Interventional catheter devices

Abstract

The utility model discloses an interventional catheter device, including a pump housing, a drive shaft, an impeller and a blocking structure, wherein the pump housing is provided with a blood inlet and a blood outlet; the drive shaft is inserted into the pump housing; the impeller is provided in the pump housing and can be driven by the drive shaft to rotate and pump blood from the blood inlet to the blood outlet; the blocking structure is provided on the outside of the pump housing and covers at least a part of the blood inlet, the blocking structure is provided with a reversing flow channel, the reversing flow channel is provided with a liquid inlet and a liquid outlet, the liquid outlet is connected to the blood inlet, and the liquid inlet and the blood inlet have different directions. The utility model greatly prolongs the path length of blood entering the blood inlet, and effectively increases the difficulty of blood entering the blood inlet, and finally achieves the purpose of blocking tissue debris outside the impeller, which helps to prevent tissue debris from being entangled by the impeller during rotation, resulting in abnormal operation or functional failure of the interventional catheter device.

Description

Technical Field

[0001] The utility model relates to the technical field of medical equipment, in particular to an interventional catheter device. Background Art

[0002] Heart disease is a health problem with a high mortality rate, and doctors are increasingly using mechanical circulatory support systems to treat heart failure. Treatment of acute heart failure requires a device that can quickly provide support to the patient, and doctors want to be able to deploy treatment options quickly and minimally invasively.

[0003] Mechanical circulatory support (MCS) systems and ventricular assist devices (VADs) are gaining increasing acceptance in the treatment of acute heart failure. For example, in the treatment of acute myocardial infarction (MI) or compensated heart failure, to stabilize patients after cardiogenic shock, or to support patients during high-risk percutaneous coronary intervention (PCI). An example of an MCS system is a rotary catheter pump that is placed percutaneously via a catheter.

[0004] In conventional methods, a catheter pump is inserted into the body and connected to the cardiovascular system (e.g., connecting the left ventricle and the ascending aorta) to assist the pump function of the heart. Other known applications include pumping venous blood from the right ventricle to the pulmonary artery to support the right side of the heart. Typically, acute circulatory support devices are used to reduce the load on the myocardium for a period of time, stabilize the patient before heart transplantation, or for continuous support.

[0005] There are two types of catheter pumps. The first is an external motor catheter pump represented by CN113856036A, and the second is an internal motor catheter pump represented by CN210698361U. Among them, the motor of the external motor catheter pump is placed outside the body during operation, and the motor transmits the rotational power to the distal impeller through a slender soft shaft. The impeller of the internal motor catheter pump generally does not need to be connected to the motor with the help of the above-mentioned slender and soft drive shaft, but is connected in other ways, such as the impeller is directly connected to the motor shaft, connected to the motor shaft with the help of a short shaft, magnetic coupling connection, etc.

[0006] As described in CN115038491A, after the pump head of the catheter pump is inserted into the ventricle, the pump head may suck the blood due to the rotation of the impeller. When the blood inlet is close to the inner wall of the ventricle, the ventricle wall tissues such as chordae tendineae, trabeculae, papillary muscles, etc. may be sucked into the pump head. The above-mentioned tissue suction phenomenon may cause ventricular tissue damage, and the sucked tissue may entangle the drive shaft or even the impeller, causing the impeller to stop rotating and blood pumping failure.

[0007] Therefore, how to reduce or even avoid the risk of ventricular tissue being sucked into the pump head is a technical problem that needs to be solved urgently.

[0008] Known embodiments represented by CN115038491A, US10898629B2, US20210077676A, etc. generally solve the technical problem of ventricular tissue aspiration by setting a filter at the blood inlet or upstream of the pump head. The filter has a filter mesh for filtering the blood entering the blood inlet, thereby blocking the ventricular tissue and preventing the ventricular tissue from entering the pump housing. However, setting a filter will cause the flow area of ​​the blood inlet to decrease, resulting in difficulty in blood drainage, which is not conducive to increasing the blood flow rate of the pump. Utility Model Content

[0009] The main purpose of the utility model is to provide an interventional catheter device, which aims to solve the problem that the ventricular tissue is easily sucked into the impeller in the traditional technology, and at least partially overcome the defects of the above-mentioned prior art.

[0010] To achieve the above-mentioned purpose, the utility model provides an interventional catheter device, comprising:

[0011] A pump housing, wherein a blood inlet is provided at a distal end of the pump housing, and a blood outlet is provided at a proximal end of the pump housing;

[0012] A drive shaft is inserted into the pump housing;

[0013] an impeller, disposed in the pump housing and capable of being driven to rotate by the drive shaft to pump blood from the blood inlet to the blood outlet; and

[0014] A blocking structure is arranged on the outer side of the pump housing and covers at least a part of the blood inlet. The blocking structure is provided with a reversing flow channel, and the reversing flow channel is provided with a liquid inlet and a liquid outlet. The liquid outlet is connected to the blood inlet, and the liquid inlet and the blood inlet have different directions.

