WO2023087198A1 - 球囊导管 - Google Patents

球囊导管 Download PDF

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Publication number
WO2023087198A1
WO2023087198A1 PCT/CN2021/131402 CN2021131402W WO2023087198A1 WO 2023087198 A1 WO2023087198 A1 WO 2023087198A1 CN 2021131402 W CN2021131402 W CN 2021131402W WO 2023087198 A1 WO2023087198 A1 WO 2023087198A1
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WO
WIPO (PCT)
Prior art keywords
electrode
balloon catheter
electrodes
insulating tube
tube
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PCT/CN2021/131402
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English (en)
French (fr)
Inventor
秦泗海
向章
陈佳
胡清
李文松
Original Assignee
科塞尔医疗科技（苏州）有限公司
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Application filed by 科塞尔医疗科技（苏州）有限公司 filed Critical 科塞尔医疗科技（苏州）有限公司
Priority to PCT/CN2021/131402 priority Critical patent/WO2023087198A1/zh
Priority to CN202180063040.9A priority patent/CN116322534A/zh
Publication of WO2023087198A1 publication Critical patent/WO2023087198A1/zh

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    • 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

Definitions

  • the invention relates to the technical field of medical instruments, in particular to a balloon catheter.
  • Vascular calcification is a common pathological manifestation of atherosclerosis, hypertension, diabetic vascular disease, vascular injury, chronic kidney disease, and aging. In recent years, affected by diet and living habits, vascular calcification has occurred There is an increasing trend year by year.
  • balloon dilatation is guided by medical imaging equipment, using precision instruments such as catheters and guide wires to send the balloon catheter into the atherosclerotic or stenotic lesion area in the human body.
  • the sac can expand and reconstruct the stenosis of blood vessels or non-vascular channels, dilate blood vessels to improve blood flow, and locally treat cardiovascular diseases and other pathological conditions in the human body.
  • For moderate or severe calcified lesions even if the inflation pressure of the balloon is high, usually 20atm-30atm, it is difficult to completely expand the calcified lesions, and it is easy to retract after expansion and cause restenosis; Mutations can easily cause blood vessel damage and rupture.
  • the density of calcified lesions is high, the drug absorption is slow, and the therapeutic effect is poor.
  • the easily disintegrated carrier is conducive to the release of the drug, it will gradually disintegrate during the drug delivery process and release the drug, resulting in the failure of the drug to reach the treatment site.
  • the dose of the drug is small, so it can’t play a therapeutic role; and the non-disintegrating carrier reduces the loss of the drug during the delivery of the balloon, but after the balloon reaches the site to be treated, the release time of the drug is longer, which leads to surgery. The prolonged time increases the risk of surgery.
  • the current balloon catheter adopts a shock wave balloon catheter with a coaxial structure of positive and negative electrodes.
  • the negative electrode is designed with a coaxial electrode structure.
  • the direction of the strongest shock wave energy is along the direction of the blood vessel, while the energy transmitted to the calcified lesion is small, and the energy utilization rate is low. increase, and the outer diameter of this electrode is large, the final size of the balloon catheter is large, and the location of vascular calcification lesions is generally narrow, and the ability of the balloon catheter with coaxial structure electrodes to pass through the lesion is reduced.
  • the coaxial electrode structure emits shock waves at random positions in the electrode circumference. For the common clinical vascular localized calcified lesions, it is necessary to increase the shock wave energy or increase the number of treatments, which increases the risk of surgery.
  • the current shock wave pulse voltage is relatively high, about 3000 volts.
  • the high voltage makes the fluid between the electrode pairs completely breakdown and discharges, and the current is large. On the one hand, it puts forward higher requirements for insulating materials and materials. When high voltage or high current passes through the human body, it will cause uncontrollable danger.
  • the present invention provides a balloon catheter, including an inner tube, an insulating tube, a balloon body, a conductive component, a conductive liquid, and at least one electrode pair, wherein:
  • the insulating tube is sleeved on the inner tube and located in the capsule, the insulating tube is made of a superhydrophobic material, and the surface water contact angle is greater than 150°;
  • the inner tube runs through the capsule, and is filled with the conductive liquid between the capsule and the capsule;
  • each electrode pair includes a first electrode and a second electrode forming positive and negative electrodes, the first electrode and the second electrode are sleeved on the insulating tube at intervals, and are respectively connected to the The conductive components are electrically connected.
  • the number of the electrode pairs is multiple, and the plurality of first electrodes and the plurality of second electrodes in the plurality of electrode pairs are connected in series; or, the plurality of electrode pairs in the plurality A plurality of first electrodes are connected in parallel, and a plurality of second electrodes are connected in parallel.
  • At least one of the first electrode and the second electrode is a protruding electrode
  • the protruding electrode includes at least one electrode protrusion protruding from the end of the insulating tube.
  • the current can be generated at the end of the insulating tube, and the distance between the two protruding electrodes is controlled to be less than 0.1mm-0.80mm.
  • the voltage can be controlled from the original 3000V high voltage to within 1000V.
  • the shock wave pulse can be greatly reduced by protruding the electrode setting and controlling the distance between the electrodes.
  • the insulating pipe is set to be set on the protruding electrode, and the plasma arc is generated at the tip using short medium frequency pulse excitation, and the pre-discharge at the protruding electrode of the insulating tube is controlled to generate seed electrons, so that the density of seed electrons around it increases, thereby forming
  • the uniform amplification of dispersion can reduce the electrode discharge voltage to within 400V.
  • the protruding electrode includes a first shaft end and a plurality of electrode protrusions, the first shaft end is sheathed on the insulating tube, and the electrode protrusions are arranged at a distance from the first shaft end. one side of the end of the insulating tube.
  • a plurality of electrodes protrude on both sides of the axis of the first shaft end.
  • a plurality of electrodes protrude from one side of the axis of the first shaft end.
  • the plurality of electrode protrusions are evenly distributed in the circumferential direction of the first shaft end.
  • the protruding electrodes include a plurality of sets of third electrodes arranged at intervals, the third electrodes include the electrode protrusions and a second shaft end, and the second shaft end is fixed on the outside of the insulating tube , the second shaft ends of each of the protruding electrodes are connected in parallel, and the electrodes protrude on a side of the second shaft ends away from the end of the insulating tube.
  • the balloon catheter further includes an outer tube, the outer tube is connected to one end of the balloon body, the conductive assembly includes a catheter base, a wire set, and an external power supply, and the wire set includes a plurality of wires , the wires are electrically connected to the first electrode or the second electrode, the catheter adapter is connected to the outer tube, and an accommodating space is formed inside, the wire group includes a plurality of wires, the The wire is electrically connected with the first electrode or the second electrode, and is connected with the external power supply through the accommodating space of the capsule body, the outer tube and the catheter adapter.
  • the tip shape of the electrode protrusion is one of rectangle, trapezoid, circular arc, and elliptical arc.
  • the interval between the first electrode and the second electrode is relatively sleeved on the insulating tube, so that the electrode pairs are arranged along the direction of the blood vessel, and the shock wave energy generated by the electrode pair diverges and propagates perpendicular to the axial direction of the blood vessel.
  • the distance between the first electrode and the second electrode is relatively sleeved on the insulating tube, so that the electrode pair is arranged along the direction of the blood vessel, the size of the electrode pair is reduced, and the overall size of the balloon catheter is reduced. Easy to pass through the lesion site.
  • the first electrode and the second electrode are set on the insulating tube so that the electrode pair is fixed on the insulating tube, reducing damage to the insulating tube, inner tube and other components when the shock wave occurs, and improving Service life of balloon catheters.
