Catheter pump sleeve assembly and catheter pump

Abstract

The utility model discloses a catheter pump cannula assembly and a catheter pump, and relates to the field of medical instruments, the catheter pump cannula assembly comprises a cannula which penetrates through an aortic valve and is used for communicating a ventricle with an aorta, two ends of the cannula are respectively provided with a blood inflow cage arranged in the ventricle and a blood outflow cage arranged in the aorta, and the periphery of the cannula is provided with a balloon. After the balloon is inflated, a concave part matched with the aortic valve in position is formed in the middle of the balloon, flexible protection can be formed on the periphery of a catheter pump sleeve, damage to a patient suffering from intracardiac depressive scars is reduced, and auxiliary positioning and limiting can be conducted on the position of the balloon in a heart chamber; the possibility of displacement of the catheter pump in the using process can be reduced while the positioning mode of the catheter pump is simplified; on the other hand, the inflated balloon is in contact with the aortic valve, so that the contact area with the aortic valve is increased, and blood can be prevented from flowing back to the ventricle.

Description

Technical Field

[0001] The utility model relates to the field of medical devices, in particular to a catheter pump sleeve assembly and a catheter pump. Background Technique

[0002] A catheter pump is an intravascular microaxial flow pump that provides hemodynamic support for patients with cardiogenic shock or heart failure. During percutaneous coronary intervention (PCI), the catheter pump can be percutaneously inserted into the heart to pump blood from the left ventricle into the aorta, assisting blood circulation and maintaining the life of the patient.

[0003] As shown in the attached Figure 3 As shown in the figure, the catheter pump is sequentially connected by structures such as a pigtail tube 10, a blood inflow cage 20, a flexible sleeve 30, a blood outflow cage 40, a micro motor 50, and a catheter 60. The intervention process of the catheter pump is as follows: under the guidance of a guide wire, a sheath is placed into the patient's body, and then the catheter pump is placed into the sheath. After the catheter pump is intervened to a specific position through the sheath, the sheath is removed. During the operation of the catheter pump, displacement will inevitably occur. At this time, the relative position of the sleeve to the aortic valve changes, which may have a serious impact on patients with intracardiac scars. Content of the Utility Model

[0004] The purpose of the utility model is to provide a catheter pump sleeve assembly, by setting an annular balloon on the outer periphery of the catheter pump sleeve to solve the problems raised in the above background technique.

[0005] To achieve the above purpose, the utility model provides the following technical solutions:

[0006] A catheter pump sleeve assembly includes a sleeve that passes through the aortic valve and is used to connect the ventricle and the aorta. Blood inflow cages placed in the ventricle and blood outflow cages placed in the aorta are respectively arranged at both ends of the sleeve. A balloon is arranged on the outer periphery of the sleeve. After the balloon is inflated, a depression adapted to the position of the aortic valve is formed in the middle of the balloon.

[0007] As a further scheme of the utility model: the balloon is annular and is evenly distributed radially on the outer periphery of the sleeve.

[0008] As a further scheme of the utility model: the balloon includes a first balloon at the proximal end of the sleeve, a second balloon in the middle section of the sleeve, and a third balloon at the distal end of the sleeve. The radial cross-sectional diameter of the second balloon is smaller than the radial cross-sectional diameters of the first balloon and the third balloon.

[0009] As a further scheme of the utility model: the outer diameter of the first balloon gradually decreases from the proximal end to the distal end, and the outer diameter of the third balloon gradually increases from the proximal end to the distal end.

[0010] As a further solution of the present utility model: the first balloon, the second balloon and the third balloon are integrally formed and smoothly transition.

[0011] As a further solution of the present utility model: the balloon comprises a flexible bladder having elastic or non-elastic properties and a bladder cavity having a fixed or variable volume.

[0012] As a further solution of the present utility model: the balloon is connected to an external inflation and deflation device through a trachea, and the trachea constitutes an inflation and deflation channel of the balloon.

[0013] As a further solution of the present utility model: a part of the trachea is accommodated in the catheter.

[0014] As a further solution of the present utility model: grooves for accommodating the trachea are formed on both the outer surface of the motor and the blood outflow cage.

