WO2024131262A1 - Procédé et dispositif de mesure de la pression artérielle à la sortie d'une pompe à sang - Google Patents

Procédé et dispositif de mesure de la pression artérielle à la sortie d'une pompe à sang Download PDF

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Publication number
WO2024131262A1
WO2024131262A1 PCT/CN2023/126204 CN2023126204W WO2024131262A1 WO 2024131262 A1 WO2024131262 A1 WO 2024131262A1 CN 2023126204 W CN2023126204 W CN 2023126204W WO 2024131262 A1 WO2024131262 A1 WO 2024131262A1
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WO
WIPO (PCT)
Prior art keywords
fluid
pressure
motor
outlet
blood
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PCT/CN2023/126204
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English (en)
Chinese (zh)
Inventor
吕骁
吕世文
古珮瑶
Original Assignee
上海炫脉医疗科技有限公司
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Publication of WO2024131262A1 publication Critical patent/WO2024131262A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
    • A61M60/554—Regulation using real-time blood pump operational parameter data, e.g. motor current of blood pressure
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
    • Y02A90/00—Technologies having an indirect contribution to adaptation to climate change
    • Y02A90/10—Information and communication technologies [ICT] supporting adaptation to climate change, e.g. for weather forecasting or climate simulation

Definitions

  • the present application relates to the field of medical device technology, for example, to a method and device for measuring blood pressure at an outlet of a blood pump.
  • interventional cardiac treatment surgery is a common treatment scheme, which uses a stable hemodynamic assist device in conjunction with the surgery, and a blood pump assists the patient's heart to eject blood.
  • the blood pressure of ejection is an important indicator, and its fluid pressure needs to be accurately monitored.
  • the related technology discloses an intravascular blood pump with an outflow hose.
  • the technical defects of this design are: first, the second pressure sensor is also flushed by the blood while measuring the blood pressure of the outflowing blood. Under long-term blood flow flushing, the pressure sensor is prone to damage or displacement, resulting in inaccurate received pressure values or directly affecting the blood pumping function of the blood pump; secondly, during the process of blood flowing from the outflow hose into the aorta, it rubs against the outflow hose and the discharge port, and the blood pressure inside the outflow hose is actually different from the blood pressure in the aorta, making it difficult to obtain accurate aortic blood pressure.
  • the setting of the pressure sensor increases the implants in the patient's body, increasing the surgical risk; second, the pressure sensor is easily damaged by long-term blood flow impact during operation, and the error of the long-term implant measurement value is large; third, the measurement position of the aortic blood pressure is inaccurate.
  • the present application provides a method for measuring blood pressure at the outlet of a blood pump in order to address situations such as the placement of a pressure sensor in the body and inaccurate pressure measurement results.
  • the present application provides a method for measuring blood pressure at an outlet of a blood pump, wherein the blood pump comprises a motor and a delivery tube, a fluid enters the motor through the delivery tube, and the outlet is located in the aorta or the pulmonary artery after the blood pump is implanted, comprising: retrieving a reference data set obtained from a test environment, wherein the reference data set comprises the following reference data: a pressure difference of the fluid before and after flowing through the motor and a fluid flow rate in the delivery tube under conditions of different working parameters and different driving parameters; wherein the working parameters comprise a first working parameter, and the driving parameters comprise a first driving parameter; after the blood pump is placed in a patient, measuring or calculating the fluid flow rate under conditions of the first working parameter and the first driving parameter, And obtain the corresponding fluid pressure difference through the benchmark data set; measure the fluid pressure flowing in front of the motor, thereby obtaining the fluid pressure flowing after the motor, wherein the fluid pressure flowing after the motor is the sum of the fluid pressure flowing in front of the motor and the
  • a device for measuring blood pressure at the outlet of a blood pump which executes the above method, includes: a power unit, a retrieval unit, a control unit and a calculation unit; wherein the power unit is configured to drive the motor of the blood pump and adjust the motor speed; the retrieval unit is configured to retrieve a reference data set obtained from a test environment, thereby obtaining a fluid pressure difference corresponding to the fluid flow rate; the control unit includes a fluid drive device and a pressure sensor, the drive device is configured to control the flow rate and pressure of the fluid, and the pressure sensor is configured to measure the fluid pressure before flowing through the motor; the calculation unit is configured to obtain the fluid pressure difference of the retrieval unit and the fluid pressure of the control unit, and obtain the fluid pressure after flowing through the motor through calculation.
