CN216090750U - High-pressure-resistance ablation catheter - Google Patents

Abstract

The utility model discloses a high-voltage-resistance ablation catheter which comprises a catheter, wherein the far end of the catheter is provided with a flexible section, a head end electrode is arranged at the far end tip of the flexible section, at least one ring electrode is arranged on the flexible section and/or the other parts of the catheter body except the flexible section, the ring electrode and the head end electrode can release electric signals simultaneously or independently, and an electrode lead of the head end electrode and an electrode lead of the ring electrode are insulated from each other, and the head end electrode and the ring electrode are insulated from each other. Compared with the prior art, the electrode lead of head end electrode and ring electrode sets up in the body of pipe, guarantees the insulation between the electrode lead and the insulation between head end electrode, the ring electrode to make head end electrode and ring electrode can apply the high pressure alone or simultaneously and melt the signal, realize that a plurality of electrodes participate in simultaneously and melt the transmission of energy, thereby improve and melt efficiency.

Description

High-pressure-resistance ablation catheter

Technical Field

The utility model relates to a medical appliance, in particular to a high-pressure-resistance ablation catheter.

Background

Atrial fibrillation is a rapid arrhythmia, and the incidence rate of atrial fibrillation increases with age, and reaches 10% in people over 75 years old. The atrial excitation frequency during atrial fibrillation reaches 300-600 times/minute, the ventricular rate is often fast and irregular and sometimes can reach 100-160 times/minute, the heartbeat is much faster than that of a normal person, the heart beat is absolutely irregular, and the atrium loses effective contraction function. The incidence of atrial fibrillation is also closely related to coronary heart disease, hypertension, heart failure and other diseases.

The tip structure of a conventional rf ablation catheter typically includes a tip electrode, a ring electrode, a catheter, and the like. The typical internal structure is a tip electrode fixed to the distal end of a catheter formed of an insulating material, and an annular electrode attached to the distal end of the catheter. Electrode leads welded to the ring electrode and the tip electrode enter the lumen of the catheter through perforations in the tube and exit through the proximal end of the catheter to an electrical connector at the proximal end of the handle. Such catheters have only a tip electrode for transmitting the ablation electrical signal. The discharge circuit is composed of an ablation energy generator, a head electrode, a human body and a back plate, the ring electrode is only used for recording intracardiac electric signals, so that ablation can be carried out on one point every time, the ablation mode is low in efficiency and long in time consumption, and discontinuity of ablation lines is easy to form (namely, when ablation is carried out on one surface, as the conventional ablation is carried out only by the head electrode, ablation may not be carried out at a certain point on the surface).

SUMMERY OF THE UTILITY MODEL

The utility model aims to provide a high-voltage-resistance ablation catheter, which solves the technical problem of insulation of high-voltage discharge, thereby realizing that a single electrode or a plurality of electrodes can participate in the high-voltage discharge singly or simultaneously, and further improving the ablation efficiency.

In order to solve the problems, the utility model adopts the following technical scheme: the utility model provides a high withstand voltage ablation catheter, includes the pipe, the distal end of pipe has flexible section, is equipped with the head electrode on the distal end tip of flexible section, is equipped with at least one ring electrode on flexible section and/or the pipe body portion that the other of flexible section is gone up, ring electrode can release the signal of telecommunication with the head electrode simultaneously or alone, all insulate from each other between the electrode lead wire of head electrode and the electrode lead wire of ring electrode, head electrode and ring electrode.

Furthermore, the far end of the catheter is provided with a metal mesh basket, the flexible section is coated on the support arm of the metal mesh basket, and the head end electrode is arranged on the far end head of the metal mesh basket.

Furthermore, the far end of the catheter is provided with an annular body formed by winding memory metal, and the flexible section is covered outside the annular body, so that the flexible section is annular or spiral in a free state.

Further, the distances between the head electrode and the adjacent ring electrodes and between the ring electrodes are equal.

