Interventional ventricular auxiliary oxygen generation device

Abstract

The invention provides an interventional ventricular auxiliary oxygen generation device, a blood flow channel strides over an aortic valve from an ascending aorta to enter a left ventricle, a blood inlet of the blood flow channel is located in the left ventricle, and a blood outlet of the blood flow channel is located in the ascending aorta; the first conveying pipe and the second conveying pipe convey hydrogen peroxide and catalase into the left ventricle respectively to react to generate oxygen and water, and the pumping unit acts to pump oxygen-enriched blood in the left ventricle to the ascending aorta. An oxygen generation function is added to the ventricular auxiliary device, oxygen-enriched blood in the ventricle is pumped into the aorta through the ventricular auxiliary device, on one hand, the myocardial anoxia condition is directly improved, heart recovery is facilitated, on the other hand, the oxygen-enriched blood is pumped into the ascending aorta and directly participates in systemic circulation, and therefore the systemic circulation oxygen supply condition is directly and rapidly improved.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to an interventional ventricular auxiliary oxygen generation device. Background Art

[0002] An interventional ventricular assist device usually involves percutaneously inserting a micro-axial flow pump into the human body, wherein the inlet of the micro-axial flow pump is placed in the left ventricle and the outlet is placed in the ascending aorta. When the micro-axial flow pump is running, blood is drawn from the left ventricle and transported to the ascending aorta, thereby providing blood pumping power for patients with heart failure. For patients with heart failure, the deterioration of their myocardial contractile function is often accompanied by pulmonary insufficiency, and the two affect each other. This causes hypoxia in the patient's myocardium and systemic circulation. Although the interventional ventricular assist device in the prior art can assist the left ventricle in pumping blood, it cannot directly improve the hypoxia condition. Summary of the invention

[0003] The object of the present invention is to provide an invasive ventricular auxiliary oxygenation device which can supplement oxygen for the blood in the left ventricle while assisting in pumping blood.

[0004] In order to achieve the above-mentioned purpose, the technical solution adopted by the present invention is: an interventional ventricular auxiliary oxygen generation device, including a pumping unit and a blood flow channel, the blood flow channel crosses the aortic valve from the ascending aorta into the left ventricle, and the blood inlet of the blood flow channel is located in the left ventricle, and the bleeding outlet is located in the ascending aorta. The device is also provided with a first delivery tube and a second delivery tube, the first delivery tube and the second delivery tube respectively transport hydrogen peroxide and catalase and react in the left ventricle to generate oxygen and water, the oxygen is released into the blood in the left ventricle, and the pumping unit operates to pump the oxygen-rich blood in the left ventricle to the ascending aorta.

[0005] Furthermore, the blood flow channel includes a sleeve and a blood inflow cage and a blood outflow cage fixed at both ends of the sleeve. A window is opened on the blood inlet cage to form a blood inlet, and a window is opened on the blood outflow cage to form a bleeding outlet. A micro-reaction chamber is arranged on the blood inlet cage, and the hydrogen peroxide and catalase transported by the first delivery tube and the second delivery tube undergo a chemical reaction in the micro-reaction chamber and release oxygen.

[0006] Furthermore, the first delivery tube is in the shape of a tube cluster composed of multiple hollow fiber tubes, and the second delivery tube is also in the shape of a tube cluster composed of multiple hollow fiber tubes. The multiple hollow fiber tubes of the first delivery tube and the multiple hollow fiber tubes of the second delivery tube connected to the micro-reaction chamber are arranged alternately.

[0007] Furthermore, the pumping unit includes a motor and an impeller, a blood outflow cover is arranged on the outer periphery of the impeller and is fixedly connected to the distal end of the motor, the proximal end of the motor is connected to the extracorporeal control system through a catheter, and a restraint is arranged in the catheter adjacent to the motor, the restraint is in the shape of a circular plate, and the circular plate is provided with through holes corresponding to the hollow fiber tubes one by one, and the multiple hollow fiber tubes of the first delivery tube and the multiple hollow fiber tubes of the second delivery tube are interlaced in the through holes.

