CN115192872A - Balloon catheter and shock wave device - Google Patents
Balloon catheter and shock wave device Download PDFInfo
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- CN115192872A CN115192872A CN202210840914.3A CN202210840914A CN115192872A CN 115192872 A CN115192872 A CN 115192872A CN 202210840914 A CN202210840914 A CN 202210840914A CN 115192872 A CN115192872 A CN 115192872A
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- 230000035939 shock Effects 0.000 title claims abstract description 25
- 238000005452 bending Methods 0.000 claims abstract description 62
- 239000002184 metal Substances 0.000 claims description 15
- 238000009941 weaving Methods 0.000 claims description 12
- 238000007789 sealing Methods 0.000 claims description 5
- 239000007788 liquid Substances 0.000 claims description 4
- 210000005077 saccule Anatomy 0.000 description 5
- 208000004434 Calcinosis Diseases 0.000 description 4
- 210000004204 blood vessel Anatomy 0.000 description 4
- 230000002308 calcification Effects 0.000 description 4
- 238000009940 knitting Methods 0.000 description 4
- 230000003902 lesion Effects 0.000 description 4
- 238000007599 discharging Methods 0.000 description 3
- 208000024172 Cardiovascular disease Diseases 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000012530 fluid Substances 0.000 description 2
- 238000013467 fragmentation Methods 0.000 description 2
- 238000006062 fragmentation reaction Methods 0.000 description 2
- 210000003709 heart valve Anatomy 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 230000003068 static effect Effects 0.000 description 2
- 206010058968 Heart valve calcification Diseases 0.000 description 1
- 208000005475 Vascular calcification Diseases 0.000 description 1
- 239000011248 coating agent Substances 0.000 description 1
- 238000000576 coating method Methods 0.000 description 1
- 230000006835 compression Effects 0.000 description 1
- 238000007906 compression Methods 0.000 description 1
- 238000005336 cracking Methods 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 230000002526 effect on cardiovascular system Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000000338 in vitro Methods 0.000 description 1
- 238000009434 installation Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000036285 pathological change Effects 0.000 description 1
- 231100000915 pathological change Toxicity 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 238000007747 plating Methods 0.000 description 1
- 239000002861 polymer material Substances 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
- 230000007306 turnover Effects 0.000 description 1
- 238000003466 welding Methods 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M25/1002—Balloon catheters characterised by balloon shape
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B17/22004—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M25/1018—Balloon inflating or inflation-control devices
- A61M25/10181—Means for forcing inflation fluid into the balloon
- A61M25/10183—Compressible bulbs
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B2017/22051—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M2025/1043—Balloon catheters with special features or adapted for special applications
- A61M2025/109—Balloon catheters with special features or adapted for special applications having balloons for removing solid matters, e.g. by grasping or scraping plaque, thrombus or other matters that obstruct the flow
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- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Animal Behavior & Ethology (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- General Health & Medical Sciences (AREA)
- Biomedical Technology (AREA)
- Pulmonology (AREA)
- Hematology (AREA)
- Anesthesiology (AREA)
- Biophysics (AREA)
- Child & Adolescent Psychology (AREA)
- Surgery (AREA)
- Mechanical Engineering (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Vascular Medicine (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Media Introduction/Drainage Providing Device (AREA)
Abstract
The invention provides a balloon catheter and a shock wave device, relating to the technical field of medical instruments, wherein the balloon catheter comprises: the device comprises an inner tube, a braided sleeve and a balloon, wherein the braided sleeve comprises a sliding tube section and a braided net tube section from a near end to a far end, the braided net tube section is provided with a discharge unit, the braided net tube section is positioned on the inner side of the balloon, and the discharge unit is provided with a transmitting hole for transmitting shock waves; the far end of the mesh-woven pipe section is fixed relative to the inner pipe, the near end of the mesh-woven pipe section is connected with the far end of the sliding pipe section, and the sliding pipe section can move towards the far end along the axial direction, so that the mesh-woven pipe section is bent and deformed towards the circumferential outer side from an initial state to be in a working state; under the working condition, the bending position of the woven mesh pipe section is located between the near end and the far end of the woven mesh pipe section, the bent woven mesh pipe section comprises a first bending part located between the far end and the bending position of the woven mesh pipe section and a second bending part located between the near end and the bending position of the woven mesh pipe section, and the discharge unit is located on the first bending part.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a balloon catheter and a shock wave device.
