Device suitable for blood degassing and blood circulation system

Abstract

The invention provides a device suitable for blood degassing and a blood circulation system. The device suitable for blood degassing comprises a body and an exhaust mechanism, and the body is provided with an inner cavity, a liquid inlet, a liquid outlet, an exhaust port and a filtering piece; the liquid inlet, the liquid outlet and the exhaust port are respectively communicated with the inner cavity; the exhaust mechanism comprises a ventilation part and a valve part, the valve part is arranged at the exhaust port and can control opening and closing of the exhaust port, and the ventilation part is arranged in the inner cavity and used for isolating liquid but not isolating gas; the filter part divides the inner cavity into a first space and a second space, the first space is communicated with the liquid inlet and the exhaust port, the second space is communicated with the liquid outlet, and the filter part is provided with a plurality of through holes. By means of the device suitable for blood degassing, the problem that in the prior art, a blood circulation system is in a negative pressure state for a long time during degassing, and consequently blood is damaged can be solved.

Description

Technical Field

[0001] The embodiments of the present application belong to the field of medical devices, and in particular relate to a blood degassing device. Background Art

[0002] Extracorporeal circulation of blood and other body fluids is typically used for patients undergoing heart surgery or dialysis. During extracorporeal circulation for heart surgery, the patient's blood is directed outside the body, processed by an artificial heart-lung system placed outside the patient's body, and then returned to the body. Extracorporeal circulation typically uses an extracorporeal circuit consisting of a chamber (or blood reservoir), a blood pump, an artificial lung, filters, and tubing.

[0003] When providing emergency treatment to critically ill patients with severe cardiopulmonary failure, extracorporeal membrane oxygenation (ECMO) is used to provide the patient with continuous extracorporeal respiratory and circulatory support, buying more precious time for emergency treatment. Extracorporeal circulation needs to be established during this process. A serious problem with extracorporeal blood circulation is the formation of blood clots. One cause of thrombosis is the gas mixed in the blood and the extracorporeal circulation circuit. Specifically, the air mixed in the extracorporeal circulation circuit activates the blood coagulation system and promotes thrombosis. Therefore, the extracorporeal circulation circuit usually includes a device for removing air, which is used to eliminate bubbles contained in the blood or other body fluids to ensure that there are no more bubbles before the liquid is about to enter the patient's body.

[0004] During extracorporeal circulation, blood flows through a system of catheters and mechanical devices, where a pump draws blood out of the body, oxygenates it through an oxygenator, and then returns it to the body. This flow occurs under a constant positive pressure to ensure continuous blood flow and maintain proper oxygenation and blood flow. Therefore, the degassing device included in the extracorporeal circulation system is also typically pressurized internally to maintain circulation stability and functionality.

[0005] If trapped bubbles accumulate in the degassing device and are not removed, they can cause platelet aggregation and thrombosis. This can lead to blockage of the blood degassing device, compromising its proper filtration function. Therefore, vents are often provided, such as in US6267926B1, EP204222B1, and US8439858B2. However, these designs employ knob-type plugs, making venting inconvenient. Alternatively, US7798985B2 utilizes a multi-way valve, which offers greater convenience than the aforementioned designs. Because the device maintains positive pressure, removing the valve to the atmosphere allows both liquid and gas inside to flow to the outside atmosphere. Some designs also connect the vent to a vacuum or negative pressure generator to enhance venting. However, these designs often result in some blood being expelled during venting. Furthermore, these venting methods require human observation and active control, and lack automatic venting, which can lead to excessive bubble accumulation. Therefore, some solutions have been proposed to prevent blood loss and automatically vent by placing a hydrophobic, breathable membrane at the vent. However, if blood contacts the membrane for a long time, the membrane's permeability will decrease, and prolonged blood retention can also cause blood coagulation. Solutions such as those in US Pat. No. 5,849,065A, US Pat. No. 5,707,431A, and CN102014985B aim to avoid this by allowing the blood to flow. However, such a setup still presents problems. After the hydrophobic membrane is connected to the atmosphere, the external atmosphere becomes a negative pressure relative to the blood within the device, causing the blood within the device to be under negative pressure for a long time. Prolonged negative pressure can damage and destroy cell membranes, causing blood cells to lose their normal cell membrane integrity and function. It can also stretch and distort red blood cells in the blood. This stretching and deformation can lead to erythrocyte anemia, where the shape and structure of the red blood cells change, affecting their function and lifespan. It can also cause red blood cells and platelets in the blood to aggregate and form thrombi or blood clots. In addition, this design of opening the membrane to the outside may cause condensation to form on the outside membrane due to inconsistent internal and external temperatures, resulting in blockage and inability to vent air normally, or other foreign matter may block the membrane above and cause it to lose its venting function. Summary of the Invention

