Membrane lung exhaust device in extracorporeal circulation system and extracorporeal circulation system

Abstract

The application relates to the technical field of medical devices, and provides a membrane lung exhaust device in an extracorporeal circulation system and the extracorporeal circulation system. The membrane lung exhaust device in the extracorporeal circulation system comprises a membrane lung, a negative pressure source and a connecting pipeline connected between a gas exhaust port of the membrane lung and the negative pressure source, the negative pressure source is in fluid connection with the gas exhaust port and is configured to apply a negative pressure at the gas exhaust port to exhaust gas in the membrane lung. The membrane lung exhaust device in the extracorporeal circulation system provided by the application replaces traditional passive exhaust with active suction through negative pressure, can forcibly exhaust gas remaining in a complex flow field region in the membrane lung, effectively removes trace sporadic gas continuously generated in a circulation pipeline, realizes rapid exhaust when a large amount of gas suddenly enters the membrane lung, avoids gas entering an arterial pipeline, and thus significantly improves the exhaust efficiency of the membrane lung and the safety of the extracorporeal circulation system.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a membrane lung exhaust device and extracorporeal circulation system in an extracorporeal circulation system. Background Technology

[0002] Extracorporeal circulation (ECG) is an indispensable life support technology in cardiac surgery. Its core components include a blood pump, a membrane oxygenator (membrane lung), and a blood reservoir. The membrane lung is a key component in the ECG circuit, enabling blood oxygenation and carbon dioxide removal. It typically contains a gas exchange membrane, with blood flowing on one side and oxygen on the other, facilitating gas exchange. During ECG, gas inevitably accumulates in the membrane lung and circulatory tubing. These gases originate from: incomplete removal of residual gas from the tubing and membrane lung during the initial pre-filling phase; gas inhaled during venous drainage due to leaks in the venous tubing or low blood reservoir levels; microbubbles released by the oxygenator itself during oxygenation due to pressure or temperature changes; and large amounts of gas introduced during surgery when poor venous drainage causes the blood reservoir level to drop or even empty. If these gases enter the patient's arterial system via the bloodstream, they can cause gas embolism, potentially leading to serious consequences such as neurological damage, myocardial ischemia, or even death.

[0003] Existing extracorporeal circulation systems typically include a vent in the membrane lung, which connects to the top of the gas exchange chamber or blood chamber inside the membrane lung to expel accumulated gas. However, current venting methods mostly employ passive venting. Specifically, gas rises naturally to the vent using its own buoyancy, and is then released to the external environment by opening the vent valve. However, the internal flow field of the membrane lung is complex, and gas may be impeded by blood flow during its ascent, becoming trapped in localized areas and unable to reach the vent in time. This is especially true for rhomboid or irregularly shaped membrane lungs, which have multiple bends and narrow areas within their chambers, making it easy for gas to accumulate in these areas. Furthermore, when the membrane lung experiences a period of depletion due to poor venous drainage and then resumes blood supply, a large amount of gas rapidly enters the membrane lung with the blood. Passive venting cannot handle this sudden surge in gas load in time, causing gas to enter the arterial tubing from the membrane lung outlet with the blood, directly threatening patient safety. Simultaneously, during routine cardiopulmonary bypass, the persistent trace amounts of gas in the circulatory tubing cannot be effectively removed by passive venting. Summary of the Invention

[0004] Therefore, this invention addresses the problem that existing membrane lung systems typically employ passive venting, relying on the gas's own buoyancy to rise naturally to the vent. However, the complex internal flow field of the membrane lung causes gas to easily stagnate in localized areas and fail to reach the vent in a timely manner. When the membrane lung experiences a depletion due to poor venous drainage and then resumes blood supply, a large amount of gas surges in instantaneously, which passive venting cannot handle in time, leading to gas entering the arterial tubing with the blood and endangering patient safety. Furthermore, the persistent trace amounts of gas in the circulatory tubing during routine cardiopulmonary bypass are difficult to remove effectively using passive methods. This invention provides a membrane lung venting device and an extracorporeal circulation system.