[0015] Optionally, at least at the portion covering the blood inlet, the outer surface of the blocking structure remains closed except for the liquid inlet; the liquid inlet extends radially along the pump housing and is arranged toward the proximal end of the pump housing.

[0016] Optionally, the blocking structure includes a cover shell, which is arranged at the distal end of the pump casing, and the radial inner wall of the cover shell and the radial outer wall of the pump casing jointly define the reversing flow channel; the proximal opening of the cover shell forms the liquid inlet; the cover shell is a conical setting with a radial cross-sectional area gradually decreasing from near to far.

[0017] Optionally, the radial inner wall of the cover housing abuts against a portion of the radial outer wall of the pump housing, and the abutment between the two is located at the far side of the blood inlet.

[0018] Optionally, the interventional catheter device also includes a distal bearing chamber, the distal end of the drive shaft is rotatably mounted in the distal bearing chamber, the distal end of the distal bearing chamber extends outward from the distal end of the pump housing, and the cover shell is sleeved on the radially outer side of the extended portion of the distal bearing chamber.

[0019] Optionally, the blocking structure also includes an extension cylinder, which is connected to the proximal end of the cover shell and extends toward the proximal side of the pump shell. The radial inner wall of the extension cylinder and the radial outer wall of the pump shell jointly define an extended flow channel, and the extended flow channel is connected to the reversing flow channel. The shape of the extension cylinder is adapted to the shape of the outer surface of the pump shell at its position.

[0020] Optionally, the blocking structure is entirely made of hard material.

[0021] Optionally, the blocking structure includes a support frame body and a flexible membrane covering the radial outer wall of the support frame body; the support frame body includes a proximal support ring, a distal support ring and a plurality of connecting frames connected between the proximal support ring and the distal support ring; each of the connecting frames is radially arranged with the proximal support ring as the center; and the connecting frames are made of rigid material.

[0022] Optionally, the support frame body further includes at least one reinforcing support ring concentrically arranged between the proximal support ring and the distal support ring, and the reinforcing support ring is connected to each of the connecting skeletons.

[0023] Optionally, the proximal ends and / or distal ends of each two adjacent connecting skeletons are connected in a shuttle shape to form a skeleton group, and each skeleton group is radially arranged with the proximal support ring as the center.

[0024] In the technical solution provided by the utility model, the driving shaft is driven by the motor to rotate around the distal-proximal axis, and drives the impeller to rotate, so that the blood can flow from the blood inlet through the pump casing and then be pumped toward the blood outlet to achieve the purpose of pumping blood; before this process, the blocking structure is arranged on the outer side of the pump casing and at least partially covers the blood inlet, so that before the blood and tissue debris and other fluids enter the blood inlet, they first need to flow through the blocking structure; and because the liquid inlet of the reversing flow channel in the blocking structure is in a different direction from the blood inlet, the blood and tissue debris and the like need to be reversed to the liquid inlet and flow through the reversing flow channel before they can flow to the blood inlet, which greatly extends the path length of the blood entering the blood inlet and effectively increases the difficulty of the blood entering the blood inlet, so that in this process, the tissue debris and the like are easily trapped outside the blocking structure or retained in the reversing flow channel due to mass or density, and cannot enter the blood inlet, and finally the purpose of blocking the tissue debris outside the impeller is achieved, which helps to prevent the tissue debris from being entangled by the impeller during the rotation process and causing abnormal operation or functional failure of the interventional catheter device. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] Figure 1 A three-dimensional schematic diagram of an embodiment of an interventional catheter device provided by the utility model;

[0026] Figure 2 for Figure 1 A schematic diagram of the partial structure of the working components of the interventional catheter device;

[0027] Figure 3 for Figure 1 Schematic diagram of part of the structure when the middle pump head is not equipped with a blocking structure;

[0028] Figure 4 for Figure 1 Schematic diagram of the assembly of the middle pump head and the blocking structure;

[0029] Figure 5 A three-dimensional schematic diagram of a first embodiment of a blocking structure provided by the utility model;

[0030] Figure 6 A three-dimensional schematic diagram of a second embodiment of the blocking structure provided by the utility model;

[0031] Figure 7 A schematic diagram of the near structure of the first embodiment of the support frame provided by the utility model;

[0032] Figure 8 A schematic diagram of the near structure of the second embodiment of the support frame provided by the utility model;

[0033] Fig. 9 This is a schematic diagram of the near structure of the third embodiment of the support frame provided by the utility model.