[0006] In order to solve the problems in the prior art, the present invention provides a blood degassing device and a blood circulation system which can automatically exhaust the air, reduce the damage of negative pressure to the blood, and can be used for a long time.

[0007] In a first aspect, the device for degassing blood comprises a body and an exhaust mechanism, wherein the body has an inner cavity, a liquid inlet, a liquid outlet, an exhaust port, and a filter element;

[0008] The liquid inlet, the liquid outlet and the exhaust port are respectively connected to the inner cavity, and the exhaust port is arranged on the top of the body;

[0009] The exhaust mechanism includes a breathable member and a valve member, wherein the valve member is provided at the exhaust port and can control the opening and closing of the exhaust port, and the breathable member is provided in the inner cavity and is used to isolate liquid but not gas;

[0010] The filter element separates the inner cavity into a first space and a second space, the first space is connected to the liquid inlet and the exhaust port, and the second space is connected to the liquid outlet. The filter element has a plurality of through holes, and the liquid inlet is arranged below the filter element;

[0011] Blood flows from the liquid inlet into the first space, passes through the filter element, enters the second space, and finally flows out from the liquid outlet;

[0012] The gas enters the first space through the liquid inlet and is blocked by the filter element from entering the second space, and then is discharged from the exhaust port through the air permeable element.

[0013] As a preferred embodiment of the present application, the exhaust mechanism further includes an ultrasonic sensor, which can sense bubbles in the inner cavity to control the opening and closing of the valve member.

[0014] As a preferred embodiment of the present application, the exhaust mechanism further includes a floating member, which floats on the blood and moves up and down with the change in the height of the blood to control the opening and closing of the valve member.

[0015] As a preferred embodiment of the present application, the valve component includes a fixed part and a movable part, the fixed part is fixed at the exhaust port and is rotatably connected to the movable part, and the movable part is rotated to cause the movable part and the fixed part to rotate relative to each other to control the opening and closing of the valve component.

[0016] As a preferred embodiment of the present application, the valve component further includes an elastic component, and two ends of the elastic component are respectively connected to the fixed portion and the movable portion.

[0017] As a preferred embodiment of the present application, the air permeable member is arranged to be inclined relative to the horizontal plane, and the lowest point of the air permeable member is located at the exhaust port.

[0018] As a preferred embodiment of the present application, the exhaust port is arranged to be inclined relative to the horizontal plane, and the highest point of the bottom area of ​​the exhaust port is located below the lowest point of the breathable member.

[0019] As a preferred embodiment of the present application, the liquid inlet is arranged along the tangential direction of the body so that the blood flows in a spiral manner in the first space.

[0020] As a preferred embodiment of the present application, the liquid inlet is arranged at the bottom of the main body, and the upper end of the first space is narrower than the lower end.

[0021] In a second aspect, an embodiment provides a blood circulation system, comprising a liquid inlet pipe, a liquid outlet pipe and a device for blood degassing as described in any one of the first aspects, wherein the liquid inlet pipe is connected to the liquid inlet, and the liquid outlet pipe is connected to the liquid outlet.

[0022] Compared with the existing technology, blood enters the inner cavity of the main body from the liquid inlet and is then discharged from the liquid outlet. In the process of blood entering and exiting the inner cavity, the gas accumulated in the blood in the inner cavity is intermittently discharged by controlling the opening and closing of the valve component. Since the breathable component can isolate the liquid but not the gas, the blood will not splash out from the exhaust port. The filter component concentrates the gas in the first space, preventing the gas from flowing out of the liquid outlet again. Finally, the first space inside the device is intermittently connected to the outside world, so that the blood is not always in a negative pressure state, which is less harmful to the blood.

