CN218922634U - Intravascular interventional catheter - Google Patents

Abstract

The utility model relates to an intravascular interventional catheter, which comprises an actuating mechanism, a displacement mechanism and an injection mechanism, wherein the actuating mechanism comprises a supporting tube and a transmission shaft movably arranged in the supporting tube, a first gap is formed between the transmission shaft and the supporting tube, the supporting tube is provided with a through hole communicated with the first gap, the displacement mechanism comprises a first tube and a second tube, the first tube is hermetically connected with the peripheral surface of the supporting tube in a manner of wrapping the through hole in the first tube, the second tube is movably sleeved on the first tube, a second gap communicated with the first gap through the through hole is formed between the first tube and the supporting tube, the second tube is provided with an injection port communicated with a tube cavity, and the injection mechanism is communicated with the injection port. According to the present utility model, an intravascular interventional catheter capable of discharging air in a displacement mechanism can be provided.

Description

Intravascular interventional catheter

Technical Field

The present utility model relates to an intravascular interventional catheter.

Background

An endovascular access catheter may be advanced to the vascular lesion area via radial or femoral artery puncture. The miniature ultrasonic transducer at the front end of the transmission shaft of the catheter can carry out ultrasonic imaging on the structural information of the lumen of the blood vessel and the section of the wall of the vessel. Before the intravascular interventional catheter enters the human body, physiological saline needs to be injected into the catheter from an injection port by using an injector, air of the intravascular interventional catheter is discharged to improve imaging quality, and the physiological saline can be used as an acoustic coupling medium required by the imaging of the miniature ultrasonic transducer.

Currently, in order to image the section structures of the lumen and the tube wall at different positions of a blood vessel, a retracting operation of a transmission shaft is required during imaging, so that a displacement mechanism linked with the transmission shaft is usually arranged in an intravascular interventional catheter to assist in retracting the transmission shaft.

The displacement mechanism is usually a telescopic component formed by a plurality of sleeved pipe bodies, however, in the imaging process of the miniature ultrasonic transducer, air in the pipe bodies can cause the phenomenon of generating bubble artifact areas in images formed by the miniature ultrasonic transducer, so that the imaging quality of the miniature ultrasonic transducer on vascular lumen and wall section structures is reduced.

Disclosure of Invention

The present utility model has been made in view of the above-described conventional circumstances, and an object thereof is to provide an intravascular interventional catheter capable of discharging air in a displacement mechanism.

To this end, the present utility model provides an intravascular interventional catheter comprising an actuator including a support tube, and a transmission shaft movably disposed within the support tube, a first gap being formed between the transmission shaft and the support tube, and the support tube having a through hole communicating with the first gap, a displacement mechanism including a first tube hermetically connected to an outer peripheral surface of the support tube in such a manner as to wrap the through hole inside, and a second tube movably sleeved to the first tube, a second gap communicating with the first gap via the through hole being formed between the first tube and the support tube, the second tube having an infusion port communicating with a lumen, and an injection mechanism communicating with the infusion port.

In the intravascular interventional catheter, air in the displacement mechanism can be discharged out of the second gap through the through hole, so that the frequency of liquid injection to the infusion port can be reduced, the complexity of operation is reduced, and the simplicity of operation is improved; in addition, the air is discharged out of the displacement mechanism, so that the probability of generating a bubble artifact region phenomenon in an image can be greatly reduced, and the influence of air on the imaging quality of the intravascular interventional catheter can be reduced.

In addition, in the endovascular interventional catheter according to the present utility model, optionally, the transmission shaft is linked with the second tube, which is moved along the lumen of the first tube to move the transmission shaft along the lumen of the support tube. Thereby, the drive shaft can be moved between different positions in the blood vessel.

In addition, in the endovascular interventional catheter according to the utility model, optionally, the actuator further comprises an actuator unit located at an end of the transmission shaft and adapted to image the blood vessel. Thereby, the morphology of the different regions of the blood vessel can be obtained by the execution unit.