Background
Cardiovascular diseases are always one of the important factors of death of people in the world, and the death rate of cardiovascular diseases is greatly reduced along with the development of medical knowledge and medical technology in the last half century.
In order to remove calcified focus in blood vessel, one or several pairs of discharge electrodes are set inside the saccule to constitute one shock wave generator, and the electrodes are connected via wires to the high voltage pulse power source unit in the other end of the saccule conduit. When the saccule is placed at the calcified focus in the blood vessel, the host machine applies high-voltage electric pulse to enable the pressure wave generator in the saccule to release shock waves, and the shock waves can damage the calcified focus in the blood vessel and can avoid damaging the blood vessel.
However, the shock wave balloon is limited in the pulse release direction and the acting distance when treating calcified heart valves, and therefore, a shock wave balloon catheter is needed to be used at the heart valve position.
Disclosure of Invention
The invention aims to provide a balloon catheter and a shock wave device, which are used for relieving the technical problem of poor effect of shock waves generated in the conventional balloon catheter.
In a first aspect, an embodiment of the present invention provides a balloon catheter, including: the device comprises an inner tube, a braided sleeve and a balloon which are sequentially arranged from inside to outside, wherein the braided sleeve comprises a sliding tube section and a braided net tube section from the near end to the far end, a discharge unit is arranged on the braided net tube section, the braided net tube section is positioned on the inner side of the balloon, and a transmitting hole for transmitting shock waves is formed in the discharge unit;
the far end of the mesh-woven pipe section is fixed relative to the inner pipe, the near end of the mesh-woven pipe section is connected with the far end of the sliding pipe section, and the sliding pipe section can move towards the far end along the axial direction, so that the mesh-woven pipe section is bent and deformed towards the circumferential outer side from the initial state to be in a working state;
wherein, in an initial state, the emission hole faces a circumferential outer side;
in a working state, the bending position of the woven mesh tube section is located between the near end and the far end of the woven mesh tube section, the bent woven mesh tube section comprises a first bending part located between the far end and the bending position of the woven mesh tube section and a second bending part located between the near end and the bending position of the woven mesh tube section, and the discharge unit is located on the first bending part and/or the second bending part.
Further, the balloon catheter comprises a shell, a control end connected with the near end of the sliding pipe section is arranged at the tail end of the shell, and the control end can move along the axial direction to drive the sliding pipe section to move along the axial direction.
Further, the control end is in threaded connection with the outer shell, the screwing direction of the threaded connection is consistent with the axial direction of the mesh-weaving pipe section, the control end and the sliding pipe section are relatively static in the axial direction, and the control end can freely rotate relative to the sliding pipe section;
or,
the control end is connected with the shell in a sliding mode, and the sliding direction of the control end is consistent with the axial direction of the movable sliding pipe section.
Further, the mesh-grid-knitted pipe section comprises a plurality of interwoven knitting wires, and the discharge units are fixed on the knitting wires.
Furthermore, the discharge unit comprises an outer electrode, an insulating ring and an inner electrode which are sequentially sleeved from outside to inside, the outer electrode and the insulating ring are respectively provided with a notch for forming a transmitting hole, and the outer electrode and the inner electrode are respectively connected with an external high-voltage pulse generator through leads.
Furthermore, the insulating ring is sleeved on the outer side of one weaving wire, and the weaving wire and the inner electrode are both positioned outside the insulating ring.