[0005] To solve the above-mentioned technical problems, the technical solution of the present invention is as follows: On one hand, the present invention provides a membrane lung exhaust device in an extracorporeal circulation system, comprising: a membrane lung having a gas exhaust port; a negative pressure source; and a connecting pipe connected between the gas exhaust port and the negative pressure source to connect the negative pressure source and the gas exhaust port; wherein the negative pressure source is used to apply negative pressure at the gas exhaust port to extract gas from inside the membrane lung from the gas exhaust port.

[0006] Furthermore, the membrane lung is a rhomboid membrane lung, and the gas outlet is located at the top of the rhomboid membrane lung.

[0007] Furthermore, a gas permeation component is provided at the gas outlet, which allows gas to pass through while preventing liquid from passing through.

[0008] Furthermore, a pressure regulating valve is provided on the connecting pipeline, which is used to adjust the negative pressure value applied by the negative pressure source to the gas discharge port.

[0009] Furthermore, a pressure monitor is installed on the connecting pipeline, which is used to detect the pressure value at the gas discharge port.

[0010] Furthermore, a one-way valve is provided between the gas outlet and the connecting pipe. The one-way valve allows gas to flow from the inside of the membrane lung toward the connecting pipe and prevents gas or liquid from flowing from the connecting pipe toward the inside of the membrane lung.

[0011] Furthermore, the negative pressure source is a vacuum-assisted venous drainage device, which has a negative pressure interface, and the connecting pipe is connected between the negative pressure interface and the gas discharge port.

[0012] Furthermore, the connecting pipeline is a flexible pipeline, with its first end connected to the gas discharge port and its second end connected to the negative pressure source.

[0013] On the other hand, the present invention also provides an extracorporeal circulation system, including the membrane lung exhaust device in the extracorporeal circulation system described in any one of the above-mentioned methods.

[0014] The technical solution of this invention has the following advantages: The membrane lung exhaust device in the extracorporeal circulation system provided by this invention is fluidly connected to the gas exhaust port of the membrane lung via a negative pressure source and a connecting pipe. It actively applies negative pressure at the gas exhaust port, changing passive exhaust to active suction. This overcomes the limitation that gas rises solely by its own buoyancy and forcibly extracts the gas trapped in the complex flow field area inside the membrane lung. It effectively solves the problem of gas stagnation in local areas and inability to be discharged in a timely manner in existing passive exhaust methods, and significantly improves the efficiency and thoroughness of gas discharge from inside the membrane lung.

[0015] The membrane lung exhaust device in the extracorporeal circulation system provided by this invention can continuously remove trace amounts of gas generated in the circulation tubing and inside the membrane lung during extracorporeal circulation by using the continuous suction action of a negative pressure source. This prevents these trace amounts of gas from gradually accumulating inside the membrane lung and effectively improves the perfusion quality during extracorporeal circulation.

[0016] The membrane lung exhaust device in the extracorporeal circulation system provided by this invention can forcibly extract a large amount of gas at a speed and efficiency far exceeding that of passive exhaust methods when the membrane lung is depleted due to poor venous drainage and then blood supply is restored, resulting in a sudden surge of gas into the membrane lung. This timely response to the sudden large gas load prevents gas from entering the arterial pipeline from the membrane lung outlet with the blood, thereby improving the safety and emergency response capability of the extracorporeal circulation system.

[0017] The membrane lung exhaust device in the extracorporeal circulation system provided by this invention only requires adding a connecting pipeline between the gas exhaust port of the existing membrane lung and the negative pressure source. It does not require structural modification of the membrane lung itself. The structure is simple, the cost is low, and it is easy to promote and apply directly to existing extracorporeal circulation equipment. It has good industrial applicability. Attached Figure Description

[0018] To more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0019] Figure 1 This is a schematic diagram of the membrane lung exhaust device in the extracorporeal circulation system provided in an embodiment of the present invention.

[0020] Explanation of reference numerals in the attached figures: 1. Membrane lung; 101. Gas outlet; 2. Negative pressure source; 201. Negative pressure interface; 3. Connecting pipeline. Detailed Implementation

[0021] The technical solution of the present invention will now be clearly and completely described with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. 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.

[0022] In the description of this invention, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are used only for the convenience of describing the invention and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the invention. Furthermore, the terms "first," "second," and "third" are used for descriptive purposes only and should not be construed as indicating or implying relative importance.

