blood flow value, reduces the correction threshold, and improves the accuracy of the target pump blood flow value.

[0161] In some embodiments of this application, after determining the target pump blood flow value, the target pump blood flow value can be displayed, and it can also be displayed... Figures 2-10 Any graph in the image can be used to quickly and intuitively view the target pump blood flow value, and Figures 2-10 The various diagrams within the image enhance the user experience.

[0162] It should be noted that the blood pump flow rate determination method for a blood pump provided in this application embodiment can be executed by a blood pump flow rate determination device or a control module within that device for executing the blood pump flow rate determination method. This application embodiment uses the execution of the blood pump flow rate determination method by a blood pump flow rate determination device as an example to illustrate the blood pump flow rate determination device provided in this application embodiment.

[0163] Based on the same inventive concept as the above-described method for determining the pumping flow rate of a blood pump, this application also provides a device for determining the pumping flow rate of a blood pump. The following is in conjunction with... Figure 11 The blood flow determination device for a blood pump provided in the embodiments of this application will be described in detail.

[0164] Figure 11 This is a structural block diagram of a blood pump flow rate determination device according to an exemplary embodiment.

[0165] like Figure 11 As shown, the blood flow rate determination device 1100 of the blood pump may include:

[0166] The first acquisition module 1110 is used to acquire the first correspondence between the absolute value of the first current difference and the blood flow value of the first pump when the blood pump is in an in vitro test simulation environment at different speeds.

[0167] The second acquisition module 1120 is used to acquire the first reference current value of each current cycle during the operation of the blood pump at each rotation speed in the actual human body environment of the test object.

[0168] The first determining module 1130 is used to, for each current cycle in each rotational speed, subtract the first reference current value from the current value at different times in the current cycle to obtain at least one absolute value of the second current difference.

[0169] The second determining module 1140 is used to search in the first correspondence for at least one absolute value of the second current difference corresponding to each current cycle in each rotation speed, and to obtain at least one second pump blood flow value corresponding to at least one absolute value of the second current difference.

[0170] The third determining module 1150 is used to determine the target pump blood flow value for each rotational speed, based on at least one second pump blood flow value under each current cycle.

[0171] In the embodiments of this application, a first acquisition module acquires a first correspondence between the absolute value of the first current difference and the first pump blood flow value at different rotation speeds in an in vitro test simulation environment. A second acquisition module acquires a first reference current value for each current cycle during operation at each rotation speed in the actual human body environment of the test object. A first determination module subtracts the first reference current value from the current value at different times within each current cycle for each rotation speed to obtain at least one second absolute current difference. The second determination module searches within the first correspondence for the at least one second absolute current difference corresponding to each current cycle at each rotation speed to obtain at least one second pump blood flow value corresponding to the at least one second absolute current difference. A third determination module determines the target pump blood flow value for each rotation speed based on the at least one second pump blood flow value at each current cycle. Thus, the pump blood flow value of the blood pump is effectively characterized by the difference in current changes. Compared to directly using current to characterize the pump blood flow value, using the current difference can effectively reduce the error caused by differences between different blood pump catheters, achieving the effect of accurately determining the pump blood flow.

[0172] In some embodiments of this application, in order to further accurately determine the pumping flow rate value of the blood pump, the second acquisition module 1120 may include:

[0173] The first acquisition unit is used to acquire the first current value of each current cycle during the operation of the blood pump at each speed.

[0174] The first determining unit is configured to determine the largest first current value in each current cycle as the first reference current value of the current cycle for each current cycle.

[0175] In some embodiments of this application, in order to accurately determine the target pump blood flow value, the third determining module 1150 may include:

[0176] The second determining unit is used to integrate at least one second pump blood flow value under each current cycle in each rotational speed to obtain the first total pump blood flow value under the current cycle.

[0177] The third determining unit is used to determine the average pump blood flow value under the current cycle for each current cycle in each rotation speed, based on the first total pump blood flow value and the current cycle value.

