Pulsatile control method and device for infusion pump

Abstract

This application proposes a pulsation control method and apparatus for an infusion pump. The method includes: acquiring a uniform peristaltic cycle, which is the pulsation cycle of the pressure inside the infusion tubing when the peristaltic unit operates at a first speed; calculating a rapid peristaltic cycle based on the uniform peristaltic cycle; and, if the pressure inside the infusion tubing equals the target pressure within the uniform peristaltic cycle, controlling the peristaltic unit to operate at a second speed for the rapid peristaltic cycle, and stopping operation after the rapid peristaltic cycle, thereby reducing the pulsation amplitude of the pressure inside the infusion tubing. In this application, when the pressure inside the infusion tubing drops to the target pressure within the uniform peristaltic cycle, a second speed peristaltic cycle is used, and operation stops for the remaining time of the uniform peristaltic cycle. This reduces the amplitude of the pressure pulsation within the infusion tubing while maintaining the pressure inside the infusion tubing, thus providing a more stable and reliable back pressure for the ventricular assist device.

Description

Technical Field

[0001] This application relates to the field of mechanical control technology, and in particular to a method and apparatus for controlling the pulsation of an infusion pump. Background Technology

[0002] An infusion pump typically includes a base and a pump door. The base contains a peristaltic plate and an infusion tube connected to the peristaltic plate. The peristaltic plate generates a wave-like motion, and the infusion tube between the peristaltic plate and the squeezing plate is squeezed by the peristaltic plate. This causes the liquid in the infusion tube to be subjected to a continuous thrust related to the movement sequence of the peristaltic plate, thereby causing the liquid to flow and achieving the effect of infusion.

[0003] However, the peristaltic plate causes the fluid in the infusion tube to pulsate, which may not meet the needs of some high-precision medical devices for precise fluid or pressure control. Summary of the Invention

[0004] This application provides a method and apparatus for controlling the pulsation of an infusion pump, which can improve the problem of large pressure pulsation in the fluid in the infusion tube when the infusion pump is moving at a constant speed.

[0005] In a first aspect, embodiments of this application provide a pulsation control method for an infusion pump, the infusion pump including an infusion tubing for conveying fluid and a peristaltic unit for driving fluid flow in the infusion tubing; the method includes:

[0006] Obtain the uniform peristaltic cycle, wherein the uniform peristaltic cycle is the pulsation cycle of the pressure inside the infusion tube when the peristaltic unit runs at a first speed at a uniform speed;

[0007] The rapid peristalsis time of the peristaltic unit is calculated based on the uniform peristalsis cycle;

[0008] During the uniform peristaltic cycle time, when the pressure inside the infusion tube drops to the target pressure, the peristaltic unit is controlled to run at a second speed for the rapid peristaltic time, and stops running for the remaining time to reduce the pulsation amplitude of the pressure inside the infusion tube. The second speed is greater than the first speed.

[0009] Secondly, an infusion pump is provided in the embodiments of this application, the infusion pump comprising:

[0010] Infusion tubing is used to transport fluids;

[0011] The peristaltic unit is used to drive the fluid flow in the infusion tube;

[0012] The control unit, which is communicatively connected to the peristaltic unit, is used for:

[0013] Obtain the uniform peristaltic cycle, wherein the uniform peristaltic cycle is the pulsation cycle of the pressure inside the infusion tube when the peristaltic unit runs at a first speed at a uniform speed;

[0014] Calculate the rapid peristalsis cycle based on the uniform peristalsis cycle;

[0015] During the uniform peristaltic cycle, if the pressure inside the infusion tube is equal to the target pressure, the peristaltic unit is controlled to run the rapid peristaltic cycle at a second speed, and stops running after running the rapid peristaltic cycle, so as to reduce the pulsation amplitude of the pressure inside the infusion tube. The second speed is greater than the first speed.

[0016] Thirdly, embodiments of this application provide a medical device, the medical device including a processor, a memory, a communication interface, and one or more programs, the one or more programs being stored in the memory and configured to be executed by the processor, the programs including instructions for performing some or all of the steps described in the method described in the first aspect above.

[0017] Fourthly, embodiments of this application provide a computer-readable storage medium storing a computer program for electronic data interchange, wherein the computer program causes a computer to perform some or all of the steps described in the method described in the first aspect above.

[0018] Fifthly, embodiments of this application provide a computer program product, wherein the computer program product includes a non-transitory computer-readable storage medium storing a computer program, the computer program being operable to cause a computer to perform some or all of the steps described in the method described in the first aspect of embodiments of this application. The computer program product may be a software installation package.

