CN222056146U - A blood circulation assist device and system - Google Patents
A blood circulation assist device and system Download PDFInfo
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- CN222056146U CN222056146U CN202420316360.1U CN202420316360U CN222056146U CN 222056146 U CN222056146 U CN 222056146U CN 202420316360 U CN202420316360 U CN 202420316360U CN 222056146 U CN222056146 U CN 222056146U
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Abstract
The utility model relates to the technical field of blood circulation auxiliary systems, and provides a blood circulation auxiliary device and a blood circulation auxiliary system, wherein the blood circulation auxiliary device comprises: the membrane pump cavity is internally provided with a flexible membrane which separates the membrane pump cavity to at least form a blood containing cavity; the actuating end of the driving device is connected with the flexible film and is suitable for driving the flexible film to be protruded or recessed; the execution end of the driving device drives the deformation quantity of the flexible membrane protruding outwards and inwards to be constant and consistent. Compared with the IABP host with high cost improvement, the blood circulation auxiliary device provided by the utility model provides another replaceable blood circulation auxiliary device to realize blood transfusion effect, and because the driving device of the blood circulation auxiliary device adopts a fixed-stroke driving mode, the deformation of the flexible membrane, which is driven by the execution end to be convex and concave, is constant and consistent, the stable flow of pumping can be ensured under medium and high heart rates, the phenomenon of drop can not occur, and the blood circulation auxiliary device is safer and more reliable.
Description
Technical Field
The utility model relates to the technical field of blood circulation auxiliary systems, in particular to a blood circulation auxiliary device and system.
Background
In recent years, the incidence of cardiovascular disease has increased. Research shows that most cardiovascular diseases finally affect ventricular functions, and ventricular functions such as ventricular failure, cardiogenic shock and the like are caused. Currently, for ventricular functional disorders, ventricular blood is drained to the aorta, primarily through ventricular assist devices, to provide circulatory support. As a traditional blood circulation auxiliary system, the existing gas-driven blood pump product is generally connected with a membrane pump by adopting a driving device, and gas medium in the driving device is pumped and inflated according to a set pulsation frequency, so that the pumping of blood in the membrane pump is driven, and the pulsating blood circulation effect is achieved.
Studies have shown that existing driving devices such as the aortic balloon counterpulsation (Intra-aortic balloon pump, IABP) host can effectively generate 1.0L/min to 1.5L/min flow. In the use process, the IABP host has a driving work boundary, the output quantity of the air source is difficult to break through the limit, and particularly under the medium and high heart rate, the phenomenon that the flow of the pumped air-driven blood pump product is reduced is common. In theory, in order to break through the output of the air source and simultaneously maintain the electrocardiographic synchronization and the pressure synchronization (arterial blood pressure, systolic diastolic blood pressure), the air-driven blood pump product requires higher manufacturing cost, and also brings about compatibility of software and hardware, mechanical size and a series of safety problems.
Disclosure of utility model
Therefore, the utility model aims to solve the technical problems that when the existing blood circulation auxiliary system is used for assisting the blood circulation through an axial flow pump, the blades rotating at high speed have great damage to red blood cells and are easy to destroy the original components of the blood, so that the blood circulation auxiliary device and system are provided.
In order to solve the technical problems, the technical scheme of the utility model is as follows:
In one aspect, the present utility model provides a blood circulation assistance device comprising: a membrane pump cavity, in which a flexible membrane is arranged, the flexible membrane separating the membrane pump cavity to form at least a blood-containing cavity; the actuating end of the driving device is connected with the flexible membrane and is suitable for driving the flexible membrane to be outwards convex or inwards concave so as to adjust the volume in the blood containing cavity; the execution end of the driving device drives the deformation quantity of the outer protrusion and the inner recess of the flexible film to be constant and consistent; when the flexible membrane protrudes outwards to one side of the blood containing cavity, the volume in the blood containing cavity is reduced, and fluid in the blood containing cavity is pumped out of the blood containing cavity; when the flexible membrane is concave inwards towards one side away from the blood containing cavity, the volume in the blood containing cavity is increased, and fluid is sucked into the blood containing cavity.
