A multiple pump cooperative control system for an artificial heart-lung machine

Abstract

The application belongs to the technical field of extracorporeal circulation control, and discloses a multiple-pump cooperative control system of a heart-lung machine, which comprises a main circulation loop, an auxiliary recovery loop, a pump set, a parameter acquisition unit and a control unit. The control unit determines a target single transfusion volume according to perfusion flow, drainage flow, venous pressure, blood storage level and recovery liquid level, and controls the recovery pump to transfuse in batches. After transfusion, the parameters are re-acquired, and the transfusion condition is re-judged. Meanwhile, when abnormality is acquired, the limited safety mode is entered. The system is used for multiple-pump cooperative control in the extracorporeal circulation process of the heart-lung machine.

Description

Technical Field

[0001] This invention belongs to the field of extracorporeal circulation control technology, specifically a multi-pump collaborative control system for an artificial heart-lung machine. Background Technology

[0002] During extracorporeal circulation support, artificial heart-lung machines typically include basic pathways such as venous drainage, blood storage, blood processing, and arterial perfusion. Some systems also have auxiliary recovery pathways such as surgical field suction or cardiac chamber drainage to return the recovered blood to the main circulation. In existing devices, the perfusion and drainage regulation on the main circulation side and the blood return action on the auxiliary recovery side are often controlled separately. Although the pathways are structurally connected, they are often adjusted locally based on a single flow rate, a single fluid level, or a single pressure parameter during operation.

[0003] In actual operation, when the auxiliary blood recovery enters the blood storage unit, it interacts with the drainage volume, perfusion volume, and changes in the blood storage level in the main circulation. When the rhythm of blood recovery does not match the current state of the main circulation, it is easy to cause a short-term increase in the blood storage level, rapid changes in fluid level, and increased fluctuations in venous pressure. When the blood storage level is too low, if only the drainage side load is increased, it may be limited by the venous side pressure conditions. In other words, the auxiliary recovery circuit and the main circulation circuit are not simply in a reflux relationship, but have the operational characteristics of fluid level, pressure, and flow rate being coupled together.

[0004] In existing technologies, if adjustments are made based solely on the liquid level at a certain moment, the flow rate of a certain channel, or a single pressure threshold, it is often difficult to simultaneously ensure the stability of perfusion, the continuity of drainage, and the reinfusion rhythm of auxiliary blood recovery on the main circulation side. In particular, when blood recovery is continuously entering and the blood storage level is changing, the single parameter control method cannot accurately reflect the real-time receiving status of auxiliary blood recovery in the main circulation, which can easily lead to insufficient coordination between the reinfusion action and the main circulation status. Summary of the Invention

[0005] The purpose of this invention is to provide a multi-pump collaborative control system for an artificial heart-lung machine to solve the problems mentioned in the background art.

[0006] To achieve the above objectives, the present invention provides the following technical solution: a multi-pump collaborative control system for an artificial heart-lung machine, the system comprising a main circulation loop, an auxiliary recovery loop, a pump set, a parameter acquisition unit, and a control unit; the main circulation loop includes a venous drainage path, a blood storage unit, a blood processing path, and an arterial perfusion path, used to complete extracorporeal circulation processing of blood; the auxiliary recovery loop includes an suction path, a recovery temporary storage unit, and a reinfusion path, wherein the recovery temporary storage unit is independently located outside the blood storage unit, and the blood recovered by the suction path first enters the recovery temporary storage unit, and then is sent to the blood storage unit through the reinfusion path.

[0007] By temporarily storing the auxiliary recovered blood before reinfusing it, the recovered blood is not directly and continuously incorporated into the main circulation, thus providing a buffer process for the auxiliary recovered blood to enter the blood storage unit and reducing sudden fluctuations in blood storage level and venous pressure.

[0008] The pump set includes a perfusion pump installed in the arterial perfusion pathway, a drainage adjustment component installed in the venous drainage pathway, and a recovery pump installed in the reinfusion pathway. The perfusion pump is used to maintain the perfusion flow rate in the main circulation, the drainage adjustment component is used to adjust the drainage flow rate in the venous drainage pathway, and the recovery pump is used to return the blood in the recovery storage unit to the blood storage unit. The parameter acquisition unit includes a perfusion flow rate acquisition component, a drainage flow rate acquisition component, a venous pressure acquisition component, a blood storage level acquisition component, a recovery fluid level acquisition component, and a reinfusion flow rate acquisition component, used to acquire the operating parameters in the main circulation loop and the auxiliary recovery loop, respectively.