  • the above-mentioned insulating tube is made of super-hydrophobic material, which reduces the infiltration ability of the conductive liquid to the insulating tube. When the product is in operation, it is beneficial to resist the erosion of the insulating tube by the high voltage between the electrode pairs.
  • the shock wave is generated between the electrode protruding tips of the electrode pair, which improves the positional stability of the shock wave generation.
  • the shape of the tip of the protruding electrode is rectangle, trapezoid, circular arc, or elliptical arc, which can not only ensure the stability of the shock wave emission position, but also ensure that the life of the electrode pair meets the needs of actual clinical use.
  • Fig. 1 is a schematic structural view of a balloon catheter provided by the present invention
  • Fig. 2 is the working schematic diagram of a kind of balloon catheter provided by the present invention.
  • Fig. 3 is a schematic diagram of electrical connection of electrode pairs in a balloon catheter provided by the present invention.
  • FIG. 4 is a schematic diagram of electrical connection of another electrode pair in a balloon catheter provided by the present invention.
  • FIG. 5 is a schematic diagram of the distribution of electrode pairs in a balloon catheter provided by the present invention.
  • FIG. 6 is a schematic diagram of the distribution of another electrode pair in a balloon catheter provided by the present invention.
  • Fig. 7 is a schematic diagram of the distribution of another electrode pair in a balloon catheter provided by the present invention.
  • Fig. 8 is a schematic structural view of a protruding electrode in a balloon catheter provided by the present invention.
  • FIG. 9 is a schematic structural view of another protruding electrode in a balloon catheter provided by the present invention.
  • Fig. 10 is a schematic structural view of another protruding electrode in a balloon catheter provided by the present invention.
  • Fig. 11 is a schematic structural diagram of another protruding electrode in a balloon catheter provided by the present invention.
  • first and second are used for descriptive purposes only, and cannot be interpreted as indicating or implying relative importance or implicitly specifying the quantity of indicated technical features.
  • the features defined as “first” and “second” may explicitly or implicitly include at least one of these features.
  • “plurality” means at least two, such as two, three, etc., unless otherwise specifically defined.
  • the first feature may be in direct contact with the first feature or the first and second feature may be in direct contact with the second feature through an intermediary. touch.
  • “above”, “above” and “above” the first feature on the second feature may mean that the first feature is directly above or obliquely above the second feature, or simply means that the first feature is higher in level than the second feature.
  • “Below”, “beneath” and “beneath” the first feature may mean that the first feature is directly below or obliquely below the second feature, or simply means that the first feature is less horizontally than the second feature.
  • the present invention provides a balloon catheter 10, the balloon catheter 10 is used for balloon dilation to treat calcification of a blood vessel 20, the balloon catheter 10 includes an inner tube 110, an insulating tube 120, The capsule body 130, the conductive component 140, the conductive liquid 150 and at least one electrode pair 160, wherein:
  • the insulating tube 120 is sleeved on the inner tube 110, and the insulating tube 120 is located in the capsule body 130; when specifically arranged, the insulating tube 120 is a superhydrophobic material, and the specific material can be ceramics, polytetrafluoroethylene, polyimide, Phenolic resin, polyvinyl chloride, polyethylene, polypropylene, neoprene rubber, silicone resin, polyester, powder mica and derivative materials mixed with the above materials.
  • the material of the insulating tube 120 is not limited to this, and can also be other materials. Materials capable of achieving insulating support processes.
  • the surface water contact angle of the insulating tube 120 is greater than 150°, specifically, the surface water contact angle of the insulating tube 120 can be 151°, 153°, 155°, 157°, 159°, 160°, of course, the insulating tube 120
  • the surface water contact angle is not limited thereto, and may be other values within the range greater than 150°.
  • the inner tube 110 runs through the capsule 130 , and a conductive liquid 150 is filled between the inner tube 110 and the capsule 130 .
  • each electrode pair 160 includes a first electrode 161 and a second electrode 162 forming positive and negative poles, the first electrode 161 and the second electrode 162 are sleeved on the insulating tube 120 at intervals, and the first electrode 161 and the second electrode 162 are respectively electrically connected to the conductive component 140; when specifically arranged, the number of electrode pairs 160 is one, two, three, four or more than four; the first electrode in each electrode pair 160 161 can be a positive pole, and the second electrode 162 can be a negative pole, or, in each electrode pair 160, the first electrode 161 can be a negative pole, and the second electrode 162 can be a positive pole; the first electrode 161 and the second electrode 162 are arranged at intervals, and The gap between the first electrode 161 and the second electrode 162 can be 0.1mm-1mm, preferably, the gap between the first electrode 161 and the second electrode 162 is 0.1mm, 0.2mm, 0.3mm, 0.4mm, 0.5mm mm,
  • a high voltage is applied to the electrode pair 160 through the conductive component 140. Due to the hydroelectric effect and cavitation effect, a shock wave will be generated near the electrode pair 160, and the energy of the shock wave will be transmitted to the wall of the blood vessel 20 through the conductive liquid 150.
  • the calcified lesion 21 is located at the location of the calcified lesion 21, and the energy of the shock wave is used to crush the calcified lesion 21 to realize the treatment of the lesion.
  • the first electrode 161 and the second electrode 162 are sheathed on the insulating tube 120 at intervals, so that the electrode pair 160 is arranged along the direction of the blood vessel 20, on the one hand, it is ensured that the shock wave energy generated by the electrode pair 160 diverges perpendicular to the axial direction of the blood vessel 20.
  • Propagation is conducive to the transmission of shock waves to the location of calcified lesions 21, improving the crushing and processing ability of calcified lesions 21, and reducing the energy dissipated in blood vessels 20, improving the utilization rate of shock wave energy, reducing the output energy of equipment, and improving surgical safety;
  • the pair 160 is fixed on the insulating tube 120 to reduce the damage to the insulating tube 120 , the inner tube 110 and other components when the shock wave occurs, and improve the service life of the balloon catheter 10 .
  • the insulating tube 120 as a super-hydrophobic material, the infiltration ability of the conductive liquid 150 to the insulating tube 120 is reduced, and the balloon catheter 10 is beneficial to resist the erosion of the insulating tube 120 by the high voltage between the electrode pair 160 when it is in operation.
  • the sound pressure generated by the shock wave of the capsule 130 was tested with a hydrophone, and the results are shown in Table 1.
  • the sound pressure of the shock wave generated by the electrode pairs 160 arranged at intervals is 2.5 times that of the shock wave generated by the coaxial electrodes.
  • an electrode pair 160 is arranged side by side along the direction of the blood vessel 20, and the propagation direction of the generated shock wave is perpendicular to the wall of the blood vessel 20.
  • the path for the shock wave to be transmitted to the calcified lesion 21 is the shortest, and the energy dissipation is also the least.
  • the balloon catheter 10 also includes an outer tube 170, the outer tube 170 is connected to one end of the balloon body 130, the conductive component 140 includes The wire set 141 and the external power supply 142, the wire set 141 includes a plurality of wires, the wires are electrically connected to the first electrode 161 or the second electrode 162, the catheter adapter is connected to the outer tube 170, and an accommodation space is formed inside the catheter adapter, the wires
  • the group 141 includes a plurality of wires, the wires are electrically connected to the first electrode 161 or the second electrode 162 , and the wires pass through the accommodating space of the capsule 130 , the outer tube 170 and the catheter adapter to be connected to the external power source 142 .
  • the outer tube 170 leads the wire 141 from the balloon body 130 to the wire holder, and then leads out to the external power supply 142 so as to apply voltage to the first electrode 161 and the second electrode 162 .