Further, the membrane pump cavity comprises a first shell and a second shell which are connected with each other; the edge of the flexible film is clamped between the first shell and the second shell; the space enclosed by the flexible membrane and the inner wall of the first shell is the blood containing cavity, the space enclosed by the flexible membrane and the inner wall of the second shell is the mounting cavity, and the execution end of the driving device at least partially stretches into the mounting cavity and is connected with the flexible membrane.
Further, the sealing ring is also included; sealing grooves matched with the sealing rings are formed in the connection positions of the first shell and the second shell; the edge of the flexible membrane is hermetically arranged in the sealing groove through the sealing ring.
Further, the driving device further comprises a first pushing seat and a second pushing seat which are connected; the first pushing seat is movably arranged in the blood accommodating cavity, the second pushing seat is movably arranged in the mounting cavity, and the flexible membrane is clamped between the first pushing seat and the second pushing seat; the actuating end of the driving device is connected with the second pushing seat.
Further, a connecting cylinder is arranged on one surface of the first pushing seat facing the flexible membrane, and a mounting hole matched with the connecting cylinder is arranged on one surface of the second pushing seat facing the flexible membrane; the flexible film is sleeved on the connecting cylinder, and the connecting cylinder is inserted into the mounting hole and enables the first pushing seat and the second pushing seat to be abutted to the flexible film.
Further, the surface of the first pushing seat, which is close to and far from the flexible film, is a convex curved surface.
Further, one surface of the second pushing seat, which is close to the flexible film, is a convex curved surface.
Further, the execution end of the driving device is a push rod, one end of the push rod penetrates through the second push seat and is inserted into the connecting cylinder, and the other end of the push rod is connected with the control end of the driving device.
In another aspect, the present utility model provides a blood circulation assistance system comprising a blood circulation assistance device according to any one of the preceding claims, further comprising an interventional catheter; the blood-holding cavity comprises an interface connected with the interventional catheter, and the inner peripheral wall of the interface extends along the tangential direction of the outlet edge of the blood-holding cavity.
Further, the shock absorber also comprises a shock absorber tube; the damping tube is sleeved at one end of the intervention catheter close to the membrane pump cavity, and a preset buffer gap is reserved between the damping tube and the intervention catheter.
The technical scheme of the utility model has the following advantages:
According to the blood circulation auxiliary device provided by the utility model, the flexible membrane is controlled to deform by utilizing the driving device so as to change the volume of the blood containing cavity, wherein when the flexible membrane is outwards protruded, the volume in the blood containing cavity is reduced, and the blood in the blood containing cavity is pumped out; when the flexible membrane is concave, the volume in the blood containing cavity is increased, and the blood in the patient is sucked into the blood containing cavity. Compared with the improvement of an IABP host with high cost, the utility model provides another alternative blood circulation auxiliary device to realize the blood circulation auxiliary effect, and the driving device of the blood circulation auxiliary device adopts a fixed-stroke driving mode, so that the deformation of the execution end driving the flexible membrane to be convex and concave is constant and consistent, the stable flow of pumping can be ensured under medium and high heart rate, the phenomenon of drop can not occur, and the blood circulation auxiliary device is safer and more reliable.
Drawings
In order to more clearly illustrate the embodiments of the present utility model or the technical solutions in the prior art, the drawings that are needed in the description of the embodiments or the prior art will be briefly described, and it is obvious that the drawings in the description below are some embodiments of the present utility model, and other drawings can be obtained according to the drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic diagram of a blood circulation assistance system according to an embodiment of the present utility model;
FIG. 2 is a schematic diagram showing the internal structure of a membrane pump chamber in the blood circulation assistance system according to the embodiment of the present utility model;
FIG. 3 is a schematic diagram of an intermediary catheter in a blood circulation assistance system according to an embodiment of the present utility model;
fig. 4 is a cross-sectional view of a blood-holding chamber in a blood circulation assistance system according to an embodiment of the present utility model.