Furthermore, the braided wire provided with the discharge unit comprises an insulating sleeve and a metal wire positioned in the insulating sleeve, a stripping section communicated with the metal wire is arranged on the insulating sleeve, the insulating sleeve is sleeved on the outer side of the stripping section, and the metal wire forms the inner electrode.
Further, a sealing structure is arranged between the control end and the shell and used for avoiding liquid in the saccule from leaking.
Furthermore, the number of the mesh grid pipe sections is multiple, the mesh grid pipe sections are sequentially connected end to end, the far end of the mesh grid pipe section at the farthest end side is fixed relative to the inner pipe, and the near end of the mesh grid pipe section at the nearest side is connected with the far end of the sliding pipe section;
in two adjacent woven mesh pipe sections, the near end of the woven mesh pipe section close to the far side is connected with the original far end of the woven mesh pipe section close to the far side through a sliding sleeve, and the sliding sleeve is positioned outside the inner pipe and is in sliding connection with the inner pipe;
and/or, the sliding pipe section comprises a hypotube structure.
In a second aspect, embodiments of the present invention provide a shock wave device, including the balloon catheter described above.
The balloon catheter provided by the embodiment of the invention comprises: the device comprises an inner tube, a braided sleeve and a balloon which are sequentially arranged from inside to outside, wherein the braided sleeve comprises a sliding tube section and a braided net tube section from the near end to the far end, a discharge unit is arranged on the braided net tube section, the braided net tube section is positioned on the inner side of the balloon, and a transmitting hole for transmitting shock waves is formed in the discharge unit; the far end of the woven mesh pipe section is fixed relative to the inner pipe, the near end of the woven mesh pipe section is connected with the far end of the sliding pipe section, and the sliding pipe section can move towards the far end along the axial direction, so that the woven mesh pipe section is bent and deformed towards the circumferential outer side from the initial state to be in a working state; wherein, in an initial state, the emission hole faces a circumferential outer side; in a working state, the bending position of the mesh grid pipe section is located between the near end and the far end of the mesh grid pipe section, the bent mesh grid pipe section comprises a first bending portion located between the far end and the bending position of the mesh grid pipe section and a second bending portion located between the near end and the bending position of the mesh grid pipe section, and the discharge unit is located on the first bending portion and/or the second bending portion. Before use, the mesh grid pipe section is in an initial state, the discharge units on the mesh grid pipe section are close to the inner pipe, and the emission holes on the discharge units face the circumferential outer side; in use, the distal end of the balloon catheter is advanced to the site of the lesion and the balloon is inflated. The sliding pipe section is controlled to move towards the far end, so that the woven net pipe section is bent towards the outer side in the circumferential direction after being extruded and deformed, the first bending part uses the far end as a hinge point to gradually turn over towards the direction of the far end, the discharge unit on the first bending part is gradually close to the focus on the outer side in the circumferential direction, and along with the bending of the first bending part, the emission hole on the discharge unit also gradually rotates towards the direction of the far end, and the pulse expansion direction can be enabled to face towards the far end of the balloon catheter, and similarly, the discharge unit on the second bending part is gradually close to the focus on the outer side in the circumferential direction, and along with the bending of the second bending part, the emission hole on the discharge unit on the second bending part also gradually rotates towards the direction of the near end, and the pulse expansion direction can be enabled to face towards the near end of the balloon catheter. The high-voltage pulse generator in vitro is controlled, and the discharge unit releases instantaneous high-voltage pulse to the periphery, so that the aim of forward fragmentation and calcification is fulfilled.
The shock wave device provided by the embodiment of the invention comprises the balloon catheter. Because the shock wave device provided by the embodiment of the invention adopts the balloon catheter, the shock wave device provided by the embodiment of the invention also has the advantages of the balloon catheter.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the embodiments or the prior art descriptions will be briefly described below, and it is obvious that the drawings in the following description are some embodiments of the present invention, and other drawings can be obtained by those skilled in the art without creative efforts.