[0015] As a further solution of the present utility model: the first groove on the motor is connected to the second groove of the blood outflow cage.

[0016] A catheter pump, comprising a catheter pump sleeve assembly as described above.

[0017] Compared with the prior art, the beneficial effects of the present utility model are: the structure of the present utility model is novel. By providing an annular balloon on the outer periphery of the catheter pump sleeve, the balloon separates the sleeve from the patient's aortic valve. During actual use, when the catheter pump is inserted, the balloon is in a non-inflated state with a small volume, which does not affect inserting the catheter pump into the sheath and then into the patient's body. After the catheter pump is inserted, the balloon is in an inflated state, forming a flexible protection on the outer periphery of the catheter pump sleeve. When the position of the catheter pump sleeve changes relative to the aortic valve, the balloon can play a buffering and protective role, effectively reducing the damage to patients with intracardiac scars; at the same time, after the catheter pump is inserted, the balloon can assist in positioning and limiting the position of the catheter pump in the ventricle. On the one hand, it simplifies the method of positioning the catheter pump, and on the other hand, it reduces the possibility of the catheter pump shifting during use, thereby reducing the damage to the patient. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] Figure 1 It is a schematic structural diagram of the catheter pump in the state where the balloon is inflated;

[0019] Figure 2 It is Figure 1 an enlarged view of the structure at position A of

[0020] Figure 3 It is a schematic structural diagram of the catheter pump in the state where the balloon is not inflated;

[0021] Figure 4 It is a balloon with no special treatment on its shape;

[0022] Figure 5 A balloon after special treatment for its shape;

[0023] Figure 6 A schematic diagram of the catheter pump being inserted into the patient's heart;

[0024] In the figure: 10 - pigtail catheter, 20 - blood inflow cage, 30 - cannula, 31 - balloon, 311 - first balloon, 312 - second balloon, 313 - third balloon, 40 - blood outflow cage, 41 - second groove, 50 - motor, 51 - first groove, 60 - catheter, 70 - trachea. Specific embodiments

[0025] Next, the technical solutions in the embodiments of the present utility model will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present utility model. Obviously, the described embodiments are only a part of the embodiments of the present utility model, rather than all the embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without making creative efforts shall fall within the protection scope of the present utility model.

[0026] In the present application, the "distal end" refers to the end far from the operator, and the "proximal end" refers to the end close to the operator.

[0027] As Figure 1 shown, in the embodiment of the present utility model, a catheter pump cannula 30 assembly includes a cannula 30 for penetrating the patient's ventricle and aorta. One end of the cannula 30 is fixedly connected to a blood inflow cage 20 placed in the ventricle, and the other end is fixedly connected to a blood outflow cage 40 placed in the aorta. A balloon 31 is provided on the outer periphery of the cannula 30. After the balloon 31 is inflated, a concave portion adapted to the position of the aortic valve is formed in the middle of the balloon 31.

[0028] By providing a balloon 31 on the outer periphery of the catheter pump cannula 30, after the catheter pump is inserted into the patient's body, the balloon 31 is inflated to expand its volume. The position of the aortic valve is just located at the concave portion formed after the balloon 31 is inflated. Compared with the way that the catheter pump cannula 30 directly contacts the aortic valve, the present application increases the contact area between the aortic valve and the inserted body to a certain extent. The aortic valve is closely attached to the balloon 31. On the one hand, it reduces the pressure on the aortic valve, and on the other hand, it can prevent blood reflux. At the same time, the material of the balloon 31 is relatively soft compared with the catheter pump, further reducing the damage to the aortic valve when the catheter pump is displaced.

[0029] When the catheter pump is inserted, the catheter pump is inserted into the approximate position in the patient's body. After the balloon 31 is inflated, it can guide the catheter pump to the accurate position. Compared with the prior art method of inserting into the ventricle with the aid of X-rays by setting a radiopaque ring on the cannula 30, the present application can insert the catheter pump into the accurate position in the patient's body through structural design without setting X-rays and radiopaque rings on the catheter pump.