Further, the ring electrodes are equal in length.

Furthermore, the catheter comprises an insulating inner tube, the ring electrodes are sleeved on the insulating inner tube, an insulating outer tube is arranged between the head end electrode and each ring electrode, and the head end electrode and electrode leads of each ring electrode are arranged between the insulating inner tube and the insulating outer tube.

Further, the spacing between the tip electrode and the adjacent ring electrode and between the ring electrodes is equal and/or the length of the ring electrodes is equal.

Furthermore, a first insulating sleeve is arranged on the electrode lead of the head electrode and the electrode lead of the ring electrode.

Further, a pressure sensor and/or a magnetic positioning sensor is arranged in the far-end tube body of the flexible section.

Furthermore, a second insulating sleeve is wrapped outside the pressure sensor and the magnetic positioning sensor.

Compared with the prior art, the electrode leads of the head electrode and the ring electrode are arranged in the catheter body of the catheter, so that the insulation between the electrode leads and the insulation between the head electrode and the ring electrode are ensured, the head electrode and the ring electrode can apply high-voltage ablation signals independently or simultaneously, the single or simultaneous participation of a plurality of electrodes in the transmission of ablation energy is realized, and the ablation efficiency is improved.

Drawings

Fig. 1 is a schematic structural view of embodiment 1 of the present invention.

Fig. 2-1 is a schematic view of the internal structure of a first catheter according to the present invention.

Fig. 2-2 is a schematic view of the internal structure of a second catheter of the present invention.

Fig. 3 is a schematic view showing a first position of the electrode lead of the present invention.

Fig. 4 is a schematic diagram of a sensor arrangement according to the present invention.

Fig. 5-1 is a schematic of a single electrode discharge of the present invention.

FIG. 5-2 is a schematic diagram of a finite element simulation of a single electrode discharge of the present invention.

Fig. 6-1 is a schematic diagram of the simultaneous discharge of two electrodes according to the present invention.

FIG. 6-2 is a schematic diagram of a finite element simulation of a two-electrode discharge of the present invention.

Fig. 7-1 is a schematic diagram of the simultaneous discharge of four electrodes according to the present invention.

FIG. 7-2 is a schematic diagram of a finite element simulation of a four-electrode discharge of the present invention.

FIG. 8-1 is a schematic view of example 2 of the present invention.

Fig. 8-2 is a schematic structural view of a flexible segment in embodiment 2 of the present invention.

Fig. 9 is a schematic structural view of embodiment 3 of the present invention.

Fig. 10 is a schematic view of a second position of the electrode lead of the present invention.

Detailed Description

The present invention will be described in further detail with reference to the accompanying drawings and examples.

In the present invention, distal end refers to the end remote from the operator; proximal refers to the end near the operator. The handle and the electrical connector are all the prior art and are not improved correspondingly.

Example 1:

as shown in fig. 1 and 2-1, the present invention discloses a high voltage-resistant ablation catheter, which includes a catheter 1, a flexible section 11 is provided at a distal end of the catheter 1, a tip electrode 2 is provided at a distal end of the flexible section 11, at least one ring electrode 3 is provided on the flexible section 11, the ring electrode 3 and the tip electrode 2 can release electrical signals simultaneously or separately, the electrical signals may be radio frequency signals or pulsed electric field signals, and are not specifically limited herein, it is only required to ensure that the released electrical signals can be used for ablation, a first electrode lead 21 of the tip electrode 2 and a second electrode lead 31 of the ring electrode 3 are provided in a catheter body of the catheter 1, so as to realize mutual insulation between the second electrode lead 31 of the ring electrode 3 and the first electrode lead 21 of the tip electrode 2, and between the tip electrode 2 and the ring electrode 3, thereby achieving an effect of insulation and high voltage resistance, therefore, high-voltage ablation signals can be applied among the multiple electrodes, so that the multiple electrodes can participate in the transmission of ablation energy at the same time, and the ablation efficiency is improved.