[0008] Furthermore, the first delivery tube and the second delivery tube are single-lumen tubes, and a dispersion unit is arranged between the two single-lumen tubes and the micro-reaction chamber. The dispersion unit includes an outer shell, a joint is arranged at the proximal end of the outer shell, and the inner cavity of the joint is divided into two liquid storage chambers isolated from each other by a partition, and the two liquid storage chambers are respectively communicated with the first delivery tube and the second delivery tube. A tube cluster formed by multiple hollow fiber tubes is arranged in the outer shell, the proximal end of the tube cluster is communicated with the two liquid storage chambers, and the distal end is constrained in a constraint component arranged at the other end of the outer shell. At the constraint component, the multiple hollow fiber tubes communicated with the first delivery tube and the multiple hollow fiber tubes communicated with the second delivery tube are arranged in an interlaced manner, and hydrogen peroxide and catalase enter the hollow fiber tubes and enter the micro-reaction chamber from the distal end of the hollow fiber tubes for chemical reaction.

[0009] Furthermore, the pumping unit includes a motor and an impeller, the blood outflow cage is arranged on the periphery of the impeller and is fixedly connected to the distal end of the motor, the proximal end of the motor is connected to the extracorporeal control system through a catheter, and the dispersion unit is arranged in the catheter near the tail end of the motor.

[0010] Furthermore, two clusters of hollow fiber tubes are combined into a cluster of delivery tubes from the distal end of the catheter. The delivery tubes extend from the outer wall of the motor and the inner wall of the sleeve to the blood inflow cage and communicate with the micro-reaction chamber. The outer wall of the motor is provided with a groove along its axial direction. The delivery tubes are embedded in the grooves and fixed with epoxy resin glue.

[0011] Furthermore, the sleeve includes a spring tube and an inner membrane and an outer membrane covering the inner and outer sides of the spring tube. The spring tube is formed by winding a shape memory wire. A channel is sandwiched between the spring tube and the outer membrane, and the delivery tube passes through the channel.

[0012] Furthermore, a plane is arranged on the outer wall of the blood inflow cage along its axial direction, the micro-reaction chamber is fixed on the plane, the outer cover of the micro-reaction chamber is provided with a protective cover, the outer wall of the protective cover is constructed as an arc-shaped guide surface extending from the distal end to the proximal end, and the two ends of the protective cover are also fixed on the plane.

[0013] Furthermore, the micro-reaction chamber is a micro-channel reactor, the diameter of the reaction channel therein is 10-100um, and a diaphragm is provided at the outlet of the reactor, and the diaphragm allows oxygen and water to pass through and prevents blood from passing through.

[0014] In the above scheme, an oxygen-generating function is added to the ventricular assist device, and hydrogen peroxide and catalase are used to produce oxygen. The products of the reaction are water and oxygen, which are mixed into the blood in the left ventricle to supplement the blood with oxygen. Water is also needed by the human body, so it will not cause any harm to the human body. The oxygen-rich blood in the ventricle is pumped into the aorta by the ventricular assist device, which directly improves myocardial hypoxia and helps the heart recover. On the other hand, the oxygen-rich blood is pumped into the ascending aorta and directly participates in the systemic circulation, thereby directly and quickly improving the oxygen supply of the systemic circulation. BRIEF DESCRIPTION OF THE DRAWINGS

[0015] Figure 1 It is a schematic diagram of the overall structure of the ventricular auxiliary oxygen generation device; Figure 2 for Figure 1 A partially enlarged schematic diagram of Figure 3 For Example 1 Figure 1 AA section view; Figure 4 For Example 1 Figure 1 BB section view; Figure 5 It is a schematic diagram of the structure of the internal restraint member of the catheter and its accessories in Example 1; Figure 6 is a three-dimensional diagram of the restraining member in Example 1; Figure 7 For Example 2 Figure 1 AA section view; Figure 8 For Example 2 Figure 1 BB section view; Fig. 9 It is a schematic diagram of the structure of the dispersion unit in Example 2; Fig.10 is a cross-sectional view of the casing; Fig.11 for Fig.10 Middle CC section view; Fig.12 Schematic diagram of the structure of blood inflow cage and micro-reaction chamber; Fig.13 for Fig.12 main view. DETAILED DESCRIPTION

[0016] To facilitate understanding, let us first define the direction: "proximal" and "proximal side" refer to the side close to the operator / doctor, and "distal" and "distal side" refer to the side away from the operator / doctor, that is, the side close to the heart. Figure 1-Figure 13 The present invention is described in further detail.