In the intravascular interventional catheter according to the present utility model, the first tube may have an inner diameter substantially equal to an outer diameter of the second tube, and the first tube may be sleeved on an outer periphery of the second tube. Thereby, the second tube can be moved along the lumen of the first tube.

In the intravascular interventional catheter according to the present utility model, the displacement mechanism may further include a seal ring provided between the first tube and the second tube, and inner and outer edges of the seal ring are respectively bonded to side walls of the second tube and the first tube. In this case, the contact of the in-vivo environment with the external environment can be reduced, whereby the risk of use of the endovascular access catheter can be reduced.

In addition, in the intravascular interventional catheter according to the present utility model, optionally, the liquid enters the lumen of the second tube via the infusion port and flows into the second gap, the liquid flowing into the second gap enters the lumen of the support tube via the through hole and flows into the first gap, and the liquid in the first gap flows out via the orifice of the support tube. In this case, the air can be more conveniently discharged out of the second gap through the through hole under the extrusion of the liquid, thereby reducing the number of times of discharging the air through the injection of the liquid, further reducing the complexity of the operation and improving the simplicity of the operation; in addition, the air is discharged out of the displacement mechanism, so that the influence of the air on the imaging quality of the intravascular interventional catheter can be reduced.

In addition, in the endovascular access catheter according to the present utility model, the through-hole may be located in the vicinity of the junction of the support tube and the first tube. Thereby, it is possible to facilitate the air to flow from the second gap into the first gap.

In addition, in the intravascular interventional catheter according to the present utility model, optionally, a plurality of through holes arranged at predetermined intervals are provided on a wall of the support tube, and the plurality of through holes are one or more of circular, square, elliptical and triangular in shape. Thereby, the plurality of through holes can facilitate the air to flow from the second gap into the first gap, thereby improving the effect of exhausting the air; and the through holes can be made to have a suitable shape to facilitate the flow of air from the second gap into the first gap.

In addition, in the endovascular access catheter according to the present utility model, optionally, the diameter of the through-hole is not less than 0.2mm. Thereby, the through holes can be made to have a suitable size to facilitate the air flow from the second gap into the first gap.

In addition, in the endovascular interventional catheter according to the present utility model, the support tube may be optionally elongate tubular. Thereby, it is possible to facilitate the access of the support tube into the lumen of the blood vessel.

Thus, an intravascular interventional catheter capable of exhausting air in a displacement mechanism can be provided.

Drawings

The utility model will now be explained in further detail by way of example only with reference to the accompanying drawings, in which:

fig. 1 is a schematic diagram showing the structure of an intravascular interventional catheter according to an example of the present embodiment.

Fig. 2 is a cross-sectional view showing an intravascular interventional catheter according to an example of the present embodiment.

Fig. 3 is a cross-sectional view showing an actuator and a displacement mechanism according to an example of the present embodiment.

Fig. 4 is a cross-sectional view showing a displacement mechanism and an injection mechanism according to an example of the present embodiment.

Fig. 5 is a cross-sectional view showing an actuator and an injection mechanism according to an example of the present embodiment.

Detailed Description

Hereinafter, preferred embodiments of the present utility model will be described in detail with reference to the accompanying drawings. In the following description, the same members are denoted by the same reference numerals, and overlapping description thereof is omitted. In addition, the drawings are schematic, and the ratio of the sizes of the components to each other, the shapes of the components, and the like may be different from actual ones.

It should be noted that the terms "comprises" and "comprising," and any variations thereof, such as a process, method, system, article, or apparatus that comprises or has a list of steps or elements is not necessarily limited to those steps or elements expressly listed or inherent to such process, method, article, or apparatus, but may include or have other steps or elements not expressly listed or inherent to such process, method, article, or apparatus.