[0009] The control unit is connected to the pump group and the parameter acquisition unit respectively. It collects perfusion flow rate, drainage flow rate, venous pressure, blood storage level and recovery level according to the preset sampling cycle, and calculates the blood storage level rise rate based on the continuous sampling results of the blood storage level. When the blood storage level is lower than the preset upper limit level, the blood storage level rise rate is not greater than the preset rise rate threshold, the venous pressure is greater than or equal to the preset lower limit of venous pressure, the difference in blood volume between drainage flow rate and perfusion flow rate within the preset measurement time reaches the preset difference blood volume threshold, and the recovery level is greater than or equal to the preset minimum reinfusion level, the control unit determines the target single reinfusion volume of blood in the current recovery storage unit and controls the recovery pump to perform one reinfusion.

[0010] During the reinfusion process, the control unit accumulates the actual reinfusion volume based on the reinfusion flow rate collected by the reinfusion flow rate acquisition unit. When the actual reinfusion volume reaches the target single reinfusion volume, or the recovery fluid level drops below the preset minimum reinfusion fluid level, the recovery pump stops. After the recovery pump stops, the control unit re-acquires the perfusion flow rate, drainage flow rate, venous pressure, blood storage level, and recovery fluid level after a preset stabilization time, and re-determines whether the conditions for the next reinfusion are met. If the conditions for the next reinfusion are not met, the recovery pump remains stopped.

[0011] Through the above structure and control method, the blood in the auxiliary recovery circuit is temporarily stored in the recovery storage unit and then reinfused into the blood storage unit in stages. Before and after each reinfusion, the perfusion flow, drainage flow, venous pressure and blood level in the main circulation circuit are judged. This makes the auxiliary recovery circuit and the main circulation circuit form a controlled coordination relationship, which is conducive to maintaining the stability of the blood storage unit fluid level and venous pressure when the recovered blood re-enters the main circulation.

[0012] In one embodiment of the present invention, the blood storage unit is a venous blood storage device, and the blood processing passage includes a membrane oxygenator; the recovery and temporary storage unit includes a degassing chamber and a blood storage chamber that are interconnected, the suction passage is connected to the degassing chamber, the reinfusion passage is connected to the blood storage chamber, a first one-way conduction structure is provided between the degassing chamber and the blood storage chamber, and a second one-way conduction structure is provided between the blood storage chamber and the reinfusion passage; the blood that is suctioned and recovered first enters the degassing chamber, then enters the blood storage chamber, and is subsequently sent to the blood storage unit via the reinfusion passage.

[0013] By temporarily storing and diverting the blood in the auxiliary recovery circuit before reinfusing it into the blood storage unit, the auxiliary recovered blood will not directly and continuously enter the main circulation circuit, thereby reducing the instantaneous fluctuations in the blood storage level and venous pressure during the reinfusion process.

[0014] In one embodiment of the present invention, the drainage adjustment component is a drainage pump or a drainage regulator installed in the venous drainage path; when the drainage adjustment component is a drainage regulator, a drainage flow sensor is installed in the venous drainage path to acquire the drainage flow; the control unit determines the differential blood volume based on the blood volume difference formed by the drainage flow and the perfusion flow within a preset measurement time, and determines the blood level rise rate based on the ratio of the difference between two adjacent blood level acquisition values ​​to the corresponding sampling time interval; the target single reinfusion volume is determined based on the differential blood volume and the preset single reinfusion upper limit.

[0015] Therefore, the amount of blood reinfused in the auxiliary recovery circuit is no longer a fixed set value, but corresponds to the drainage state, perfusion state and blood storage level change state in the main circulation circuit, so that the reinfusion action is coordinated with the operation state of the main circulation circuit.

[0016] In one embodiment of the present invention, when the blood level in the storage unit is lower than the preset lower limit, the control unit first determines whether the venous pressure is greater than or equal to the preset lower limit of venous pressure; when the venous pressure is greater than or equal to the preset lower limit of venous pressure, the control unit controls the drainage adjustment component to increase the drainage flow rate in the venous drainage path to increase the amount of blood entering the blood storage unit; when the venous pressure is lower than the preset lower limit of venous pressure, the control unit controls the perfusion pump to reduce the perfusion flow rate and keeps the recovery pump from reinfusing.