[0023] Compared with the prior art, the blood circulation system has a liquid inlet tube, a liquid outlet tube and a device suitable for blood degassing, so it can also solve the problem of the blood circulation system in the prior art being in a negative pressure state for a long time during degassing, which causes damage to the blood. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] The drawings described herein are used to provide a further understanding of the present application and constitute a part of the present application. The illustrative embodiments of the present application and their descriptions are used to explain the present application and do not constitute an improper limitation of the present application. Some specific embodiments of the present application will be described in detail in an illustrative and non-restrictive manner with reference to the drawings. The same reference numerals in the drawings indicate the same or similar components or parts. It should be understood by those skilled in the art that these drawings are not necessarily drawn to scale. In the drawings:

[0025] Main body 10; exhaust mechanism 20; inner cavity 110; liquid inlet 120; liquid outlet 130; exhaust port 140; breathable member 210; valve member 220; ultrasonic sensor 230; floating member 240; fixed portion 2210; movable portion 2220; elastic member 2230; filter member 30; abutting member 2250; tilting member 2240; first space 1110; second space 1120.

[0026] Figure 1 A schematic diagram showing the overall structure of a device suitable for blood degassing in the present invention is shown;

[0027] Figure 2 A schematic structural diagram showing another angle of a device for blood degassing according to the present invention is shown;

[0028] Figure 3 Shown Figure 2 Schematic diagram of the cross section along the middle edge BB;

[0029] Figure 4 Shown Figure 1 A cross-sectional view of the valve at the center edge AA when it is open;

[0030] Figure 5 Shown Figure 1 Schematic cross-section of the valve at the middle edge AA in the closed state;

[0031] Figure 6 A schematic diagram of the exploded structure of a device suitable for blood degassing in the present application is shown;

[0032] Figure 7 A partial cross-sectional schematic diagram of a device suitable for blood degassing in the present application is shown;

[0033] Figure 8 A schematic cross-sectional view along CC of a device suitable for blood degassing in the present application is shown. DETAILED DESCRIPTION

[0034] In order to enable those skilled in the art to better understand the present invention, the technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments in the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts should fall within the scope of protection of this application.

[0035] In order to solve the problem in the prior art that a blood circulation system is in a negative pressure state for a long time during degassing, causing damage to the blood, the present invention provides a device and a blood circulation system suitable for blood degassing.

[0036] First, please refer to Figures 1-6 The device for blood degassing comprises a body 10 and an exhaust mechanism 20 , wherein the body 10 has an inner cavity 110 , a liquid inlet 120 , a liquid outlet 130 , an exhaust port 140 and a filter element 30 ;

[0037] The liquid inlet 120, the liquid outlet 130, and the exhaust port 140 are respectively connected to the inner cavity 110. The exhaust port 140 is arranged at the top of the body 10. Blood flows into the inner cavity 110 from the liquid inlet 120 and then flows out from the liquid outlet 130. The other end of the exhaust port 140 is connected to the outside world or to a vacuum pump.

[0038] The exhaust mechanism 20 includes a breathable member 210 and a valve member 220. The valve member 220 is arranged at the exhaust port 140 and can control the opening and closing of the exhaust port 140. The breathable member 210 is arranged in the inner cavity 110. The breathable member 210 is used to isolate the liquid but cannot isolate the gas. The gas enters the inner cavity 110 from the liquid inlet 120 and is then discharged from the exhaust port 140 through the breathable member 210.

[0039] The filter element 30 separates the inner cavity 110 into a first space 1110 and a second space 1120. The first space 1110 communicates with the liquid inlet 120 and the exhaust port 140, and the second space 1120 communicates with the liquid outlet 130. The filter element 30 has a plurality of through holes, and the liquid inlet 120 is disposed below the filter element 30.