Fig. 1 is a schematic view of a balloon catheter provided in an embodiment of the present invention in an initial state;
fig. 2 is a schematic view of a balloon catheter provided in an embodiment of the present invention in an operating state;
FIG. 3 is a schematic view of a balloon catheter provided in an embodiment of the present invention with the braided wires in an initial state;
FIG. 4 is a schematic view of a balloon catheter according to an embodiment of the present invention with the braided wires in an operative state;
FIG. 5 is a schematic view of a mesh-woven tube segment of a balloon catheter provided in accordance with an embodiment of the present invention;
FIG. 6 is a schematic view of another braided mesh tube segment of a balloon catheter provided in accordance with embodiments of the present invention;
FIG. 7 is a cross-sectional view of a balloon catheter provided in accordance with an embodiment of the present invention (balloon not shown);
FIG. 8 is a schematic view of a discharge unit of a balloon catheter provided in accordance with an embodiment of the present invention;
FIG. 9 isbase:Sub>A cross-sectional view taken along line A-A of FIG. 8;
FIG. 10 is a partial cross-sectional view of the trailing end of a balloon catheter provided in accordance with an embodiment of the present invention (inner tube not shown);
fig. 11 is a schematic view of another discharge unit of the balloon catheter provided in the embodiment of the present invention;
FIG. 12 is a cross-sectional view taken along line B-B of FIG. 11;
fig. 13 is a schematic view of a braided sleeve of a balloon catheter provided in accordance with an embodiment of the present invention;
fig. 14 is a schematic view of another braided mesh tube segment of a balloon catheter according to an embodiment of the present invention.
Icon: 100-inner tube; 210-a sliding tube section; 211-hypotube structure; 212-a bump; 220-mesh-woven pipe sections; 221-a first bend; 222-a second bend; 223-weaving silk; 2231-metal lines; 2232-an insulating sleeve; 300-balloon;
400-discharge cell; 410-an emission aperture; 420-an outer electrode; 430-an insulating ring; 440-an inner electrode; 450-a wire;
500-a control terminal; 510-a circular rim;
600-a housing; 610-a chute; 700-guide wire.
Detailed Description
The technical solutions of the present invention will be described clearly and completely with reference to the following embodiments, and it should be understood that the described embodiments are some, but not all, embodiments of the present invention. All other embodiments, which can be obtained by a person skilled in the art without making any creative effort based on the embodiments in the present invention, belong to the protection scope of the present invention.
As shown in fig. 1 to 7, a balloon catheter provided in an embodiment of the present invention includes: an inner tube 100, a braided sleeve and a balloon 300 arranged in sequence from the inside to the outside. Wherein, the inner tube 100 is provided with a hollow hole in the middle, which is convenient for injecting liquid into the inner body or leading the guide wire 700 to pass through the guide balloon catheter to enter the body. The balloon 300 has a conventional structure, and a fluid connected to the outside is supplied to the balloon 300, and the balloon 300 is inflated by injecting the fluid into the balloon 300.
For convenience of description, one end of the balloon catheter extending into the human body is defined as a distal end, the other opposite end is defined as a proximal end, and the braided sleeve comprises a sliding pipe section 210 and a braided net pipe section 220 from the proximal end to the distal end, the braided net pipe section 220 is provided with a discharge unit 400, the braided net pipe section 220 is positioned inside the balloon 300, and the discharge unit 400 is provided with a transmitting hole 410 for transmitting shock waves; the distal end of the mesh-woven tube segment 220 is fixed relative to the inner tube 100, the proximal end of the mesh-woven tube segment 220 is connected with the distal end of the sliding tube segment 210, and the sliding tube segment 210 can move axially towards the distal end, so that the mesh-woven tube segment 220 is bent and deformed towards the circumferential outer side from the initial state to be in the working state.