[0017] Accordingly, when the blood storage level is higher than the preset upper limit level, or when the rate of increase of the blood storage level is greater than the preset rate of increase threshold, the control unit immediately stops the recovery pump; after the blood storage level falls below the preset upper limit level again and the rate of increase of the blood storage level is no greater than the preset rate of increase threshold again, the control unit re-determines whether to perform reinfusion; through the above-mentioned adjustment process on both sides of the high and low liquid levels, the blood storage unit is kept within the predetermined operating range during the reinfusion process, so as to maintain stable cooperation between the main circulation loop and the auxiliary recovery loop.

[0018] In one embodiment of the present invention, when the perfusion flow acquisition component, drainage flow acquisition component, venous pressure acquisition component, blood storage level acquisition component, recovery fluid level acquisition component, or reinfusion flow acquisition component has no output signal, or when any acquisition value exceeds the corresponding preset effective range, the control unit enters a restricted safety mode; in the restricted safety mode, the control unit stops outputting reinfusion control commands to the recovery pump and limits the driving change rate of the perfusion pump and drainage adjustment component to within a preset upper limit of change rate.

[0019] By setting a restricted safety mode, the reinfusion action and the perfusion and drainage adjustment process in the main circulation loop are still constrained when parameter acquisition is abnormal, thereby avoiding imbalance in multi-pump coordinated control due to abnormal acquisition signals.

[0020] The beneficial effects of this invention are as follows: 1. This invention separates the recovery storage unit in the auxiliary recovery circuit from the blood storage unit, so that the blood drawn back is no longer directly and continuously fed into the main circulation circuit, but is first stored independently and then controlled to be reinfused into the blood storage unit. In this way, the blood recovered by the auxiliary recovery circuit has a separate buffer path and adjustment mechanism before entering the main circulation, which can reduce the instantaneous impact on the blood storage level and venous pressure during the blood return process, and avoid rapid fluctuations or short-term increases in the blood storage unit level due to the direct flow of recovered blood. Thus, the relationship between the auxiliary recovery circuit and the main circulation circuit is transformed from a direct superposition relationship to a coordinated relationship that can be adjusted in time and in parts. 2. This invention simultaneously collects perfusion flow rate, drainage flow rate, venous pressure, blood storage level, and recovery fluid level, and combines this with differential blood volume, the rate of rise of blood storage level, and a preset single reinfusion upper limit to determine the target single reinfusion volume. This ensures that each reinfusion action of the recovery pump is based on the current operating state of the main circulation. In other words, this invention does not reinfuse blood according to a fixed reinfusion volume or a single fluid level threshold, but rather determines whether to reinfuse and how much to reinfuse based on the actual drainage state, perfusion state, and fluid level change trend of the main circulation at the current stage. This makes the single reinfusion volume correspond to the real-time carrying capacity of the main circulation, thereby improving the coordination between multiple pumps and reducing the control imbalance problem caused by the mismatch between the reinfusion rhythm and the main circulation state. 3. This invention establishes corresponding linkage control strategies for low liquid level conditions, high liquid level conditions, and abnormal acquisition conditions. This enables the system to not only perform segmented reinfusion under normal conditions but also maintain basic stability of the main circulation loop under boundary and abnormal conditions. Specifically, at low liquid levels, the system prioritizes increasing drainage flow or decreasing perfusion flow based on venous pressure. At high liquid levels or when the liquid level rises too rapidly, the recovery pump is stopped promptly. When the acquisition signal is abnormal, the system enters a restricted safety mode and limits the variation of relevant actuators. Thus, this invention forms a complete control chain covering normal reinfusion, liquid level regulation, and abnormal protection, enabling the multi-pump collaborative control process of the cardiopulmonary bypass machine to have better continuity, stability, and controllability. Attached Figure Description

[0021] Figure 1 This is a flowchart of the multi-pump collaborative control system for the artificial heart-lung machine of the present invention; Figure 2 This is a flowchart of the multi-pump collaborative control process of the present invention; Figure 3 This is a flowchart illustrating the security protection process of the present invention. Detailed Implementation

[0022] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0023] like Figures 1 to 3 As shown, this embodiment of the invention provides a multi-pump collaborative control system for an artificial heart-lung machine, including a main circulation loop, an auxiliary recovery loop, a pump group, a parameter acquisition unit, and a control unit.