[0040] Blood flows from the liquid inlet 120 into the first space 1110 , passes through the filter element 30 , and then enters the second space 1120 , and finally flows out from the liquid outlet 130 ;

[0041] The gas enters the first space 1110 from the liquid inlet 120 and is blocked by the filter element 30 to enter the second space 1120 , and then is discharged from the exhaust port 140 through the air permeable element 30 .

[0042] More specifically, the breathable member 210 can be mounted on the top of the inner cavity 110 by welding or adhesive bonding, wherein the welding method is performed by ultrasonic, hot melt, or high frequency, and the adhesive bonding is generally performed by directly pasting waterproof adhesive. Preferably, ultrasonic welding is used in this solution.

[0043] Compared with the prior art, blood enters the inner cavity 110 of the main body 10 from the liquid inlet 120 and is then discharged from the liquid outlet 130. In the process of blood entering and exiting the inner cavity 110, the gas accumulated in the blood in the inner cavity 110 is intermittently discharged by controlling the switch of the valve component 220. Since the breathable component 210 can isolate the liquid but not the gas, the blood will not splash out from the exhaust port 140. The filter component 30 concentrates the gas in the first space 1110, preventing the gas from flowing out from the liquid outlet 130 again. Finally, the first space 1110 inside the device is intermittently connected to the outside world, so that the blood is not always in a negative pressure state, and the damage to the blood is relatively small. The implementation of the device suitable for blood degassing in the present invention can solve the problem in the prior art that the blood circulation system is in a negative pressure state for a long time during degassing, causing damage to the blood.

[0044] The gas-permeable member 210 allows gas to pass but does not allow blood to pass through, and is preferably a hydrophobic membrane. Examples of materials constituting the hydrophobic membrane include polytetrafluoroethylene (PTFE), a copolymer of tetrafluoroethylene and hexafluoropropylene (FEP), a copolymer of tetrafluoroethylene and perfluoroalkyl vinyl ether (PFA), polychlorotrifluoroethylene (PCTFE), polyvinylidene fluoride (PVDF), a copolymer of ethylene and tetrafluoroethylene (ETFE), a copolymer of ethylene and chlorotrifluoroethylene (ECTFE), and polypropylene (PP).

[0045] Generally speaking, the breathable member 210 is built into the interior of a device suitable for blood degassing to prevent it from being contaminated by pollutants such as dust.

[0046] The filter 30 is a porous material. Examples of the porous material of the filter 30 include mesh, net, foam, woven fabric, non-woven fabric, and combinations thereof, but any similar type of material may be used.

[0047] In particular, it is preferred to use a mesh made of resin fibers, a netting, a woven fabric, a non-woven fabric, etc. to form a laminated sheet consisting of one or more layers. An example of such a sheet is a mesh made of polypropylene or polyester, which is then sandwiched with a net made of polypropylene or polyester.

[0048] Furthermore, the porous material used for the screens and netting is preferably selected to have a minimum pore size in the range of 20 micrometers to 200 micrometers, and in particular, preferably in the range of 20 micrometers to 60 micrometers.

[0049] The bubbles in the blood are generally present in the form of foam composed of a large number of bubbles. The diameter of the bubbles is usually larger than the aperture of the filter element 30, so that the bubbles can be concentrated in the first space 1110.

[0050] It should be noted that the liquid inlet 120 is located below the filter compartment 30, thereby facilitating the separation of air and blood once blood enters the first space 1110. More specifically, when blood enters the first space through the bottom liquid inlet 120, since the filter element 30 is located above the liquid inlet 120, the blood must pass through the filter element 30 into the second space 1120 before being discharged from the liquid outlet 130. This causes the blood to flow upward after entering the liquid inlet 120 (due to the negative pressure generated by the filter element 30 located above). Since the air permeable element 210 and the exhaust port 140 are also located above the liquid inlet 120, the bubbles (air) in the blood also move upward due to buoyancy. This aligns the blood flow and exhaust directions with the air flow, further facilitating air discharge.

[0051] In one embodiment of the present application, the exhaust mechanism 20 further includes an ultrasonic sensor 230 , which can sense bubbles in the inner cavity 110 and thereby control the opening and closing of the valve member 220 .