In addition, headings and the like referred to in the following description of the utility model are not intended to limit the scope or content of the utility model, but rather are merely indicative of reading. Such subtitles are not to be understood as being used for segmenting the content of the article, nor should the content under the subtitle be limited only to the scope of the subtitle.

In the present utility model, relative positional and relative directional terms such as "above", "upward", "downward", "upward-downward", "left", "leftward", "rightward", "leftward", "rightward", "front", "forward", "backward", "front-rear" and the like are used, reference is made to a normal operating posture and should not be considered limiting.

Embodiments of the present utility model relate to an intravascular interventional catheter that may be used to detect conditions of the lumen and inner wall of a blood vessel to obtain a health status of a target area of the blood vessel, thereby facilitating guidance to a physician or the like as to whether to perform some clinical therapeutic procedure, such as an interventional procedure for implantation of a cardiovascular stent. The intravascular interventional catheter according to the present embodiment can help to acquire a target vascular region such as a lumen shape and a vascular wall structure.

In some use scenarios of the endovascular access catheter according to embodiments of the present utility model, the displacement mechanism of the endovascular access catheter may be coupled to the actuator in the case where the actuator of the endovascular access catheter may be moved between different positions within the vessel to obtain different regions of the vessel. However, the displacement mechanism and the actuator, which are formed by sleeving the first tube and the second tube, form a second gap, and the air in the second gap affects the imaging quality of the intravascular interventional catheter. Based on the above, the present utility model provides an intravascular interventional catheter capable of facilitating the evacuation of air in a displacement mechanism to improve the imaging quality of the intravascular interventional catheter.

The intravascular interventional catheter according to the present embodiment may be also referred to as, for example, an interventional catheter, an ultrasound catheter, an intravascular ultrasound catheter, an IVUS catheter, an OCT catheter, an NIRS catheter, or the like. The names are used for the purpose of the present embodiment, and are not to be construed as limiting, and the device is used for the purpose of the present embodiment, such as the form of a blood vessel lumen that can reach a target position of a blood vessel and can acquire the target position, and the structure of a blood vessel wall.

Fig. 1 is a schematic diagram showing the structure of an intravascular interventional catheter 1 according to an example of the present embodiment. Fig. 2 is a cross-sectional view showing an intravascular interventional catheter 1 according to an example of the present embodiment. Fig. 3 is a cross-sectional view showing the actuator 11 and the displacement mechanism 12 according to the present embodiment example.

In some examples, the endovascular access catheter 1 may have a distal end a and a proximal end b. In operation, the distal end a of the endovascular access catheter 1 may be advanced into the lumen of a blood vessel and an operator may operate the endovascular access catheter 1 at the proximal end b of the endovascular access catheter 1.

In some examples, the endovascular access catheter 1 may include an actuator 11, a displacement mechanism 12, and an injection mechanism 13 (see fig. 1 and 2). The actuator 11 can be used to move within a vessel lumen and acquire the morphology of the vessel lumen, the structure of the vessel wall, and the like. The displacement mechanism 12 may be wrapped around the outer periphery of the actuator 11 and coupled to the actuator 11. The injection mechanism 13 may be used to infuse liquid into the actuator 11 and the displacement mechanism 12.

In some examples, the actuator 11 may include a support tube 112 and a drive shaft 111. The lumen of the support tube 112 may extend in a first direction c from the proximal end b to the distal end a. The drive shaft 111 may be movably disposed in a lumen of the support tube 112. The drive shaft 111 may be arranged along the first direction c. In some examples, the drive shaft 111 may move along the first direction c. Thereby, the drive shaft 111 can be retracted in the lumen of the support tube 112. In some examples, the support tube 112 and the drive shaft 111 may partially enter the lumen of the blood vessel when the endovascular access catheter 1 acquires the morphology of the lumen of the blood vessel. In other examples, the portion of the support tube 112 proximal to the distal end a and the portion of the drive shaft 111 proximal to the distal end a may enter the lumen of the vessel when the endovascular access catheter 1 acquires the configuration of the lumen of the vessel.