[0178] The fourth determining unit is used to sum the average pump blood flow values ​​under each current cycle for each rotation speed to obtain the second total pump blood flow value under the said rotation speed.

[0179] The fifth determining unit is used to calculate the average value of the second total pump blood flow for each rotational speed, so as to obtain the target pump blood flow value at the given rotational speed.

[0180] In some embodiments of this application, in order to accurately determine the recovery function of the test object, the blood pump flow rate determination device may further include:

[0181] The fourth determining module is used to determine the cardiac output value at each rotational speed based on the target pump blood flow value at that rotational speed.

[0182] In some embodiments of this application, the fourth determining module may specifically be used for:

[0183] For each rotational speed, the vascular resistance of the test subject at the initial moment is determined based on the total cardiac output and mean aortic pressure of the test subject at the initial moment;

[0184] For each rotational speed, the total cardiac output of the test subject at each time point is determined based on the mean aortic pressure value of the test subject at each time point and the vascular resistance of the test subject at the initial time point.

[0185] For each rotational speed, the cardiac output value of the subject at each rotational speed is determined based on the total cardiac output value of the subject at each time point and the target pump blood flow value.

[0186] In some embodiments of this application, in order to further accurately determine the target pumping flow rate value of the blood pump, the pumping flow rate determination device of the blood pump may further include:

[0187] The third acquisition module is used to acquire, in an in vitro test simulation environment, the second correspondence between the pressure difference and the second current value, and the third correspondence between the pressure difference and the blood flow rate of the first pump at different speeds of the blood pump.

[0188] The fifth determining module is used to take the second current value corresponding to zero differential pressure as the second reference current value for each rotational speed.

[0189] The sixth determining module is used to obtain the second current value under each pressure difference at each speed based on the second correspondence relationship for each speed, and to subtract the second reference current value from the second current value under each pressure difference at each speed to obtain the absolute value of the first current difference under each pressure difference.

[0190] The seventh determining module is used to obtain, for each rotational speed, a first correspondence between the absolute value of the first current difference and the first pump blood flow value at that rotational speed, based on the absolute value of the first current difference and the third correspondence.

[0191] In some embodiments of this application, in order to further accurately determine the target pumping flow rate value of the blood pump, the pumping flow rate determination device of the blood pump may further include:

[0192] The eighth determining module is used to calibrate the first reference current value as the second reference current value.

[0193] Correspondingly, the first determining module 1130 can be specifically used for:

[0194] For each current cycle in each rotational speed, the difference between the second reference current value and the current value at each moment in the current cycle is calculated to obtain at least one absolute value of the second current difference.

[0195] In some embodiments of this application, in order to further accurately determine the target pump blood flow value of the blood pump, when the blood pump is in an in vitro test simulation environment, the state of the blood pump catheter has a first state and a second state; the second current value includes a first sub-current value and a second sub-current value, wherein the first sub-current value is the current value of the blood pump catheter in the first state at each speed and at each pressure difference, and the second sub-current value is the current value of the blood pump catheter in the second state at each speed and at each pressure difference;

[0196] The blood pump flow rate determination device may also include:

[0197] The correction module is used to, for each pressure difference at each rotational speed, subtract the first sub-current value and the second sub-current value under the pressure difference to obtain the absolute value of the third current difference; and to, for each pressure difference at each rotational speed, correct the absolute value of the first current difference under the target state based on the absolute value of the third current difference; wherein the target state is the first state or the second state.

[0198] In some embodiments of this application, in order to determine that the current during the operation of the blood pump changes periodically, the blood pump flow rate determination device may further include:

[0199] The tenth determining module is used to determine the current cycle of the blood pump at each rotation speed based on the cardiac cycle of the detected object at each rotation speed;

[0200] The comparison module is used to compare the current cycle at each rotational speed with the predicted current cycle corresponding to the cardiac cycle.