[0023] In the description of this invention, it should be noted that, unless otherwise explicitly specified and defined, the terms "installation," "connection," and "linking" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0024] Furthermore, the technical features involved in the different embodiments of the present invention described below can be combined with each other as long as they do not conflict with each other.

[0025] like Figure 1 As shown, this embodiment provides a membrane lung exhaust device in an extracorporeal circulation system, including a membrane lung 1, a negative pressure source 2, and a connecting pipe 3 connecting the two.

[0026] The membrane lung 1 is a key component in the extracorporeal circulation loop, enabling blood oxygenation and carbon dioxide removal. The membrane lung 1 contains a gas exchange membrane; blood flows through one side of the membrane, while oxygen or oxygenated gas flows through the other, achieving gas exchange through the concentration gradient across the membrane. The membrane lung 1 has a blood inlet, a blood outlet, an oxygen inlet, and a gas outlet 101. The blood inlet is used to introduce venous blood awaiting oxygenation, the blood outlet is used to discharge oxygenated arterial blood, and the oxygen inlet is used to introduce fresh oxygenated gas. The gas outlet 101 is located at the top of the membrane lung 1 to expel excess gas accumulated inside. The gas outlet 101 is positioned at the top because gas density is less than liquid density; gas generated inside the membrane lung 1 will automatically rise to the top area due to buoyancy, making top placement of the outlet most conducive to gas collection and expulsion.

[0027] It should be noted that this embodiment does not strictly limit the specific type of membrane lung 1. In a preferred embodiment, membrane lung 1 is a rhomboid membrane lung, such as the Quadrox series membrane lung manufactured by Maquet. The overall shape of the rhomboid membrane lung is rhomboid or approximately rhomboid, and its internal flow channel design results in uniform blood flow distribution, low resistance, low pre-fill volume, and relatively high heat exchange efficiency. However, the rhomboid structure also brings a problem: there are multiple corners and flow channel turning areas in the internal chamber, which can easily become dead zones for air bubbles to stagnate. Once air bubbles enter these areas, it is difficult for them to rise naturally to the exhaust port at the top using their own buoyancy. Therefore, the need for active exhaust methods is more urgent for rhomboid membrane lungs than for traditional square or circular membrane lungs. Of course, the technical solution of this invention is also applicable to square membrane lungs, circular membrane lungs, or other irregularly shaped membrane lungs, and its technical effect is not lost due to the different shapes of the membrane lungs.

[0028] Negative pressure source 2 is used to generate pressure below atmospheric pressure, i.e., negative pressure. Negative pressure source 2 can take various forms. In a preferred embodiment, negative pressure source 2 uses a vacuum-assisted venous drainage device, a commonly used existing device in extracorporeal circulation surgery, which has relatively precise negative pressure regulation capabilities. Its negative pressure interface 201 is connected to the gas exhaust port 101 of the membrane lung 1 via connecting pipe 3. The advantage of using a vacuum-assisted venous drainage device as negative pressure source 2 is that extracorporeal circulation operating rooms are usually already equipped with this device, eliminating the need to purchase a dedicated negative pressure generating device, facilitating rapid implementation in clinical practice. In other implementations, negative pressure source 2 can also be a separate medical vacuum suction device, a negative pressure pump, or a hospital central negative pressure system, etc.

[0029] Connecting tubing 3 is used to establish a gas passage between gas outlet 101 and negative pressure source 2. The first end of connecting tubing 3 is connected to the gas outlet 101 of the membrane lung 1, and the second end is connected to the negative pressure interface 201 of the negative pressure source 2. Connecting tubing 3 is preferably made of medical flexible tubing, and the material can be silicone rubber, polyvinyl chloride, or thermoplastic polyurethane, etc., which have good biocompatibility and flexibility. Flexible tubing can adapt to the complex equipment layout in the operating room and can be flexibly routed between the membrane lung 1 and the negative pressure source 2 without space limitations. Connectors are provided at both ends of connecting tubing 3 to form a sealed connection with the gas outlet 101 and the negative pressure interface 201. The connector type is preferably a standard tapered Luer connector to ensure the reliability and versatility of the connection.