[0030] The aortic valve is located in the recess of the balloon 31, which can further limit the position of the catheter pump after insertion, effectively prevent the displacement of the catheter pump during use, and further reduce the impact of the displacement of the catheter pump on patients with intracardiac scars during use.

[0031] The balloon 31 is annular and evenly distributed radially on the outer periphery of the cannula 30. After the balloon 31 is inflated, an annular recess adapted to the position of the aortic valve is formed in the middle of the balloon 31. The annular balloon 31 further increases the contact area between the aortic valve and the inserted body, makes the aortic valve fit tightly with the balloon 31, effectively prevents blood reflux, and can reduce the damage to the aortic valve when the catheter pump is displaced.

[0032] The annular balloon 31 includes a first balloon 311 at the proximal end of the cannula 30, a second balloon 312 in the middle section of the cannula 30, and a third balloon 313 at the distal end of the cannula 30. The radial cross-sectional diameter of the second balloon 312 is smaller than that of the first balloon 311 and the third balloon 313, which is convenient for forming the annular recess of the annular balloon 31 at the second balloon 312. Specifically: the outer diameter of the first balloon 311 gradually decreases from the proximal end to the distal end, and the outer diameter of the third balloon 313 gradually increases from the proximal end to the distal end. The balloon 31 will show an annular recessed shape as a whole. The recess formed by the annular balloon 31 can be located at the aortic valve of the patient after the catheter pump is inserted into the patient's body. After the catheter pump is inserted, the recess formed by the balloon 31 can assist in positioning the catheter pump to a certain extent.

[0033] The first balloon 311, the second balloon 312 and the third balloon 313 are connected and smoothly transition, and can be but not limited to integrally formed. When the catheter pump is inserted into the correct position, the catheter pump cannula 30 contacts the aortic valve. At this time, the inflatable balloon 31 arranged on the outer periphery of the cannula 30 can play a role of double buffering and protection.

[0034] The annular balloon 31 includes a flexible bladder with elastic or non-elastic properties and a bladder cavity with a fixed or variable volume. The annular balloon 31 is connected to an external inflation and deflation device through a trachea 70, and the trachea 70 constitutes the inflation and deflation channel of the annular balloon 31. The trachea 70 can be connected to the balloon 31 through a suitable path, and can be but not limited to being accommodated in the catheter 60, extending out at the distal end of the catheter 60 and then connected to the balloon 31 through the outer peripheral surface of the motor 50 and the blood outflow cage 40 in sequence.

[0035] A part of the trachea 70 is accommodated in the catheter 60. The trachea 70 is introduced into the body from outside the patient through the catheter 60 and is connected to an external inflation and deflation device outside the body, enabling the annular balloon 31 to contract or expand according to the need of the catheter pump intervention, so that it is applicable to different states such as catheter pump intervention, use, and removal.

[0036] Grooves for accommodating the trachea 70 are formed on the outer surfaces of both the motor 50 and the blood outflow cage 40, which can enable the trachea 70 to communicate with the balloon while not changing the outer diameter of the motor 50. Specifically, the first groove 51 on the motor 50 is connected to the second groove 41 on the blood outflow cage 40. By setting the first groove 51 and the second groove 41, the trachea 70 can be arranged on the outer peripheral surface of the catheter pump without changing the structural outer diameter of the catheter pump itself, while ensuring the flatness of the surface of the catheter pump structure, further reducing the occurrence of thrombus and hemolysis events.

[0037] To ensure the overall working stability of the catheter pump and prevent blood from entering and causing equipment failures, especially for the part applied to the patient's body, the joints of the trachea 70 with the catheter 60 and the balloon 31 need to be sealed. A feasible sealing solution is to bond with glue.

[0038] A catheter pump includes the above-mentioned catheter pump sleeve 30 assembly.