[0017] See also Figure 1-Figure 2 As shown, an interventional ventricular auxiliary oxygen generation device includes a pumping unit 10 and a blood flow channel 20. The blood flow channel 20 enters the left ventricle from the ascending aorta across the aortic valve, and the blood inlet a of the blood flow channel is located in the left ventricle, and the bleeding outlet b is located in the ascending aorta. The device is also provided with a first delivery tube 31 and a second delivery tube 32. The first delivery tube 31 and the second delivery tube 32 respectively deliver hydrogen peroxide and catalase and react in the left ventricle to generate oxygen and water. The oxygen is released into the blood in the left ventricle. The pumping unit 10 operates to pump the oxygen-rich blood in the left ventricle to the ascending aorta.

[0018] In the above scheme, an oxygen-generating function is added to the ventricular assist device, and hydrogen peroxide and catalase are used to produce oxygen. The products of the reaction are water and oxygen, which are mixed into the blood in the left ventricle to supplement the blood with oxygen. Water is also needed by the human body, so it will not cause any harm to the human body. The oxygen-rich blood in the ventricle is pumped into the aorta by the ventricular assist device, which directly improves myocardial hypoxia and helps the heart recover. On the other hand, the oxygen-rich blood is pumped into the ascending aorta and directly participates in the systemic circulation, thereby directly and quickly improving the oxygen supply of the systemic circulation.

[0019] Hydrogen peroxide undergoes a dismutation reaction with catalase:

[0020] In this way, the two The molecules encounter CAT successively and collide with the active center, and a disproportionation reaction occurs to generate two molecules and a molecular.

[0021] In addition, directly supplementing oxygen into the left ventricle will change the blood composition and pressure distribution in the ventricular cavity, thereby improving aortic regurgitation; at the same time, by precisely controlling the amount of oxygen generated, it will not affect the hemodynamics inside the heart.

[0022] The blood flow channel 20 includes a sleeve 21 and a blood inflow cage 22 and a blood outflow cage 23 fixed at both ends of the sleeve 21. A window is provided on the blood inflow cage 22 to form a blood inlet a, and a window is provided on the blood outflow cage 23 to form a bleeding outlet b. A micro-reaction chamber 40 is provided on the blood inflow cage 22. The hydrogen peroxide and catalase transported by the first delivery tube 31 and the second delivery tube 32 react chemically in the micro-reaction chamber 40 and release oxygen. The blood inflow cage 22 is located in the left ventricle, and the blood outflow cage 23 is located in the ascending aorta. The blood inflow cage 22 is made of metal and has a certain rigidity. The micro-reaction chamber 40 is fixed on the blood inflow cage 22, and the connection is firm, and the position is stable and reliable. The pumping unit 10 operates to draw the oxygen-rich blood in the left ventricle from the blood inlet a on the blood inflow cage 22 into the inner cavity of the sleeve 21, and then ejected into the aorta from the bleeding outlet b on the blood outflow cage 23.

[0023] During the delivery of hydrogen peroxide and catalase, we hope that they can be delivered at ultra-small flow rates, and that hydrogen peroxide and catalase can be quickly mixed and reacted when they reach the micro-reaction chamber 40 in the ventricle. To achieve the above purpose, the two technical solutions provided in Examples 1 and 2 are included but are not limited thereto. Example 1