1. A membrane pump cavity; 2. an interventional catheter; 3. a driving device; 4. a first housing; 5. a second housing; 6. a flexible membrane; 7. a blood-holding cavity; 8. a mounting cavity; 9. a push rod; 10. a first pushing seat; 11. a second pushing seat; 12. a seal ring; 13. a connecting cylinder; 14. a switching valve; 15. a shock tube; 16. an interface.
Detailed Description
The following description of the embodiments of the present utility model will be made apparent and fully in view of the accompanying drawings, in which some, but not all embodiments of the utility model are shown. All other embodiments, which can be made by those skilled in the art based on the embodiments of the utility model without making any inventive effort, are intended to be within the scope of the utility model.
In the description of the present utility model, it should be noted that the directions or positional relationships indicated by the terms "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inner", "outer", etc. are based on the directions or positional relationships shown in the drawings, are merely for convenience of describing the present utility model and simplifying the description, and do not indicate or imply that the devices or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present utility model. Furthermore, the terms "first," "second," and "third" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance.
In the description of the present utility model, it should be noted that, unless explicitly specified and limited otherwise, the terms "mounted," "connected," and "connected" are to be construed broadly, and may be either fixedly connected, detachably connected, or integrally connected, for example; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the above terms in the present utility model will be understood in specific cases by those of ordinary skill in the art.
In addition, the technical features of the different embodiments of the present utility model described below may be combined with each other as long as they do not collide with each other.
As shown in fig. 1, 2 and 3, the present embodiment provides a blood circulation assistance device, including: the membrane pump cavity is internally provided with a flexible membrane which separates the membrane pump cavity to at least form a blood containing cavity; the actuating end of the driving device is connected with the flexible membrane and is suitable for driving the flexible membrane to be outwards convex or inwards concave so as to adjust the volume in the blood accommodating cavity; when the flexible membrane protrudes outwards to one side of the blood accommodating cavity, the volume in the blood accommodating cavity is reduced, and fluid in the blood accommodating cavity is pumped out of the blood accommodating cavity; when the flexible membrane is concave inwards towards one side away from the blood containing cavity, the volume in the blood containing cavity is increased, and fluid is sucked into the blood containing cavity.
The execution end of the driving device drives the deformation quantity of the flexible membrane protruding outwards and inwards to be constant and consistent. For example, the stroke and the speed can be set in advance by the execution end, the flexible membrane is driven to reciprocate outwards or inwards, and the counterpulsation with large volume of blood is realized to assist the heart circulation.
The flexible membrane 6 is made of flexible material, specifically polyurethane, silicone rubber or rubber, polyethylene or other high polymer materials or biological membrane, and can also be made of other elastic materials.
According to the blood circulation auxiliary device provided by the embodiment, the driving device is used for controlling the flexible membrane to deform so as to change the volume of the blood containing cavity, wherein when the flexible membrane is outwards protruded, the volume in the blood containing cavity is reduced, and blood in the blood containing cavity is pumped out; when the flexible membrane is concave, the volume in the blood containing cavity is increased, and the blood in the patient is sucked into the blood containing cavity. Compared with the improvement of an IABP host with high cost, the application provides another alternative blood circulation auxiliary device to realize the blood circulation auxiliary effect, and the driving device of the blood circulation auxiliary device adopts a fixed-stroke driving mode, so that the deformation of the execution end driving the flexible membrane to be convex and concave is constant and consistent, the stable flow of pumping can be ensured under medium and high heart rate, the phenomenon of drop can not occur, and the blood circulation auxiliary device is safer and more reliable.