[0052] In this embodiment, ultrasonic sensor 230 can sense bubbles within inner cavity 110 and, more specifically, open and close the valve based on the size of the bubbles. Valve 220 is preferably a solenoid valve. A control unit electrically connects ultrasonic sensor 230 and the solenoid valve, automatically controlling the opening and closing of valve 220 based on information fed back from ultrasonic sensor 230.

[0053] Generally speaking, it can be preset that the valve member 220 will be controlled to open only when the bubbles in the inner cavity 110 reach a certain level, which can reduce the time that the blood is in a negative pressure state.

[0054] For example, the initial detection volume for the ultrasonic sensor to send a signal to open the valve is 1ml, that is, the signal will be sent only when the gas accumulation volume is 1ml or above. This can avoid the continuous opening of the valve and connection to the atmosphere due to some small bubbles, and avoid more damage to the blood. The 1ml is the amount determined by the manufacturer based on the existing volume. Specifically, it is not deliberately set. It can be 1ml, 0.5ml, 2ml, etc. The amount of 1ml is based on multiple tests on the capacity of the existing degassing device. The amount of 1ml will not affect the service life of the membrane component and will not affect the attraction of the filter element to it when filtering blood. Please refer to Figure 4 The multiple arrows in the figure indicate the paths through which the gas passes.

[0055] In one embodiment of this application, please refer to Figure 3-Figure 5 The exhaust mechanism 20 further includes a floating member 240 , which floats on the blood. The floating member 240 moves up and down as the height of the blood changes, thereby controlling the opening and closing of the valve member 220 .

[0056] In this embodiment, as the volume of bubbles in the inner cavity 110 increases, or as the number of small bubbles increases, resulting in an increase in the total volume of bubbles, the blood level in the inner cavity 110 decreases, and the floating member 240 also descends. When the floating member 240 descends to a certain distance, it controls the valve member 220 to open.

[0057] The specific method by which the floating member 240 controls the valve member 220 can be electrical signal control. For example, when the upper portion of the floating member 240 abuts a fixed member, the valve member 220 closes. When the blood level of the floating member 240 drops, the upper portion of the floating member 240 disconnects from the fixed member, and the electrical signal of the controller changes, thereby triggering the valve member 220 to open. When the bubbles are expelled and the floating member 240 rises, the upper portion of the floating member 240 abuts the fixed member again, and the valve member 220 closes.

[0058] Alternatively, a mechanical linkage (such as the linkage structure of a flush toilet) may be employed. Specifically, the largest diameter of the floating member 240 is smaller than the narrowest diameter within the first space 1110, and a gap is left between the floating member 240 and the first space 1110 to allow for gas circulation. The floating member 240 is provided with an inclined member 2240, and the movable portion 2220 is fixedly provided with an abutment member 2250, which abuts against the inclined member 2240. When the bubbles float up and the liquid level drops, the floating member 240 also drops. During this process, the inclined member 2240 moves on the abutment member 2250, thereby forcing the abutment member 2250 to drive the moving member 2220 to rotate, and the moving member 2220 rotates to control the valve member 220 to open; when the bubbles are completely eliminated and the liquid surface rises, the floating member 240 also floats up, and the elastic member 2230 causes the moving part 2220 to reset, thereby closing the valve member 220; or because the liquid surface rises, the floating member 240 generates corresponding buoyancy, which reduces the external force on the elastic member 2230, allowing the elastic member 2230 to reset, thereby pushing the inclined member through the abutment member 2250 to reset and open the valve member 220.

[0059] In a more preferred embodiment, the floating member 240 is slidably connected to the fixed portion 2210, the floating member 240 is provided with at least one sliding groove, and the fixed portion 2210 has a protruding column matching it. This arrangement can prevent the floating member 240 from rotating in the first space 1110, so that the floating member 240 is only allowed to float up and down.

[0060] In one embodiment of the present application, the valve component 220 includes a fixed portion 2210 and a movable portion 2220. The fixed portion 2210 is fixed at the exhaust port 140 and is rotatably connected to the movable portion 2220. Rotating the movable portion 2220 causes the movable portion 2220 and the fixed portion 2210 to rotate relative to each other, thereby controlling the opening and closing of the valve component 220.