[0019] The technical solution provided in this application obtains a uniform peristaltic cycle, which is the pulsation cycle of the pressure inside the infusion tube when the peristaltic unit runs at a first speed. A rapid peristaltic cycle is calculated based on the uniform peristaltic cycle. If the pressure inside the infusion tube equals the target pressure within the uniform peristaltic cycle, the peristaltic unit is controlled to run at a second speed for the rapid peristaltic cycle, and stops running after the rapid peristaltic cycle to reduce the amplitude of the pressure pulsation inside the infusion tube. The second speed is greater than the first speed. In this application, when the pressure inside the infusion tube drops to the target pressure within the uniform peristaltic cycle, the rapid peristaltic cycle is run at the second speed, and the unit stops running for the remaining time of the uniform peristaltic cycle. This reduces the amplitude of the pressure pulsation inside the infusion tube while maintaining the pressure inside the infusion tube, thereby providing a more stable and reliable back pressure for the ventricular assist device. Attached Figure Description

[0020] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0021] Figure 1 This is a schematic diagram of the structure of an infusion pump with the pump door cover closed, according to an embodiment of this application;

[0022] Figure 2 This is a schematic diagram of the structure of an infusion pump with the pump door omitted, according to an embodiment of this application;

[0023] Figure 3 This is a schematic diagram of the structure of an infusion pipeline and pump door provided in an embodiment of this application;

[0024] Figure 4 This is a structural block diagram of a ventricular assist system provided in an embodiment of this application;

[0025] Figure 5 This is a schematic flowchart of a pulsation control method for an infusion pump provided in an embodiment of this application;

[0026] Figure 6 This is a schematic diagram of the structure of a medical device provided in an embodiment of this application. Detailed Implementation

[0027] To help those skilled in the art 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. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. Based on the description of the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0028] The terms "first," "second," etc., in the specification, claims, and accompanying drawings of this application are used to distinguish different objects, not to describe a specific order. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion. For example, a process, method, software, product, or apparatus that includes a series of steps or units is not limited to the listed steps or units, but also includes steps or units not listed, or other steps or units inherent to such processes, methods, products, or apparatus.

[0029] In this document, the term "embodiment" means that a particular feature, structure, or characteristic described in connection with an embodiment may be included in at least one embodiment of this application. The appearance of this phrase in various places throughout the specification does not necessarily refer to the same embodiment, nor is it a separate or alternative embodiment mutually exclusive with other embodiments. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described herein can be combined with other embodiments.

[0030] An infusion pump typically includes a base and a pump gate. The base houses a peristaltic pump and an infusion tubing connected to the peristaltic pump. The peristaltic pump has multiple pump vanes arranged sequentially along the extension direction of the infusion tubing. The pump vanes and the pump gate are located on opposite sides of the infusion tubing in the radial direction and work together to act on the tubing. Specifically, each pump vane can reciprocate radially along the infusion tubing, and the multiple vanes can move sequentially. When the pump vanes move towards the infusion tubing, they work together with the pump gate to compress the infusion tubing, thereby achieving fluid delivery.

[0031] The fluid in the infusion tubing flows in the desired direction through the compression between the pump blades and the pump valve, generating a pulse flow as the pump blades compress the tubing. When multiple pump blades sequentially compress the tubing, the pressure within the tubing exhibits periodic pulsations. This pulsation cannot guarantee a smooth and stable fluid pressure output from the infusion pump, failing to meet the fluid delivery requirements of various application scenarios. Currently, one solution to reduce pulsation is to increase the number of pump blades, but this reduces the flow rate; another method is to use a pulse suppressor, which requires additional components, such as special pump head structures or damping modules, increasing both cost and failure rate.

[0032] To address the aforementioned issues, this application proposes a pulsation control method for an infusion pump. By adjusting the periodic uniform peristalsis of the peristaltic pump to a periodic non-uniform peristalsis, and by controlling the peristaltic time of the pump, the amplitude of pressure pulsation within the infusion tubing is reduced. This saves costs while ensuring that the infusion pump outputs a balanced and smooth fluid, thus ensuring safer product use.

[0033] See Figures 1 to 3 The infusion pump 10 provided in this embodiment is used to periodically squeeze the infusion tube 400, thereby driving the flow of liquid in the infusion tube 400 and realizing the delivery of liquid by the infusion pump 10. Specifically, the infusion pump 10 includes components such as a base 200, a pump door 120, a pressure sensor 130, and a peristaltic unit 140.

[0034] In some embodiments, the pump door 120 is movably connected to the base 200, for example, the pump door 120 is rotatably connected to the base 200. For example, the pump door 120 may be slidably connected to the base 200. When the pump door 120 rotates close to the base 200 until it abuts against the base 200, the pump door 120 will close the base 200; when the pump door 120 rotates away from the base 200 at a certain angle, the pump door 120 will open the base 200.

[0035] The infusion tube 400 can pass through the infusion pump 10. Specifically, the infusion tube 400 is located between the base 200 and the pump door 120. The base 200 can be provided with a channel, such as a hole or groove, for the infusion tube 400 to pass through. Both ends of the infusion tube 400 extend out of the base 200.

[0036] The peristaltic unit 140 has multiple peristaltic plates 141, which are arranged sequentially along the extension direction of the infusion tube 400. The peristaltic plates 141 and the pump gate 120 are distributed on two opposite sides of the radial direction of the infusion tube 400 (specifically the first tube segment 410) and can work together on the infusion tube 400.

[0037] In one embodiment, the peristaltic unit 140 further includes a rotating shaft (not shown in the figure), on which multiple cams are mounted sequentially along the axial direction. Each cam is fitted with a peristaltic plate 141. The cams on the rotating shaft cause the peristaltic plate 141 to peristalse in a certain sequence. Each peristaltic plate 141 can move back and forth radially along the infusion tube 400. When the peristaltic plate 141 moves toward the infusion tube 400, it can work together with the pump door 120 to squeeze the infusion tube 400, so that the fluid in the infusion tube 400 is subjected to a continuous thrust related to the movement sequence of the peristaltic plate 141, thereby causing the fluid to flow and achieving the effect of fluid delivery.