[0030] The diameter of the connecting pipe 3 needs to be selected while considering both gas flow rate and negative pressure resistance. An excessively large diameter will increase the gas stagnation space inside the pipe, while an excessively small diameter will increase gas flow resistance and affect exhaust efficiency. In a preferred embodiment, the inner diameter of the connecting pipe 3 is 3mm to 8mm. Furthermore, a helical spring or a braided reinforcing layer can be embedded in the wall of the connecting pipe 3 to prevent the pipe from being sucked down and deformed under negative pressure, ensuring that the gas passage remains unobstructed.

[0031] The working principle of the device provided in this embodiment will be explained below.

[0032] Before extracorporeal circulation begins, the connecting tube 3 is connected between the gas outlet 101 of the membrane lung 1 and the negative pressure port 201 of the negative pressure source 2. After extracorporeal circulation begins, the negative pressure source 2 is activated, and a pressure environment lower than atmospheric pressure is immediately formed at the gas outlet 101. The gas inside the membrane lung 1, including residual bubbles from the initial pre-filling stage, tiny bubbles that precipitate due to temperature and pressure changes during operation, and larger bubbles that enter due to fluctuations in venous drainage, is forcibly extracted from inside the membrane lung 1 through the gas outlet 101 under the suction of the negative pressure, transported along the connecting tube 3 to the negative pressure source 2, and finally discharged into the external environment.

[0033] Compared to traditional passive venting methods, the technological advantage of this device lies in its reliance on the buoyancy of the gas itself. Air bubbles must rise to the venting port to be expelled. However, the fluid environment inside the membrane lung 1 is not static; the shear force and turbulence generated by the continuous flow of blood can push air bubbles away from their rising path, causing them to stagnate in a localized area. This device, through active negative pressure suction, continuously generates suction at the gas outlet 101. Even if air bubbles haven't reached the top, they are driven towards the outlet by the pressure difference generated by the negative pressure and extracted. This active suction venting method is particularly crucial in cases of sudden large-scale air intake in the membrane lung 1. When venous drainage is impaired, causing a significant drop in the fluid level inside the membrane lung 1, resulting in a depletion state, and then blood supply is restored, a large amount of gas rushes into the membrane lung 1 instantly. The passive venting port simply cannot expel such a large amount of gas in time, and the gas will enter the arterial system through the blood outlet of the membrane lung 1 along with the blood. In this device, the negative pressure source 2 can extract a large amount of gas at a rate far exceeding that of passive venting, effectively preventing gas from entering the arterial system.

[0034] Furthermore, during extracorporeal circulation, a small number of tiny air bubbles always exist in the circulation pipeline. Although the number of individual bubbles is small, their accumulation over a long period of time can also affect the perfusion quality. This device, through continuous suction from negative pressure source 2, can continuously remove these trace amounts of gas in real time throughout the entire extracorporeal circulation process without manual intervention.

[0035] In the above basic scheme, the gas outlet 101 is directly connected to the connecting pipe 3, which may draw out the blood inside the membrane lung 1 during negative pressure suction. To prevent this from happening, this embodiment provides a gas permeation component at the gas outlet 101.

[0036] The gas permeation component can be disposed within the internal channel or at the port of the gas outlet 101. Its core function is to allow gas to pass freely while preventing the passage of liquids (especially blood). In a preferred embodiment, the gas permeation component employs a hydrophobic breathable membrane. The hydrophobic breathable membrane is a polymer membrane material with a microporous structure and a hydrophobic surface. The micropore diameter of the hydrophobic breathable membrane is between 0.1 μm and 5 μm, allowing gas molecules to pass freely through these micropores, while red blood cells (average diameter approximately 7 μm) and large molecular components in blood plasma cannot pass through. More importantly, the hydrophobic properties of the hydrophobic breathable membrane prevent blood from spreading or permeating on the membrane surface when in contact with blood, even if a pressure difference exists across the membrane, blood cannot pass through.

[0037] The hydrophobic and breathable membrane can be made of polymers with good hydrophobic properties, such as polytetrafluoroethylene, polyvinylidene fluoride, or polypropylene. These materials also have good chemical stability and biocompatibility, making them suitable for long-term indirect contact with blood. The hydrophobic and breathable membrane can be embedded in the internal channel of the gas outlet 101 in the form of a circular membrane. Its outer edge is sealed to the inner wall of the gas outlet 101 by bonding or interference fit, ensuring that gas can only pass through the micropores of the hydrophobic and breathable membrane and cannot leak from the gap between the membrane and the tube wall.