[0024] See also Figure 3-Figure 6 As shown, the first delivery pipe 31 is a tube cluster composed of multiple hollow fiber tubes, and the second delivery pipe 32 is also a tube cluster composed of multiple hollow fiber tubes. The multiple hollow fiber tubes of the first delivery pipe 31 and the multiple hollow fiber tubes of the second delivery pipe 32 that are connected to the micro-reaction chamber 40 are arranged in an interlaced manner. It should be noted that the hollow fiber tubes here are non-permeable and are simply used to transport liquid. In this embodiment, the first delivery pipe 31 and the second delivery pipe 32 are themselves tube clusters composed of multiple hollow fiber tubes, which can transport trace amounts of hydrogen peroxide and catalase, and at the position of the micro-reaction chamber 40, the multiple hollow fiber tubes of the first delivery pipe 31 and the multiple hollow fiber tubes of the second delivery pipe 32 are arranged in an interlaced manner, thereby ensuring that hydrogen peroxide and catalase can be mixed evenly and react quickly to generate oxygen and water. The hollow fiber tube can adopt an ultra-small diameter hollow fiber tube with an inner diameter of 10-50um, which can transport a trace amount of solution to ensure that oxygen is generated in small amounts. While replenishing oxygen for the blood in the ventricle, it will not have an adverse effect on hemodynamics.

[0025] In order to achieve the purpose of staggered arrangement of hollow fiber tubes, the pumping unit 10 includes a motor 11 and an impeller 12. The blood outflow cage 23 is arranged on the outer periphery of the impeller 12 and is fixedly connected to the distal end of the motor 11. The proximal end of the motor 11 is connected to the extracorporeal control system through a catheter 50. A restraint 51 is arranged in the catheter 50 adjacent to the motor 11. The restraint 51 is in the shape of a circular plate, and a through hole 511 corresponding to the hollow fiber tube is opened on the circular plate. The multiple hollow fiber tubes of the first delivery tube 31 and the multiple hollow fiber tubes of the second delivery tube 32 are staggered and inserted into the through hole 511. After the rearrangement of the restraint 51, the hollow fiber tubes for conveying hydrogen peroxide and the hollow fiber tubes for conveying catalase are staggered, preferably, the single hollow fiber tube for conveying hydrogen peroxide is surrounded by hollow fiber tubes for conveying catalase, and the single hollow fiber tube for conveying catalase is surrounded by hollow fiber tubes for conveying hydrogen peroxide, so as to ensure that hydrogen peroxide and catalase are mixed evenly and react quickly. The hollow fiber tubes passing through the through hole 511 can be regarded as a whole cluster, and the outer periphery thereof is preferably coated with a film or an ultra-thin tube to minimize the outer diameter of the conveying tube 32. Since there are also optical fiber lines and flushing liquid tubes (not marked in the figure) inside the catheter 50, the restraint 51 should also be provided with corresponding through holes for these pipelines to pass through, which will not be described in detail here. Example 2

[0026] See also Figure 7-Figure 9As shown, the first delivery tube 31 and the second delivery tube 32 are single-lumen tubes, and a dispersion unit 60 is arranged between the two single-lumen tubes and the micro-reaction chamber 40. The dispersion unit 60 includes a shell 61, and a joint 62 is arranged at the proximal end of the shell 61. The inner cavity of the joint 62 is divided into two liquid storage chambers isolated from each other by a partition, and the two liquid storage chambers are respectively communicated with the first delivery tube 31 and the second delivery tube 32. A tube cluster formed by a plurality of hollow fiber tubes is arranged in the shell 61, and the proximal end of the tube cluster is communicated with the two liquid storage chambers, and the distal end is constrained in a constraint member 63 arranged at the other end of the shell 61. At the constraint member 63, the plurality of hollow fiber tubes communicated with the first delivery tube 31 and the plurality of hollow fiber tubes communicated with the second delivery tube 32 are arranged alternately, and hydrogen peroxide and catalase enter the hollow fiber tubes and enter the micro-reaction chamber 40 from the distal end of the hollow fiber tubes for chemical reaction. In this embodiment, the first delivery tube 31 and the second delivery tube 32 are single-lumen tubes, the proximal ends of which are connected to hydrogen peroxide and catalase storage tanks outside the body, and the distal ends of the single-lumen tubes disperse the liquid in the hollow fiber tubes through the dispersion unit 60 for trace and uniform delivery, and the hollow fiber tubes in the outer shell 61 are staggered to space and stagger the positions of the hollow fiber tubes for delivering hydrogen peroxide and for delivering catalase, and the purpose is to ensure that hydrogen peroxide and catalase are mixed evenly and react rapidly, that is, the single hollow fiber tube for delivering hydrogen peroxide is surrounded by hollow fiber tubes for delivering catalase, and the single hollow fiber tube for delivering catalase is surrounded by hollow fiber tubes for delivering hydrogen peroxide.