In some examples, the first gap 14 may be formed between the drive shaft 111 and the support tube 112. The first gap 14 may provide sufficient space for movement of the drive shaft 111 within the lumen of the support tube 112. In some examples, the drive shaft 111 may move in the lumen of the support tube 112 in a translational or rotational manner about an axis.

In some examples, the actuator 11 may also include an actuator unit. The execution unit may be used for imaging a blood vessel. In some examples, the execution unit may be a miniature ultrasound transducer. The actuator unit may be located at the end of the drive shaft 111 near the distal end a. In this case, the micro-ultrasonic transducer can be sent to a predetermined region of the blood vessel through the transmission shaft 111, so that the micro-ultrasonic transducer can be ultrasonically imaged while being retracted within the blood vessel, thereby obtaining an intravascular ultrasound image of the region.

In some examples, the support tube 112 may be elongate tubular. Thereby, the support tube 112 can be facilitated to enter the lumen of the blood vessel. In some examples the portion of the support tube 112 near the distal end a may be made of a material having a low acoustic impedance. Thus, the ultrasonic wave emitted from the miniature ultrasonic transducer can be facilitated to penetrate. In other examples, the portion of the support tube 112 near the proximal end b may be made of a stiffer material. Thereby, the stability of the portion near the proximal end b can be improved, and the operation is facilitated. In other examples, the stiffness of the support tube 112 may gradually increase from the distal end a to the proximal end b. In this case, the rigidity of the support pipe 112 can be uniformly increased, thereby reducing the possibility of breakage of the support pipe 112.

In some examples, the support tube 112 may be made of a rubber-plastic material or resin. Specifically, in some examples, the support tube 112 may be made of ethylene-vinyl acetate copolymer (EVA), polyetheretherketone, polyethylene, or linear low density polyethylene.

In some examples, a through hole 113 (see fig. 3) may be provided in a wall of the support tube 112. The through hole 113 may communicate with the first gap 14. In some examples, the through hole 113 may be used to communicate the first gap 14 and the second gap 15 (described in detail later). The through hole 113 may have a circular shape. In some examples, the diameter of the through hole 113 may be not less than 0.2mm. Preferably, the diameter of the through hole may be not less than 0.3mm. For example, the diameter of the through holes may be 0.32mm, 0.34mm, 0.36mm, 0.38mm or 0.4mm. In other examples, the shape of the through-hole 113 may also be square, oval, or triangular.

In some examples, the support tube 112 may have a plurality of through holes 113 disposed in a wall of the support tube. The shape of the plurality of through holes 113 may be one or more of a circle, a square, an ellipse, and a triangle. For example 2, 3, 4. In the embodiment shown in fig. 3, for example, the number of through holes 113 is 3, and the through holes 113 may include through holes 113a, 113b, and 113c. In some examples, the plurality of through holes 113 may be arranged at predetermined intervals along the radial direction of the support tube 112. In other examples, the plurality of through holes 113 may also be arranged at predetermined intervals along the axial direction of the support tube 112. In other examples, the plurality of through holes 113 may be arranged in any manner on the wall of the support tube 112.

In some examples, the through holes 113 may be formed in the side walls of the support tube 112 by laser engraving or mechanical micromachining.

In some examples, the drive shaft 111 may be a spring. In this case, the drive shaft 111 can be rotated, bent, or the like, so that the drive shaft 111 can be moved in the lumen of the blood vessel conveniently.

In some examples, the displacement mechanism 12 may include a first tube 121 and a second tube 122 (see fig. 3). The first tube 121 and the second tube 122 may be movably coupled to each other. In some examples, the first tube 121 and the second tube 122 may be hollow tubes (see fig. 3). The hollow portions of the first and second pipes 121 and 122 may be arranged along the first direction c. The first tube 121 and the second tube 122 may be sleeved on the outer circumference of the support tube 112. The first tube 121 may be disposed at a side near the distal end a. The second tube 122 may be disposed on a side near the proximal end b.