[0038] Furthermore, the infusion tubing 400 may include a first tubing segment 410 and a second tubing segment 420 connected to each other. A peristaltic unit 140 is disposed on the base 200 and corresponds to the first tubing segment 410 of the infusion tubing 400. When the pump door 120 closes the base 200, the first tubing segment 410 is located between the peristaltic unit 140 and the pump door 120. When the peristaltic unit 140 starts working, it moves towards the pump door 120, thereby working with the pump door 120 to squeeze the infusion tubing 400, squeezing out the liquid from the infusion tubing 400, thus realizing the pumping function of the infusion pump 10.

[0039] The base 200 has an installation channel 330 for the infusion tube 400 to pass through and a cover plate 300 covering part of the installation channel 330. A second tube section 420 is installed in the installation channel 330, and the position of the second tube section 420 corresponds to the position of the cover plate 300. When the pump door 120 closes the base 200, the pump door 120 can compress the first tube section 410, and the second tube section 420 does not contact the pump door 120, thus preventing the pump door 120 from compressing the second tube section 420. During infusion, the liquid can flow from the first tube section 410 to the second tube section 420.

[0040] The infusion pump 10 also includes a pressure sensor 130, which contacts the second segment 420 in the infusion tubing 400. The position of the pressure sensor 130 corresponds to the position of the cover plate 300, and the pressure sensor 130 is located between the cover plate 300 and the second segment 420; or, in other words, the pressure sensor 130 is disposed on the outer wall of the infusion tubing 400 (specifically the second segment 420) to detect the fluid pressure within the second segment 420. When the infusion pump 10 is operating, by closing the cover plate 300 or fixing the cover plate 300 downwards, the pressure sensor 130 contacts the second segment 420 in the infusion tubing 400, thereby enabling the pressure sensor 130 to detect the pressure in the second segment 420.

[0041] In some embodiments, the base 200 is provided with a receiving cavity 220. When the pump door 120 closes or opens the base 200, it can be understood that the pump door 120 closes or opens the receiving cavity 220. The peristaltic unit 140 may be at least partially housed in the receiving cavity 220, and the cover structure 300 may also be partially disposed within the receiving cavity 220. In addition, a clearance channel may be provided within the receiving cavity 220 for the infusion tube 400 to pass through.

[0042] For example, the infusion pump 10 also includes a control unit electrically connected to the peristaltic unit 140, which can control the fluid pressure and flow rate in the infusion tubing 400 by controlling the operating speed of the peristaltic unit 140. The faster the shaft rotates, the faster the fluid delivery speed.

[0043] In some application scenarios, such as Figure 4As shown, in an interventional ventricular assist system, the system includes a ventricular assist device 30, a control device 20, and an infusion pump 10. When the ventricular assist device 30 acts on the patient's left ventricle, it crosses the aortic valve, with its proximal end located within the aorta and its distal end within the left ventricle. This allows the ventricular assist device 30 to pump blood from the left ventricle into the aorta, providing partial or complete assistance to the left ventricular circulatory system. The control device 20 and the infusion pump 10 are located externally. The control device 20 controls and displays data on the ventricular assist device 30 and the infusion pump 10, and performs functions such as fault detection alarms and data recording.

[0044] For example, the control unit in the infusion pump 10 can be integrated into the infusion pump 10 (e.g., located in the accommodating cavity 220) or integrated into the control device 20. This application embodiment does not limit this.

[0045] The infusion tubing 400 is connected to the drive unit of the ventricular assist device 30. One end of the infusion tubing 400 can be connected to an infusion bottle or infusion bag, which can provide flushing fluids such as saline or heparin. The other end of the infusion tubing 400 can be connected to the drive unit of the ventricular assist device 30, which is equipped with a motor that drives the impeller to rotate. The fluid delivered by the infusion tubing 400 flows through the motor of the ventricular assist device 30 and then into the aorta. The flow direction of the fluid delivered by the infusion pump 10 is opposite to the direction of the blood pumped in the ventricular assist device 30, thereby achieving a fluid seal for the motor inside the ventricular assist device 30 and preventing blood from entering the motor through the gaps between the motor and the motor housing and / or bearings, which could lead to motor failure.

[0046] To ensure a fluid sealing effect, the infusion pump 10 needs to maintain the fluid pressure in the infusion tube 400 within a certain range to provide reliable back pressure to the ventricular assist device 30 and ensure the safe operation of the ventricular assist device 30.

[0047] Based on the above description, this application will now be described from the perspective of method examples.

[0048] Please see Figure 5 , Figure 5 This is a schematic flowchart of a pulsation control method for an infusion pump provided in an embodiment of this application, which is applied to, for example... Figure 1 The infusion pump shown. (As shown) Figure 5 As shown, the method includes the following steps.

[0049] S510. Obtain the uniform peristaltic cycle, wherein the uniform peristaltic cycle is the pulsation cycle of the pressure inside the infusion tube when the peristaltic unit runs at a first speed.