[0038] Besides hydrophobic and breathable membranes, gas permeation components can also adopt other structural forms. For example, an exhaust membrane core composed of multiple hollow fiber membranes bundled together, or a breathable plug made of sintered porous material. As long as the component can achieve selective permeation of gas and liquid, it can be applied to the technical solution of this invention.

[0039] After the gas permeation component is installed, the suction force of the negative pressure source 2 acts on the inner surface of the membrane lung 1 of the gas permeation component. Under the pressure difference, the gas inside the membrane lung 1 is drawn through the micropores to the side of the connecting pipe 3, while the blood is blocked inside the membrane lung 1 and cannot enter the connecting pipe 3. This ensures the exhaust function while avoiding blood loss and pipe blockage.

[0040] The magnitude of the negative pressure generated by negative pressure source 2 directly affects exhaust efficiency and safety. If the negative pressure is too low, the suction force is insufficient, resulting in unsatisfactory exhaust performance; if the negative pressure is too high, although the exhaust speed is fast, it may affect the hemodynamics inside membrane lung 1, and may even force excessive gas through the blood components on the component side towards the membrane surface. Therefore, the ability to adjust the negative pressure value according to actual operating conditions is of significant practical importance.

[0041] Therefore, this embodiment includes a pressure regulating valve on the connecting pipe 3. The pressure regulating valve is located between the negative pressure source 2 and the gas outlet 101 of the membrane lung 1, and adjusts the negative pressure value transmitted to the gas outlet 101 by changing the valve opening. The pressure regulating valve can be manually adjustable; the operator can change the negative pressure by rotating the adjusting knob according to clinical needs, making the operation intuitive and responsive. Alternatively, the pressure regulating valve can be electrically adjustable, linked to the control system of the negative pressure source 2, to achieve automatic and precise adjustment of the negative pressure.

[0042] In a more refined design, a pressure monitor is also installed on the connecting pipe 3. The pressure monitor detects the actual pressure value at the gas outlet 101 in real time and displays it to the operator in digital or pointer form. The core component of the pressure monitor is a pressure sensor, which can be installed at the port of the gas outlet 101 or at the end of the connecting pipe 3 near the gas outlet 101 to most accurately reflect the pressure status at the gas outlet 101. The display of the pressure monitor can be installed in a conspicuous location near the membrane lung 1 for easy observation by the perfusionist during operation.

[0043] By using a pressure regulating valve and a pressure monitor in conjunction, the operator can adjust the negative pressure while monitoring the pressure value in real time, thus precisely controlling the negative pressure value at the gas outlet 101. In a preferred embodiment, the negative pressure value at the gas outlet 101 is controlled within the range of -40 mmHg to -80 mmHg, with an optimal value of -60 mmHg.

[0044] Furthermore, an alarm module can be configured. When the negative pressure value detected by the pressure monitor exceeds the preset normal range, the alarm module emits an audible and visual alarm signal to remind operators to check for leaks, blockages, or malfunctions of the negative pressure source 2 in the pipeline. This design further enhances the safety of the device.

[0045] Extracorporeal circulation involves patient safety, and any step that may introduce risks should be carefully considered. There is a potential risk between the connecting tube 3 and the gas exhaust port 101 of the membrane lung 1: if the negative pressure source 2 stops working for any reason or the connecting tube 3 is accidentally disconnected, gas or even liquid in the external environment may enter the membrane lung 1 through the connecting tube 3, causing contamination or gas embolism risks.

[0046] To address this issue, this embodiment incorporates a check valve between the gas outlet 101 and the connecting pipe 3. This check valve is configured to allow gas to flow only from the inside of the membrane lung 1 towards the connecting pipe 3, while blocking it from flowing in the opposite direction. When the negative pressure source 2 is operating normally, the gas inside the membrane lung 1 pushes open the check valve core under the pressure differential and is discharged along the connecting pipe 3. When the negative pressure source 2 stops operating or the connecting pipe 3 accidentally detaches, the check valve quickly closes under the action of the reverse pressure differential or its own restoring force, cutting off the passage between the connecting pipe 3 and the inside of the membrane lung 1, preventing external fluid from entering the inside of the membrane lung 1 through the gas outlet 101.