As shown in fig. 3, in some examples, the first tube 121 may wrap around the through hole 113. The first tube 121 may be hermetically connected to the support tube 112. In some examples, the first tube 121 may be hermetically connected with the outer circumferential surface of the support tube 112 in such a manner as to wrap the through-hole 113 inside. In some examples, the inner diameter of the first tube 121 may be substantially the same as the outer diameter of the second tube 122. The second tube 122 may be coupled with the drive shaft 111. In some examples, the second tube 122 may be moved along the lumen of the first tube 121 to move the drive shaft 111 along the lumen of the support tube 112. Thus, the miniature ultrasonic transducer can obtain the blood vessel morphology of different areas.

In some examples, displacement mechanism 12 may also include a seal ring 123. A sealing ring 123 may be disposed between the first pipe 121 and the second pipe 122. In some examples, the inner and outer edges of the sealing ring 123 may be respectively fitted to the sidewalls of the second tube 122 and the first tube 121. In this case, the contact of the in-vivo environment with the external environment can be reduced, whereby the risk of use of the endovascular access catheter 1 can be reduced.

In some examples, the first tube 121 may form a second gap 15 with the support tube 112 (see fig. 3). The second gap 15 may communicate with the first gap 14 via a through hole 113. In some examples, the support tube 112 may have a fluid inlet. The fluid inlet may be in communication with the lumen of the support tube 112. In some examples, the fluid inlet may be located in a lumen of the second tube 122. In some examples, the second tube 122 may have an infusion port 122a. The infusion port 122a may be in communication with a lumen of the second tube 122.

In some examples, liquid may be injected into the injection port 122a. The injected liquid may enter the lumen of the second tube 122 via the injection port 122a and flow into the second gap 15, the liquid flowing into the second gap 15 may enter the lumen of the support tube 112 via the through hole 113 and flow into the first gap 14, and the liquid in the first gap 14 may flow out of the support tube 112 via the orifice of the support tube 112. In this case, the air can be more conveniently discharged out of the second gap 15 through the through hole 113 under the extrusion of the liquid, thereby reducing the number of times of discharging the air by injecting the liquid, thereby reducing the complexity of the operation and improving the simplicity of the operation; in addition, the air is discharged out of the displacement mechanism 12, so that the influence of the air on the imaging quality of the intravascular interventional catheter 1 can be reduced.

In some examples, the through-hole 113 may be located near the connection of the support tube 112 with the first tube 121. In other words, the through hole 113 may be disposed near the distal end a. Thereby, air can be facilitated to flow from the second gap 15 into the first gap 14.

In some examples, the injected liquid may also enter the lumen of the support tube 112 via the liquid inlet after entering the lumen of the second tube 122. In other words, the first gap 14. In this case, the air in the support tube 112 can be discharged, so that the influence of the air on the imaging quality of the intravascular interventional catheter 1 can be reduced.

In some examples, the injected liquid may be heparinized saline. Thus, the required acoustic coupling medium can be provided for ultrasonic imaging by the miniature ultrasonic transducer. In other examples, the injected liquid may also be a 5% dextrose solution, amino acid, or vitamin solution.

In some examples, the first tube 121 and the second tube 122 may be made of a rubber-plastic material or resin. Specifically, in some examples, the first tube 121 and the second tube 122 may be made of ethylene-vinyl acetate copolymer (EVA), polyetheretherketone, polyethylene, or linear low density polyethylene.

Fig. 4 is a cross-sectional view showing the displacement mechanism 12 and the injection mechanism 13 according to the present embodiment example. Fig. 5 is a cross-sectional view showing the actuator 11 and the injection mechanism 13 according to the example of the present embodiment.