[0050] During operation, the peristaltic vanes 141 sequentially squeeze the infusion tubing 400. This sequential peristalsis of the vanes 141 causes inherent pressure pulsation within the tubing 400. Specifically, as the peristaltic vanes squeeze the tubing 400 from the first to the last, the fluid in the tubing 400 is transported from the position of the first vane to the position of the last vane, generating pulses in the fluid during this process. The periodic peristalsis of the vanes 141 causes periodic pulsation of the fluid in the tubing 400. If the pulsation is too large, it may prevent the delivery of a stable and smooth fluid pressure to the user.

[0051] In practical applications, the peristaltic plate 141 peristalts at a set speed in a uniform and periodic manner. When the peristaltic plate 141 contacts and squeezes the infusion tube 400, due to the lag in the pressure response within the infusion tube 400, the pressure within the infusion tube 400 gradually increases from its lowest point until it reaches its maximum value, and then gradually decreases. In the next cycle, when the peristaltic plate 141 contacts and squeezes the infusion tube 400 again, the pressure within the infusion tube 400 gradually increases from its lowest point to its maximum value again. The time interval between the same peristaltic plate 141 contacting and squeezing the infusion tube 400 is the peristaltic cycle, thus causing the target pressure curve within the infusion tube 400 to exhibit periodic pulsations.

[0052] In the application scenario of the ventricular assist system, the infusion pump 10 includes an adjustment phase and a stabilization phase during operation. During the stabilization phase, the flow rate of the infusion tubing 400 is greater than that during the adjustment phase. The adjustment phase is defined as the absolute value of the flow rate difference within the infusion tubing 400 continuously exceeding a second threshold. The stabilization phase is defined as the absolute value of the pressure difference within the infusion tubing 400 continuously being less than or equal to a first threshold, and the absolute value of the flow rate difference within the infusion tubing 400 continuously being less than or equal to a second threshold, within a preset time period.

[0053] When the infusion pump 10 is started to provide back pressure to the ventricular assist device 30, the fluid flow rate in the infusion tubing 400 enters an adjustment phase, a stabilization phase, and a flushing phase, respectively. After the infusion pump 10 starts, fluid begins to be delivered through the infusion tubing 400. Within a certain period after the infusion pump 10 starts, it enters the adjustment phase. During the adjustment phase, the speed of the peristaltic unit 140 gradually increases to rapidly raise the outlet pressure of the infusion tubing 400, and the fluid flow rate also increases rapidly. When the outlet pressure of the infusion tubing 400 rises to a certain value, it reaches a stable state, while the fluid flow rate continues to gradually increase. When the fluid flow rate rises to a certain value and tends to stabilize, the infusion pump 10 enters the stabilization phase. During the stabilization phase, the peristaltic unit 140 moves at a uniform speed to stabilize both the outlet pressure and fluid flow rate of the infusion tubing 400 within a certain range.

[0054] The first speed is the peristaltic speed of the peristaltic unit when the infusion pump reaches the stable phase. During operation of the ventricular assist device 30, the infusion pump 10 needs to be within a preset operating pressure range. After the infusion pump 10 starts, it transitions from an adjustment phase to a stable phase, providing stable back pressure to the ventricular assist device 30 during this phase. The pressure maintained by the infusion tubing 40 from startup to the stable phase may vary each time the infusion pump 10 reaches this stage, but it remains within the operating pressure range. After the infusion pump 10 enters the stable phase, the peristaltic unit 140 continues to move at a constant peristaltic speed at the same rate as when the stable phase was reached. Therefore, when detecting the constant peristaltic cycle of the peristaltic unit 140, the speed of the peristaltic unit 140 at the moment the infusion pump 10 enters the stable phase can be used for measurement.

[0055] In one embodiment, obtaining the uniform peristaltic cycle includes: obtaining a target pressure curve, which is a curve of the pressure inside the infusion tube during a preset time when the peristaltic unit runs at a first speed after the infusion tube has reached a stable stage; and determining the uniform peristaltic cycle by the average time between adjacent troughs or peaks in the target pressure curve.

[0056] In practical applications, the infusion pump 10 mainly operates in the stable phase. Therefore, before the ventricular assist system is used or shipped, the uniform peristaltic cycle of the infusion pump 10 at different peristaltic speeds can be tested. Specifically, after the infusion pump 10 enters the stable phase, the peristaltic unit 140 is controlled to peristalse at different speeds for a preset time, and the pressure value in the infusion tube 400 is measured in real time using the pressure sensor 130 within the preset time period and fed back to the control unit. The control unit generates and stores pressure curves at different speeds based on the pressure values. When the ventricular assist system is running, the control unit can first obtain the peristaltic speed of the infusion pump 10 when it is in the stable phase, and then determine the target pressure curve corresponding to the first speed from multiple pressure curves based on this peristaltic speed. By calculating the average interval time between adjacent peaks or troughs in the target pressure curve, the uniform peristaltic cycle Ta at the first speed can be estimated.

[0057] In this embodiment of the application, the uniform peristaltic cycle of the infusion pump at different peristaltic speeds is measured in advance before use, which can reduce the time to obtain the uniform peristaltic cycle and accelerate the reduction of pressure pulsation in the infusion tube 400.