The membrane pump cavity 1 comprises a first shell 4 and a second shell 5 which are mutually buckled and connected; the edge of the flexible film 6 is clamped between the connecting surfaces of the first shell 4 and the second shell 5; the space enclosed by the flexible membrane 6 and the inner wall of the first shell 4 is a blood containing cavity 7, the space enclosed by the flexible membrane 6 and the inner wall of the second shell 5 is an installation cavity 8, and the execution end of the driving device 3 at least partially stretches into the installation cavity 8 and is connected with the flexible membrane 6. For example, the first housing 4 and the second housing 5 may be made of nontoxic plastic, plexiglas, glass or metal. The arrangement ensures that the blood containing cavity 7 has the characteristics of better biocompatibility, less antigenicity, no heat source and the like, and is safer to use. The first shell 4 and the second shell 5 are spliced to form a hollow area inside, and the cross section of the hollow area can be round, square, cylindrical and the like. Of course, in other embodiments, the first housing 4 and the second housing 5 may be connected in other removable manners, such as a threaded connection, an interference fit connection, a pin connection, etc.
Wherein the blood circulation auxiliary system further comprises a sealing ring 12, for example, when in processing, the sealing ring can be arranged separately with the flexible membrane or processed by adopting an integrated forming process; the connection parts of the first shell 4 and the second shell 5 are provided with sealing grooves matched with the sealing rings 12. The edge of the flexible membrane 6 is sealingly mounted to the sealing groove by means of the sealing ring 12. For example, the edge of the flexible membrane 6 can be pressed into the sealing groove by the sealing ring 12 during installation, so that the sealing performance of the membrane pump cavity 1 is improved.
Wherein the driving device 3 further comprises a first pushing seat 10 and a second pushing seat 11 which are connected; the first pushing seat 10 is movably arranged in the blood accommodating cavity 7, the second pushing seat 11 is movably arranged in the mounting cavity 8, and the flexible membrane 6 is clamped between the first pushing seat 10 and the second pushing seat 11; the actuating end of the drive 3 is connected to the second push seat 11. For example, the first pushing seat 10 and the second pushing seat 11 may have a circular plate structure, and the diameters of the first pushing seat 10 and the second pushing seat 11 are smaller than the diameter of the flexible film 6. When bleeding, a force for making the flexible film 6 convex is applied by the second pushing seat 11, and when drawing blood, a force for making the flexible film 6 concave is applied by the first pushing seat 10. Through pressing from both sides flexible membrane 6 between first push away seat 10 and second push away seat 11, drive control in-process, drive arrangement is more firm with the connection of flexible membrane, guarantees the even atress of flexible membrane, guarantees that the seal is good, does not produce leakage.
The surface of the flexible membrane 6 is smooth, has good toughness, is not easy to damage, and has good biocompatibility. The flexible membrane 6 has little damage and injury to the blood components during the back and forth stretching of the push rod 9.
Specifically, the first pushing seat 10 is provided with a connecting cylinder 13 on one surface facing the flexible membrane 6, the second pushing seat 11 is provided with a mounting hole adapted to the connecting cylinder 13 on one surface facing the flexible membrane 6, for example, an external thread may be provided on an outer wall of the connecting cylinder 13, and an internal thread may be provided on an inner wall of the mounting hole, so that the connecting cylinder 13 is connected with the mounting hole through threads. For example, a through hole is formed in the middle of the flexible film 6, the flexible film 6 is sleeved on the connecting cylinder 13, in order to enable the flexible film 6 to be tightly connected with the connecting cylinder 13, the size of the through hole can be slightly smaller than the diameter of the connecting cylinder 13, and after the connecting cylinder 13 is inserted into the mounting hole, the first pushing seat 10 is screwed until the first pushing seat 10 and the second pushing seat 11 are abutted against the flexible film 6. So set up, flexible membrane 6 is by joint in connecting cylinder 13 to extrude and be fixed in between first push away seat 10 and the second push away seat 11, whether inwards extrude flexible membrane 6 through first push away seat 10, or outwards extrude flexible membrane 6 through second push away seat 11, flexible membrane 6 can not the drunkenness, guarantees the reliability of blood transfusion.