[0061] Due to the unique nature of medical devices, it is crucial to ensure the blood degassing device of the present invention operates properly even in power outages. Medical personnel can move the movable portion 2220 to create relative motion with the fixed portion 2210, thereby controlling the opening and closing of the valve element 220. Similarly, reference can be made to various commonly used valve structures.

[0062] Generally speaking, the valve member 220 is realized by the relative rotation of the fixed portion 2210 and the movable portion 2220. In this case, the movable portion 2220 is generally provided with anti-slip grooves or a handle. Usually, a housing is fixedly connected to the body 10 on the outside of the valve member 220 for sealing and aesthetic reasons.

[0063] Specifically, the fixed portion 2210 is provided with a first opening, and the movable portion 2220 is provided with a second opening. The first opening is aligned with the exhaust port 140. When the valve member 220 is open, the first opening aligns with the second opening, and the exhaust port is connected to the first opening and the second opening. When the valve member 220 is closed, the movable portion 2220 rotates, causing the second opening, which was aligned with the first opening, to deflect, until the exhaust port is disconnected from the first opening and the second opening.

[0064] It should be noted that, in some cases, the moving portion 2220 can be linked with the floating member 240 to reduce the design of the electronic control end.

[0065] In one embodiment of this application, please refer to Figure 1 and Figure 8 The valve member 220 further includes an elastic member 2230 , and two ends of the elastic member 2230 are respectively connected to the fixed portion 2210 and the movable portion 2220 .

[0066] The elastic member 2230 mainly plays a resetting role. In any case, as long as the moving part 2220 loses the effect of external force, the elastic member 2230 will ensure that the moving part 2220 is reset and thus close the valve member 220 to prevent the blood from being in a negative pressure state for a long time and causing damage to the blood.

[0067] In one embodiment, the floating member 240 rotates the movable portion 2220 as it moves up and down. Specifically, the movable portion 2220 and the floating member 240 are connected by a screw thread. When the floating member 240 descends, it rotates the movable portion 2220 relative to the fixed portion 2210, thereby opening the valve member 220. After the bubbles are exhausted, the movable portion 2220 returns to its original position under the action of the elastic member 2230, simultaneously returning the floating member 240 to its original position and closing the valve member 220.

[0068] Typically, a solenoid valve controlling the ultrasonic sensor 230 is also installed in the above embodiment. This allows the ultrasonic sensor 230 to be controlled automatically by the ultrasonic sensor 230, assisted by the floating member 240, or manually by manual intervention. Alternatively, the ultrasonic sensor 230 can be controlled by one, two, or all three of the following: automatic control of the valve member 220 by the ultrasonic sensor 230, auxiliary control of the valve member 220 by the floating member 240, and manual control of the valve member 220.

[0069] In one embodiment of the present application, the air permeable member 210 is tilted relative to the horizontal plane, and the lowest point of the air permeable member 210 corresponds to the location of the exhaust port 140 .

[0070] The inclined arrangement of the air permeable member 210 can prevent water droplets from condensing on the exhaust port 140 and covering the air permeable member 210 in some cases, thereby affecting the exhaust function of the air permeable member 210. If water droplets condense, they will flow along the inclined surface of the air permeable member 210 to the lowest point and then flow out of the exhaust port 140.

[0071] In one embodiment of the present application, the exhaust port 140 is arranged to be inclined relative to the horizontal plane, and the highest point of the bottom area of ​​the exhaust port 140 is located below the lowest point of the air permeable member 210 .

[0072] In this embodiment, the highest point of the bottom area of ​​the exhaust port 140 is located below the lowest point of the breathable member 210, which can quickly guide the condensed water droplets to quickly flow out of the breathable member 210, eliminating the possibility of water accumulation in the breathable member 210.

[0073] As mentioned above, the inclination angle between the air permeable member 210 and the exhaust port 140 and the horizontal plane is generally between 0° and 45°.

[0074] In one embodiment of the present application, the liquid inlet 120 is arranged along the tangential direction of the body 10 so that the blood flows in a spiral manner in the first space 1110 .