[0058] It should be noted that in the application scenario of ventricular assist system, the first speed is within the range of the normal operating speed of the infusion pump, such as the first preset speed being within the range of 2mL / h-30mL / h.

[0059] In another embodiment, obtaining the uniform peristaltic cycle includes: after detecting that the infusion pump is in a stable phase, recording n first times, where the first time is the time between two consecutive times when the pressure in the infusion tube reaches a preset pressure when the peristaltic unit is running at a first speed, and n is a positive integer; and determining the average value of the calculated n first times as the uniform peristaltic cycle of the first speed.

[0060] When the ventricular assist system is running, after detecting that the infusion pump 10 has entered a stable phase for a preset time, the control unit can record the first time when the pressure value reaches the preset pressure twice consecutively, based on the pressure value fed back in real time by the pressure sensor 130. This preset pressure can be set within the pressure range of the infusion pump during normal operation, such as a preset pressure of 600 mmHg. Then, the average value of these n first times is calculated, and this average value is determined as the uniform peristaltic cycle Ta. For example, the uniform peristaltic cycle can be measured within the preset time after the infusion pump 10 enters the stable phase. Based on experience, this preset time can be set much longer than the uniform peristaltic cycle, such as 5 min, 10 min, or 15 min.

[0061] This application provides an embodiment for estimating the uniform peristaltic cycle of the peristaltic unit 140 during the operation of the ventricular assist system. The estimation can be made based on the current operating data of the infusion pump 10, which can further improve the accuracy of the uniform peristaltic cycle estimation.

[0062] S520. Calculate the rapid peristalsis cycle based on the uniform peristalsis cycle.

[0063] In this application, the control unit can control the peristaltic unit 140 to quickly complete a non-uniform peristalsis within a uniform cycle time, thereby reducing pressure pulsation within the infusion tube 400 and ensuring that the back pressure supplied to the ventricular assist device remains stable and smooth.

[0064] Optionally, calculating the rapid peristaltic cycle based on the uniform peristaltic cycle includes: calculating the peristaltic stroke of the peristaltic unit based on the uniform peristaltic cycle and the first speed; and calculating the rapid peristaltic time based on the peristaltic stroke and the second speed, wherein the second speed is m times the first speed, and m is greater than 1.

[0065] During the operation of the ventricular assist device 30, the infusion pump 10 moves at a constant peristaltic speed. The peristaltic stroke of the peristaltic unit 140 is fixed, and the peristaltic stroke is the distance between the first and second peristaltic plates. Since the peristaltic stroke of the peristaltic unit 140 is constant, the peristaltic stroke can be calculated based on the constant peristaltic period Ta and the first speed Va. Then, the time of rapid peristalsis is calculated based on the second speed Vr and the peristaltic stroke. Specifically, the formula for calculating the rapid peristaltic period is: Tr = Va * Ta / Vr. Where * indicates multiplication.

[0066] The second speed can be set to m times the first speed. For example, m can be 10.

[0067] S530. During the uniform peristaltic cycle, if the pressure inside the infusion tube is equal to the target pressure, the peristaltic unit is controlled to run the rapid peristaltic cycle at a second speed, and stops running after running the rapid peristaltic cycle, so as to reduce the pulsation amplitude of the pressure inside the infusion tube. The second speed is greater than the first speed.

[0068] In this application, after calculating the rapid peristalsis cycle, the control unit can stop peristalsis after the time of the rapid peristalsis cycle at the second speed within the time of the uniform peristalsis cycle. This ensures that the pressure in the infusion tube 400 is maintained within the normal working pressure range while reducing the amplitude of pressure pulsation in the infusion tube 400, thereby reducing the pressure pulsation of the fluid in the infusion pump 10.

[0069] Optionally, the method further includes: obtaining peak value and trough value, wherein the peak value is the average of all peaks in the target pressure curve, and the trough value is the average of all troughs in the target pressure curve; calculating the peak average value, which is the average of the peak value and the trough value; obtaining the application error magnitude and application error direction, wherein the application error magnitude is the pressure error required by the infusion pump in the current application scenario, and the application error direction is the error direction of the application error magnitude required by the infusion pump in the current application scenario; and adjusting the peak average value according to the application error magnitude and application error direction to obtain the target pressure.

[0070] The control unit can improve the large pressure pulsation phenomenon in the infusion tubing caused by the uniform peristalsis of the infusion pump 10 by reducing the maximum pressure value during pressure pulsation in the infusion tubing 400 and increasing the minimum pressure value during pressure pulsation in the infusion tubing 400. Specifically, when the pressure in the infusion tubing 400 is the target pressure, the control unit can control the peristaltic unit 140 to peristalse rapidly at a second speed, so that the pressure in the infusion tubing 400 begins to rise or fall at the target pressure, thereby increasing the minimum or decreasing the maximum pressure value during pressure pulsation in the infusion tubing 400, and thus reducing the amplitude of pressure pulsation in the infusion tubing 400.

[0071] In this application, to adapt the infusion pump 10 to the pressure requirements of different scenarios, the control unit can adjust the target pressure according to the requirements of the current application scenario of the infusion pump 10 to control the pulsation amplitude of the pressure in the infusion tubing 400. The target pressure is located within the pulsation amplitude range of the pressure in the infusion tubing 400.