[0024] The main circulation circuit includes a venous drainage circuit, a blood storage unit, a blood processing circuit, and an arterial perfusion circuit. The auxiliary recovery circuit includes a suction circuit, a recovery storage unit, and a reinfusion circuit. The recovery storage unit is set up independently outside the blood storage unit, and the reinfusion circuit is connected to the blood storage unit.

[0025] The pump set includes an infusion pump installed in the arterial perfusion pathway, a drainage adjustment component installed in the venous drainage pathway, and a recovery pump installed in the reinfusion pathway; the parameter acquisition unit includes an infusion flow rate acquisition component installed in the arterial perfusion pathway, a drainage flow rate acquisition component and a venous pressure acquisition component installed in the venous drainage pathway, a blood storage level acquisition component installed in the blood storage unit, a recovery liquid level acquisition component installed in the recovery temporary storage unit, and a reinfusion flow rate acquisition component installed in the reinfusion pathway; the control unit is connected to the pump set and the parameter acquisition unit respectively.

[0026] During system operation, the control unit collects perfusion flow, drainage flow, venous pressure, blood storage level, and recovery fluid level according to a preset sampling cycle, and calculates the rate of increase of blood storage level based on the difference between two adjacent blood storage level collection values ​​and the corresponding sampling time interval. At the same time, the control unit uses the blood volume corresponding to the positive part of the difference between drainage flow and perfusion flow within a preset measurement time as the difference blood volume, and uses the smaller value between the difference blood volume and the preset single reinfusion upper limit as the target single reinfusion volume.

[0027] When the blood level in the storage unit is lower than the preset upper limit, the rate of increase of the blood level in the storage unit is not greater than the preset rate of increase threshold, the venous pressure is greater than or equal to the preset lower limit of venous pressure, the differential blood volume is greater than or equal to the preset differential blood volume threshold, and the recovery level is greater than or equal to the preset minimum reinfusion level, the control unit controls the recovery pump to start, so that the blood in the recovery temporary storage unit is transported to the blood storage unit through the reinfusion pathway.

[0028] During the return process, the control unit accumulates the actual return volume based on the return flow rate collected by the return flow rate acquisition component; when the actual return volume reaches the target single return volume, or when the recovery liquid level is lower than the preset minimum return liquid level, the control unit controls the recovery pump to stop working.

[0029] After the recovery pump stops, the control unit, after a preset stabilization time, collects perfusion flow, drainage flow, venous pressure, blood reservoir level, and recovery fluid level again, and recalculates the rate of rise of the blood reservoir level and the differential blood volume to determine whether the conditions for the next reinfusion are still met. If the conditions for the next reinfusion are still met after the reassessment, the control unit controls the recovery pump to perform the next reinfusion; if the conditions for the next reinfusion are not met after the reassessment, the recovery pump remains stopped.

[0030] In this way, the blood in the auxiliary recovery circuit is not continuously reinfused into the blood storage unit, but is reinfused in stages when the blood storage level, the rate of increase of the blood storage level, the venous pressure, the differential blood volume, and the recovery fluid level meet the corresponding conditions, so that the reinfusion process is coordinated with the perfusion, drainage, and blood storage status in the main circulation circuit.

[0031] In this embodiment, the blood storage unit adopts a venous blood storage device, and the blood processing pathway includes a membrane oxygenator. The venous blood storage device is arranged between the venous drainage pathway and the blood processing pathway to receive blood introduced by the venous drainage pathway and blood returned by the auxiliary recovery circuit, and to provide a transitional storage space for blood that subsequently enters the membrane oxygenator.

[0032] A membrane oxygenator is positioned between the venous blood reservoir and the arterial perfusion pathway to oxygenate and exchange gases in the extracorporeal circulation. The venous blood reservoir and membrane oxygenator are arranged in series, ensuring that blood in the main circulation loop undergoes both storage and buffering stages and blood processing before entering the arterial perfusion pathway, thus providing a stable upstream blood supply for the perfusion process in the main circulation loop. In this embodiment, both the venous blood reservoir and the membrane oxygenator can employ commonly used structures in the art, with their cooperation focusing on forming a synergistic relationship with the auxiliary recovery circuit, pump assembly, and control unit.