When only the head electrode 2 releases the electrical signal, unipolar ablation of discharge is performed between the head electrode and the back plate, when the head electrode 2 and the ring electrode 3 release the electrical signal simultaneously, at least one ring electrode 3 of the head electrode 2 and the ring electrode 3 or the head electrode 2 has a positive polarity, and the others may be negative polarities, that is, when the electrical signal is released simultaneously, it is only necessary to ensure that both the positive and negative polarities participate in the release of the electrical signal, for example, the polarity arrangement sequence of the head electrode 2 and the ring electrode 3 is + - - - +, + - + -, or- + - -, etc.

The first electrode lead 21 of the tip electrode 2 and the second electrode lead 31 of the ring electrode 3 of the present invention are electrically connected to the electrical connector 7 at the proximal end of the handle by passing through the body of the catheter 1 and the handle 9.

As shown in fig. 1, the ring electrodes 2 are arranged at intervals along the axial direction of the catheter 1, and in this embodiment, the ring electrodes 3 are preferably arranged on the tube body of the flexible segment 11, but the present invention is not limited thereto, and the ring electrodes 3 may be distributed on the flexible segment 11 and the remaining tube body portion of the catheter 1 except the flexible segment 11.

When a plurality of electrodes participate in discharging at the same time, a linear continuous ablation zone can be formed at one time, and the problems that the ablation points cannot be connected into a line and are discontinuous due to the fact that actual ablation points deviate from a preset ablation line in single-point ablation are avoided. The utility model meets the requirements of tricuspid isthmus linear ablation, left atrium top line, left atrium bottom line, mitral isthmus line and other operations in arrhythmia treatment, and can improve the operation efficiency and success rate.

In this embodiment, the catheter 1 may be a straight tube.

Example 2

As shown in fig. 9, on the basis of the above embodiment 1, the distal end of the catheter 1 is provided with the metal basket 14, the flexible section 11 is coated on each arm of the metal basket 14, the tip electrode 2 is arranged on the distal tip of the metal basket 14, the metal basket 14 is in an expanded state in a free state, and the metal basket 14 can be contracted after being pressed.

In this embodiment, the flexible segments 11 can be formed on the arms of the metal basket 14 by heat-melting the flexible segments 11 or the flexible segments 11 can be directly sleeved on the arms.

Example 3

As shown in fig. 8-1 and 8-2, in addition to the above embodiment 1, the distal end of the catheter 1 is provided with the annular body 7 formed by winding the memory metal, and the flexible segment 11 is wrapped around the annular body 7 so that the flexible segment 11 is annular or spiral in a free state, but the present embodiment is not limited thereto, and the flexible segment 11 may be directly formed into the annular body 7, and may be deformed by an external force and restored in a free state.

In this embodiment, the flexible segments 11 as described in embodiment 2 may also be formed on the annular body 7 by hot-melting the flexible segments 11 or the flexible segments 11 may be directly sleeved on the annular body 7.

As shown in fig. 2-1, on the basis of the above embodiment, the distances between the head electrode 2 and the adjacent ring electrodes 3 and between the ring electrodes 3 are equal, so as to ensure that the damage characteristics between the electrodes are similar, and avoid the situation of discontinuous damage between a certain electrode pair, and the distance may be set according to the actual operation requirement, which is not limited specifically herein.

Of course, as shown in fig. 2-1, the lengths of the ring electrodes 3 can also be set to be equal, so that energy can be uniformly output between the electrodes, and the size of the lesion area formed by each electrode is approximately the same, thereby avoiding the problems of insufficient local ablation or excessive ablation.