[0072] Specifically, after the infusion tubing 400 enters a stable phase, the control unit acquires the target pressure curve within the infusion tubing 400 via the pressure sensor 130, and calculates the peak and trough values ​​in the target pressure curve. These peak and trough values ​​are the average of the maximum and minimum pressure values ​​during a certain time period of pressure pulsation in the infusion tubing 400 within the stable phase, respectively. Further, the control unit acquires the magnitude and direction of the application error for the application scenario of the infusion pump 10. The magnitude of the application error is the allowable range of pressure pulsation in the current application scenario, and the direction of the application error is the allowable direction of pressure error in the current application scenario. If the application error direction is higher than the preset pressure range, meaning the maximum pressure within the infusion tubing 400 will not harm the user, then the target pressure can be greater than the peak average, increasing the minimum pressure pulsation value within the infusion tubing 400. If the application error direction is lower than the preset pressure range, meaning the minimum pressure within the infusion tubing 400 will not harm the user, then the target pressure can be less than the peak average, reducing the maximum pressure pulsation value within the infusion tubing 400. For example, in a ventricular assist system, the pressure within the infusion tubing 400 mm is allowed to be higher than the preset pressure range, but it is not allowed to be lower than the preset pressure range.

[0073] The control unit calculates the average peak value of the peak and trough values, and then adjusts the average peak value based on the magnitude and direction of the application error to obtain the target pressure.

[0074] For example, in a ventricular assist system, the preset pressure range of the infusion pump 10 is 500 mmHg-700 mmHg, the applied pressure error is 150 mmHg, and the applied error direction is higher than the preset pressure range. If the calculated peak average value is 600 mmHg, then the target pressure can be determined as 625 mmHg.

[0075] For example, in an infusion scenario, if the preset pressure range of the infusion pump 10 is 200 mmHg-600 mmHg, the applied pressure error is 100 mmHg, and the applied error direction is below the preset pressure range, and if the calculated peak average value is 400 mmHg, then the target pressure can be determined as 200 mmHg.

[0076] As can be seen, this application proposes a pulsation control method for an infusion pump. It obtains a uniform peristaltic cycle, which is the pulsation cycle of the pressure inside the infusion tubing when the peristaltic unit operates at a first speed. A rapid peristaltic cycle is calculated based on the uniform peristaltic cycle. If the pressure inside the infusion tubing equals the target pressure within the uniform peristaltic cycle, the peristaltic unit is controlled to operate at a second speed for the rapid peristaltic cycle, and stops operating after the rapid peristaltic cycle to reduce the amplitude of the pressure pulsation inside the infusion tubing. The second speed is greater than the first speed. Within the uniform peristaltic cycle, when the pressure inside the infusion tubing drops to the target pressure, this application uses the second speed to operate the rapid peristaltic cycle and stops operating for the remaining time of the uniform peristaltic cycle. While maintaining the pressure inside the infusion tubing, it can reduce the amplitude of the pressure pulsation, thereby providing a more stable and reliable back pressure for the ventricular assist device and ensuring the safe use of the ventricular assist device.

[0077] The above primarily describes the solutions of the embodiments of this application from the perspective of the method execution process. It is understood that, in order to achieve the above functions, the network device includes corresponding hardware structures and / or software modules for executing each function. Those skilled in the art should readily recognize that, in conjunction with the units and algorithm steps of the various examples described in the embodiments provided herein, this application can be implemented in hardware or a combination of hardware and computer software. Whether a function is executed in hardware or by computer software driving hardware depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0078] For example, this application provides an infusion pump, the infusion pump comprising:

[0079] Infusion tubing is used to transport fluids;

[0080] The peristaltic unit is used to drive the fluid flow in the infusion tube;

[0081] The control unit, which is communicatively connected to the peristaltic unit, is used for:

[0082] Obtain the uniform peristaltic cycle, wherein the uniform peristaltic cycle is the pulsation cycle of the pressure inside the infusion tube when the peristaltic unit runs at a first speed at a uniform speed;

[0083] Calculate the rapid peristalsis cycle based on the uniform peristalsis cycle;

[0084] During the uniform peristaltic cycle, if the pressure inside the infusion tube is equal to the target pressure, the peristaltic unit is controlled to run the rapid peristaltic cycle at a second speed, and stops running after running the rapid peristaltic cycle, so as to reduce the pulsation amplitude of the pressure inside the infusion tube. The second speed is greater than the first speed.

[0085] Optionally, in obtaining the uniform peristaltic cycle, the control unit is specifically used to: obtain a target pressure curve, which is a curve of the pressure inside the infusion tube during a preset time when the peristaltic unit runs at a first speed after the infusion tube has reached a stable stage; and determine the average time between adjacent troughs or peaks in the target pressure curve as the uniform peristaltic cycle.

[0086] Optionally, in obtaining the uniform peristaltic cycle, the control unit is specifically used to: after detecting that the infusion pump is in a stable phase, record n ​​first times, where the first time is the time when the pressure in the infusion tube reaches a preset pressure twice consecutively when the peristaltic unit is running at a first speed, and n is a positive integer; and determine the average value of the calculated n first times as the uniform peristaltic cycle of the first speed.