Wherein the surface of the first pushing seat 10, which is close to and far from the flexible film 6, is a convex curved surface; the surface of the second pushing seat 11 close to the flexible membrane 6 is a convex curved surface. So set up for the first bending radian that pushes away seat 10 and second pushes away seat 11 and flexible membrane 6 the one side of contact is the bending radian when flexible membrane 6 deformation of adaptation more, and the force that flexible membrane 6 received is more even, prevents that stress concentration from damaging flexible membrane 6, is favorable to improving flexible membrane 6's life. Moreover, the surface of the first pushing seat, which is contacted with blood, is a curved surface, so that components in the blood are not easily damaged, and the safety of auxiliary blood transfusion is improved.
Wherein the actuating end of the driving device 3 is a push rod 9, one end of the push rod 9 passes through the second push seat 11 and is inserted into the connecting cylinder 13, and the other end of the push rod 9 is connected with the control end of the driving device 3. For example, the inner wall of the connecting cylinder 13 can be provided with internal threads, the outer wall of the push rod 9 can be provided with external threads, and the push rod 9 and the connecting cylinder 13 can be in threaded connection, so that the connection strength of the push rod 9 and the connecting cylinder is improved, and the transmission precision of the push rod 9 is ensured. For example, the control end may be a linear motor by which the push rod 9 is driven to reciprocate. For example, the control end may be another screw mechanism, a cam mechanism, a sheave mechanism, a link mechanism, various gas or liquid driving devices, or the like capable of reciprocating the push rod 9. By the arrangement, the blood circulation auxiliary device adopts the reciprocating push rod, the first push seat and the second push seat to drive the flexible membrane with the fixed edge to be protruded or recessed, and compared with an IABP host in the prior art, the blood circulation auxiliary device does not have a driving work boundary, is not limited by the output quantity of an air source, does not need to consume high-cost manufacturing of the air-driven blood pump product for breaking through the limitation of the output quantity of the air source, and avoids generating software and hardware, mechanical size compatibility and a series of safety problems.
Wherein, the actuating end of the driving device 3 drives the flexible membrane 6 to have constant and consistent deformation of the outer convex and inner concave. For example, the control end can set the stroke and the speed in advance, so as to drive the push rod 9 to reciprocate, and meanwhile, the push rod 9 drives the flexible membrane 6 to reciprocate outwards or inwards through the first push seat 10 and the second push seat 11, so that the back-pulsation of blood with one row of large capacity is realized, and the heart circulation is assisted.
Another embodiment provides a blood circulation assistance system comprising a blood circulation assistance device according to any one of the preceding claims, further comprising an interventional catheter; the blood-holding chamber comprises a mouthpiece 16 connected to the interventional catheter, the inner peripheral wall of the mouthpiece 16 extending tangentially to the outlet edge of the blood-holding chamber.
Wherein, for the interventional catheter 2, the existing interventional catheter 2 can be adopted, the proximal end of the interventional catheter 2 is communicated with the blood containing cavity 7, and the distal end of the interventional catheter extends into the ventricle through the aortic valve for sucking blood; a switching valve 14 is arranged at the distal end of the interventional catheter 2, and the switching valve 14 has two states of opening and closing; when the valve port of the switching valve 14 is closed, the blood in the ventricle is sucked and enters the blood containing cavity 7 through the intervention catheter 2; when the valve port of the switching valve 14 is opened, the blood in the blood-containing chamber 7 is discharged into the aorta through the interventional catheter 2.
As shown in fig. 4, the inner wall of the blood-containing chamber 7 is smooth, the cross-section of the blood-containing chamber 7 may be circular, and the inner peripheral wall of the interface of the blood-containing chamber 7 for connecting with the interventional catheter 2 extends along the tangential direction of the outlet edge of the blood-containing chamber. By the arrangement, the suction and discharge of blood can be smoother and more in accordance with blood flow dynamics, so that blood coagulation in the blood accommodating cavity 7 can be effectively prevented.