[0201] The comparison and determination module is used to determine, based on the comparison results, whether the current value at each rotational speed has undergone periodic changes.

[0202] Correspondingly, the second acquisition module 1120 can be specifically used for:

[0203] Given that the current value changes periodically at each rotation speed, the first reference current value for each current cycle is obtained when the blood pump is in the actual human body environment of the test subject, during the operation of each rotation speed.

[0204] The blood pump flow rate determination device provided in this application embodiment can be used to execute the blood pump flow rate determination method of the blood pump provided in the above method embodiments. Its implementation principle and technical effect are similar, and will not be described again here for the sake of brevity.

[0205] Based on the same inventive concept, embodiments of this application also provide an electronic device.

[0206] Figure 12 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. For example... Figure 12 As shown, the electronic device may include a processor 1201 and a memory 1202 storing computer programs or instructions.

[0207] Specifically, the processor 1201 may include a central processing unit (CPU), an application specific integrated circuit (ASIC), or one or more integrated circuits that can be configured to implement the embodiments of the present invention.

[0208] Memory 1202 may include a large-capacity storage device for data or instructions. For example, and not limitingly, memory 1202 may include a hard disk drive (HDD), a floppy disk drive, flash memory, optical disk, magneto-optical disk, magnetic tape, or a Universal Serial Bus (USB) drive, or a combination of two or more of these. Where appropriate, memory 1202 may include removable or non-removable (or fixed) media. Where appropriate, memory 1202 may be internal or external to the integrated gateway disaster recovery device. In a particular embodiment, memory 1202 is a non-volatile solid-state memory. In a particular embodiment, memory 1202 includes read-only memory (ROM). Where appropriate, the ROM may be a mask-programmed ROM, a programmable ROM (PROM), an erasable PROM (EPROM), an electrically erasable PROM (EEPROM), an electrically rewritable ROM (EAROM), or flash memory, or a combination of two or more of these.

[0209] The processor 1201 reads and executes computer program instructions stored in the memory 1202 to implement any of the methods for determining the pumping flow rate of a blood pump in the above embodiments.

[0210] In one example, the electronic device may also include a communication interface 1203 and a bus 1210. For example, Figure 12 As shown, the processor 1201, memory 1202, and communication interface 1203 are connected through bus 1210 and complete communication with each other.

[0211] The communication interface 1203 is mainly used to realize communication between various modules, devices, units and / or devices in the embodiments of the present invention.

[0212] Bus 1210 includes hardware, software, or both, that couples components of an electronic device together. For example, and not limitingly, the bus may include an Accelerated Graphics Port (AGP) or other graphics bus, an Enhanced Industry Standard Architecture (EISA) bus, a Front Side Bus (FSB), HyperTransport (HT) interconnect, an Industry Standard Architecture (ISA) bus, an Infinite Bandwidth Interconnect, a Low Pin Count (LPC) bus, a memory bus, a Microchannel Architecture (MCA) bus, a Peripheral Component Interconnect (PCI) bus, a PCI-Express (PCI-X) bus, a Serial Advanced Technology Attachment (SATA) bus, a Video Electronics Standards Association Local (VLB) bus, or other suitable buses, or combinations of two or more of these. Where appropriate, bus 1210 may include one or more buses. Although specific buses are described and illustrated in embodiments of the invention, the invention contemplates any suitable bus or interconnect.

[0213] This electronic device can execute the method for determining the pumping blood flow rate of the blood pump in the embodiments of the present invention, thereby achieving... Figures 1-10 Methods for determining the pumping blood flow rate of any described blood pump.

[0214] Furthermore, in conjunction with the blood pump flow rate determination method of the blood pump in the above embodiments, this invention can be implemented using a readable storage medium. This readable storage medium stores program instructions; when executed by a processor, these program instructions implement any of the blood pump flow rate determination methods in the above embodiments.