[0027] The pumping unit 10 includes a motor 11 and an impeller 12. The blood outflow cage 23 is disposed on the outer periphery of the impeller 12 and is fixedly connected to the distal end of the motor 11. The proximal end of the motor 11 is connected to the extracorporeal control system through a catheter 50. The dispersion unit 60 is disposed in the catheter 50 near the tail end of the motor 11. Considering that the dispersion unit 60 has a certain diameter, it is best not to be disposed on the pumping assembly 10 and the blood flow channel 20, so as not to increase the outer diameter of the entire device. Therefore, the dispersion unit 60 is disposed in the catheter 50 here, which will not increase the outer diameter of the entire ventricular assist device, and can also increase the strength of the catheter 50 at the tail end of the motor 11, which is beneficial to the pushing of the motor 11.

[0028] In Example 1, only a simple structural component such as a restraint 51 is required inside the catheter 50 to realize the rearrangement of the hollow fiber tubes in the first delivery tube 31 and the second delivery tube 32, which has a simple structure and is easy to assemble. In Example 2, only the inside of the catheter 50 near the motor 11 needs to be provided with a dispersion unit 60. The first delivery tube 31 and the second delivery tube 32 in the catheter 50 near the dispersion unit 60 are both single-lumen tubes with small diameters. The diameter of the catheter outside is small and has a certain degree of curvature, which can adapt to the curved path of human blood vessels. In the entire length direction of the catheter 50, only the section of the catheter where the dispersion unit 60 is provided needs to slightly increase the diameter for installing the dispersion unit 60. If the outer diameter of the dispersion unit 60 is set small enough, the diameter of the catheter section does not need to be increased, and it only needs to be consistent with the diameter of other catheter sections. However, due to the setting of the dispersion unit 60, the rigidity of the catheter 50 near the motor 11 is increased, which can better push the motor 11 and the components far from the motor.

[0029] In both Example 1 and Example 2, two clusters of hollow fiber tubes are combined into a cluster of delivery tubes 30 from the distal end of the catheter 50. Here, a cluster of delivery tubes 30 refers to two separate clusters of hollow fiber tubes that are combined into a cluster in space, and the number of hollow fiber tubes has not changed. When two clusters of hollow fiber tubes are extended distally, on the one hand, it is not convenient to arrange, and on the other hand, the space occupied by the whole is also large. When two clusters of hollow fiber tubes are combined into a cluster, it is convenient to extend and arrange distally, and the space occupied is also small. The outer wall of the delivery tube 30 can be coated to minimize its outer diameter and reduce the outer diameter of the entire auxiliary device. The delivery tube 30 reaches the blood inflow cage 22 from the outer wall of the motor 11 and the inner wall of the sleeve 21 and communicates with the micro-reaction chamber 40. The outer wall of the motor 11 is provided with a groove along its axial direction, and the delivery tube 30 is embedded in the groove and fixed with epoxy resin glue to keep the small size and surface smoothness of the motor 11 as much as possible.

[0030] How to arrange the delivery pipe 30 from the casing 21 is a problem that needs to be considered, such as Figure 10-11 As shown, the sleeve 21 includes a spring tube 211 and an inner film 212 and an outer film 213 covering the inner and outer sides of the spring tube 211. The spring tube 211 is formed by winding a shape memory wire (such as a nickel-titanium alloy wire). A channel 214 is sandwiched between the spring tube 211 and the outer film 213, and the delivery tube 30 passes through the channel 214. In this way, the delivery tube 30 passes through the inner wall of the sleeve 21, which, on the one hand, ensures the smoothness of the inner and outer walls of the sleeve 21, and on the other hand, the position of the delivery tube 30 is relatively fixed to prevent it from twisting and hindering the delivery of hydrogen peroxide and catalase. The delivery tube 30 is protected in the channel 214 to prevent the blood flow from affecting the delivery of hydrogen peroxide and catalase, thereby ensuring the quantitative and stable delivery of hydrogen peroxide and catalase.