In an operating state, the bending position of the mesh-woven tube segment 220 is located between the proximal end and the distal end, and the bent mesh-woven tube segment 220 includes a first bending portion 221 located between the distal end and the bending position and a second bending portion 222 located between the proximal end and the bending position, according to different patient positions, the discharge unit 400 may be located on the first bending portion 221, or on the second bending portion 222, or both the first bending portion 221 and the second bending portion 222 may be provided with the discharge unit 400.
In an initial state, the first bending part 221 and the second bending part 222 may be both disposed along the axial direction; or, the first bending portion 221 and the second bending portion 222 are disposed approximately along the axial direction, and a large-angle included angle protruding outward or a large-angle arc angle may be formed between the first bending portion and the second bending portion, so that when the sliding pipe section 210 is pushed, the connection position between the first bending portion 221 and the second bending portion 222 is deformed by moving outward, thereby bending.
As shown in fig. 5 and 6, when not in use, the proximal and distal ends of the woven mesh tube segment 220 are furthest apart, and the first and second folds 221, 222 may rest against the outside of the inner tube 100. In use, after the distal end of the balloon catheter is advanced to the lesion site, the balloon 300 is inflated by the operation. Controlling the sliding pipe section 210 to move towards the far end, so that the woven mesh pipe section 220 is bent towards the circumferential outer side after being extruded and deformed, the first bending part 221 is gradually turned towards the direction of the far end by taking the far end as a hinge point, the discharge unit 400 on the first bending part 221 is gradually close to the focus on the circumferential outer side, and the emission hole 410 on the discharge unit 400 is gradually rotated towards the direction of the far end along with the bending of the first bending part 221, and the pulse expansion direction can be towards the far end of the balloon catheter; similarly, the emitting hole 410 of the discharging unit 400 on the second bending part 222 rotates towards the proximal direction, and the pulse expanding direction can be towards the distal end and the proximal end of the balloon catheter, so as to control the external high-voltage pulse generator, and the discharging unit 400 releases the instantaneous high-voltage pulse to the periphery, thereby achieving the purpose of forward fragmentation and calcification.
Specifically, as shown in fig. 3 and 4, the direction indicated by the arrow in fig. 3 and 4 is the direction of shock wave emission, and the distance of the sliding tube section 210 moving towards the distal end is adjusted, so that the first bending part 221 can rotate and stay at different positions, the distance from the discharge unit 400 on the first bending part 221 to the lesion is also different, and the direction of the emission hole 410 on the discharge unit 400 is also different, thereby better adapting to different surgical situations.
The balloon catheter comprises a shell 600, wherein a control end 500 connected with the proximal end of the sliding tube section 210 is arranged at the tail end of the shell 600, and the control end 500 can move along the axial direction to drive the sliding tube section 210 to move along the axial direction.
Specifically, in an implementation, the control end 500 is screwed with the outer shell 600, and the screwing direction of the screwed connection is consistent with the axial direction of the braided mesh tube segment 220, the control end 500 and the sliding tube segment 210 are relatively static in the axial direction, and the control end 500 can freely rotate relative to the sliding tube segment 210. Specifically, as shown in fig. 10, an annular groove may be formed on the outer wall of the sliding pipe section 210, an annular rim 510 extending into the annular groove may be formed on the control end 500, the annular rim 510 may rotate in the annular groove, and when the control end 500 moves in the axial direction, the annular rim 510 pushes and pulls the sliding groove, thereby moving the sliding pipe section 210 in the axial direction.
In order to avoid the rotation of the sliding pipe section 210, a limiting structure may be disposed on the sliding pipe section 210 and the inner pipe 100, the limiting structure may be a protrusion 212 disposed on the outer wall of the inner pipe 100 and extending in the axial direction, and a sliding groove 610 slidably connected with the protrusion 212 and extending in the axial direction is disposed on the side wall of the sliding pipe section 210.