[0034] Description of Figure Numbers:

[0035] 1 catheter pump; 100 driving assembly; 110 motor housing; 200 working assembly; 211 catheter; 212 driving catheter handle; 221 proximal bearing; 222 distal bearing; 223 proximal bearing chamber; 224 distal bearing chamber; 231 stopper; 232 limiting portion; 240 protective head; 30 pump head; 310 pump housing; 311 blood inlet; 312 blood outlet; 320 bracket; 330 coating; 40 driving shaft; 410 hard shaft; 420 soft shaft; 50 impeller; 510 blade; 520 hub; 600 blocking structure; 610 reversing flow channel; 611 liquid inlet; 620 cover shell; 630 extension cylinder; 631 extension flow channel; 640 support frame; 641 proximal support ring; 642 distal support ring; 643 connecting skeleton; 644 strengthening support ring. DETAILED DESCRIPTION

[0036] The following will be combined with the drawings in the embodiments of the utility model to clearly and completely describe the technical solutions in the embodiments of the utility model. Obviously, the described embodiments are only part of the embodiments of the utility model, not all of the embodiments. Based on the embodiments of the utility model, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the utility model.

[0037] It should be noted that if the embodiments of the present invention involve directional indications (such as up, down, left, right, front, back...), the directional indications are only used to explain the relative position relationship, movement status, etc. between the components under a certain specific posture (as shown in the accompanying drawings). If the specific posture changes, the directional indication will also change accordingly.

[0038] In addition, if there are descriptions involving "first", "second", etc. in the embodiments of the utility model, the descriptions of "first", "second", etc. are only used for descriptive purposes and cannot be understood as indicating or implying their relative importance or implicitly indicating the number of technical features indicated. Therefore, the features defined as "first" and "second" may explicitly or implicitly include at least one of the features. In addition, the meaning of "and / or" appearing in the full text includes three parallel schemes. Taking "A and / or B" as an example, it includes scheme A, or scheme B, or a scheme that satisfies both A and B. In addition, the technical solutions between the various embodiments can be combined with each other, but it must be based on the ability of ordinary technicians in this field to implement. When the combination of technical solutions is contradictory or cannot be implemented, it should be deemed that such a combination of technical solutions does not exist and is not within the scope of protection required by the utility model.

[0039] See also Figures 1 to 3The utility model provides an interventional catheter device, which is, for example, an interventional catheter pump 1.

[0040] The catheter pump 1 in the embodiment of the utility model can at least partially assist the pumping function of the heart, thereby at least partially alleviating the burden on the heart. In an illustrative scenario, the catheter pump 1 can be used as a left ventricular assist, and its working part (specifically, the pump head 30) can be inserted into the left ventricle, and the pump head 30 can pump blood in the left ventricle to the ascending aorta when in operation.

[0041] It is worth noting that the above example of being used as a left ventricular assist is only one feasible application scenario of the catheter pump 1. In other feasible scenarios that cannot be explicitly excluded, the catheter pump 1 can also be used as a right ventricular assist, and the pump head 30 can be inserted into the right ventricle, and the pump head 30 pumps the blood in the vein to the right ventricle when it is in operation. Of course, the catheter pump 1 can also be used to assist the kidneys, as a renal pump.

[0042] The following mainly describes the scenario in which the catheter pump 1 is used as a left ventricular assist. However, based on the above description, it can be seen that the protection scope of the embodiment of the utility model is not limited thereto.

[0043] like Figure 1 As shown, the catheter pump 1 includes a driving assembly 100 and a working assembly 200. The driving assembly 100 includes a motor housing 110, a motor (not shown) housed in the motor housing 110, and an active member (not shown) driven by the motor. Figure 2 and Figure 3 As shown, the working assembly 200 includes a catheter 211, a drive shaft 40 passing through the catheter 211, a follower connected to the proximal end of the drive shaft 40, and a drive catheter handle 212 and a pump head 30 respectively connected to the proximal end and the distal end of the catheter 211. The pump head 30 includes a pump housing 310 having a blood inlet 311 and a blood outlet 312, and an impeller 50 housed in the pump housing 310, and the impeller 50 is connected to the distal end of the drive shaft 40. When the impeller 50 rotates, blood can be sucked into the pump housing 310 from the blood inlet 311, and then pumped out of the pump housing 310 from the blood outlet 312.

[0044] The pump housing 310 includes a support 320 and an elastic coating 330 covering the support 320. The metal lattice of the support 320 has a mesh design, and the coating 330 covers the middle and rear end of the support 320. The mesh of the front end of the support 320 that is not covered by the coating 330 forms a blood inlet 311. The rear end of the coating 330 is coated on the outside of the distal end of the catheter 211, and the blood outlet 312 is an opening formed at the rear end of the coating 330.