[0075] If blood is in contact with the breathable member 210 for a long time, the permeability of the breathable member 210 will decrease due to physical blockage of blood components, adsorption of blood proteins, etc. By continuously rotating the blood, the long-term contact between the blood and the breathable member 210 can be avoided, thereby reducing the permeability and allowing the device to be used for a longer time.

[0076] The blood flows in a spiral in the first space 1110 and can use centrifugal force to make the bubbles gather in the middle area of ​​the first space 1110. The bubbles will then float up due to their own characteristics, so that the bubbles can be quickly collected in the first space 1110.

[0077] In one embodiment of this application, please refer to Figure 3 The liquid inlet 120 is arranged at the bottom of the body 10, and the upper end of the first space 1110 is narrower than the lower end.

[0078] In this embodiment, the upper end of the first space 1110 is narrower than the lower end, so bubbles in the upper end of the first space 1110 will quickly gather and have a more significant impact on the blood level. In some embodiments with a float 240, a more sensitive response can be provided.

[0079] Alternatively, the main body 10 is designed to be transparent, so that medical staff can observe the changes in the liquid level in the first space 1110 and manually control the opening and closing of the valve member 220.

[0080] When the flow rate remains unchanged, the angular velocity will increase as the diameter decreases, so the blood will flow in a spiral at a faster speed, which is more conducive to bubble aggregation under the action of centrifugation.

[0081] In a second aspect, an embodiment of the present application further provides a blood circulation system, comprising a liquid inlet pipe, a liquid outlet pipe and any device suitable for blood degassing as described in the first aspect, wherein the liquid inlet pipe is connected to the liquid inlet 120 and the liquid outlet pipe is connected to the liquid outlet 130.

[0082] In some embodiments, the blood degassing device is often configured in extracorporeal circulation and can meet the blood flow rate of 2L / min to 8L / min for filtration; it can also be configured for pediatric or infant patients and has a smaller perfusion volume than conventional devices, which is 35ml. In other embodiments, the volume is 20ml to 150ml. The volume is not limited in the present invention.

[0083] Compared with the prior art, the blood circulation system has a liquid inlet pipe, a liquid outlet pipe and a device suitable for blood degassing, so it can also solve the problem of the prior art blood circulation system being in a negative pressure state for a long time during degassing, which causes damage to the blood.

[0084] The above-mentioned control modes of the valve element 220 can be two or three at the same time. Specific examples are as follows:

[0085] Blood enters the first space 1110 through the liquid inlet 120. Blood flows upward in a spiral within the first space 1110, causing bubbles in the blood to gather in the center due to the centrifugal effect. The overall upward flow and the bubbles' own buoyancy cause the bubbles to rise in the center. As the blood passes through the filter, it enters the second space 1120 through the pores of the filter element 30. Some larger bubbles are intercepted by the pores of the filter element 30. Alternatively, bubbles larger than the pore diameter may experience resistance when passing through these pores, slowing their flow. In this case, the centrifugal force of the liquid flow prevents the bubbles from "drilling" into the space, causing them to gather in the center. Once the bubbles rise to the top and accumulate to a certain volume, the ultrasonic sensor 230 detects their presence and sends a signal to the valve element 220 control unit. This signal is transmitted to the electromagnetic closing mechanism, causing the valve element 220 to open. Since the exhaust port 140 is connected to the outside atmosphere or a vacuum pump, which is at a negative pressure relative to the air pressure within the device, this causes gas to flow toward the negative pressure side. After the gas has finished flowing out, the ultrasonic sensor 230 no longer detects the bubble signal, and further sends a signal to the valve member 220 to control the valve member 220 to close. At this time, the air pressure in the device for blood degassing is restored to balance.

[0086] Alternatively, when any one or all of the ultrasonic sensor 230 , the electromagnetic closing mechanism, and the floating member 240 fails, the moving portion 2220 may be manually moved (usually by twisting) to control the opening and closing of the valve member 220 .