[0033] In this embodiment, the recovery and temporary storage unit includes a degassing chamber and a blood storage chamber that are interconnected; the suction passage is connected to the degassing chamber, and the reinfusion passage is connected to the blood storage chamber. A first one-way conduction structure is provided between the degassing chamber and the blood storage chamber, and a second one-way conduction structure is provided between the blood storage chamber and the reinfusion passage; the blood recovered by the suction passage first enters the degassing chamber, and then enters the blood storage chamber through the first one-way conduction structure. The blood temporarily stored in the blood storage chamber is reinfused into the venous blood storage device through the second one-way conduction structure and the reinfusion passage under the action of the recovery pump.

[0034] With the above structure, the blood in the auxiliary recovery circuit undergoes an independent temporary storage and diversion process before entering the venous blood reservoir, instead of directly and continuously entering the main circulation circuit after suction. Thus, the process of auxiliary blood recovery entering the venous blood reservoir is divided into three stages: suction recovery, temporary storage buffer, and controlled reinfusion. This allows the control unit to determine whether to perform reinfusion and how much reinfusion to perform based on the venous blood reservoir level, level change trend, venous pressure, differential blood volume, and recovery level before the recovered blood actually enters the venous blood reservoir.

[0035] In this embodiment, the drainage adjustment component uses a drainage pump or a drainage regulator installed in the venous drainage path. When the drainage adjustment component uses a drainage pump, the drainage flow rate in the venous drainage path is changed by adjusting the pump's rotation speed. When the drainage adjustment component uses a drainage regulator, a drainage flow sensor is installed in the venous drainage path to acquire the drainage flow rate. In other words, this embodiment does not limit the drainage-side control method to a single pump control scheme, but allows for both pump control and regulator control. Regardless of the method used, the control unit uses the actual drainage flow rate as the basis for subsequent control. The calculation of differential blood volume, the determination of the target single reinfusion volume, and the adjustment actions under high and low fluid levels are all based on the actual drainage flow rate, and do not replace the actual flow rate data with the theoretical opening or theoretical rotation speed of the actuator.

[0036] In this embodiment, the differential blood volume is the positive portion of the difference between the drainage flow rate and the perfusion flow rate within a preset measurement period. Specifically, the control unit reads the drainage flow rate and the perfusion flow rate simultaneously in each measurement cycle. When the drainage flow rate is greater than the perfusion flow rate, the difference between the two is taken as the effective flow difference. When the drainage flow rate is less than or equal to the perfusion flow rate, the effective flow difference in that cycle is recorded as zero.

[0037] The control unit accumulates and converts the effective flow difference within each metering cycle according to the preset metering duration to obtain the difference blood volume. Using this calculation method, the difference blood volume reflects the flow rate that the main circulation loop can accept for auxiliary blood recovery within the current period, avoiding the introduction of negative difference values ​​generated when reinfusion conditions are not met into the calculation of subsequent reinfusion volume.

[0038] In this embodiment, the rate of increase of the blood level in the reservoir is determined by the ratio of the difference between two adjacent blood level measurements to the corresponding sampling time interval. The control unit continuously acquires the blood level in the venous blood reservoir according to a preset sampling cycle, and substitutes the results of two adjacent level measurements with the corresponding sampling time interval into the calculation to obtain the current rate of increase of the blood level. When the rate of increase of the blood level is large, it indicates that the blood in the venous blood reservoir is increasing significantly. In this case, even if the current level has not yet reached the preset upper limit level, it is not advisable to immediately continue reinfusing auxiliary blood recovery. When the rate of increase of the blood level is small and within the allowable range, the venous pressure, differential blood volume, and recovery level can be further combined to determine whether reinfusion conditions are met. Thus, the rate of increase of the blood level in the reservoir is used to characterize the trend of change in the venous blood reservoir level, so that the control unit considers not only the current level height but also the rate of change of the level when determining whether to perform reinfusion.

[0039] In this embodiment, the target single reinfusion volume is the smaller of the difference in blood volume and the preset single reinfusion upper limit. After the reinfusion start condition is met, the control unit first compares the current difference in blood volume with the preset single reinfusion upper limit. When the difference in blood volume is less than the preset single reinfusion upper limit, the target single reinfusion volume is the difference in blood volume. When the difference in blood volume is greater than or equal to the preset single reinfusion upper limit, the target single reinfusion volume is the preset single reinfusion upper limit. By adopting this method, the target single reinfusion volume corresponds to the current flow state of the main circulation loop and is also constrained by the preset single reinfusion upper limit, thereby avoiding excessive blood input to the venous blood reservoir during a single reinfusion.