[0045] The impeller 50 includes a hub 520 and blades 510 supported on the outer wall of the hub 520. The blades 510 are made of a flexible material, and further form a foldable pump head 30 together with the bracket 320 and the coating 330 made of nickel and titanium memory alloy.

[0046] Of course, the pump head 30 may also be a non-foldable type. Accordingly, the pump housing 310 may be a metal sleeve that cannot be radially folded and self-expanded. The impeller 50 is also made of a hard but biocompatible material.

[0047] The driving shaft 40 includes a bendable soft shaft 420 and a hard shaft 410 connected to the distal end of the soft shaft 420. The soft shaft 420 is inserted into the catheter 211, and the hard shaft 410 is inserted into the hollow channel of the hub 520. The outer wall of the hard shaft 410 and the inner wall of the hollow channel of the hub 520 are fixed by bonding.

[0048] The proximal end and the distal end of the bracket 320 are respectively connected to the proximal bearing chamber 223 and the distal bearing chamber 224, and the proximal bearing chamber 223 and the distal bearing chamber 224 are respectively provided with a proximal bearing 221 and a distal bearing 222. The proximal end and the distal end of the hard shaft 410 are respectively penetrated in the proximal bearing 221 and the distal bearing 222. In this way, the two ends of the hard shaft 410 are supported by two bearings, and the high rigidity of the hard shaft 410 can make the impeller 50 better retained in the pump housing 310.

[0049] As in CN114225213A, the proximal bearing chamber 223 may be an additional component connected between the distal end of the catheter 211 and the bracket 320. Of course, the proximal bearing chamber 223 may also be a part of the bracket 320 structure, formed by the proximal secondary tube of the bracket 320.

[0050] The hard shaft 410 is provided with a stopper 231 located proximal to the proximal bearing 221, which is used to limit the movement of the hard shaft 410 and the impeller 50 to the distal side, and prevent the impeller 50 from moving distally due to the reverse action of the blood when rotating to pump blood. The hard shaft 410 is also provided with a limiter 232 located proximal to the stopper 231, which is used to limit the movement of the hard shaft 410 and the stopper 231 to the proximal side, and prevent the stopper 231 from wearing the distal end of the catheter 211 and causing the release of particulate matter.

[0051] A protective head 240 made of flexible material is provided at the distal end of the distal bearing chamber 224. The protective head 240 can be supported on the inner wall of the ventricle in a non-invasive or non-destructive manner to separate the blood suction inlet 311 of the pump head 30 from the inner wall of the ventricle, thereby preventing the blood suction inlet 311 from sticking to the inner wall of the ventricle due to the reaction force of the blood during the operation of the pump head 30, thereby ensuring the pumping area.

[0052] The driving catheter handle 212 and the driving assembly 100 are detachably connected, and the connection method can adopt a locking nut or a snap connection provided by US9421311B2. The driven member and the active member are non-contact coupled to transmit the rotational power of the motor to the driving shaft 40, thereby driving the impeller 50 to rotate and pump blood. As mentioned above, the driven member and the active member can adopt a magnetic coupling method such as provided by CN103120810B or CN101820933B, or a coupling method such as an eddy current coupling (Eddy Current Coupling) provided by CN216061675U or CN114452527A, which is not limited in this embodiment.

[0053] The above is a foldable catheter pump 1, and the pump housing 310 and the impeller 50 are both foldable. It is worth noting that the application scenario of the embodiment of the utility model is not limited to this. In fact, the non-foldable catheter pump 1 is also applicable to the solution of the utility model.

[0054] Similarly, the catheter pump 1 is an external motor. Based on the above, the catheter pump 1 can also adopt a motor built-in structure. In this case, the motor is connected to the distal end of the catheter 211, and the catheter 211 is no longer provided with a slender flexible drive shaft 40. The motor drives the impeller 50 through a hard short shaft, magnetic coupling, etc.

[0055] The installation method between the impeller 50 and the rigid shaft 410 affects to a certain extent whether axial movement is easy to occur between the two. For example, in the prior art, when the installation between the rigid shaft 410 and the wheel hub 520 is achieved by passing the rigid shaft 410 through the wheel hub 520, if the outer diameter of the rigid shaft 410 is smaller than the inner diameter of the wheel hub 520, it helps to facilitate the installation of the rigid shaft 410 and the wheel hub 520 to a certain extent, but it is easy to form a gap between the radial outer wall of the rigid shaft 410 and the radial inner wall of the wheel hub 520. Then, during long-term use, due to reasons such as material expansion, the gap increases, causing the impeller 50 to be axially displaced relative to the rigid shaft 410; conversely, if the outer diameter of the rigid shaft 410 is larger than the inner diameter of the wheel hub 520, it helps to reduce the probability of relative axial displacement between the rigid shaft 410 and the wheel hub 520 to a certain extent, but it is not conducive to the convenient installation of the rigid shaft 410 and the wheel hub 520.