[0031] Considering the convenience of inserting into blood vessels and the low damage to blood vessels, such as Figure 12-13 As shown, a plane is provided on the outer wall of the blood inflow cage 22 along its axial direction, and the micro-reaction chamber 40 is fixed on the plane to increase the reliability of the connection between the micro-reaction chamber 40 and the blood inflow cage 22. The outer cover of the micro-reaction chamber 40 is provided with a protective cover 41, and the outer wall of the protective cover 41 is constructed as an arc-shaped guide surface extending from the distal end to the proximal end, and the two ends of the protective cover 41 are also fixed on the plane. As shown in the figure, the distal end of the protective cover 41 of this C-shaped structure has no notch to prevent blood from directly impacting the micro-reaction chamber 40, and the two sides are open to avoid obstruction to oxygen release. A notch is provided at the proximal end for the delivery tube 30 to pass through. At the same time, the arc-shaped guide surface can guide the blood to move proximally, and its smooth outer surface can also reduce damage to blood vessels and other tissues.

[0032] Furthermore, the micro-reaction chamber 40 is a micro-channel reactor, and the diameter of the reaction channel therein is 10-100um, which ensures that the speed of generating oxygen is rapid, and the amount of oxygen generated each time is small, thereby avoiding excessive generation of oxygen and causing other adverse reactions. A diaphragm is provided at the outlet of the reactor, and the diaphragm allows oxygen and water to pass through and prevents blood from passing through.

[0033] Of course, it is obvious to those skilled in the art that the present invention is not limited to the details of the exemplary embodiments described above, but also includes the same or similar structures that can be implemented in other specific forms without departing from the spirit or essential features of the present invention. Therefore, no matter from which point of view, the embodiments should be regarded as exemplary and non-limiting, and the scope of the present invention is defined by the appended claims rather than the above description, and it is intended that all changes falling within the meaning and scope of the equivalent elements of the claims are included in the present invention. Any reference numerals in the claims should not be regarded as limiting the claims involved.

[0034] In addition, it should be understood that although the present specification is described according to implementation modes, not every implementation mode contains only one independent technical solution. This description of the specification is only for the sake of clarity. Those skilled in the art should regard the specification as a whole. The technical solutions in each embodiment may also be appropriately combined to form other implementation modes that can be understood by those skilled in the art.

Claims

1. An invasive ventricular oxygen assist device, comprising a pumping unit (10) and a blood flow channel (20), wherein the blood flow channel (20) enters the left ventricle from the ascending aorta across the aortic valve, wherein the blood inlet (a) of the blood flow channel is located in the left ventricle, and the bleeding outlet (b) is located in the ascending aorta, and wherein: The device is also provided with a first delivery tube (31) and a second delivery tube (32). The first delivery tube (31) and the second delivery tube (32) respectively deliver hydrogen peroxide and catalase and react in the left ventricle to generate oxygen and water. The oxygen is released into the blood in the left ventricle. The pumping unit (10) operates to pump the oxygen-rich blood in the left ventricle to the ascending aorta.

2. The invasive ventricular oxygen assist device according to claim 1, characterized in that: The blood flow channel (20) comprises a sleeve (21) and a blood inflow cage (22) and a blood outflow cage (23) fixed at both ends of the sleeve (21); a window is provided on the blood inflow cage (22) to form a blood inlet (a); a window is provided on the blood outflow cage (23) to form a blood outlet (b); a micro-reaction chamber (40) is provided on the blood inflow cage (22); hydrogen peroxide and catalase transported by the first transport tube (31) and the second transport tube (32) undergo a chemical reaction in the micro-reaction chamber (40) and release oxygen.

3. The invasive ventricular assist oxygen generation device according to claim 2, characterized in that: The first delivery tube (31) is in the form of a tube cluster consisting of a plurality of hollow fiber tubes, and the second delivery tube (32) is also in the form of a tube cluster consisting of a plurality of hollow fiber tubes. The plurality of hollow fiber tubes of the first delivery tube (31) and the plurality of hollow fiber tubes of the second delivery tube (32) communicating with the micro-reaction chamber (40) are arranged in an interlaced manner.