  • FIG. 1 a is a schematic diagram of a blood pump according to an embodiment of the present application, wherein the solid arrows and the hollow arrows respectively indicate the flow path of the cleaning fluid and the flow path of the blood.
  • FIG1 b is a schematic diagram of components for measuring blood pressure at the outlet of a blood pump according to an embodiment of the present application, wherein hollow arrows indicate the flow path of blood.
  • FIG. 2 is a schematic diagram of multiple components when measuring P, N, and Q under a test environment in an embodiment of the present application.
  • FIG. 3 a shows data at a first fluid concentration according to an embodiment of the present application.
  • FIG. 3 b is a schematic diagram of a first curve at a first fluid concentration according to an embodiment of the present application.
  • FIG. 4 a shows data at a second fluid concentration according to an embodiment of the present application.
  • FIG. 4 b is a schematic diagram of a second curve at a second fluid concentration according to an embodiment of the present application.
  • FIG5 is a method for measuring blood pressure at the outlet of a blood pump provided in an embodiment of the present application.
  • 1-blood pump 11-motor, 111-first bearing, 112-second bearing, 12-delivery tube, 13-blade, 14-housing, 141-inlet, 142-outlet, 2-fluid driving device, 21-speed measuring motor, 22-push pump, 3-pressure sensor, 4-flow meter, 5-cleaning box.
  • proximal or “proximal side” refers to the end or side closer to the operator
  • distal or “distal side” refers to the end or side closer to the operator. It refers to the end or side that is farther away from the operator.
  • FIG. 1a a schematic diagram of a blood pump is shown, wherein the solid arrows and the hollow arrows respectively indicate the flow path of the cleaning fluid and the flow path of the blood.
  • FIG. 1b a schematic diagram of the components for measuring the blood pressure at the outlet of the blood pump is shown, wherein the hollow arrows indicate the flow path of the blood.
  • FIG. 1b a schematic diagram of the components for measuring the blood pressure at the outlet of the blood pump is shown, wherein the hollow arrows indicate the flow path of the blood.
  • Step 1 retrieve a benchmark data set obtained from a test environment, wherein the benchmark data set includes the following benchmark data: Under the conditions of different working parameters including a first working parameter and different driving parameters including a first driving parameter, the pressure difference H of the fluid flowing before and after the motor 11 and the pressure difference H of the fluid located at the outlet 142 of the blood pump 1 The fluid flow Q in the delivery tube 12; Step 2: after the blood pump 1 is placed in the patient, measure or calculate the fluid flow Q1 under the conditions of the first working parameter and the first driving parameter, and obtain the corresponding fluid pressure difference H1 through the reference data set; Step 3: measure the fluid pressure N before flowing through the motor 11, thereby obtaining the fluid pressure
  • the working parameter is fluid concentration
  • the driving parameter is the rotation speed of the motor
  • the fluid is a cleaning fluid
  • the cleaning fluid includes heparin, glucose and sodium bicarbonate solution.
  • several groups of fluid pressure differences H and fluid flow rates Q in the benchmark data set form different curves; and, when the concentration of the fluid is a first fluid concentration and the speed of the motor is a first speed, several groups of fluid pressure differences H1 and fluid flow rates Q1 in the benchmark data set form a first curve.
  • the first fluid concentration is 5%
  • the first rotational speed is 24000 r/min
  • several groups of fluid pressure differences H1 before and after the motor 11 and the fluid flow rate Q1 in the delivery pipe 12 are measured in a test environment, and a first curve is formed, as shown in Figures 3a and 3b.
  • factors affecting the shape of the curve formed by the fluid pressure difference H and the fluid flow rate Q include the resistance formed by the delivery tube and its tortuous shape and the transmission loss caused by the resistance formed by the blood pump structure.
  • H-Q curves of different shapes can be obtained by changing the fluid concentration.
  • H-Q curves of different shapes can be obtained by changing the rotation speed of the motor.
  • the reference data set includes the pressure difference H of the fluid before and after flowing through the motor and the fluid flow rate Q in the delivery pipe under several fluid concentration conditions.
  • the reference data set includes the pressure difference H of the fluid before and after the motor and the fluid flow rate Q in the delivery pipe under several motor speed conditions.
  • the fluid flows in front of the motor 11 from entering the delivery tube 12 to entering the motor 11; and, the measuring position for measuring the fluid pressure N in front of the motor 11 is outside the patient's body, that is, the pressure sensor 3 for measuring the fluid pressure N in front of the motor 11 is outside the body, as shown in Figure 1b.
  • the fluid flow rate Q1, the fluid pressure difference H1, and the fluid pressure N are real-time data, and the calculated fluid pressure P is also real-time data; and, as the pressure P at the outlet 142 of the blood pump 1 increases, the fluid flow rate Q1 decreases, and the fluid pressure N and the fluid pressure difference H1 before flowing through the motor 11 increase.