[0056] It should be noted that the impeller 50 generally has a liquid inlet end corresponding to the blood inlet 311, and a liquid outlet end corresponding to the blood outlet 312. Since the impeller 50 can be a centrifugal impeller assembly or an axial flow impeller assembly according to its working mechanism. Among them, when the impeller 50 is a centrifugal impeller assembly, the liquid inlet end of the impeller 50 is located at its axial end, and the liquid outlet end of the impeller 50 is located at its peripheral side, so as to guide the blood to enter from its axial direction and be centrifugally thrown out through the peripheral side; and when the impeller 50 is an axial flow impeller assembly, the liquid inlet end of the impeller 50 is located at one axial end, and the liquid outlet end of the impeller 50 is located at the other axial end, so as to guide the blood to enter and exit along its axial direction.

[0057] See also Figure 4 The interventional catheter device provided by the utility model includes, in addition to the pump housing 310, the drive shaft 40 and the impeller 50 as described above, a blocking structure 600. The blocking structure 600 is arranged on the outer side of the pump housing 310 and covers the blood inlet 311. The blocking structure 600 is penetrated by a reversing flow channel 610. The reversing flow channel 610 is provided with a liquid inlet 611 and a liquid outlet. The liquid outlet is communicated with the blood inlet 311, and the liquid inlet 611 and the blood inlet 311 have different directions.

[0058] In the technical solution provided by the utility model, the driving shaft 40 is driven by the motor to rotate around the distal-proximal axis, and drives the impeller 50 to rotate, so that the blood can flow from the blood inlet 311 through the pump housing 310 and then be pumped toward the blood outlet 312 to achieve the purpose of pumping blood; before this process, the blocking structure 600 is arranged on the outer side of the pump housing 310 and covers the blood inlet 311, so that before the blood and tissue debris and other fluids enter the blood inlet 311, they first need to flow through the blocking structure 600; and because the liquid inlet 611 of the reversing flow channel 610 in the blocking structure 600 is in a different direction from the blood inlet 311, the blood and tissue debris and other fluids need to flow through the blocking structure 600. The blood can flow to the blood inlet 311 only after it changes direction to the liquid inlet 611 and flows through the reversing channel 610, which greatly prolongs the path length of the blood entering the blood inlet 311 and effectively increases the difficulty of the blood entering the blood inlet 311. As a result, in this process, tissue debris and the like are easily retained outside the blocking structure 600 or retained in the reversing channel 610 due to mass or density reasons, and cannot enter the blood inlet 311, thereby ultimately achieving the purpose of blocking the tissue debris outside the impeller 50, and helping to prevent the tissue debris from being entangled by the impeller 50 during rotation, causing abnormal operation or functional failure of the interventional catheter device.

[0059] In the present design, the blocking structure 600 is arranged on the outside of the pump housing 310: in one embodiment, the blocking structure 600 can be obtained by integrally molding with the pump housing 310, without the need for additional disassembly and assembly of the two, and the connection between the blocking structure 600 and the pump housing 310 is more stable, and the properties such as materials are more uniform and consistent; in another embodiment, the blocking structure 600 can be obtained by fixed connection or detachable connection after being separately molded from the pump housing 310. In particular, when the pump housing 310 includes a bracket 320 and a coating 330 as described above, the separately arranged blocking structure 600 and the pump housing 310 do not interfere with each other in terms of structural design. For example, the two can be made of different materials according to actual needs. The blocking structure 600 can be obtained by being separately molded from the pump housing 310 and then connected. There is no restriction on the connection scheme between the two, such as interference fit, gluing, welding, snap connection, etc.

[0060] Based on the above, in one embodiment, at least at the portion covering the blood inlet 311, the outer surface of the blocking structure 600 is kept closed except for the liquid inlet 611. It can be understood that keeping the closed setting means that at least at the portion covering the blood inlet 311, the outer surface of the blocking structure 600 is not hollowed out or drilled except for the liquid inlet 611, thereby ensuring that the blood carrying tissue debris can only enter the reversing flow channel 610 through the liquid inlet 611 and finally enter the blood inlet 311, effectively ensuring the extension of the flow path.

[0061] There is no limitation on the location of the liquid inlet 611 on the blocking structure 600. The liquid inlet 611 can be set at the distal end of the pump housing 310, the proximal end of the pump housing 310, or the middle section of the pump housing 310. The orthographic projection area of ​​the liquid inlet 611 on the pump housing 310 can be staggered with the blood inlet 311 and located on the proximal side or the distal side of the blood inlet 311, or can at least partially overlap with the blood inlet 311.