As shown in fig. 2-2, the catheter 1 of the present invention can be implemented by a structure in which the catheter 1 includes an insulating inner tube 12, ring electrodes 3 are fitted on the insulating inner tube 12, an insulating outer tube 13 is disposed between the tip electrode 2 and each ring electrode 3, and a first electrode lead 21 of the tip electrode 2 and a second electrode lead 31 of each ring electrode 3 are disposed between the insulating inner tube 12 and the insulating outer tube 13; the conduit 1 can be made of a high polymer insulator material to ensure the insulation effect between the welding points of the electrode leads and the electrode leads, and the electrical signals are high-voltage signals to insulate the electrode leads of a plurality of electrodes, so that short circuit can be avoided.

As shown in fig. 3, the first electrode lead 21 of the tip electrode 2 and the second electrode lead 31 of the ring electrode 3 provided in the tubular body of the catheter 1 are distributed in the axial direction of the tubular body of the catheter 1 and are staggered from each other, and since the voltage of the pulse discharge can reach one thousand volts, the electrode leads can be prevented from being broken down by staggering the electrode leads from each other, so that the high voltage resistance is better.

In the present invention, the insulating outer tube 13 is formed by fixing the insulating material on the surface of the insulating inner tube 12 by heat fusing through the heat fusing process, and then the insulating outer tube 13 is formed. The ring electrode 3 can be knocked by adopting a mould pressing process through mechanical rapid 360-degree rotation, so that the outer diameter of the ring electrode is uniformly reduced, and the ring electrode is tightly pressed on the insulating inner tube 12; the present invention is not limited thereto, and can be realized by tightly combining the metal ring and the plastic pipe in the prior art, which is not limited in detail herein.

In the present invention, the insulating outer tube 13 may partially extend to the tip electrode 2 to partially wrap the tip electrode 2, and of course, the tip electrode 2 may also be directly fixed on the catheter 1 by using the prior art.

As shown in fig. 10, the insulation between the electrode leads may also be implemented by disposing a first insulating sleeve 8 on the first electrode lead 21 of the tip electrode 2 and the second electrode lead 31 of the ring electrode 3, and disposing the first electrode lead 21 of the tip electrode 2 and the second electrode lead 31 of the ring electrode 3 in the lumen of the catheter 1; the first insulating sheath 8 can also be fixed to the electrode lead by means of heat fusion.

However, the present invention is not limited thereto, and the first insulating sheath 8 (shown in fig. 3) may be disposed on the first electrode lead 21 of the tip electrode 2 and the second electrode lead 31 of the ring electrode 3, in addition to the arrangement of the catheter 1 as the insulating inner tube 12 and the insulating outer tube 13, so as to achieve a better insulating effect.

In the present invention, the hardness of the proximal tube of the catheter 1 is greater than the hardness of the flexible segment 11, so that twisting the tube of the catheter 1 can be achieved to adjust the orientation of the flexible segment 11.

As shown in fig. 4, a pressure sensor 4 and/or a magnetic positioning sensor 5 may also be disposed in the distal tube body of the flexible segment 11, specifically, the pressure sensor 4 and the magnetic positioning sensor 5 are disposed adjacent to the tip electrode 2, and the lead wires thereof are led out from the proximal end of the catheter 1 through the lumen of the catheter; in order to ensure the insulation requirements of the sensor and the electrode lead, a second insulating sleeve 6 is coated outside the pressure sensor 4 and the magnetic positioning sensor 5, the near end of the second insulating sleeve 6 is subjected to glue sealing treatment, the leads of the pressure sensor 4 and the magnetic positioning sensor 5 can be arranged in the pipe body of the catheter 1 or directly pass through the second insulating sleeve 6 to realize the insulation purpose, and the second insulating sleeve 6 is made of a high polymer insulator material; more precisely, the leads of the pressure sensor 4 and of the magnetic position sensor 5 are placed between the insulating inner tube 12 and the insulating outer tube 13.

As shown in fig. 5-1 and 5-2, a monopolar ablation mode is adopted in which discharge is generated between the head electrode and the back electrode plate, and in this way, the ablation on the injury area is point contact, and the ablation range is small.