[0047] There are several structural options for check valves. One implementation is a duckbill valve, with a one-piece structure made of elastic material. Forward fluid pressure opens the duckbill opening, and reverse pressure closes it to seal, resulting in a simple and reliable structure. Another implementation is a ball check valve, where one-way flow is achieved by the ball moving away from the valve seat under forward pressure and pressing against the valve seat under reverse pressure. Regardless of the form used, the flow port diameter of the check valve should not be smaller than the inner diameter of the connecting pipe 3 to avoid additional flow resistance.

[0048] As mentioned earlier, the negative pressure source 2 can be a vacuum-assisted venous drainage device, which is commonly used in extracorporeal circulation surgery, providing convenient conditions for the implementation of this invention. A vacuum-assisted venous drainage device typically includes a main unit, a vacuum adjustment module, a pressure sensing module, and a negative pressure interface 201. The main unit contains a negative pressure generating unit, the vacuum adjustment module allows the operator to set a target negative pressure value, and the pressure sensing module monitors the actual pressure at the output end in real time and stabilizes the actual pressure near the set value through closed-loop control.

[0049] In this embodiment, the negative pressure interface 201 of the vacuum-assisted venous drainage device is no longer connected to the venous blood reservoir as is customary, but is instead connected to the gas exhaust port 101 of the membrane lung 1 via the connecting pipe 3. This is equivalent to shifting the negative pressure output of the vacuum-assisted venous drainage device from the venous drainage side to the membrane lung exhaust side, realizing a new application method. Using the vacuum-assisted venous drainage device as the negative pressure source 2, its negative pressure output range is typically -20 mmHg to -100 mmHg, completely covering the -40 mmHg to -80 mmHg operating range required by this device, eliminating the need for an additional negative pressure source.

[0050] Of course, if the operating room is not equipped with a vacuum-assisted intravenous drainage device, or if the device needs to be used for intravenous drainage and cannot be allocated to the membrane lung for exhaust, an independent negative pressure pump or a hospital wall-mounted negative pressure system can be used as the negative pressure source 2. When using a hospital wall-mounted negative pressure system, a dedicated negative pressure regulator should be connected in series on the connecting pipe 3, because the vacuum degree of a hospital wall-mounted negative pressure system is usually high (up to -200 mmHg to -700 mmHg), and direct connection to the gas exhaust port 101 may exceed the tolerance range of the membrane lung 1. The negative pressure regulator reduces the wall negative pressure to the working range of -40 mmHg to -80 mmHg before supplying it to the gas exhaust port 101.

[0051] The present invention also provides an extracorporeal circulation system, which integrates the membrane lung exhaust device in any of the above implementations.

[0052] In addition to the membrane lung 1 and negative pressure source 2, an extracorporeal circulation system typically includes a blood pump, a blood reservoir, a temperature control unit, and circulation tubing connecting these components. The blood pump drives blood to flow unidirectionally in the extracorporeal circuit. The blood reservoir collects returning blood from the patient's venous system and provides a stable blood supply to the blood pump. The temperature control unit regulates the blood temperature via a heat exchanger. The membrane lung 1 is connected downstream of the blood reservoir, receiving venous blood from the reservoir, oxygenating it, and then returning it to the patient through arterial tubing.

[0053] In this extracorporeal circulation system, the gas outlet 101 of the membrane lung 1 is connected to the negative pressure source 2 via the connecting pipe 3. The negative pressure source 2 applies negative pressure at the gas outlet 101 to continuously extract gas from the inside of the membrane lung 1 and the circulation tubing. This integrated design enables the entire extracorporeal circulation system to have active exhaust capability, solving the risk of gas entering the arterial tubing at the system level and improving the overall safety of extracorporeal circulation.

[0054] The gas permeation components, pressure regulating valves, pressure monitors, check valves, and other features described in the above embodiments are not necessarily all required to be used simultaneously. Instead, they can be selected and combined according to actual clinical needs and the usage environment.

[0055] In a preferred embodiment, the membrane lung exhaust device includes both a gas permeation component and a one-way valve. The gas permeation component is located inside the gas outlet 101 and performs gas-liquid separation; the one-way valve is located between the gas outlet 101 and the connecting pipe 3 and performs backflow prevention. Both components function independently without interference, together providing dual safety protection at the exhaust port, preventing both blood leakage and external fluid backflow.