[0040] In this embodiment, when the blood level in the venous blood reservoir is lower than the preset lower limit, the control unit first determines whether the venous pressure is greater than or equal to the preset lower limit of venous pressure.

[0041] If the venous pressure is greater than or equal to the preset lower limit of venous pressure, the control unit controls the drainage adjustment component to increase the drainage flow rate, thereby increasing the amount of blood entering the venous reservoir; if the venous pressure is lower than the preset lower limit of venous pressure, the control unit controls the perfusion pump to reduce the perfusion flow rate and keeps the recovery pump stopped from reinfusing.

[0042] By adopting the above treatment sequence, the adjustment action under low fluid level conditions is based on maintaining the venous pressure within the allowable range, and avoids further increasing the drainage flow when the venous pressure is already too low.

[0043] In this embodiment, when the blood level in the venous blood reservoir is higher than the preset upper limit level, or when the rate of increase of the blood level is greater than the preset rate of increase threshold, the control unit immediately stops the recovery pump. After the recovery pump stops, the reinfusion does not resume immediately. Instead, the control unit re-determines whether to perform reinfusion only after the blood level falls below the preset upper limit level again and the rate of increase of the blood level is no greater than the preset rate of increase threshold. Thus, the reinfusion control is simultaneously limited by the liquid level height condition and the liquid level change trend condition, avoiding the continuation of reinfusion when the liquid level is already too high or is still rising rapidly.

[0044] In this embodiment, the control unit is also equipped with a restricted safety mode. When the perfusion flow acquisition component, drainage flow acquisition component, venous pressure acquisition component, blood storage level acquisition component, recovery fluid level acquisition component, or reinfusion flow acquisition component has no output signal, or any acquisition value exceeds the corresponding preset effective range, the control unit enters the restricted safety mode. In the restricted safety mode, the control unit stops outputting reinfusion control commands to the recovery pump and limits the driving change rate of the perfusion pump and drainage adjustment component to within the preset upper limit of change rate.

[0045] The absence of output signal here includes situations where no valid data is acquired for several consecutive sampling cycles. If the data exceeds the corresponding preset valid range, the judgment is made based on the calibration detection range of each acquisition component. By setting a restricted safety mode, the feedback action and the perfusion and drainage adjustment actions in the main circulation loop are still constrained when the acquisition is abnormal.

[0046] In practice, preset sampling period, preset metering duration, preset stabilization time, preset upper limit liquid level, preset lower limit liquid level, preset rise rate threshold, preset lower limit of venous pressure, preset minimum reinfusion liquid level, preset upper limit of single reinfusion, and preset upper limit of change rate can be set through equipment calibration or pre-experiment tuning based on the venous blood storage device volume range, the target perfusion range of the main circulation loop, the safe pressure range of venous drainage, the effective volume range of the recovery and temporary storage unit, and the detection response speed of each acquisition component.

[0047] The above parameters can take different values ​​under different equipment specifications, different extracorporeal circulation application scenarios and different circuit volume configurations, but their setting principle remains consistent. That is, the start, stop and restart of the recovery pump are all based on the aforementioned reinfusion judgment conditions, rather than the existence of blood to be reinfused in the auxiliary recovery circuit as the sole judgment criterion.

[0048] It should be noted that, in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such process, method, article, or apparatus.