As shown in fig. 6-1 and 6-2, a bipolar discharge pattern of the tip electrode and the ring electrode adjacent thereto has a wider lesion range in the long axis direction of the catheter, so that the ablation range is larger than that in the monopolar ablation mode.

As shown in fig. 7-1 and 7-2, a bipolar discharge pattern of the tip electrode and the ring electrode adjacent thereto has a wider lesion range in the long axis direction of the catheter, so that the ablation range is larger than that in the monopolar ablation mode.

After the ablation catheter enters an atrium through a femoral vein, the ablation position is determined according to the diagnosis result of an operator, and then the operator operates the catheter handle to guide the head end of the catheter to be attached to the myocardium at the ablation position. During the induction process, if a pressure or magnetic positioning sensor is arranged in the catheter head, information such as the head-myocardial contact degree and the position of the catheter head is provided for a user respectively.

The bipolar ablation of the utility model can also limit the ablation energy in the peripheral area of the electrode, thus avoiding the condition that the ablation energy flows through the body and then is converged on the back plate in the traditional monopolar ablation mode, namely avoiding the side effects of nerve stimulation (pain), muscle contraction, back plate burn and the like which are easy to occur in the process, and further improving the safety of the operation.

Claims (10)

1. A high withstand voltage ablation catheter comprising a catheter (1), characterized in that: the far end of pipe (1) has flexible section (11), is equipped with head end electrode (2) on the distal end tip of flexible section (11), is equipped with at least one ring electrode (3) on flexible section (11) and/or pipe (1) other than flexible section (11) body part, ring electrode (3) can release the signal of telecommunication with head end electrode (2) simultaneously or alone, all insulate from each other between the electrode lead of head end electrode (2) and the electrode lead of ring electrode (3), between head end electrode (2) and ring electrode (3).

2. The high withstand voltage ablation catheter of claim 1, wherein: the far end of the catheter (1) is provided with a metal basket (14), the flexible section (11) is coated on the support arm of the metal basket (14), and the head end electrode (2) is arranged on the far end head of the metal basket (14).

3. The high withstand voltage ablation catheter of claim 1, wherein: the far end of the catheter (1) is provided with an annular body (7) formed by winding memory metal, and the flexible section (11) is coated outside the annular body (7) so that the flexible section (11) is annular or spiral in a free state.

4. The high withstand voltage ablation catheter according to any of claims 1-3, wherein: the distances between the head electrode (2) and the adjacent ring electrodes (3) and between the ring electrodes (3) are equal.

5. The high withstand voltage ablation catheter of claim 4, wherein: the ring electrodes (3) are of equal length.

6. The high withstand voltage ablation catheter according to any of claims 1-3, wherein: the catheter (1) comprises an insulating inner tube (12), ring electrodes (3) are sleeved on the insulating inner tube (12), insulating outer tubes (13) are arranged between the head end electrodes (2) and the ring electrodes (3), and electrode leads of the head end electrodes (2) and the ring electrodes (3) are arranged between the insulating inner tube (12) and the insulating outer tubes (13).

7. The high withstand voltage ablation catheter of claim 6, wherein: the distances between the head electrode (2) and the adjacent ring electrodes (3) and between the ring electrodes (3) are equal and/or the lengths of the ring electrodes (3) are equal.

8. The high withstand voltage ablation catheter of claim 1, wherein: and a first insulating sleeve (8) is arranged on the electrode lead of the head electrode (2) and the electrode lead of the ring electrode (3).

9. The high withstand voltage ablation catheter according to any of claims 1-3, wherein: and a pressure sensor (4) and/or a magnetic positioning sensor (5) are/is arranged in the far-end pipe body of the flexible section (11).

10. The high withstand voltage ablation catheter of claim 9, wherein: and a second insulating sleeve (6) is coated outside the pressure sensor (4) and the magnetic positioning sensor (5).

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