[0062] Due to the application scenario of the interventional catheter device, the radial dimensions of the pump housing 310 and the blocking structure 600 should not be set too large, which will easily increase the intervention size. Therefore, by setting the direction of the liquid inlet 611 to be different from the direction of the blood inlet 311, a reversing flow channel 610 with a different flow direction from the blood inlet 311 can be formed in a smaller space, thereby changing the direction and path length of blood flowing through the blood inlet 311.

[0063] Based on this, in order to increase the angle between the direction of the liquid inlet 611 and the direction of the blood inlet 311 as much as possible, in one embodiment, the liquid inlet 611 extends along the radial direction of the pump housing 310 and is arranged toward the proximal end of the pump housing 310. In this way, the blood flowing from the radial direction of the pump housing 310 or from the distal direction of the pump housing 310 toward the pump housing 310 needs to flow toward the proximal direction of the pump housing 310 to a certain distance, and then enter the reversing flow channel 610 from the liquid inlet 611 after a reversal of nearly 180 degrees. During this reversing process, at least part of the tissue debris will be retained outside the reversing flow channel 610 due to the influence of mass or density, effectively reducing the amount of tissue debris entering. A small amount of tissue debris entering the reversing flow channel 610 will also be trapped in the reversing flow channel 610 during the circulation process in the reversing flow channel 610 with a longer length and a changed direction. In addition, it can be understood that by setting the liquid inlet 611 toward the proximal end of the pump housing 310, larger-sized tissue debris flowing radially from the pump housing 310 or from the distal direction of the pump housing 310 toward the pump housing 310 as described above will move away along the outer surface of the blocking structure 600 and the outer surface of the pump housing 310, thereby preventing large-sized tissue debris from being driven by power to directly enter the liquid inlet 611 or the blood inlet 311, causing the liquid inlet 611 or the blood inlet 311 to be blocked.

[0064] In addition, please combine Figure 5 In one embodiment, the blocking structure 600 is a conical setting with a radial cross-sectional area gradually decreasing from near to far. In this way, a guide surface that is more suitable for blood circulation can be formed on the outer surface of the blocking structure 600. The blood and tissue debris flowing from the radial direction of the pump housing 310 or from the distal direction of the pump housing 310 toward the pump housing 310 will continue to flow smoothly toward the proximal side along the guide surface, avoiding being blocked and interfered by any protrusions on the outer surface of the blocking structure 600 during the flow process, resulting in unstable blood flow rate and uneven flow, affecting the blood pumping quality of the interventional catheter device. In addition, the conical setting of the blocking structure 600 can dampen the impact of the consumed blood on the blocking structure 600 to a certain extent, thereby ensuring that the blocking structure 600 maintains a desired shape to facilitate normal blood pumping of the interventional catheter device.

[0065] Based on any of the above embodiments, please combine Figure 5In a further embodiment, the blocking structure 600 includes a cover 620, and the cover 620 is disposed at the distal end of the pump housing 310, and the radial inner wall of the cover 620 and the radial outer wall of the pump housing 310 jointly define the reversing flow channel 610. The cover 620 has a uniform wall thickness and is provided with a recessed portion. By disposing the cover 620 at the distal end of the pump housing 310, the reversing flow channel 610 can be directly defined at the recessed portion together with the outer wall of the pump housing 310, without the need to additionally provide a groove or channel structure on the outer wall of the blocking structure 600 and / or the pump housing 310.

[0066] Specifically, the distal end of the cover 620 may be provided with a through hole, and the through hole may be sleeved on the distal end of the pump housing 310, for example, directly sleeved on the radial outer wall of the distal bearing chamber 224. Alternatively, in one embodiment, when a portion of the distal end of the distal bearing chamber 224 extends outward from the pump housing 310, and the interventional catheter device further includes a protective cover, which is disposed on the extended section of the distal bearing chamber 224, the cover 620 may be sleeved on the radial outer wall of the protective cover through the through hole.

[0067] Furthermore, in addition to the blocking structure 600 being in contact with the distal end of the pump housing 310 through, for example, the above-mentioned through-hole structure, in one embodiment, the radial inner wall of the housing 620 is in contact with a portion of the radial outer wall of the pump housing 310, and the contact point between the two is located at the distal side of the blood inlet 311. The partial contact between the radial inner wall of the housing 620 and the radial outer wall of the pump housing 310, on the one hand, helps to form another contact point between the housing 620 and the pump housing 310, helps to firmly connect the two, and to a certain extent helps to maintain the expanded shape of the housing 620; on the other hand, because the contact point between the two is at the distal side of the blood inlet 311, it can be sufficiently spaced from the reversing flow channel 610 and the blood inlet 311, and will not cause any interference with the circulation of blood, thereby ensuring the normal blood pumping of the interventional catheter device.