[0215] It should be clarified that the present invention is not limited to the specific configurations and processes described above and shown in the figures. For the sake of brevity, detailed descriptions of known methods are omitted here. In the above embodiments, several specific steps are described and shown as examples. However, the method process of the present invention is not limited to the specific steps described and shown. Those skilled in the art can make various changes, modifications, and additions, or change the order of steps, after understanding the spirit of the present invention.

[0216] The functional blocks shown in the above-described structural diagram can be implemented as hardware, software, firmware, or a combination thereof. When implemented in hardware, they can be, for example, electronic circuits, application-specific integrated circuits (ASICs), appropriate firmware, plug-ins, function cards, etc. When implemented in software, the elements of this invention are programs or code segments used to perform the required tasks. The programs or code segments can be stored on a machine-readable medium or transmitted over a transmission medium or communication link via data signals carried in a carrier wave. "Machine-readable medium" can include any medium capable of storing or transmitting information. Examples of machine-readable media include electronic circuits, semiconductor memory devices, ROM, flash memory, erasable ROM (EROM), floppy disks, CD-ROMs, optical disks, hard disks, fiber optic media, radio frequency (RF) links, etc. Code segments can be downloaded via computer networks such as the Internet, intranets, etc.

[0217] It should also be noted that the exemplary embodiments mentioned in this invention describe methods or systems based on a series of steps or apparatus. However, this invention is not limited to the order of the steps described above; that is, the steps can be performed in the order mentioned in the embodiments, or in a different order, or several steps can be performed simultaneously.

[0218] The above description is merely a specific embodiment of the present invention. Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the specific working processes of the systems, modules, and units described above can be referred to the corresponding processes in the foregoing method embodiments, and will not be repeated here. It should be understood that the protection scope of the present invention is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in the present invention, and these modifications or substitutions should all be covered within the protection scope of the present invention.

Claims

1. A device for determining the pump flow rate of a blood pump, characterized in that, The device is configured to perform the following method: The first correspondence between the absolute value of the first current difference and the first pump blood flow value is obtained when the blood pump is in an in vitro test simulation environment at different speeds. The first current value of each current cycle is obtained when the blood pump is in the actual human body environment of the test subject, at each rotation speed. For each current cycle, the largest first current value in the current cycle is determined as the first reference current value of the current cycle, thus obtaining the first reference current value for each current cycle. For each current cycle in each rotational speed, the difference between the first reference current value and the current value at different times within the current cycle is calculated to obtain at least one absolute value of the second current difference. For each current cycle in each rotational speed, at least one absolute value of the second current difference is searched in the first correspondence to obtain at least one second pump blood flow value corresponding to at least one absolute value of the second current difference; For each rotational speed, the target pump blood flow value is determined based on at least one second pump blood flow value under each current cycle.

2. The apparatus according to claim 1, characterized in that, The determination of the target pump blood flow value for each rotational speed, based on at least one second pump blood flow value under each current cycle, includes: For each current cycle in each rotational speed, at least one second pump blood flow value under the current cycle is integrated to obtain the first total pump blood flow value under the current cycle. For each current cycle at each rotational speed, the average pump blood flow value under the current cycle is determined based on the first total pump blood flow value and the current cycle value. For each rotational speed, the average pump blood flow value under each current cycle is summed to obtain the second total pump blood flow value at that rotational speed; For each rotational speed, the average value of the second total pump blood flow is calculated to obtain the target pump blood flow value at that rotational speed.

3. The apparatus according to any one of claims 1-2, characterized in that, After determining the target pump blood flow value for each rotational speed based on at least one second pump blood flow value under each current cycle, the device is further configured to perform the following method: For each rotational speed, the cardiac output value at that rotational speed is determined based on the target pump blood flow value at that rotational speed.