  • the end of the balloon catheter 10 away from the catheter adapter 184 also includes a lining wire 181 and an end tube 182, the end tube 182 is inserted and connected to the balloon body 130 as a whole, and the end of the balloon catheter 10 away from the catheter adapter includes a Ring 183 , the developing ring 183 is disposed in the capsule body 130 , and the developing ring 183 is located on the inner tube 110 .
  • the number of electrode pairs 160 is multiple, and the number of electrode pairs 160 is multiple.
  • Multiple first electrodes 161 and multiple second electrodes 162 in 160 are connected in series; or, multiple first electrodes 161 in multiple electrode pairs 160 are connected in parallel, and multiple second electrodes 162 in multiple electrode pairs 160 are connected in parallel.
  • the electrodes 162 are connected in parallel.
  • all the first electrodes 161 and all the second electrodes 162 are connected in series through the first wire 1411 in the wire group 141, and then the second wire 1412, the third wire
  • the wire 1413 is electrically connected to the external power supply 142, so that multiple electrode pairs 160 can obtain high voltage at the same time, and then can synchronously generate shock waves, crush the calcified lesion 21 at the same time, and realize the treatment of the lesion quickly.
  • all the first electrodes 161 are connected in parallel with the external power supply 142 through the fourth wire 1414 in the wire group 141 respectively, and all the second electrodes 162 are respectively connected through the third wire in the wire group 141.
  • 1413 is electrically connected to the external power supply 142 after being connected in parallel, so that multiple electrode pairs 160 can generate shock waves at a lower voltage, the output energy of the equipment is reduced, and the operation safety is improved.
  • At least one of the first electrode 161 and the second electrode 162 is a protruding electrode 163, the protruding electrode 163 includes at least one electrode protrusion 1631, and the electrode protrusion 1631 is away from the end of the insulating tube 120; in a specific setting, the first electrode 161 can be the protruding electrode 163, or the second electrode 162 can be the protruding electrode 163, or the first The electrode 161 and the second electrode 162 are protruding electrodes 163 at the same time; the number of electrode protrusions 1631 in the protruding electrodes 163 can be one, two, three, four or more than four.
  • the current can be generated at the end of the insulating tube 120, and the distance between the two protruding electrodes 163 is controlled to be less than 0.1mm-0.80mm.
  • the voltage can be changed from The original 3000V high voltage is controlled within 1000V, therefore, the shock wave pulse can be greatly reduced by setting the protruding electrodes 163 and controlling the distance between the electrodes.
  • the location where the shock wave is generated is between the tip of the electrode protruding 1631 of the electrode pair 160 and another electrode or between the tips of the two electrode protruding 1631, improving The location stability of the shock wave generation is improved.
  • the insulating tube 120 is set to be set on the protruding electrode 163, and the medium-frequency short pulse is used to excite the plasma arc at the tip, and the pre-discharge at the protruding electrode of the insulating tube 120 is controlled to generate seed electrons, so that the seed electron density around it increases , so as to form a diffuse uniform amplification, which can reduce the electrode discharge voltage to within 400V.
  • the protruding electrode 163 includes a first shaft end 1632 and a plurality of electrode protrusions 1631, the first The end 1632 is sleeved on the insulating tube 120 , and the electrode protrusion 1631 is disposed on a side of the first shaft end 1632 away from the end of the insulating tube 120 .
  • the first shaft end 1632 is electrically connected to the conductive component 140
  • the first shaft end 1632 and the electrode protrusion 1631 can be an integral structure, prepared by casting, cutting and other processes, the first shaft end 1632 and the electrode protrusion
  • the 1631 can be a split structure, which is fixed as a whole by welding, screw connection and other processes.
  • the protruding electrode 163 is defined in the form of a first shaft end 1632 and a plurality of electrode protrusions 1631 , so as to facilitate the installation between the protruding electrode 163 and the insulating tube 120 .
  • the plurality of electrode protrusions 1631 are located on both sides of the axis of the first shaft end 1632, and the spacing between the teeth can be flexibly arranged uniformly or non-uniformly. arrangement.
  • a plurality of electrode protrusions 1631 can be arranged symmetrically on both sides of the axis of the first shaft end 1632, and a plurality of electrode protrusions 1631 can also be arranged asymmetrically on both sides of the axis of the first shaft end 1632; the above-mentioned balloon catheter In 10, a plurality of electrode protrusions 1631 are defined to be located on both sides of the axis of the first shaft end 1632, so that shock waves can be excited on both sides of the axis of the first shaft end 1632, so as to cut the lesion around the inner wall of the blood vessel 20.
  • the plurality of electrode protrusions 1631 are located on one side of the axis of the first shaft end 1632, so that shock waves can be excited on one side of the axis of the first shaft end 1632, so as to facilitate the
  • the lesion position on one side of the inner wall of the blood vessel 20 is cut to be suitable for the treatment of local calcified lesion 21 around the blood vessel 20.
  • the electrode position is aligned with the position of the calcified lesion 21 for delivery, and shock waves are emitted after reaching the lesion position. Shock waves The energy can be accurately and effectively released at the lesion position; of course, for a lesion with calcification in the local area around the 20th blood vessel, a single-tooth protruding electrode 163 can also be selected.
  • the plurality of electrode protrusions 1631 are evenly distributed in the circumferential direction of the first shaft end 1632, and shock waves can be generated in the circumferential direction after multiple excitations of shock waves. Shock wave, and ensure that the shock wave energy at any point in the circumference is relatively balanced, so that it is suitable for the treatment of vascular lesions with complete calcification in the 20 circumferential direction.
  • the protruding electrodes 163 There are various structural forms of the protruding electrodes 163. As shown in FIG. The protrusion 1631 and the second shaft end 1634, the second shaft end 1634 is fixed on the outer side of the insulating tube 120 through snap connection, concave-convex fit, etc., the second shaft ends of each protruding electrode 163 are connected in parallel, and the electrode protrusion 1631 is arranged on the second The shaft end 1634 is away from the side of the end of the insulating tube 120; in specific settings, the number of the third electrodes 1633 can be two groups, three groups, four groups or more than four groups, and multiple groups of third electrodes 1633 can be Evenly distributed along the circumferential direction of the insulating tube 120, of course, the distribution of multiple sets of third electrodes 1633 is not limited to this; the second shaft end 1634 and the electrode protrusion 1631 can be an integral structure, prepared by casting, cutting and other processes , The second shaft end 1634 and the electrode protrusion 1631 can be
  • the protruding electrodes 163 are defined to include multiple groups of third electrodes 1633, and the third electrodes 1633 include an electrode protrusion 1631 and a second shaft end 1634, so that the protruding electrodes 163 are arranged on the insulating tube 120. Determine the position, so as to be suitable for the disease treatment of the local calcified lesion 21 around the blood vessel 20.
  • the shape of the tip of the electrode protrusion 1631 has various forms, as shown in Figure 8, Figure 9, Figure 10 and Figure 11, a preferred embodiment, the shape of the tip of the electrode protrusion 1631 is rectangular, trapezoidal, circular arc, elliptical arc It can not only ensure the stability of the shock wave emission position, but also ensure that the life of the electrode pair 160 meets the needs of actual clinical use. Avoid using sharp or needle-shaped electrodes. High voltage will corrode the electrode tip, causing the electrode spacing to become larger. Unstable, reducing the service life of the product.
  • the tip shapes of all the electrode protrusions 1631 on the insulating tube 120 can be the same, and the tip shapes of all the electrode protrusions 1631 on the insulating tube 120 can be different.
  • Some of the electrode protrusions 1631 on the insulating tube 120 The shape of the tip is the same, but the shape of the tip of another part of the electrode protrusions 1631 can be different.
  • the shape and arrangement of the tip of the electrode protrusions 1631 are not limited to this, and other shapes and ways that can meet the requirements can also be used.