Wherein the blood circulation assistance system further comprises a shock absorbing tube 15; the shock-absorbing tube 15 is sleeved at one end of the intervention catheter 2 close to the membrane pump cavity 1, and a preset buffer gap is reserved between the shock-absorbing tube 15 and the intervention catheter 2. For example, one end of the shock-absorbing tube 15 may be fixed on the outer wall of the membrane pump cavity 1, and one end of the interventional catheter 2 close to the membrane pump cavity 1 is inserted into the shock-absorbing tube 15 and is communicated with the blood-accommodating cavity 7. By the arrangement, when sucking and discharging blood, the intervention catheter 2 can be effectively prevented from shaking violently caused by abrupt change of blood flow direction and flow velocity, and risks in the operation process are reduced.
In the ventricular systole, the driving device 3 drives the flexible membrane 6 to indent towards the second shell 5 by the driving of the control end fixed stroke, the volume of the blood containing cavity 7 is increased to form negative pressure, blood enters the blood containing cavity 7 from the ventricle through the interventional catheter 2, and the valve port of the switching valve 14 is closed to perform a blood drawing mode. The process is beneficial to reducing the pressure in the aorta, effectively reducing the afterload of the ventricle and being more beneficial to heart ejection.
In ventricular diastole, the driving device 3 drives the flexible membrane 6 to move outwards towards the first shell 4 by the push rod 9 through the driving of the control end fixed stroke, the volume of the blood containing cavity 7 after extrusion is reduced, blood enters the aorta from the blood containing cavity 7 through the interventional catheter 2, and the valve port of the switching valve 14 is opened to perform a 'blood discharging' mode. The process improves the diastolic pressure in the aorta, and effectively improves the blood perfusion of all organs and tissues of the whole body. Under the action of high-capacity counterpulsation of the membrane pump cavity 1, the blood forms pulsating blood flow in one step and in one step, so that the auxiliary flow is greatly improved, the heart load is reduced, the myocardial work is reduced, and the cardiac output is obviously improved. In conclusion, the blood circulation auxiliary system adopts a fixed-line driving mode, has a simple structure, is convenient to operate, and improves the upper limit of the pumped blood flow.
According to the blood circulation auxiliary system, the damping tube 15 at the outlet side of the membrane pump cavity 1 is designed, so that the phenomenon of severe twisting of the interventional catheter 2 caused by abrupt changes of blood flow direction and flow velocity is effectively avoided, the risk of clinical operation is fully reduced, and the safety of patients is ensured.
It is apparent that the above examples are given by way of illustration only and are not limiting of the embodiments. Other variations or modifications of the above teachings will be apparent to those of ordinary skill in the art. It is not necessary here nor is it exhaustive of all embodiments. While still being apparent from variations or modifications that may be made by those skilled in the art are within the scope of the utility model.
Claims (10)
1. A blood circulation assistance device, comprising:
A membrane pump cavity (1) in which a flexible membrane (6) is arranged, the flexible membrane (6) dividing the membrane pump cavity (1) to form at least a blood-containing cavity (7);
The actuating end of the driving device (3) is connected with the flexible membrane (6) and is suitable for driving the flexible membrane (6) to be outwards protruded or inwards recessed so as to adjust the volume in the blood accommodating cavity (7); the execution end of the driving device (3) drives the deformation quantity of the flexible film (6) which is convex and concave to be constant and consistent;
When the flexible membrane (6) protrudes outwards towards one side of the blood containing cavity, the volume in the blood containing cavity (7) is reduced, and fluid in the blood containing cavity (7) is pumped out of the blood containing cavity; when the flexible membrane (6) is concave towards one side away from the blood containing cavity, the volume in the blood containing cavity (7) is increased, and fluid is sucked into the blood containing cavity (7).