[0049] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. A multi-pump coordinated control system for an artificial heart-lung machine, characterized in that: It includes the main circulation loop, auxiliary recovery loop, pump set, parameter acquisition unit and control unit; The main circulation circuit includes a venous drainage circuit, a blood storage unit, a blood processing circuit, and an arterial perfusion circuit; The auxiliary recovery circuit includes an aspiration path, a recovery storage unit, and a reinfusion path. The recovery storage unit is independently located outside the blood storage unit, and the reinfusion path is connected to the blood storage unit. The pump assembly includes an infusion pump disposed on the arterial infusion pathway, a drainage adjustment component for adjusting the drainage flow in the venous drainage pathway, and a recovery pump disposed on the reinfusion pathway. The parameter acquisition unit includes a perfusion flow acquisition component disposed on the arterial perfusion pathway, a drainage flow acquisition component and a venous pressure acquisition component disposed on the venous drainage pathway, a blood storage level acquisition component disposed on the blood storage unit, a recovery liquid level acquisition component disposed on the recovery temporary storage unit, and a return flow acquisition component disposed on the return pathway. The control unit is electrically connected to the pump group and the parameter acquisition unit, respectively. The control unit is used to collect perfusion flow rate, drainage flow rate, venous pressure, blood storage level and recovery fluid level according to a preset sampling cycle, and calculate the blood storage level rise rate based on the blood storage level. The control unit is also used to determine the target single reinfusion volume and control the recovery pump to perform one reinfusion when the following conditions are met simultaneously: the blood level in the reservoir is lower than the preset upper limit level, the rate of rise of the blood level in the reservoir is not greater than the preset rate of rise threshold, the venous pressure is greater than or equal to the preset lower limit of venous pressure, the difference in blood volume determined by the drainage flow rate and the perfusion flow rate is greater than or equal to the preset difference in blood volume threshold, and the recovery level is greater than or equal to the preset minimum reinfusion level. The control unit is also used to accumulate the actual return volume based on the return flow collected by the return flow acquisition component, and to stop the recovery pump when the actual return volume reaches the target single return volume or the recovery liquid level is lower than the preset minimum return liquid level. The control unit is also used to collect perfusion flow, drainage flow, venous pressure, blood storage level and recovery fluid level again after a preset stabilization time after stopping the recovery pump, and recalculate the blood storage level rise rate and differential blood volume to determine whether to perform the next reinfusion again; if the conditions are not met, the control unit keeps the recovery pump stopped from reinfusing. The differential blood volume is the positive portion of the difference between the drainage flow rate and the perfusion flow rate within a preset measurement time.

2. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 1, characterized in that: The blood storage unit is a venous blood storage device, and the blood processing pathway includes a membrane oxygenator.

3. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 2, characterized in that: The recovery and temporary storage unit includes a degassing chamber and a blood storage chamber that are interconnected. The suction passage is connected to the degassing chamber, and the reinfusion passage is connected to the blood storage chamber. A first one-way conduction structure is provided between the degassing chamber and the blood storage chamber, and a second one-way conduction structure is provided between the blood storage chamber and the reinfusion passage.

4. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 3, characterized in that: The drainage adjustment component is a drainage pump or a drainage regulator installed on the venous drainage path; when the drainage adjustment component is a drainage regulator, the drainage flow acquisition component is a drainage flow sensor installed on the venous drainage path.

5. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 4, characterized in that: The rate of increase of the blood storage level is the ratio of the difference between two adjacent blood storage level acquisition values ​​to the corresponding sampling time interval.

6. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 5, characterized in that: The target single infusion amount is the smaller value between the difference in blood volume and the preset single infusion upper limit.

7. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 6, characterized in that: When the blood level in the reservoir is lower than the preset lower limit, the control unit first determines whether the venous pressure is greater than or equal to the preset lower limit of venous pressure; if the determination result is yes, the control unit controls the drainage adjustment component to increase the drainage flow rate; if the determination result is no, the control unit controls the infusion pump to reduce the infusion flow rate and keeps the recovery pump from reinfusing.

8. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 7, characterized in that: When the blood level in the reservoir is higher than the preset upper limit level, or when the rate of increase of the blood level in the reservoir is greater than the preset rate of increase threshold, the control unit immediately stops the recovery pump; after the blood level in the reservoir falls below the preset upper limit level again and the rate of increase of the blood level in the reservoir is no greater than the preset rate of increase threshold again, the control unit re-determines whether to perform the recovery pump.

9. The multi-pump coordinated control system for an artificial heart-lung machine according to claim 8, characterized in that: The control unit is configured to enter a restricted safety mode when any of the following conditions occur: the perfusion flow acquisition component has no output signal, the drainage flow acquisition component has no output signal, the venous pressure acquisition component has no output signal, the blood storage level acquisition component has no output signal, the recovery fluid level acquisition component has no output signal, the reinfusion flow acquisition component has no output signal, or any acquired value exceeds the corresponding preset effective range; in the restricted safety mode, the control unit stops outputting reinfusion control commands to the recovery pump and limits the driving change rate of the perfusion pump and the drainage adjustment component to within a preset upper limit of change rate.

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