In some examples, the injection mechanism 13 may be tubular (see fig. 4 and 5). Injection mechanism 13 may include an injection port 131 and a docking port 132. Injection port 131 may be in communication with docking port 132. The counter interface 132 may be connected to the infusion port 122a of the second tube 122 (see fig. 4). The injected liquid may enter the endovascular access catheter 1 from the injection port 131. Thereby, the operation of discharging air can be performed by injecting the liquid into the injection port 131 of the injection mechanism 13. In some examples, the drive shaft 111 may be connected to the injection mechanism 13 (see fig. 5). The drive shaft 111 may be disposed through the lumen of the injection mechanism 13. Thereby, the transmission shaft 111 and the second tube 122 can be connected by the injection mechanism 13 so that the transmission shaft 111 and the second tube 122 are interlocked.

In some examples, the inner diameter of injection mechanism 13 may be greater than the outer diameter of second tube 122. In some examples, injection mechanism 13 may be coupled to second tube 122 in a manner that the inner diameter tapers to the outer diameter of the second tube. Thereby, the possibility of breakage at the connection of the injection mechanism 13 and the second tube 122 can be reduced.

In some examples, the injection mechanism 13 may also have a connection to the withdrawal device. This allows connection to the retraction device. In some examples, a retraction mechanism may be used to apply force to the injection mechanism and drive shaft to enable movement of the second tube 122 within the lumen of the first tube 121 and movement of the drive shaft 111 within the lumen of the support tube 112.

While the utility model has been described in detail in connection with the drawings and examples thereof, it should be understood that the foregoing description is not intended to limit the utility model in any way. Modifications and variations of the utility model may be made as desired by those skilled in the art without departing from the true spirit and scope of the utility model, and such modifications and variations fall within the scope of the utility model.

Claims (10)

1. An endovascular interventional catheter, characterized by comprising an actuating mechanism, a displacement mechanism and an injection mechanism, wherein the actuating mechanism comprises a supporting tube and a transmission shaft movably arranged in the supporting tube, a first gap is formed between the transmission shaft and the supporting tube, the supporting tube is provided with a through hole communicated with the first gap, the displacement mechanism comprises a first tube hermetically connected with the outer peripheral surface of the supporting tube in a manner of wrapping the through hole in the supporting tube, and a second tube movably sleeved on the first tube, a second gap communicated with the first gap through the through hole is formed between the first tube and the supporting tube, the second tube is provided with an infusion port communicated with a lumen of the second tube, and the injection mechanism is communicated with the infusion port.

2. The endovascular access catheter of claim 1, wherein the drive shaft is in linkage with the second tube, the second tube moving along the lumen of the first tube to move the drive shaft along the lumen of the support tube.

3. The endovascular access catheter of claim 1 or 2, wherein the actuator further comprises an actuator unit located at an end of the drive shaft and configured to image a blood vessel.

4. The endovascular access catheter of claim 1, wherein the first tube has an inner diameter that is substantially the same as an outer diameter of the second tube, the first tube being disposed about an outer circumference of the second tube.

5. The endovascular access catheter of claim 4, wherein the displacement mechanism further comprises a seal disposed between the first tube and the second tube, the seal having inner and outer edges respectively conforming to sidewalls of the second tube and the first tube.

6. The endovascular access catheter of claim 1, wherein liquid enters the lumen of the second tube via the infusion port and flows into the second gap, liquid flowing into the second gap enters the lumen of the support tube via the through-hole and flows into the first gap, and liquid in the first gap flows out of the support tube via the orifice of the support tube.

7. The endovascular access catheter of claim 1, wherein the through-hole is located near a junction of the support tube and the first tube.

8. The endovascular access catheter of claim 7, wherein a plurality of the through holes are disposed in a wall of the support tube at predetermined intervals, the plurality of through holes being one or more of circular, square, oval, and triangular in shape.

9. The endovascular access catheter of claim 1, wherein the through-hole has a diameter of no less than 0.2mm.

10. The endovascular access catheter of claim 1, wherein the support tube is elongate tubular.

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