The control end 500 can be rotated clockwise to make the control end 500 advance spirally towards the inside of the casing 600, thereby pushing the sliding pipe section 210 to move towards the mesh weaving pipe section 220, the distance between the near end and the far end of the mesh weaving pipe section 220 is reduced, the inner side is limited by the inner pipe 100, therefore, the deformed mesh weaving pipe section 220 can only spread outwards along the circumferential direction, and the discharge unit 400 on the mesh weaving pipe section 220 can move outwards along the far end and the circumferential direction, thereby being closer to the focus. Conversely, after the control end 500 is rotated counterclockwise, the mesh-woven tube section 220 can be contracted and tightly attached to the outer side of the inner tube 100, so that the balloon catheter can be taken out conveniently.
In another embodiment, the control end 500 is slidably connected to the housing 600, and the sliding direction is the same as the axial direction of the movable sliding pipe section 210. The sliding tube 210 is driven to move back and forth by pushing and pulling the control end 500, so that the mesh-woven tube 220 is compressed or stretched.
The mesh-grid tube segment 220 includes a plurality of interlaced weaving wires 223, and the discharge unit 400 is fixed to the weaving wires 223. The plurality of knitting wires 223 can surround the inner tube 100 for one circle, the plurality of discharge units 400 can act on the focus from multiple angles, and the discharge units 400 can be fixed on the knitting wires 223 in a welding or bonding mode and are connected with the external high-voltage pulse generator through the lead 450. The braided wire can be made of shape memory metal, and can be processed into different shapes and different sizes through predeformation, so that the special requirements of different pathological change parts can be met. Meanwhile, the change of the position of the discharge electrode can be controlled by simple twisting without a special filling or control structure.
In one possible embodiment, as shown in fig. 8 and 9, the insulating ring 430 is disposed on the outside of one of the braided wires 223, the outer surface of the braided wire 223 may have an insulating coating/plating layer, and the braided wire 223 and the inner electrode 440 are disposed on the outside of the insulating ring 430. In this embodiment, the insulating ring 430 plays a role of fixing in addition to an insulating role, and the discharge cell 400 is fixed to the braid 223 by tightening the braid 223 and the internal motor with the insulating ring 430, thereby making the installation simpler.
In another possible implementation, as shown in fig. 11 and 12, the braided wire 223 provided with the discharge unit 400 includes an insulating sleeve 2232 and a metal wire 2231 located inside the insulating sleeve 2232, a stripped section connected to the metal wire 2231 is provided on the insulating sleeve 2232, the insulating ring 430 is sleeved on an outer side of the stripped section, and the metal wire 2231 forms the inner electrode 440.
The metal wires 2231 in the braid 223 form the inner electrode 440, thereby avoiding the use of additional material to make the inner electrode 440, saving material. Specifically, a length of the insulating sleeve 2232 is removed from the wire, and the insulating ring 430 made of polymer material and the metal outer electrode 420 are wrapped on the wire without the insulating sleeve 2232, and the outer electrode 420 is connected to the lead 450. The wire and lead 450 is connected to a high voltage pulse generator.
A sealing structure is arranged between the control end 500 and the housing 600, the control end 500 has a cylindrical structure which extends into the housing 600 and is in threaded connection with a screw hole at the tail of the housing 600, and an external thread is arranged on the outer wall of the cylindrical structure. The sealing structure may be a sealing ring or gasket disposed between the housing 600 and the cylindrical structure for preventing liquid leakage inside the balloon 300.
To improve the support performance of the woven mesh tube, the sliding tube section 210 may be made into a closed metal tube structure, which may include a hypotube structure 211, as shown in fig. 13; or may be a straight metal tube.