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Abstract

一种球囊导管（10），包括内管（110）、绝缘管（120）、囊体（130）、导电组件（140）、导电液（150）以及至少一电极对（160），其中：绝缘管（120）套设在内管（110）上，且位于囊体（130）内；内管（110）贯穿囊体（130），且与囊体（130）之间填充有导电液（150）；至少一个电极对（160），每一电极对（160）包括形成正负极的第一电极（161）和第二电极（162），第一电极（161）和第二电极（162）间隔相对套设在绝缘管（120）上，且分别与导电组件（140）连接；球囊导管（10）中，电极对（160）产生的冲击波能量垂直于血管（20）轴向方向发散传播，提高对钙化病变（21）的击碎处理能力，耗散于血管（20）内的能量减少，设备输出能量降低，手术安全性提高；并且减小电极对（160）尺寸，降低球囊导管（10）的外形尺寸，更容易通过病变（21）位置，减少冲击波发生时对绝缘管（120）、内管（110）等部件的损害，提高球囊导管（10）的使用寿命。

Description

球囊导管 技术领域
本发明涉及医疗器械技术领域，特别是涉及一种球囊导管。
背景技术
血管钙化(vascular calcification)是动脉粥样硬化、高血压、糖尿病血管病变、血管损伤、慢性肾病和衰老等普遍存在的共同的病理表现,近年来，受饮食、生活习惯等的影响，血管钙化发病有逐年增加的趋势。
目前，球囊扩张术是在医学影像设备的引导下，利用导管、导丝等精密器械将球囊导管送入到人体内动脉粥样硬化或是狭窄的病灶区域，通过球囊充压扩张球囊使得血管或非血管管道狭窄部位的扩张重建，扩张血管来改善血液流动，以对人体内心血管病等病态进行局部治疗。但对于中度或重度钙化病变，即使球囊充压压力较高，通常20atm～30atm，很难将钙化病变完全扩张，并且扩张后极易回缩造成再次狭窄；而采用高压扩张，血管壁压力突变，容易造成血管损伤及破裂。此外钙化病变密度大，对于药物吸收较缓慢，治疗效果差，虽然易崩解的载体有利于药物的释放，但是在药物输送的过程中就会逐渐崩解，将药物释放，导致到达治疗部位的药量较少，起不到治疗的作用；而不易崩解的载体虽降低了球囊输送过程中药物的损失，但是在球囊到达需要治疗的部位后，药物释放的时间较长，导致手术的时间延长，增加了手术的风险。
为了解决这一问题，能够实现效果更好的治疗，目前的球囊导管采用正负电极同轴结构的冲击波球囊导管，冲击波发生和传递的方向为正负极连线的垂直方向，对于正负极为同轴结构的电极设计，冲击波能量最强的方向为沿血管 方向，而传递到钙化病变位置的能量较小，能量利用率低，击碎钙化病变时，设备输出能量较大，手术风险增加，并且这种电极外径大，最终球囊导管的外形尺寸大，而血管钙化病变位置一般较狭窄，同轴结构电极的球囊导管通过病变的能力降低。并且同轴结构电极，冲击波在电极周向随机位置发射，对于临床常见的血管局部钙化病变，需要提高冲击波能量，或者增加治疗次数，增加了手术风险。
且目前冲击波脉冲电压较高，约3000伏，高电压使得电极对之间的流体完全击穿放电，电流大，一方面对绝缘材料和材质提出了较高要求，另一方面当球囊出现破损时，高电压或者高电流通过人体会产生无法控制的危险。
发明内容
基于此，有必要针对上述球囊导管所需能量较高及尺寸较大的问题，提供一种球囊导管。
本发明提供了一种球囊导管，包括内管、绝缘管、囊体、导电组件、导电液以及至少一电极对，其中：
所述绝缘管套设在所述内管上，且位于所述囊体内，所述绝缘管为超疏水性材料，表面水接触角大于150°；
所述内管贯穿所述囊体，且与所述囊体之间填充有所述导电液；
至少一个电极对，每一所述电极对包括形成正负极的第一电极和第二电极，所述第一电极和所述第二电极间隔相对套设在所述绝缘管上，且分别与所述导电组件电连接。
在其中一个实施例中，所述电极对的数目为多个，多个所述电极对中的多个第一电极、多个第二电极相串联；或，多个所述电极对中的多个第一电极相 并联，且多个第二电极相并联。
在其中一个实施例中，所述第一电极和所述第二电极中的至少一个为突出电极，所述突出电极包括至少一个电极突出，所述电极突出凸出所述绝缘管的端部。电流可以产生在绝缘管的端部，控制两个突出电极的间距小于0.1mm-0.80mm，当两个电极尖端的距离控制在0.5mm时，可以将电压从原来的3000V高压控制在1000V内，通过突出电极的设置以及控制电极之间的距离可以大幅度降低冲击波脉冲。
优选的，将绝缘管材设置为套装在突出电极上，使用中频短脉冲激励在尖端产生等离子弧，控制绝缘管的突出电极处预放电，产生种子电子，使其周围种子电子密度增大，从而形成弥散性的均匀放大，可以降低电极放电电压至400V以内。
在其中一个实施例中，所述突出电极包括第一轴端以及多个所述电极突出，所述第一轴端套设在绝缘管上，所述电极突出设置在所述第一轴端远离所述绝缘管的端部的一侧。
在其中一个实施例中，多个所述电极突出位于所述第一轴端轴线的两侧。
在其中一个实施例中，多个所述电极突出位于所述第一轴端轴线的一侧。
在其中一个实施例中，多个所述电极突出在所述第一轴端的周向均匀分布。
在其中一个实施例中，所述突出电极包括多组间隔设置的第三电极，所述第三电极包括所述电极突出以及第二轴端，所述第二轴端固定在所述绝缘管外侧，每一所述突出电极的所述第二轴端相并联，所述电极突出设置在所述第二轴端远离所述绝缘管的端部的一侧。