2. A blood circulation assistance device according to claim 1, wherein,
The membrane pump cavity (1) comprises a first shell (4) and a second shell (5) which are connected with each other;
The edge of the flexible film (6) is clamped between the first shell (4) and the second shell (5);
The space enclosed by the flexible membrane (6) and the inner wall of the first shell (4) is the blood containing cavity (7), the space enclosed by the flexible membrane (6) and the inner wall of the second shell (5) is the installation cavity (8), and the execution end of the driving device (3) at least partially stretches into the installation cavity (8) and is connected with the flexible membrane (6).
3. A blood circulation assistance device according to claim 2, wherein,
Also comprises a sealing ring (12);
Sealing grooves matched with the sealing rings (12) are formed in the connection positions of the first shell (4) and the second shell (5);
the edge of the flexible membrane (6) is hermetically mounted in the sealing groove through the sealing ring (12).
4. A blood circulation assistance device according to claim 2, wherein,
The driving device (3) further comprises a first pushing seat (10) and a second pushing seat (11) which are connected;
The first pushing seat (10) is movably arranged in the blood accommodating cavity (7), the second pushing seat (11) is movably arranged in the mounting cavity (8), and the flexible membrane (6) is clamped between the first pushing seat (10) and the second pushing seat (11);
The actuating end of the driving device (3) is connected with the second pushing seat (11).
5. A blood circulation assistance device according to claim 4, wherein,
A connecting cylinder (13) is arranged on one surface of the first pushing seat (10) facing the flexible membrane (6), and a mounting hole matched with the connecting cylinder (13) is arranged on one surface of the second pushing seat (11) facing the flexible membrane (6);
The flexible membrane (6) is sleeved on the connecting cylinder (13), and the connecting cylinder (13) is inserted into the mounting hole and enables the first pushing seat (10) and the second pushing seat (11) to be abutted against the flexible membrane (6).
6. A blood circulation assistance device according to claim 5, wherein,
The surfaces of the first pushing seat (10) close to and far from the flexible membrane (6) are convex curved surfaces.
7. A blood circulation assistance device according to claim 5, wherein,
One surface of the second pushing seat (11) close to the flexible membrane (6) is a convex curved surface.
8. A blood circulation assistance device according to claim 5, wherein,
The actuating end of the driving device (3) is a push rod (9), one end of the push rod (9) penetrates through the second push seat (11) and is inserted into the connecting cylinder (13), and the other end of the push rod (9) is connected with the control end of the driving device (3).
9. A blood circulation assistance system according to any one of claims 1-8, comprising a blood circulation assistance device according to any one of claims 1-8, further comprising an interventional catheter (2);
The blood containing cavity (7) comprises a connector (16) connected with the interventional catheter (2), and the inner peripheral wall of the connector (16) extends along the tangential direction of the outlet edge of the blood containing cavity (7).
10. The blood circulation assistance system according to claim 9, wherein,
Also comprises a shock absorption tube (15);
The damping tube (15) is sleeved at one end, close to the membrane pump cavity (1), of the intervention catheter (2), and a preset buffer gap is reserved between the damping tube (15) and the intervention catheter (2).
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202420316360.1U CN222056146U (en) | 2024-02-20 | 2024-02-20 | A blood circulation assist device and system |
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| CN202420316360.1U CN222056146U (en) | 2024-02-20 | 2024-02-20 | A blood circulation assist device and system |
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| GR01 | Patent grant | ||
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| PE01 | Entry into force of the registration of the contract for pledge of patent right | ||
| PE01 | Entry into force of the registration of the contract for pledge of patent right |
Denomination of utility model: A blood circulation assistance device and system Granted publication date: 20241126 Pledgee: Hangzhou Yingzhiqin No.1 Equity Investment Partnership Enterprise (Limited Partnership) Pledgor: Hangzhou Diyuan Medical Technology Co.,Ltd. Registration number: Y2025980005527 |