The number of the mesh grid pipe sections 220 is multiple, the mesh grid pipe sections 220 are sequentially connected end to end, the distal end of the mesh grid pipe section 220 at the farthest end side is fixed relative to the inner pipe 100, and the proximal end of the mesh grid pipe section 220 at the nearest side is connected with the distal end of the sliding pipe section 210; in two adjacent mesh-woven tube segments 220, the proximal end of the mesh-woven tube segment 220 near the distal side is connected with the original distal end of the mesh-woven tube segment 220 near the distal side by a sliding sleeve, and the sliding sleeve is located outside the inner tube 100 and is slidably connected with the inner tube 100.
As shown in fig. 14, the number of the mesh-woven tube segments 220 in the balloon may be multiple, in this embodiment, the number is two, for example, in the direction from the far side to the near side, in two adjacent mesh-woven tube segments 220, the near end of the mesh-woven tube segment 220 near the far side is connected with the original far end of the mesh-woven tube segment 220 near the far side by a sliding sleeve. After the sliding pipe section 210 moves towards the far end, the sliding sleeve also moves towards the far end, and the two mesh grid pipe sections 220 can be simultaneously extruded and then bent towards the circumferential outer side to be deformed to be in a working state. The placement positions of the discharge units 400 on the two mesh-grid segments 220 may be the same or different. When the placement positions are the same, for example, both of the first bent portions 221 are placed, which can have an effect of increasing the impact. When the positions of the discharge units are different, for example, one of the discharge units is placed on the first bending part 221 and the other one is placed on the second bending part 222, the discharge units 400 on different mesh-grid tube segments 220 can be opened according to different patient positions.
The balloon catheter provided by the embodiment can be used for a shock wave balloon catheter for treating heart valve calcification, and achieves the purpose of breaking calcification by enabling the discharge unit 400 to be better close to a lesion position and enabling the pulse to be transmitted towards the far end or the near end of the balloon catheter. The instrument can also be used for treating cardiovascular and peripheral vascular calcification diseases, and the pulse can be diffused along the circumferential direction only by controlling the tail end control end 500 and controlling the compression degree of the braided net pipe section 220, so as to achieve the purpose of cracking circumferential calcification.
The shock wave device provided by the embodiment of the invention comprises the balloon catheter. Because the shock wave device provided by the embodiment of the invention uses the balloon catheter, the shock wave device provided by the embodiment of the invention also has the advantages of the balloon catheter.
Finally, it should be noted that: the above embodiments are only used to illustrate the technical solution of the present invention, and not to limit the same; while the invention has been described in detail and with reference to the foregoing embodiments, it will be understood by those skilled in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some or all of the technical features may be equivalently replaced; and the modifications or the substitutions do not make the essence of the corresponding technical solutions depart from the scope of the technical solutions of the embodiments of the present invention.
Claims (10)
1. A balloon catheter, comprising: the medical balloon catheter comprises an inner tube (100), a braided sleeve and a balloon (300) which are sequentially arranged from inside to outside, wherein the braided sleeve comprises a sliding tube section (210) and a braided net tube section (220) from the near end to the far end, a discharge unit (400) is arranged on the braided net tube section (220), the braided net tube section (220) is positioned on the inner side of the balloon (300), and the discharge unit (400) is provided with a transmitting hole (410) for transmitting shock waves;
the far end of the woven mesh pipe section (220) is fixed relative to the inner pipe (100), the near end of the woven mesh pipe section (220) is connected with the far end of the sliding pipe section (210), and the sliding pipe section (210) can move towards the far end along the axial direction, so that the woven mesh pipe section (220) is bent towards the circumferential outer side after being extruded from the initial state and is deformed to be in a working state;
wherein, in an initial state, the emission hole (410) faces a circumferential outer side;
in a working state, the bending position of the woven mesh tube segment (220) is located between the near end and the far end of the woven mesh tube segment, the bent woven mesh tube segment (220) comprises a first bending part (221) located between the far end and the bending position of the woven mesh tube segment and a second bending part (222) located between the near end and the bending position of the woven mesh tube segment, and the discharge unit (400) is located on the first bending part (221) and/or the second bending part (222).