在其中一个实施例中，球囊导管还包括外管，所述外管连接于所述囊体的 一端，所述导电组件包括导管座、导线组以及外接电源，所述导线组包括多个导线，所述导线与所述第一电极或所述第二电极电连接，所述导管座与所述外管相连接，且内部形成有容置空间，所述导线组包括多个导线，所述导线与所述第一电极或所述第二电极电连接，且穿过所述囊体、所述外管以及所述导管座的容置空间与所述外接电源相连接。
在其中一个实施例中，所述电极突出的尖端形状为矩形、梯形、圆弧形、椭圆弧形的一种。
有益效果：
1、上述球囊导管中，通过限定第一电极和第二电极间隔相对套设在绝缘管上，以使得电极对沿血管方向排列，电极对产生的冲击波能量垂直于血管轴向方向发散传播，提高对钙化病变的击碎处理能力，耗散于血管内的能量减少，设备输出能量降低，手术安全性提高。
2、上述球囊导管中，通过限定第一电极和第二电极间隔相对套设在绝缘管上，以使得电极对沿血管方向排列，减小电极对尺寸，降低球囊导管的外形尺寸，更容易通过病变位置。
3、上述球囊导管中，通过限定第一电极和第二电极套设在绝缘管上，以使得电极对固定在绝缘管上，减少冲击波发生时对绝缘管、内管等部件的损害，提高球囊导管的使用寿命。
4、上述绝缘管为超疏水材料，降低导电液对绝缘管的浸润能力，产品工作时，有利于抵抗电极对之间高电压对绝缘管的侵蚀。
5、上述球囊导管中，通过限定第一电极和第二电极中的至少一个为突出电极，冲击波产生的位置在电极对的电极突出尖端之间，提高了冲击波发生的 位置稳定性。
6、上述突出电极的尖端形状为矩形、梯形、圆弧形、椭圆弧形，既可以保证冲击波发射位置的稳定，又可以保证电极对的寿命达到临床实际使用的需求。
附图说明
图1为本发明提供的一种球囊导管的结构示意图；
图2为本发明提供的一种球囊导管的工作示意图；
图3为本发明提供的一种球囊导管中电极对的电连接示意图；
图4为本发明提供的一种球囊导管中另一电极对的电连接示意图；
图5为本发明提供的一种球囊导管中电极对的分布示意图；
图6为本发明提供的一种球囊导管中另一电极对的分布示意图；
图7为本发明提供的一种球囊导管中再一电极对的分布示意图；
图8为本发明提供的一种球囊导管中突出电极的结构示意图；
图9为本发明提供的一种球囊导管中另一突出电极的结构示意图；
图10为本发明提供的一种球囊导管中再一突出电极的结构示意图；
图11为本发明提供的一种球囊导管中又一突出电极的结构示意图。
附图标记：
10、球囊导管；
110、内管；
120、绝缘管；
130、囊体；
140、导电组件；141、导线组；1411、第一导线；1412、第二导线； 1413、第三导线；1414、第四导线；1415、第五导线；142、外接电源；
150、导电液；
160、电极对；161、第一电极；162、第二电极；163、突出电极；1631、电极突出；1632、第一轴端；1633、第三电极；1634、第二轴端；
170、外管；
181、衬丝；182、末端管；183、显影环；184、导管座；
20、血管；21、钙化病变。
具体实施方式
为使本发明的上述目的、特征和优点能够更加明显易懂，下面结合附图对本发明的具体实施方式做详细的说明。在下面的描述中阐述了很多具体细节以便于充分理解本发明。但是本发明能够以很多不同于在此描述的其它方式来实施，本领域技术人员可以在不违背本发明内涵的情况下做类似改进，因此本发明不受下面公开的具体实施例的限制。
在本发明的描述中，需要理解的是，术语“中心”、“纵向”、“横向”、“长度”、“宽度”、“厚度”、“上”、“下”、“前”、“后”、“左”、“右”、“竖直”、“水平”、“顶”、“底”、“内”、“外”、“顺时针”、“逆时针”、“轴向”、“径向”、“周向”等指示的方位或位置关系为基于附图所示的方位或位置关系，仅是为了便于描述本发明和简化描述，而不是指示或暗示所指的装置或元件必须具有特定的方位、以特定的方位构造和操作，因此不能理解为对本发明的限制。
此外，术语“第一”、“第二”仅用于描述目的，而不能理解为指示或暗示相对重要性或者隐含指明所指示的技术特征的数量。由此，限定有“第一”、“第二”的特征可以明示或者隐含地包括至少一个该特征。在本发明的描述 中，“多个”的含义是至少两个，例如两个，三个等，除非另有明确具体的限定。
在本发明中，除非另有明确的规定和限定，术语“安装”、“相连”、“连接”、“固定”等术语应做广义理解，例如，可以是固定连接，也可以是可拆卸连接，或成一体；可以是机械连接，也可以是电连接；可以是直接相连，也可以通过中间媒介间接相连，可以是两个元件内部的连通或两个元件的相互作用关系，除非另有明确的限定。对于本领域的普通技术人员而言，可以根据具体情况理解上述术语在本发明中的具体含义。
在本发明中，除非另有明确的规定和限定，第一特征在第二特征“上”或“下”可以是第一和第二特征直接接触，或第一和第二特征通过中间媒介间接接触。而且，第一特征在第二特征“之上”、“上方”和“上面”可是第一特征在第二特征正上方或斜上方，或仅仅表示第一特征水平高度高于第二特征。第一特征在第二特征“之下”、“下方”和“下面”可以是第一特征在第二特征正下方或斜下方，或仅仅表示第一特征水平高度小于第二特征。
需要说明的是，当元件被称为“固定于”或“设置于”另一个元件，它可以直接在另一个元件上或者也可以存在居中的元件。当一个元件被认为是“连接”另一个元件，它可以是直接连接到另一个元件或者可能同时存在居中元件。本文所使用的术语“垂直的”、“水平的”、“上”、“下”、“左”、“右”以及类似的表述只是为了说明的目的，并不表示是唯一的实施方式。
下面结合附图介绍本发明实施例提供的技术方案。
如图1以及图2所示，本发明提供了一种球囊导管10，该球囊导管10用于球囊扩张术治疗血管20钙化，该球囊导管10包括内管110、绝缘管120、囊体130、导电组件140、导电液150以及至少一电极对160这几部分，其 中：