[0087] Alternatively, if either or both of the ultrasonic sensor 230 and the electromagnetic closing mechanism malfunction and the device is unattended, as the volume of the bubbles in the inner cavity 110 increases, the blood level in the inner cavity 110 will drop, thereby driving the floating member 240 downward. During the downward movement, the inclined member 2240 moves on the abutment member 2250, forcing the abutment member 2250 to rotate the movable member 2220. The rotation of the movable member 2220 controls the valve member 220 to open. When the bubbles are completely eliminated and the liquid surface rises, the floating member 240 also rises. At this time, because the abutment member 2250 no longer has the obstruction of the inclined member 2240, the elastic member 2230 resets the movable member 2220, thereby closing the valve member 220. Alternatively, when the bubbles are completely eliminated and the liquid surface rises, the floating member 240 is subjected to buoyancy but has not yet risen. At this time, the external force on the elastic member 2230 is reduced, causing the movable member 2220 to reset, thereby closing the valve member 220 and driving the floating member 2230 to float to a designated position.

[0088] It should be noted that the electromagnetic closing mechanism can be a proportional solenoid valve or a direct-acting solenoid valve.

[0089] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present application, rather than to limit them. Although the present application has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some or all of the technical features therein. These modifications or replacements do not deviate the essence of the corresponding technical solutions from the scope of the technical solutions of the embodiments of the present application.

Claims

1. A device for degassing blood, characterized in that: It comprises a body and an exhaust mechanism, wherein the body has an inner cavity, a liquid inlet, a liquid outlet, an exhaust port and a filter element; The liquid inlet, the liquid outlet and the exhaust port are respectively connected to the inner cavity, and the exhaust port is arranged on the top of the body; The exhaust mechanism includes a breathable member and a valve member, wherein the valve member is provided at the exhaust port and can control the opening and closing of the exhaust port, and the breathable member is provided in the inner cavity and is used to isolate liquid but not gas; The filter element separates the inner cavity into a first space and a second space, the first space is connected to the liquid inlet and the exhaust port, and the second space is connected to the liquid outlet. The filter element has a plurality of through holes, and the liquid inlet is arranged below the filter element; Blood flows from the liquid inlet into the first space, passes through the filter element, enters the second space, and finally flows out from the liquid outlet; The gas enters the first space through the liquid inlet and is blocked by the filter element from entering the second space, and then is discharged from the exhaust port through the air permeable element.

2. The device for degassing blood according to claim 1, characterized in that: The exhaust mechanism further includes an ultrasonic sensor, which can sense bubbles in the inner cavity to control the opening and closing of the valve member.

3. The device for degassing blood according to claim 1, characterized in that: The exhaust mechanism further includes a floating member, which floats on the blood and moves up and down along with the change in the height of the blood to control the opening and closing of the valve member.

4. The device for degassing blood according to claim 1, characterized in that: The valve member includes a fixed portion and a movable portion. The fixed portion is fixed at the exhaust port and is rotatably connected to the movable portion. Rotating the movable portion causes the movable portion and the fixed portion to rotate relative to each other, thereby controlling the opening and closing of the valve member.

5. The device for degassing blood according to claim 4, characterized in that: The valve component further includes an elastic component, and two ends of the elastic component are respectively connected to the fixed portion and the movable portion.

6. The device for degassing blood according to claim 1, characterized in that: The air permeable member is arranged to be inclined relative to a horizontal plane, and the lowest point of the air permeable member is located at the exhaust port.

7. The device for degassing blood according to claim 1 or 6, characterized in that: The exhaust port is arranged obliquely relative to a horizontal plane, and the highest point of the bottom area of ​​the exhaust port is located below the lowest point of the air permeable member.

8. The device for degassing blood according to claim 1, characterized in that: The liquid inlet is arranged along a tangential direction of the body so that the blood flows in a spiral manner in the first space.

9. The device for degassing blood according to claim 8, characterized in that: The liquid inlet is arranged at the bottom of the body, and the upper end in the first space is narrower than the lower end.

10. A blood circulation system, characterized in that: The device comprises a liquid inlet pipe, a liquid outlet pipe and the device for blood degassing according to any one of claims 1 to 9, wherein the liquid inlet pipe is connected to the liquid inlet, and the liquid outlet pipe is connected to the liquid outlet.

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