  • the pressure of the fluid is greater than the blood pressure at the outlet 142 ; and the pumping direction of the blood at the outlet 142 is perpendicular to the center line of the motor 11 .
  • the function of preventing blood from entering the motor 11 of the blood pump 1 can be achieved, so that the blood is ejected to the outside of the motor 11 of the blood pump 1.
  • the blood pump 1 further includes a paddle 13 and a housing 14, wherein the paddle 13 is connected to the motor 11, and the housing 14 is sleeved outside the paddle 13; and, an inlet 141 is provided at the first end (distal end) of the housing 14, and an outlet 142 is provided at the second end (proximal end) of the housing 14, as shown in FIG. 1a.
  • the fluid pressure P after flowing through the motor 11 and the fluid pressure N before flowing through the motor 11 are both measured by a pressure sensor 3, and the fluid flow Q in the delivery pipe 12 is measured by a flow meter 4; and the fluid pressure difference H before and after flowing through the motor 11 is obtained by subtracting P from N.
  • the test environment simulates a human blood vessel or organ and, therefore, substantially simulates a blood pump 1 in the human body.
  • the blood pressure in the ventricle changes, the pressure at the outlet 142 of the blood pump 1 changes, and then the pressure of the fluid after the motor 11 changes, and the pressure of the fluid before the motor 11 changes, and the fluid flow Q1 changes.
  • the pressure difference H1 of the fluid before and after the motor 11 can be obtained through the reference data set.
  • the cleaning fluid is stored in the cleaning box 5, and the cleaning box 5 can adjust the concentration of the cleaning fluid.
  • the device for executing the above-mentioned measurement method includes: a power unit, a retrieval unit, a control unit and a calculation unit; wherein the power unit is configured to drive the motor 11 of the blood pump 1 and adjust the rotation speed of the motor 11; the retrieval unit is configured to retrieve a reference data set obtained from a test environment, thereby obtaining a fluid pressure difference H corresponding to the fluid flow rate Q; the control unit includes a fluid drive device 2 and a pressure sensor 3, the drive device is configured to control the flow rate and pressure of the fluid, and the pressure sensor 3 is configured to measure the fluid pressure N before flowing through the motor 11; the calculation unit is configured to obtain the fluid pressure difference H of the retrieval unit and the fluid pressure N of the control unit, and obtain the fluid pressure P after flowing through the motor 11 through calculation.
  • the power unit is configured to drive the motor 11 of the blood pump 1 and adjust the rotation speed of the motor 11
  • the retrieval unit is configured to retrieve a reference data set obtained from a test environment, thereby obtaining a fluid pressure difference
  • the pressure sensor 3 is arranged at one end (distal end) of the driving device, and the pressure sensor 3 and the driving device are both located outside the body when the blood pump 1 is running; and the pressure sensor 3 is located at one end (proximal part) of the delivery tube 12.
  • the motor 11 includes a first bearing 111 (also called a proximal bearing) and a second bearing 112 (also called a distal bearing), and the fluid forms a dynamic seal after flowing through the second bearing 112; and the fluid pressure after passing through the second bearing 112 is greater than the blood pressure at the outlet 142.
  • the internal gap of the motor 11 is extremely small, and the pressure of the fluid increases after flowing through the motor 11.
  • the fluid pressure P after the motor 11 is greater than the fluid pressure N before flowing through the motor 11 .
  • the fluid driving device 2 includes a speed measuring motor 21 and a push pump 22
  • the push pump 22 includes a piston
  • the fluid flow rate Q is calculated by the cross-sectional area of the piston and the rotation speed of the speed measuring motor 21 .
  • the cleaning box 5 is operated to perfuse the blood pump 1 with a cleaning solution with a concentration of 5%, and the control unit is operated to make the speed of the motor 24000 r/min, thereby determining a first curve adapted to the cleaning solution concentration and the speed of the motor;
  • the control unit automatically calculates the fluid flow rate Q1 as 10 ml/hr based on the rotation speed of the speed measuring motor 21 and the cross-sectional area of the piston. At this time, H1 is 792 mmHg according to the first curve;
  • the calculation unit calculates the pressure value at the outlet 142 of the blood pump 1 in real time according to the surgical situation and presents the result visually to the operator.
  • Another embodiment of the present application is substantially the same as the aforementioned embodiment, except that the concentration of the cleaning liquid is different from the motor speed.
  • a method for measuring blood pressure at an outlet 142 of a blood pump 1, wherein the blood pump 1 comprises a motor 11 and a delivery tube 12, wherein a fluid enters the motor 11 through the delivery tube 12, and wherein the outlet 142 is located in the aorta or the pulmonary artery after the blood pump 1 is implanted comprises the following steps: Step 1: Retrieve a benchmark data set obtained from a test environment, wherein the benchmark data set comprises the following benchmark data: under different working parameters including a first working parameter and different driving parameters including a first driving parameter, the pressure difference H of the fluid flowing before and after the motor 11 and the pressure difference H at the outlet 142 The fluid flow Q in the delivery tube 12; Step 2: after the blood pump 1 is placed in the patient, measure or calculate the fluid flow Q1 under the conditions of the first working parameter and the first driving parameter, and obtain the corresponding fluid pressure difference H1 through the reference data set; Step 3: measure the fluid pressure N before flowing through the motor 11, thereby obtaining the fluid pressure P after flowing