[0087] Optionally, the stabilization phase is defined as the absolute value of the pressure difference in the infusion tube being continuously less than or equal to a first threshold and the absolute value of the flow rate difference in the fluid infusion tube being continuously less than or equal to a second threshold for a preset time period.

[0088] Optionally, the first speed is the peristaltic speed of the peristaltic unit when the infusion pump reaches a stable stage.

[0089] Optionally, in calculating the rapid peristaltic cycle based on the uniform peristaltic cycle, the control unit is specifically configured to: calculate the peristaltic stroke of the peristaltic unit based on the uniform peristaltic cycle and the first speed; and calculate the rapid peristaltic time based on the peristaltic stroke and the second speed, wherein the second speed is m times the first speed, and m is greater than 1.

[0090] Optionally, the control unit is further configured to: acquire peak value and trough value, wherein the peak value is the average of all peaks in the target pressure curve and the trough value is the average of all troughs in the target pressure curve; calculate the peak average value, which is the average of the peak value and the trough value; acquire the application error magnitude and application error direction, wherein the application error magnitude is the pressure error required by the infusion pump in the current application scenario and the application error direction is the error direction of the application error magnitude required by the infusion pump in the current application scenario; and adjust the peak average value according to the application error magnitude and application error direction to obtain the target pressure.

[0091] For example, this application also provides a medical device that includes the control unit or infusion pump described above.

[0092] The control unit of each of the above solutions has the function of implementing the corresponding steps performed by the medical device in the above method; the function can be implemented by hardware or by hardware executing corresponding software.

[0093] In embodiments of this application, the control unit may also be a chip or a chip system, such as a system on a chip (SoC).

[0094] Please see Figure 6 , Figure 6 This is a schematic diagram of the structure of a medical device provided in an embodiment of this application. The medical device includes: one or more processors, one or more memories, one or more communication interfaces, and one or more programs; the one or more programs are stored in the memories and configured to be executed by the one or more processors.

[0095] The above procedure includes instructions for performing the following steps: obtaining a uniform peristaltic cycle, wherein the uniform peristaltic cycle is the pulsation cycle of the pressure inside the infusion tube when the peristaltic unit runs at a first speed; calculating a rapid peristaltic cycle based on the uniform peristaltic cycle; and, if the pressure inside the infusion tube is equal to the target pressure within the time of the uniform peristaltic cycle, controlling the peristaltic unit to run the rapid peristaltic cycle at a second speed, and stopping operation after running the rapid peristaltic cycle, so as to reduce the pulsation amplitude of the pressure inside the infusion tube, wherein the second speed is greater than the first speed.

[0096] All relevant content in each scenario involved in the above method embodiments can be referenced from the functional description of the corresponding functional module, and will not be repeated here.

[0097] It should be understood that the aforementioned memory may include read-only memory and random access memory, and provides instructions and data to the processor. A portion of the memory may also include non-volatile random access memory. For example, the memory may also store information about the device type.

[0098] In the embodiments of this application, the processor of the above-described device may be a Central Processing Unit (CPU), which may also be other general-purpose processors, digital signal processors (DSPs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor may be a microprocessor or any conventional processor, etc.

[0099] It should be understood that "at least one" in the embodiments of this application refers to one or more, and "more than one" 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, where A and B can be singular or plural. The character " / " generally indicates that the preceding and following related objects are in an "or" relationship. "At least one of the following" or similar expressions refer to any combination of these items, including any combination of single or plural items. For example, at least one of a, b, or c can represent: a, b, c, ab, ac, bc, or abc, where a, b, and c can be single or multiple.

[0100] In implementation, each step of the above method can be completed by integrated logic circuits in the processor's hardware or by instructions in software. The steps of the method disclosed in the embodiments of this application can be directly manifested as execution by a hardware processor, or as a combination of hardware and software units within the processor. The software units can reside in random access memory, flash memory, read-only memory, programmable read-only memory, electrically erasable programmable memory, registers, or other mature storage media in the art. This storage medium is located in memory, and the processor executes the instructions in the memory, combining them with its hardware to complete the steps of the above method. To avoid repetition, detailed descriptions are omitted here.

[0101] This application also provides a computer storage medium storing a computer program for electronic data interchange, which causes a computer to perform some or all of the steps of any of the methods described in the above method embodiments.

[0102] This application also provides a computer program product, which includes a non-transitory computer-readable storage medium storing a computer program operable to cause a computer to perform some or all of the steps of any of the methods described in the above method embodiments. This computer program product can be a software installation package.

[0103] It should be noted that, for the sake of simplicity, the foregoing method embodiments are all described as a series of actions. However, those skilled in the art should understand that this application is not limited to the described order of actions, as some steps may be performed in other orders or simultaneously according to this application. Furthermore, those skilled in the art should also understand that the embodiments described in the specification are preferred embodiments, and the actions and modules involved are not necessarily essential to this application.

[0104] In the above embodiments, the descriptions of each embodiment have different focuses. For parts not described in detail in a certain embodiment, please refer to the relevant descriptions in other embodiments.