4. The apparatus according to claim 3, characterized in that, The determination of cardiac output at each rotational speed, based on the target pump blood flow rate at that speed, includes: For each rotational speed, the vascular resistance of the test subject at the initial moment is determined based on the total cardiac output and mean aortic pressure of the test subject at the initial moment; For each rotational speed, the total cardiac output of the test subject at each time point is determined based on the mean aortic pressure value of the test subject at each time point and the vascular resistance of the test subject at the initial time point. For each rotational speed, the cardiac output value of the subject at each rotational speed is determined based on the total cardiac output value of the subject at each time point and the target pump blood flow value.

5. The apparatus according to any one of claims 1-2, characterized in that, Before acquiring the correspondence between the absolute value of the first current difference and the first pump blood flow value at different rotation speeds in an in vitro test simulation environment, the device is further configured to perform the following method: In an in vitro testing simulation environment, the second correspondence between the pressure difference and the second current value, and the third correspondence between the pressure difference and the blood flow rate of the first pump are obtained at different speeds of the blood pump. For each rotational speed, the second current value corresponding to zero differential pressure is used as the second reference current value; For each rotational speed, based on the second correspondence, the second current value under each pressure difference at the rotational speed is obtained, and the difference between the second reference current value and the second current value under each pressure difference at the rotational speed is obtained to obtain the absolute value of the first current difference under each pressure difference. For each rotational speed, based on the absolute value of the first current difference and the third correspondence, a first correspondence between the absolute value of the first current difference and the first pump blood flow value is obtained at that rotational speed.

6. The apparatus according to claim 5, characterized in that, After obtaining the first reference current value for each current cycle during the operation of the blood pump at each rotational speed in a real human body environment, the device is further configured to perform the following method: The first reference current value is calibrated as the second reference current value; The step of subtracting the first reference current value from the current value at each moment within the current cycle for each rotational speed to obtain at least one absolute value of the second current difference includes: For each current cycle in each rotational speed, the difference between the second reference current value and the current value at each moment in the current cycle is calculated to obtain at least one absolute value of the second current difference.

7. The apparatus according to claim 5, characterized in that, When the blood pump is in an in vitro test simulation environment, the state of the blood pump catheter has a first state and a second state; the second current value includes a first sub-current value and a second sub-current value, wherein the first sub-current value is the current value of the blood pump catheter in the first state at each speed and at each pressure difference, and the second sub-current value is the current value of the blood pump catheter in the second state at each speed and at each pressure difference. After obtaining the absolute values ​​of the first current difference under each speed and pressure difference of the blood pump in the first state and the second state, respectively, the device is further configured to execute the following method: For each pressure difference at each rotational speed, the difference between the first sub-current value and the second sub-current value under the pressure difference is used to obtain the absolute value of the third current difference. For each pressure difference at each rotational speed, the absolute value of the first current difference under the target state is corrected based on the absolute value of the third current difference; The target state is either the first state or the second state.

8. The apparatus according to any one of claims 1-2, characterized in that, Before acquiring the first reference current value for each current cycle during operation at each rotational speed in the actual human environment of the test subject, the device is also configured to perform the following method: Based on the cardiac cycle of the detected object at each rotation speed, the current cycle of the blood pump at each rotation speed is determined; For each rotational speed, the current cycle at that rotational speed is compared with the predicted current cycle corresponding to the cardiac cycle; Based on the comparison results, determine whether the current value at each rotational speed undergoes periodic changes; The blood pump is located in a real human body environment, and during operation at each rotation speed, the first reference current value for each current cycle includes: Given that the current value changes periodically at each rotation speed, the first reference current value for each current cycle is obtained when the blood pump is in the actual human body environment of the test subject, during the operation of each rotation speed.

9. An electronic device, characterized in that, It includes a processor, a memory, and a program or instructions stored in the memory and executable on the processor, wherein the program or instructions, when executed by the processor, implement the method steps performed by the blood pump flow determination device of any one of claims 1-8.

10. A readable storage medium, characterized in that, The readable storage medium stores a program or instructions that, when executed by a processor, implement the method steps performed by the blood pump flow determination device for a blood pump as described in any one of claims 1-8.

Images