  • the several groups of fluid pressure differences H and fluid flow rates Q in the reference data set form different curves; and when the concentration of the fluid is a second fluid concentration and the motor speed is a second speed, the several groups of fluid pressure differences H2 and fluid flow rates Q2 in the reference data set form a second curve. Second curve.
  • the concentration of the second fluid is 10%, and the rotation speed of the motor is 20000 r/min.
  • the fluid flow rate Q2 decreases, and the fluid pressure N and the fluid pressure difference H2 before flowing through the motor 11 increase.
  • the blood pressure in the ventricle changes, the pressure at the outlet 142 of the blood pump 1 changes, and then the pressure of the fluid after passing through the motor 11 changes.
  • the pressure of the fluid before passing through the motor 11 changes, and the fluid flow rate Q2 changes.
  • the pressure difference H2 of the fluid before and after passing through the motor 11 can be obtained through the second curve.
  • a pressure sensor is generally connected to a blood pump or a delivery tube to measure the blood pressure at the aorta.
  • the pressure sensor is prone to malfunction or even detachment under the flushing of blood flow, causing harm to the patient.
  • the present application avoids the above situation and discloses a method for measuring the blood pressure at the outlet of a blood pump. By experimentally measuring the ejection pressure of the blood pump and several data of an extracorporeal device, the relationship between the data is obtained, which can be expressed as a function or a curve graph.
  • the ejection pressure of the blood pump can be obtained through the above function or curve graph, thereby realizing the function of measuring human blood pressure by an extracorporeal sensor.
  • the specific principle of obtaining the aortic pressure without implanting a sensor is as follows: By measuring the blood pressure at the outlet of the blood pump in a test environment, the blood pressure at the outlet of the blood pump can be measured. The ejection pressure at the outlet is measured. First, since the fluid after flowing through the motor is also located at the outlet, the measured blood pressure is equivalent to the fluid pressure flowing out of the motor.
  • the fluid pressure in the delivery tube outside the body is comprehensively measured to obtain the fluid pressure difference H before and after flowing through the motor.
  • the data relationship between the fluid pressure difference H and the fluid flow rate Q is obtained. This relationship is expressed as an H-Q curve.
  • H is obtained through the fluid flow rate Q, and the real-time fluid pressure N is measured at the position where the extracorporeal fluid pressure is measured in the test environment.
  • the sum of N and H is the blood pressure at the outlet of the blood pump.
  • the data acquisition is simple. While reducing the number of mechanical devices implanted in the patient's body, it also reduces the burden of blood pump processing and reduces the economic pressure of medical institutions and patients to a certain extent.
  • the measuring position when measuring the fluid pressure N flowing in front of the motor is located outside the patient's body, and the pressure sensor for measuring the fluid pressure N flowing in front of the motor is located at the proximal end of the delivery tube.
  • changes in the working parameters and driving parameters will affect the shape of the HQ curve.
  • several groups of fluid pressure differences H and fluid flow rates Q in the reference data set form different curves. If the cleaning fluid concentration is changed during the operation of the blood pump, the retrieval unit will confirm a certain HQ curve based on the adjusted cleaning fluid concentration and the real-time motor speed, and then obtain the fluid pressure difference H based on the real-time fluid flow rate Q. If the motor speed is changed during the operation of the blood pump, the retrieval unit will confirm a certain HQ curve based on the adjusted motor speed and the real-time cleaning fluid concentration, and then obtain the fluid pressure difference H based on the real-time fluid flow Q.
  • the coupling efficiency of multiple units is high, the data is updated in real time, and the data obtained by medical workers is accurate and efficient.
  • the power unit automatically determines different motor speeds and transmits them to the retrieval unit, and is combined with specific algorithms and devices to determine the applicable HQ curve described in this method based on the cleaning fluid concentration and motor speed set by medical personnel, thereby obtaining the required blood pressure at the ejection point of the blood pump.
  • the operation is simple, the response is rapid, and the clinical value is great.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Mechanical Engineering (AREA)
  • Anesthesiology (AREA)
  • Cardiology (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Vascular Medicine (AREA)
  • External Artificial Organs (AREA)