[0068] In addition, based on any of the above embodiments, please refer to Figure 6 In a further embodiment, the blocking structure 600 further comprises an extension cylinder 630, which is connected to the proximal end of the cover 620 and extends toward the proximal side of the pump housing 310. The radial inner wall of the extension cylinder 630 and the radial outer wall of the pump housing 310 define an extended flow channel, which is connected to the reversing flow channel 610. It can be understood that the provision of the extended flow channel helps to further extend the drainage length of the blood, thereby helping to reduce the probability of tissue debris being sucked into the pump housing 310.

[0069] Furthermore, in one embodiment, the shape of the extension cylinder 630 is adapted to the outer surface shape of the pump housing 310 at the location. That is, when the corresponding location of the pump housing 310 is cylindrical, at least the outer surface shape of the extension cylinder 630 is set to be cylindrical. In this way, it is helpful to increase the length of the extended flow channel as much as possible while reducing the space occupied by the extension cylinder 630 in the radial direction, which can reduce the increase in the intervention size of the pump housing 310.

[0070] In addition, in one embodiment, the blocking structure 600 is made of a hard material as a whole. That is, the cover 620 and / or the extension cylinder 630 are both made of a hard material. The hard material can be a metal material, a polymer material, etc. suitable for the application environment of the interventional catheter device. The hardness of the hard material is set to at least not cause unnecessary deformation during the intervention process of the interventional catheter device and the blood pumping process, resulting in abnormal operation or functional failure of the interventional catheter device.

[0071] Or in one embodiment, the blocking structure 600 includes a support frame 640 and a flexible membrane covering the radial outer wall of the support frame 640. The support frame 640 is generally configured to be made of a hard rigid material, such as a metal material, a polymer material, etc.; the flexible membrane is configured to be made of a flexible material, the thickness of which is set within a suitable range, and can produce flexible deformation to a certain extent. Furthermore, the flexible membrane can also be configured to be made of an elastic material, and with the elastic deformation ability of the elastic material, the flexible membrane can produce elastic deformation to a certain extent and also has the ability to restore deformation. In particular, when the flexible membrane covers the support frame 640, it can be fully unfolded with the elastic deformation ability of the elastic material and firmly covered on the support frame 640.

[0072] Next, in order to increase the support strength of the support frame 640:

[0073] See also Figure 7 In one embodiment, the support frame body 640 includes a proximal support ring 641 , a distal support ring 642 , and a plurality of axial skeletons 643 connected between the proximal support ring 641 and the distal support ring 642 .

[0074] The proximal support ring 641 and the distal support ring 642 are concentric rings, and the diameters of the proximal support ring 641 and the distal support ring 642 can be set to be the same. In this case, the blocking structure 600 formed by the support frame 640 and the flexible film is roughly cylindrical. Alternatively, the diameters of the proximal support ring 641 and the distal support ring 642 can be set differently, and generally, the diameter of the proximal support ring 641 is larger than the diameter of the distal support ring 642. In this case, the blocking structure 600 formed by the support frame 640 and the flexible film is roughly conical, with its cross-sectional area gradually decreasing from near to far.

[0075] Since the proximal support ring 641 and the distal support ring 642 are spaced from proximal to distal, and each axial skeleton 643 connects the proximal support ring 641 and the distal support ring 642, the axial skeleton 643 is arranged substantially along the axial extension of the pump housing 310. The axial skeleton 643 can be set as a straight rod-shaped structure or a curved rod-shaped structure that is bent at least once according to actual needs.

[0076] In one embodiment, each axial skeleton 643 is arranged at intervals along the circumference of the proximal support ring 641 / distal support ring 642. At this time, each axial skeleton 643 can be independently arranged at intervals, or at least two axial skeletons 643 are arranged crosswise along the circumference of the proximal support ring 641 / distal support ring 642. When the number of axial skeletons 643 crossing each other is large, each axial skeleton 643 is staggered in a mesh shape, which helps to increase the overall strength of the support frame body 640.

[0077] Or see Figure 7 In one embodiment, each of the axial skeletons 643 is radially arranged with the proximal support ring 641 as the center. That is, each two adjacent axial skeletons 643 are independently arranged at intervals from each other, and the connection spacing between each two adjacent axial skeletons 643 and the proximal support ring 641 is substantially the same, and the connection spacing between each two adjacent axial skeletons 643 and the distal support ring 642 is substantially the same, which helps to form a balanced and consistent structural strength in the circumferential direction of the pump housing 310.