4. The invasive ventricular oxygen assist device according to claim 3, characterized in that: The pumping unit (10) comprises a motor (11) and an impeller (12); a blood outflow cage (23) is arranged on the outer periphery of the impeller (12) and is fixedly connected to the distal end of the motor (11); the proximal end of the motor (11) is connected to an extracorporeal control system via a catheter (50); the first delivery tube (31) and the second delivery tube (32) are arranged in the catheter (50) and extend distally to the left ventricle; a restraining member (51) is arranged in the catheter (50) adjacent to the motor (11); the restraining member (51) is in the shape of a circular plate, and through holes (511) corresponding to the hollow fiber tubes are opened on the circular plate; a plurality of hollow fiber tubes of the first delivery tube (31) and a plurality of hollow fiber tubes of the second delivery tube (32) are interlaced and inserted into the through holes (511).

5. The invasive ventricular assist oxygen generation device according to claim 2, characterized in that: The first delivery tube (31) and the second delivery tube (32) are single-lumen tubes. A dispersion unit (60) is arranged between the two single-lumen tubes and the micro-reaction chamber (40). The dispersion unit (60) comprises an outer shell (61). A joint (62) is arranged at the proximal end of the outer shell (61). The inner cavity of the joint (62) is divided into two mutually isolated liquid storage chambers by a partition plate. The two liquid storage chambers are respectively connected to the first delivery tube (31) and the second delivery tube (32). A tube cluster formed by a plurality of hollow fiber tubes is arranged in the outer shell (61). The proximal end of the tube cluster is connected to the two liquid storage chambers, and the distal end is constrained in a constraining member (63) arranged at the other end of the outer shell (61). At the constraining member (63), the plurality of hollow fiber tubes connected to the first delivery tube (31) and the plurality of hollow fiber tubes connected to the second delivery tube (32) are arranged in an interlaced manner. Hydrogen peroxide and catalase enter the hollow fiber tubes and enter the micro-reaction chamber (40) from the distal end of the hollow fiber tubes for reaction.

6. The invasive ventricular auxiliary oxygen generation device according to claim 5, characterized in that: The pumping unit (10) comprises a motor (11) and an impeller (12); a blood outflow cage (23) is arranged on the periphery of the impeller (12) and is fixedly connected to the distal end of the motor (11); the proximal end of the motor (11) is connected to an extracorporeal control system via a catheter (50); and the dispersion unit (60) is arranged in the inner cavity of the catheter (50) adjacent to the rear end of the motor (11).

7. The invasive ventricular auxiliary oxygen generation device according to claim 4 or 6, characterized in that: Two clusters of hollow fiber tubes are combined from the distal end of the catheter (50) to form a cluster of delivery tubes (30). The delivery tubes (30) extend from the outer wall of the motor (11) and the inner wall of the sleeve (21) to the blood inflow cage (22) and communicate with the micro-reaction chamber (40) arranged on the outer wall of the blood inflow cage (22). The outer wall of the motor (11) is provided with a groove along its axial direction, and the delivery tubes (30) are embedded in the groove and fixed with epoxy resin glue.

8. The invasive ventricular auxiliary oxygen generation device according to claim 7, characterized in that: The sleeve (21) comprises a spring tube (211) and an inner membrane (212) and an outer membrane (213) which are covered on the inner and outer sides of the spring tube (211); the spring tube (211) is formed by winding a shape memory wire; a channel (214) is sandwiched between the spring tube (211) and the outer membrane (213); and the delivery tube (30) passes through the channel (214).

9. The invasive ventricular assist oxygen generation device according to claim 7, characterized in that: A plane is provided on the outer wall of the blood inflow cage (22) along its axial direction, and the micro-reaction chamber (40) is fixed on the plane. The outer cover of the micro-reaction chamber (40) is provided with a protective cover (41), and the outer wall of the protective cover (41) is constructed as an arc-shaped guide surface extending from the distal end to the proximal end, and the two ends of the protective cover (41) are also fixed on the plane.

10. The invasive ventricular auxiliary oxygen generation device according to claim 2, characterized in that: The micro-reaction chamber (40) is a micro-channel reactor, the diameter of the reaction channel therein is 10-100 um, and a membrane is provided at the outlet of the reactor, the membrane allows oxygen and water to pass through but prevents blood from passing through.

Images