绝缘管120套设在内管110上，并且绝缘管120位于囊体130内；在具体设置时，绝缘管120为超疏水材料，具体材料可以为陶瓷、聚四氟乙烯、聚酰亚胺、酚醛树脂、聚氯乙烯、聚乙烯、聚丙烯、氯丁橡胶、硅树脂、聚酯、粉云母和以上材料混合的衍生材料，当然，绝缘管120的材料并不局限于此，还可以为其他能够实现绝缘支撑过程的材质。并且绝缘管120的表面水接触角大于150°，具体地，绝缘管120的表面水接触角可以为151°、153°、155°、157°、159°、160°，当然，绝缘管120的表面水接触角并不局限于此，还可以为大于150°这一范围内的其他数值。
内管110贯穿囊体130，并且内管110与囊体130之间填充有导电液150。
至少一个电极对160，每一电极对160包括形成正负极的第一电极161和第二电极162，第一电极161和第二电极162间隔相对套设在绝缘管120上，并且第一电极161和第二电极162分别与导电组件140电连接；在具体设置时，电极对160的数目为一个、两个、三个、四个或是四个以上；每一电极对160中第一电极161可以为正极、第二电极162可以为负极，或者，每一电极对160中第一电极161可以为负极、第二电极162可以为正极；第一电极161和第二电极162间隔设置，第一电极161和第二电极162之间的间隙可以为0.1mm-1mm，较佳地，第一电极161和第二电极162之间的间隙为0.1mm、0.2mm、0.3mm、0.4mm、0.5mm、0.6mm、0.7mm、0.8mm、0.9mm、1mm，当然第一电极161和第二电极162之间的间隙并不局限与上述范围值，还可以为其他满足间隔要求的数值。
上述球囊导管10中，通过导电组件140对电极对160施加高压电压，由 于液电效应和空化效应，在电极对160附近会产生冲击波，冲击波的能量通过导电液150体传递到血管20壁钙化病变21位置，利用冲击波的能量将钙化病变21击碎，实现病变部位的治疗。而由于第一电极161和第二电极162间隔相对套设在绝缘管120上，以使得电极对160沿血管20方向排列，一方面确保电极对160产生的冲击波能量垂直于血管20轴向方向发散传播，有利于冲击波传递到钙化病变21位置，提高对钙化病变21的击碎处理能力，并且耗散于血管20内的能量减少，提高冲击波能量利用率，设备输出能量降低，手术安全性提高；另一方面，能够减小电极对160尺寸，降低球囊导管10的外形尺寸，更容易通过病变位置；并且通过限定第一电极161和第二电极162套设在绝缘管120上，以使得电极对160固定在绝缘管120上，减少冲击波发生时对绝缘管120、内管110等部件的损害，提高球囊导管10的使用寿命。另外，通过限定绝缘管120为超疏水材料，降低导电液150对绝缘管120的浸润能力，球囊导管10工作时，有利于抵抗电极对160之间高电压对绝缘管120的侵蚀。
采用水听器测试囊体130冲击波所产生的声压，结果如表1，电极对160间隔相对排列产生的冲击波声压为同轴电极产生冲击波声压的2.5倍。
表1电极不同排列方式球囊表面的冲击波声压
Figure PCTCN2021131402-appb-000001
通过上述表格数据可以得知，一个电极对160沿血管20方向并列排列，产生的冲击波的传播方向为垂直于血管20壁，冲击波传递到钙化病变21位置 的路径最短，能量耗散也最少。
导电组件140的结构形式具有多种，如图1以及图2所示，一种优选实施方式，球囊导管10还包括外管170，外管170连接于囊体130的一端，导电组件140包括导线组141以及外接电源142，导线组141包括多个导线，导线与第一电极161或第二电极162电连接，导管座与外管170相连接，并且导管座内部形成有容置空间，导线组141包括多个导线，导线与第一电极161或第二电极162电连接，并且导线穿过囊体130、外管170以及导管座的容置空间与外接电源142相连接。
上述球囊导管10中，外管170将导线141从囊体130内引出至导线座，进而引出外接到外接电源142上，以便于对第一电极161、第二电极162施加电压。在具体设置时，球囊导管10远离导管座184的一端还包括衬丝181、末端管182，末端管182插入并于囊体130连接为一体，球囊导管10远离导管座的一端包括由显影环183，该显影环183设置在囊体130内，并且该显影环183位于内管110上。
为了便于实现第一电极161、第二电极162与导电组件140之间的电连接，如图3以及图4所示，一种优选实施方式，电极对160的数目为多个，多个电极对160中的多个第一电极161、多个第二电极162相串联；或者，多个电极对160中的多个第一电极161相并联，并且同时多个电极对160中的多个第二电极162相并联。
上述球囊导管10中，多个电极对160中，所有的第一电极161、所有的第二电极162之间通过导线组141中的第一导线1411串联之后再通过第二导线1412、第三导线1413与外接电源142电连接，以使得多个电极对160同时获得高压电压，进而能够同步产生冲击波，同时击碎钙化病变21，以快速实现病 变位置的治疗。多个电极对160中，所有的第一电极161分别通过导线组141中的第四导线1414并联后与外接电源142相电连接，所有的第二电极162分别通过导线组141中的第三导线1413并联后与外接电源142电连接，以使得多个电极对160在较低电压下能够产生冲击波，设备输出能量降低，手术安全性提高。