[0056] In another preferred configuration, the membrane lung decompression device includes both a pressure regulating valve and a pressure monitor. The pressure regulating valve adjusts the negative pressure, while the pressure monitor displays the current pressure value. Together, they achieve closed-loop manual control of the negative pressure. The operator adjusts the pressure regulating valve while observing the pressure value to stabilize the negative pressure within the preset operating range.

[0057] In a more comprehensive configuration, the gas permeation component, check valve, pressure regulating valve, and pressure monitor are all integrated into a single device, ensuring the device's safety and controllability from four dimensions: gas-liquid separation, backflow prevention, pressure regulation, and pressure monitoring. The functional modules are arranged in the following order on the connecting pipe 3: from the gas outlet 101 outwards, the gas permeation component, check valve, pressure monitor, and pressure regulating valve are arranged sequentially, with the rear end of the pressure regulating valve connected to the negative pressure source 2. This order is rationally chosen because: the gas permeation component and check valve should be as close as possible to the gas outlet 101 to reduce the pipe volume between the gas outlet 101 and these two components, preventing gas stagnation in this area; the pressure monitor should be located between the check valve and the pressure regulating valve, and the measured pressure value should be closest to the actual pressure at the gas outlet 101; the pressure regulating valve is positioned near the negative pressure source 2 for easy coordination with the negative pressure source 2 to achieve precise pressure regulation.

[0058] Obviously, the above embodiments are merely illustrative examples for clear explanation and are not intended to cover all possible implementations. Those skilled in the art will recognize that various variations and modifications can be made based on the above description. It is neither necessary nor possible to exhaustively list all possible implementations here. However, obvious variations and modifications derived therefrom are still within the scope of protection of this invention.

Claims

1. A membrane lung exhaust device in an extracorporeal circulation system, characterized in that, include: A membrane lung (1) having a gas outlet (101). Negative pressure source (2); A connecting pipe (3) is connected between the gas outlet (101) and the negative pressure source (2) so that the negative pressure source (2) and the gas outlet (101) are connected; The negative pressure source (2) is used to apply negative pressure at the gas outlet (101) to extract the gas inside the membrane lung (1) from the gas outlet (101).

2. The membrane lung exhaust device in the extracorporeal circulation system according to claim 1, characterized in that, The membrane lung (1) is a rhomboid membrane lung (1), and the gas outlet (101) is located at the top of the rhomboid membrane lung (1).

3. The membrane lung exhaust device in the extracorporeal circulation system according to claim 1, characterized in that, A gas permeation component is provided at the gas outlet (101), which allows gas to pass through while preventing liquid from passing through.

4. The membrane lung exhaust device in the extracorporeal circulation system according to claim 1, characterized in that, A pressure regulating valve is provided on the connecting pipeline (3), which is used to adjust the negative pressure value applied by the negative pressure source (2) to the gas discharge port (101).

5. The membrane lung exhaust device in the extracorporeal circulation system according to claim 1, characterized in that, A pressure monitor is installed on the connecting pipe (3), and the pressure monitor is used to detect the pressure value at the gas discharge port (101).

6. The membrane lung exhaust device in the extracorporeal circulation system according to claim 1, characterized in that, A one-way valve is provided between the gas outlet (101) and the connecting pipe (3). The one-way valve allows gas to flow from the inside of the membrane lung (1) toward the connecting pipe (3) and prevents gas or liquid from flowing from the connecting pipe (3) toward the inside of the membrane lung (1).

7. The membrane lung exhaust device in the extracorporeal circulation system according to claim 1, characterized in that, The negative pressure source (2) is a vacuum-assisted venous drainage device. The vacuum-assisted venous drainage device has a negative pressure interface (201). The connecting pipe (3) is connected between the negative pressure interface (201) and the gas discharge port (101).

8. The membrane lung exhaust device in the extracorporeal circulation system according to claim 1, characterized in that, The connecting pipe (3) is a flexible pipe, with the first end of the flexible pipe connected to the gas discharge port (101) and the second end of the flexible pipe connected to the negative pressure source (2).

9. An extracorporeal circulation system, characterized in that, The membrane lung (1) exhaust device in the extracorporeal circulation system according to any one of claims 1-8.

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