Abstract

La présente invention concerne un procédé et un dispositif de mesure de la pression artérielle à une sortie d'une pompe à sang. Le procédé comprend : la récupération d'un ensemble de données de référence obtenu à partir d'un environnement d'essai, l'ensemble de données de référence comprenant les données de référence suivantes : dans les conditions de différents paramètres de fonctionnement et différents paramètres de commande, une différence de pression d'un fluide avant et après l'écoulement à travers un moteur et un débit de fluide dans un tube de distribution, les paramètres de fonctionnement comprenant un premier paramètre de fonctionnement, et les paramètres de commande comprenant un premier paramètre de commande ; une fois qu'une pompe à sang est placée chez un patient, la mesure ou le calcule de débits de fluide dans les conditions du premier paramètre de fonctionnement et du premier paramètre de commande, et l'obtention d'une différence de pression correspondante du fluide par l'intermédiaire de l'ensemble de données de référence ; et la mesure d'une pression du fluide avant l'écoulement à travers le moteur pour obtenir une pression du fluide après l'écoulement à travers le moteur, la pression du fluide après l'écoulement à travers le moteur étant la somme de la pression du fluide avant l'écoulement à travers le moteur et de la différence de pression de fluide correspondante obtenue par l'intermédiaire de l'ensemble de données de référence ; le fluide après l'écoulement à travers le moteur étant situé à la sortie, et la pression artérielle à la sortie étant la pression du fluide après l'écoulement à travers le moteur.
PCT/CN2023/126204 2022-12-20 2023-10-24 Procédé et dispositif de mesure de la pression artérielle à la sortie d'une pompe à sang WO2024131262A1 (fr)

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CN202211642321.2A CN115957435A (zh) 2022-12-20 2022-12-20 用于测量血泵出口处血压的方法、设备
CN202211642321.2 2022-12-20

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CN115957435A (zh) * 2022-12-20 2023-04-14 上海炫脉医疗科技有限公司 用于测量血泵出口处血压的方法、设备
CN118267605B (zh) * 2024-06-04 2024-09-24 安徽通灵仿生科技有限公司 一种基于左心室导管泵的左心室压力估计方法及系统

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CN111032112A (zh) * 2016-08-23 2020-04-17 阿比奥梅德欧洲股份有限公司 血泵
CN110312535A (zh) * 2016-09-19 2019-10-08 阿比奥梅德公司 量化心脏功能并促进心脏恢复的心血管辅助系统
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CN115957435A (zh) * 2022-12-20 2023-04-14 上海炫脉医疗科技有限公司 用于测量血泵出口处血压的方法、设备

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