[0039] By providing an annular balloon 31 with an inconsistent outer diameter in the radial cross-section on the outer periphery of the catheter pump sleeve 30, the catheter pump sleeve 30 can be separated from the patient's aortic valve. During actual use, when the annular balloon 31 is in a non-inflated state, its volume is small, which does not affect placing the catheter pump in the sheath and intervening in the patient's body; after the catheter pump is intervened, the balloon 31 is in an inflated state, forming a flexible protection on the outer periphery of the catheter pump sleeve 30, effectively reducing the damage to patients with intracardiac scars; at the same time, the present application defines the overall shape of the balloon 31 after inflation, so that after the catheter pump is intervened, the annular recess of the balloon 31 is located at the aortic valve, which can, to a certain extent, assist in positioning and limiting the position of the catheter pump in the ventricle. On the one hand, it can simplify the method of positioning the catheter pump, and on the other hand, it reduces the possibility of the catheter pump shifting during use, thereby reducing the damage to the patient; in addition, the inflated balloon 31 contacts the aortic valve, increasing the contact area with the aortic valve and preventing blood from flowing back into the left ventricle.

[0040] For those skilled in the art, it is obvious that the present utility model is not limited to the details of the above-mentioned exemplary embodiments, and the present utility model can be implemented in other specific forms without departing from the spirit or basic characteristics of the present utility model. Therefore, from any point of view, the embodiments should be regarded as exemplary and non-limiting. The scope of the present utility model is defined by the appended claims rather than the above description. Therefore, all changes falling within the meaning and scope of the equivalent elements of the claims are intended to be embraced within the present utility model. Any reference signs in the claims should not be construed as limiting the claims involved.

[0041] In addition, it should be understood that although this specification is described in terms of embodiments, not every embodiment only contains an independent technical solution. This narrative manner of the specification is only for clarity. Those skilled in the art should regard the specification as a whole, and the technical solutions in each embodiment can also be appropriately combined to form other embodiments that can be understood by those skilled in the art.

Claims

1. A catheter pump cannula assembly, comprising a cannula (30) passing through an aortic valve and used to connect a ventricle and an aorta, wherein two ends of the cannula (30) are respectively provided with a blood inflow cage (20) placed in the ventricle and a blood outflow cage (40) placed in the aorta, wherein: A balloon (31) is provided on the outer periphery of the sleeve (30); after the balloon (31) is inflated, a recessed portion adapted to the position of the aortic valve is formed in the middle of the balloon.

2. A catheter pump sleeve assembly according to claim 1, characterized in that: The balloon is annular and evenly distributed radially around the outer circumference of the sleeve.

3. A catheter pump sleeve assembly according to claim 2, characterized in that: The balloon (31) comprises a first balloon (311) located at the proximal end of the sleeve (30), a second balloon (312) located at the middle section of the sleeve (30), and a third balloon (313) located at the distal end of the sleeve (30), wherein the radial cross-sectional diameter of the second balloon (312) is smaller than the radial cross-sectional diameters of the first balloon (311) and the third balloon (313).

4. A catheter pump sleeve assembly according to claim 3, characterized in that: The outer diameter of the first balloon (311) gradually decreases from the proximal end to the distal end, and the outer diameter of the third balloon (313) gradually increases from the proximal end to the distal end.

5. A catheter pump sleeve assembly according to claim 4, characterized in that: The first balloon (311), the second balloon (312) and the third balloon (313) are integrally formed and have a smooth transition.

6. The catheter pump sleeve assembly according to claim 1, characterized in that: The balloon (31) comprises a flexible capsule body with elastic or inelastic properties and a capsule cavity with a fixed or variable volume.

7. A catheter pump sleeve assembly according to claim 4, characterized in that: The balloon (31) is connected to an external inflation and deflation device via a trachea (70), and the trachea (70) constitutes an inflation and deflation channel of the balloon (31).

8. A catheter pump sleeve assembly according to claim 7, characterized in that: The trachea (70) is partially accommodated in the catheter (60).

9. A catheter pump sleeve assembly according to claim 8, characterized in that: It also includes a motor (50), wherein the outer surfaces of the motor (50) and the blood outflow cage (40) are both formed with a groove for accommodating the trachea (70).

10. The catheter pump cannula assembly according to claim 9, characterized in that: The first groove (51) on the motor (50) is connected to the second groove (41) of the blood outflow cage.

11. A catheter pump, characterized in that: A catheter pump sleeve assembly comprising any one of claims 1-10.

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