[0078] For further information, see Figure 8In one embodiment, the support frame body 640 further includes at least one reinforcing support ring 644 concentrically disposed between the proximal support ring 641 and the distal support ring 642, and the reinforcing support ring 644 is connected to each of the axial skeletons 643. The provision of the reinforcing support ring 644 helps to increase the structural strength of each axial skeleton 643 at the suspended portion between the proximal support ring 641 and the distal support ring 642. The reinforcing support ring 644 can be provided as one or more reinforcing support rings according to actual needs, wherein when the reinforcing support ring 644 is provided as a plurality, the plurality of reinforcing support rings 644 can be arranged at equal intervals or at non-equal intervals.

[0079] Or see Fig. 9 In one embodiment, the proximal ends and / or distal ends of each two adjacent axial skeletons 643 are connected in a shuttle shape to form a skeleton group, and each skeleton group is radially arranged with the proximal support ring 641 as the center. By arranging two adjacent axial skeletons 643 in a shuttle shape, the two axial skeletons 643 in the same skeleton group can be partially bent toward each other, which helps to increase the structural strength of the skeleton group in the circumferential direction of the pump housing 310, and avoid deformation of the support frame 640 due to deformation of the axial skeleton 643, and finally deformation of the blocking structure 600, resulting in a reduction in the cross-sectional area of ​​the reversing flow channel 610 or even truncation.

[0080] The above are only preferred embodiments of the present invention, and do not limit the patent scope of the present invention. All equivalent structural changes made by using the contents of the present invention specification and drawings under the utility model concept, or directly / indirectly used in other related technical fields are included in the patent protection scope of the present invention.

Claims

1. An interventional catheter device, characterized in that: include: A pump housing, wherein a blood inlet is provided at a distal end of the pump housing, and a blood outlet is provided at a proximal end of the pump housing; A drive shaft is inserted into the pump housing; an impeller, disposed in the pump housing and capable of being driven to rotate by the drive shaft to pump blood from the blood inlet to the blood outlet; as well as, A blocking structure is arranged on the outer side of the pump housing and covers at least a part of the blood inlet. The blocking structure is provided with a reversing flow channel, and the reversing flow channel is provided with a liquid inlet and a liquid outlet. The liquid outlet is connected to the blood inlet, and the liquid inlet and the blood inlet have different directions.

2. The interventional catheter device according to claim 1, characterized in that: At least at the portion covering the blood inlet, the outer surface of the blocking structure remains closed except for the liquid inlet; the liquid inlet extends in the radial direction of the pump housing and is arranged toward the proximal end of the pump housing.

3. The interventional catheter device according to claim 1, characterized in that: The blocking structure includes a cover shell, which is arranged at the distal end of the pump housing, and the radial inner wall of the cover shell and the radial outer wall of the pump housing jointly define the reversing flow channel; the proximal opening of the cover shell forms the liquid inlet; the cover shell is a conical setting with a radial cross-sectional area gradually decreasing from near to far.

4. The interventional catheter device according to claim 3, characterized in that: The radial inner wall of the cover shell abuts against a portion of the radial outer wall of the pump shell, and the abutment between the two is located at the far side of the blood inlet.

5. The interventional catheter device according to claim 3, characterized in that: The interventional catheter device also includes a distal bearing chamber, the distal end of the drive shaft is rotatably mounted in the distal bearing chamber, the distal end of the distal bearing chamber extends outward from the distal end of the pump housing, and the cover shell is sleeved on the radially outer side of the extended portion of the distal bearing chamber.

6. The interventional catheter device according to claim 3, characterized in that: The blocking structure also includes an extension cylinder, which is connected to the proximal end of the cover shell and extends toward the proximal side of the pump shell. The radial inner wall of the extension cylinder and the radial outer wall of the pump shell jointly define an extended flow channel, and the extended flow channel is connected to the reversing flow channel. The shape of the extension cylinder is adapted to the shape of the outer surface of the pump shell at its location.

7. The interventional catheter device according to any one of claims 1 to 6, characterized in that: The blocking structure is entirely made of hard material.

8. The interventional catheter device according to any one of claims 1 to 6, characterized in that: The blocking structure includes a support frame body and a flexible membrane covering the radial outer wall of the support frame body; the support frame body includes a proximal support ring, a distal support ring and a plurality of connecting frames connected between the proximal support ring and the distal support ring; each of the connecting frames is radially arranged with the proximal support ring as the center; the connecting frames are made of rigid material.

9. The interventional catheter device according to claim 8, characterized in that: The support frame body further includes at least one reinforcing support ring concentrically arranged between the proximal support ring and the distal support ring, and the reinforcing support ring is connected to each of the connecting skeletons.

10. The interventional catheter device according to claim 9, characterized in that: The proximal ends and / or distal ends of each two adjacent connection skeletons are connected in a shuttle shape to form a skeleton group, and each skeleton group is radially arranged with the proximal support ring as the center.

Images