2. The balloon catheter according to claim 1, characterized in that the balloon catheter comprises a shell (600), the tail end of the shell (600) is provided with a control end (500) connected with the proximal end of the sliding tube section (210), and the control end (500) can move along the axial direction to drive the sliding tube section (210) to move along the axial direction.
3. The balloon catheter according to claim 2, wherein the control end (500) is screwed with the outer sheath (600) in a screwing direction corresponding to an axial direction of the mesh-woven tube segment (220), the control end (500) is relatively stationary in the axial direction with respect to the sliding tube segment (210), and the control end (500) is freely rotatable with respect to the sliding tube segment (210);
or,
the control end (500) is connected with the shell (600) in a sliding mode, and the sliding direction of the control end is consistent with the axial direction of the movable sliding pipe section (210).
4. The balloon catheter according to claim 1, wherein the braided mesh tube segment (220) comprises a plurality of interwoven braided wires (223), the discharge cells (400) being secured to the braided wires (223).
5. The balloon catheter according to claim 4, wherein the discharge unit (400) comprises an outer electrode (420), an insulating ring (430) and an inner electrode (440) which are sequentially sleeved from outside to inside, the outer electrode (420) and the insulating ring (430) are respectively provided with a notch for forming the emission hole (410), and the outer electrode (420) and the inner electrode (440) are respectively connected with an external high-voltage pulse generator through a lead (450).
6. The balloon catheter according to claim 5, wherein the insulating ring (430) is sleeved outside one of the weaving wires (223), and the weaving wire (223) and the inner electrode (440) are located outside the insulating ring (430).
7. The balloon catheter according to claim 5, wherein the braided wire (223) provided with the discharge unit (400) comprises an insulating sleeve (2232) and a metal wire (2231) positioned in the insulating sleeve (2232), the insulating sleeve (2232) is provided with a stripping section communicated with the metal wire (2231), the insulating ring (430) is sleeved outside the stripping section, and the metal wire (2231) forms the inner electrode (440).
8. The balloon catheter according to claim 2, wherein a sealing structure is provided between the control end (500) and the housing (600) for avoiding leakage of liquid inside the balloon (300).
9. The balloon catheter according to claim 1, wherein the number of the mesh-woven tube segments (220) is plural, the plurality of mesh-woven tube segments (220) are connected end to end in sequence, and a distal end of a most distal mesh-woven tube segment (220) is fixed with respect to the inner tube (100), and a proximal end of a most proximal mesh-woven tube segment (220) is connected with a distal end of a sliding tube segment (210);
in two adjacent mesh-woven pipe sections (220), the near end of the mesh-woven pipe section (220) close to the far side is connected with the original far end of the mesh-woven pipe section (220) close to the far side through a sliding sleeve, and the sliding sleeve is positioned outside the inner pipe (100) and is in sliding connection with the inner pipe (100);
and/or, the sliding pipe section (210) comprises a hypotube structure (211).
10. A shockwave device comprising a balloon catheter according to any one of claims 1-9.
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| CN202210840914.3A CN115192872B (en) | 2022-07-18 | 2022-07-18 | Balloon catheter and shock wave device |
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| CN202210840914.3A CN115192872B (en) | 2022-07-18 | 2022-07-18 | Balloon catheter and shock wave device |
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| CN115192872B CN115192872B (en) | 2023-09-26 |
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Cited By (2)
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| CN115778487A (en) * | 2023-02-02 | 2023-03-14 | 上海佳沐垚医疗科技有限公司 | Shock wave balloon catheter and catheter system for targeted therapy |
| CN117159094A (en) * | 2023-11-02 | 2023-12-05 | 苏州中荟医疗科技有限公司 | Shock wave treatment catheter and equipment thereof |
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|---|---|
| CN115192872B (en) | 2023-09-26 |
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