为了提高冲击波发生的位置稳定性，如图3、图4、图5以及图6所示，一种优选实施方式，第一电极161和第二电极162中的至少一个为突出电极163，突出电极163包括至少一个电极突出1631，电极突出1631远离绝缘管120的端部；在具体设置时，第一电极161可以为突出电极163，或者，第二电极162可以为突出电极163，或者，第一电极161和第二电极162同时为突出电极163；突出电极163中电极突出1631的数目可以为一个、两个、三个、四个或是四个以上。上述球囊导管10中，电流可以产生在绝缘管120的端部，控制两个突出电极163的间距小于0.1mm-0.80mm，当两个电极尖端的距离控制在0.5mm时，可以将电压从原来的3000V高压控制在1000V内，因此，通过突出电极163的设置以及控制电极之间的距离可以大幅度降低冲击波脉冲。通过限定第一电极161和第二电极162中的至少一个为突出电极163，冲击波产生的位置在电极对160的电极突出1631尖端和另一电极之间或是两个电极突出1631尖端之间，提高了冲击波发生的位置稳定性。优选的，将绝缘管120设置为套装在突出电极163上，使用中频短脉冲激励在尖端产生等离子弧，控制绝缘管120的突出电极处预放电，产生种子电子，使其周围种子电子密度增大，从而形成弥散性的均匀放大，可以降低电极放电电压至400V以内。
突出电极163的结构形式具有多种，一种优选实施方式，如图3、图4、图5以及图6所示，突出电极163包括第一轴端1632以及多个电极突出 1631，第一轴端1632套设在绝缘管120上，电极突出1631设置在第一轴端1632远离绝缘管120的端部的一侧。在具体设置时，第一轴端1632与导电组件140之间电连接，第一轴端1632和电极突出1631可以为一体式结构，通过铸造、切割等工艺制备，第一轴端1632和电极突出1631之间可以为分体式结构，通过焊接、螺纹连接等工艺固定为一体。上述球囊导管10中，通过限定突出电极163的形式为一个第一轴端1632和多个电极突出1631，以便于突出电极163与绝缘管120之间的安装。
多个电极突出1631的设置方式具有多种，具体地，如图5所示，多个电极突出1631位于第一轴端1632轴线的两侧，齿之间的间距可灵活选择均匀排列或非均匀排列。在具体设置时，多个电极突出1631可以对称设置在第一轴端1632轴线的两侧，多个电极突出1631还可以非对称地设置在第一轴端1632轴线的两侧；上述球囊导管10中，通过限定多个电极突出1631位于第一轴端1632轴线的两侧，以便于第一轴端1632轴线的两侧均能够激发冲击波，以便于对血管20内壁的四周病变位置进行切割。
多个电极突出1631的设置方式具有多种，具体地，多个电极突出1631位于第一轴端1632轴线的一侧，以使得在第一轴端1632轴线的一侧能够激发冲击波，以便于对血管20内壁的一侧病变位置进行切割，以适用于于血管20周向局部钙化病变21的疾病治疗，临床使用时，将电极位置对准钙化病变21位置输送，到达病变位置后发射冲击波，冲击波能量可精准有效的释放于病变位置；当然，对于血管20周向局部地方有钙化的病变，还可选用单齿的突出电极163。
多个电极突出1631的设置方式具有多种，如图6所示，具体地，多个电极突出1631在第一轴端1632的周向均匀分布，多次激发冲击波后，圆周方向 上均能产生冲击波，并且保证在圆周任何一点处的冲击波能量比较均衡，以适用于血管20周向完全钙化的病变治疗。
突出电极163的结构形式具有多种，如图7所示，一种优选实施方式，突出电极163包括多组第三电极1633，多组第三电极1633之间间隔设置，第三电极1633包括电极突出1631以及第二轴端1634，第二轴端1634通过卡扣连接、凹凸配合等方式固定在绝缘管120外侧，每一突出电极163的第二轴端相并联，电极突出1631设置在第二轴端1634远离绝缘管120的端部的一侧；在具体设置时，第三电极1633的个数可以为两组、三组、四组或是四组以上组，多组第三电极1633可以沿绝缘管120的周向方向均匀分布，当然，多组第三电极1633的分布方式并不局限于此；第二轴端1634和电极突出1631可以为一体式结构，通过铸造、切割等工艺制备，第二轴端1634和电极突出1631之间可以为分体式结构，通过焊接、螺纹连接等工艺固定为一体。
上述球囊导管10中，通过限定突出电极163包括多组第三电极1633，第三电极1633包括一个电极突出1631以及一个第二轴端1634，以便于突出电极163设置在绝缘管120上的设定位置，以适用于于血管20周向局部钙化病变21的疾病治疗。
电极突出1631的尖端形状具有多种形式，如图8、图9、图10以及图11所示，一种优选实施方式，电极突出1631的尖端形状为矩形、梯形、圆弧形、椭圆弧形的一种，既可以保证冲击波发射位置的稳定，又可以保证电极对160的寿命达到临床实际使用的需求，避免使用尖端或针状电极，高电压会腐蚀电极尖端，造成电极间距变大，能量不稳定，降低产品使用寿命，绝缘管120上所有的电极突出1631的尖端形状可以相同，绝缘管120上所有的电极突出1631的尖端形状可以均不相同，绝缘管120上一部分的电极突出1631的尖 端形状相同，另一部分电极突出1631的尖端形状可以不相同，当然，电极突出1631的尖端形状以及设置方式并不局限于此，还可以为其他能够满足要求的形状和方式。
以上所述实施例的各技术特征可以进行任意的组合，为使描述简洁，未对上述实施例中的各个技术特征所有可能的组合都进行描述，然而，只要这些技术特征的组合不存在矛盾，都应当认为是本说明书记载的范围。
以上所述实施例仅表达了本发明的几种实施方式，其描述较为具体和详细，但并不能因此而理解为对发明专利范围的限制。应当指出的是，对于本领域的普通技术人员来说，在不脱离本发明构思的前提下，还可以做出若干变形和改进，这些都属于本发明的保护范围。因此，本发明专利的保护范围应以所附权利要求为准。