[0105] If the aforementioned integrated units are implemented as software functional units and sold or used as independent products, they can be stored in a computer-readable storage device (CMD). Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a memory and includes several instructions to cause a computer device (which may be a personal computer, server, or TRP, etc.) to execute all or part of the steps of the methods of the various embodiments of this application. The aforementioned memory includes various media capable of storing program code, such as USB flash drives, read-only memory (ROM), random access memory (RAM), portable hard drives, magnetic disks, or optical disks.

[0106] Those skilled in the art will understand that all or part of the steps in the various methods of the above embodiments can be implemented by a program instructing related hardware. The program can be stored in a computer-readable storage device, which may include a flash drive, ROM, RAM, disk, or optical disk, etc.

[0107] The embodiments of this application have been described in detail above. Specific examples have been used to illustrate the principles and implementation methods of this application. The description of the above embodiments is only for the purpose of helping to understand the method and core ideas of this application. At the same time, for those skilled in the art, there will be changes in the specific implementation methods and application scope based on the ideas of this application. Therefore, the content of this specification should not be construed as a limitation of this application.

Claims

1. An infusion pump, characterized in that, The infusion pump includes: Infusion tubing is used to transport fluids; The peristaltic unit is used to drive the fluid flow in the infusion tube; The control unit, which is communicatively connected to the peristaltic unit, is used for: Obtain the uniform peristaltic cycle, wherein the uniform peristaltic cycle is the pulsation cycle of the pressure inside the infusion tube when the peristaltic unit runs at a first speed at a uniform speed; The rapid peristalsis time of the peristaltic unit is calculated based on the uniform peristalsis cycle; During the uniform peristaltic cycle time, when the pressure inside the infusion tube drops to the target pressure, the peristaltic unit is controlled to run at a second speed for the rapid peristaltic time, and stops running for the remaining time, so as to reduce the pulsation amplitude of the pressure inside the infusion tube. The second speed is greater than the first speed. In calculating the rapid peristaltic cycle based on the uniform peristaltic cycle, the control unit has the following functions: The peristaltic stroke of the peristaltic unit is calculated based on the uniform peristaltic cycle and the first speed; The rapid peristalsis time is calculated based on the peristaltic stroke and the second speed, wherein the second speed is m times the first speed, and m is greater than 1.

2. The infusion pump of claim 1, wherein, In obtaining the uniform peristaltic cycle, the control unit is specifically used for: Obtain a target pressure curve, which is the pressure inside the infusion tube during a preset time when the peristaltic unit operates at the first speed after the infusion tube has reached a stable stage. The average time between adjacent troughs or peaks in the target pressure curve is determined as the uniform peristalsis cycle.

3. The infusion pump of claim 1, wherein, In obtaining the uniform peristaltic cycle, the control unit is specifically used for: After detecting that the infusion pump is in a stable phase, n first times are recorded respectively. The first time is the time when the pressure in the infusion tube reaches the preset pressure twice consecutively when the peristaltic unit is running at the first speed, and n is a positive integer. The average value of the n first times is determined as the uniform creeping cycle of the first velocity.

4. The infusion pump of claim 2, wherein, The stable phase is defined as the absolute value of the pressure difference in the infusion tube being continuously less than or equal to a first threshold and the absolute value of the flow rate difference in the infusion tube being continuously less than or equal to a second threshold for a preset time period.

5. The infusion pump of claim 4, wherein, The first speed is the peristaltic speed of the peristaltic unit when the infusion pump reaches the stable stage.

6. The infusion pump of claim 2, wherein, The control unit is also used for: Obtain peak value and trough value, wherein the peak value is the average value of all peaks in the target pressure curve, and the trough value is the average value of all troughs in the target pressure curve; Calculate the peak average value, which is the average of the peak value and the trough value; The magnitude and direction of the application error are obtained. The magnitude of the application error is the pressure error required by the infusion pump in the current application scenario, and the direction of the application error is the error direction required by the infusion pump to achieve the magnitude of the application error in the current application scenario. The average value of the peak value is adjusted according to the magnitude and direction of the application error to obtain the target pressure.

7. The infusion pump of claim 6, wherein, In adjusting the peak average value according to the magnitude and direction of the application error to obtain the target pressure, the control unit is specifically used for: If the direction of the application error is higher than the preset pressure range, the target pressure is adjusted to be greater than the average value of the peak value according to the magnitude of the application error. If the direction of the application error is lower than the preset pressure range, the target pressure is adjusted to be lower than the average value of the peak value according to the magnitude of the application error.

8. The infusion pump of claim 5, wherein, The infusion pump operates in sequence through an adjustment phase and a stabilization phase. During the stabilization phase, the flow rate of the infusion tube is greater than that during the adjustment phase. The adjustment phase is characterized by the absolute value of the flow rate difference in the fluid flow rate within the infusion tube being continuously greater than the second threshold.

9. A medical device, characterized by The device includes a processor, a memory, and a communication interface. The memory stores one or more programs, which are executed by the processor. The one or more programs include instructions for performing the steps performed by the control unit in the infusion pump as claimed in any one of claims 1-8.

10. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores a computer program for electronic data interchange, wherein the computer program causes a computer to perform the steps performed by the control unit in the infusion pump as claimed in any one of claims 1-8.

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