Claims (10)

  1. 一种球囊导管，其特征在于，包括内管、绝缘管、囊体、导电组件、导电液以及至少一电极对，其中：
    所述绝缘管套设在所述内管上，且位于所述囊体内，所述绝缘管为超疏水性材料，表面水接触角大于150°；
    所述内管贯穿所述囊体，且与所述囊体之间填充有所述导电液；
    至少一个电极对，每一所述电极对包括形成正负极的第一电极和第二电极，所述第一电极和所述第二电极间隔相对套设在所述绝缘管上，且分别与所述导电组件电连接。
  2. 根据权利要求1所述的球囊导管，其特征在于，所述电极对的数目为多个，多个所述电极对中的多个第一电极、多个第二电极相串联；或，多个所述电极对中的多个第一电极相并联，且多个第二电极相并联。
  3. 根据权利要求1所述的球囊导管，其特征在于，所述第一电极和所述第二电极中的至少一个为突出电极，所述突出电极包括至少一个电极突出，所述电极突出远离所述绝缘管的端部。
  4. 根据权利要求3所述的球囊导管，其特征在于，所述突出电极包括第一轴端以及多个所述电极突出，所述第一轴端套设在绝缘管上，所述电极突出设置在所述第一轴端远离所述绝缘管的端部的一侧。
  5. 根据权利要求4所述的球囊导管，其特征在于，多个所述电极突出位于所述第一轴端轴线的两侧。
  6. 根据权利要求4所述的球囊导管，其特征在于，多个所述电极突出位于所述第一轴端轴线的一侧。
  7. 根据权利要求4所述的球囊导管，其特征在于，多个所述电极突出在所述第一轴端的周向均匀分布。
  8. 根据权利要求3所述的球囊导管，其特征在于，所述突出电极包括多组间隔设置的第三电极，所述第三电极包括所述电极突出以及第二轴端，所述第二轴端固定在所述绝缘管外侧，每一所述突出电极的所述第二轴端相并联，所述电极突出设置在所述第二轴端远离所述绝缘管的端部的一侧。
  9. 根据权利要求1所述的球囊导管，其特征在于，还包括外管，所述外管连接于所述囊体的一端，所述导电组件包括导管座、导线组以及外接电源，所述导线组包括多个导线，所述导线与所述第一电极或所述第二电极电连接，所述导管座与所述外管相连接，且内部形成有容置空间，所述导线组包括多个导线，所述导线与所述第一电极或所述第二电极电连接，且穿过所述囊体、所述外管以及所述导管座的容置空间与所述外接电源相连接。
  10. 根据权利要求1所述的球囊导管，其特征在于，所述电极突出的尖端形状为矩形、梯形、圆弧形、椭圆弧形的一种。
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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN117281580A (zh) * 2023-11-27 2023-12-26 沛嘉医疗科技(苏州)有限公司 一种用于处理组织钙化的电极装置及冲击波装置

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104582621A (zh) * 2012-08-06 2015-04-29 冲击波医疗公司 用于血管成形冲击波导管的低剖面电极
US20170135709A1 (en) * 2015-11-18 2017-05-18 Shockwave Medical, Inc. Shock wave electrodes
CN110811761A (zh) * 2019-05-17 2020-02-21 谱创医疗科技(上海)有限公司 应用于血管成形术的冲击波发生系统
US20200129742A1 (en) * 2018-10-25 2020-04-30 Medtronic Vascular, Inc. Cavitation catheter
US20210085347A1 (en) * 2019-09-24 2021-03-25 Shockwave Medical, Inc. Lesion crossing shock wave catheter
CN113440215A (zh) * 2021-07-23 2021-09-28 上海佳沐垚医疗科技有限公司 一种冲击波发生装置及导管系统

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104582621A (zh) * 2012-08-06 2015-04-29 冲击波医疗公司 用于血管成形冲击波导管的低剖面电极
US20170135709A1 (en) * 2015-11-18 2017-05-18 Shockwave Medical, Inc. Shock wave electrodes
US20200129742A1 (en) * 2018-10-25 2020-04-30 Medtronic Vascular, Inc. Cavitation catheter
CN110811761A (zh) * 2019-05-17 2020-02-21 谱创医疗科技(上海)有限公司 应用于血管成形术的冲击波发生系统
US20210085347A1 (en) * 2019-09-24 2021-03-25 Shockwave Medical, Inc. Lesion crossing shock wave catheter
CN113440215A (zh) * 2021-07-23 2021-09-28 上海佳沐垚医疗科技有限公司 一种冲击波发生装置及导管系统

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN117281580A (zh) * 2023-11-27 2023-12-26 沛嘉医疗科技(苏州)有限公司 一种用于处理组织钙化的电极装置及冲击波装置
CN117281580B (zh) * 2023-11-27 2024-03-15 沛嘉医疗科技(苏州)有限公司 一种用于处理组织钙化的电极装置及冲击波装置

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