CN218356351U - Ablation electrode catheter - Google Patents

Abstract

The utility model provides an ablation electrode catheter, which comprises an ablation electrode tip, a guide pipe, a pull wire and a rebound spring, wherein the ablation electrode tip comprises a spiral ring, the spiral ring comprises a shaping framework and an outer ring, and the outer ring is wrapped on the shaping framework; the end of the spiral ring is inserted into the port of the guide tube, and the guide tube is used for being inserted into a catheter handle; one end of the pull wire is connected with the end part of the shaping framework, and the other end of the pull wire penetrates out of the guide pipe; the rebound spring is arranged in the guide tube and always applies force to the pull wire in the direction of the ablation electrode head. Above-mentioned ablation electrode catheter, through the design of acting as go-between, resilience spring, can realize the adjustment of the position of ablating the electrode tip to guarantee that the electrode tip of ablating can better laminate and ablate the target tissue.

Description

Ablation electrode catheter

Technical Field

The utility model relates to the technical field of medical equipment, concretely relates to ablation electrode catheter.

Background

Atrial fibrillation is an arrhythmia with uncoordinated electrical activity of the atria, resulting in ineffective atrial contraction, which can clinically cause various serious diseases such as arrhythmia, stroke, heart failure, even fatal cardiac embolism and the like.

The pulmonary vein is the main cause of atrial fibrillation due to the presence of pulmonary vein cuffs. Myocardial cell colonies are present between the intima and adventitia of the pulmonary vein, and since the cells forming the myocardial cuff have a different origin and different electrophysiological properties from the atrial muscle, they form an abnormally excited matrix leading to atrial fibrillation.

The advanced stage of atrial fibrillation can lead to heart failure, which is an incurable disease and threatens the life of the patient all the time. The operation treatment method for treating atrial fibrillation mainly comprises three methods of radio frequency ablation, cryoablation and pulse ablation, and as the pulse ablation does not generate heat, the damage to tissues caused by the radio frequency ablation, the cryoablation and the like is avoided, and the targeting property is stronger, more attention is paid to the current pulse ablation.

The pulse ablation is to perform unilateral ablation on the great visceral nerves through a catheter, so that the sympathetic nervous system is recovered to be normal, then the viscera is returned to be normal and contracted, blood in a human body is distributed again, the pressure of the heart and the lung is normalized, and finally the symptoms of heart failure are reduced. Other tissues near the pulmonary vein can be protected from being affected during the course of the nerve therapy.

In the prior art, due to the design, in the process of conveying or melting, the electrode of the ablation electrode head cannot be completely attached to an ablation target, and particularly when the operation position of a pulmonary vein opening is small, if the position of the ablation electrode head cannot be adjusted, the operation effect is difficult to ensure.

SUMMERY OF THE UTILITY MODEL

The application aims to provide an ablation electrode catheter, which is used for solving the problem that the electrode of an ablation electrode head cannot be completely attached to an ablation target, and the operation effect is difficult to ensure.

In order to achieve the above purpose, the utility model provides a technical scheme as follows.

The utility model provides an ablation electrode catheter, include:

the ablation electrode head comprises a spiral ring, the spiral ring comprises a shaping framework and an outer ring, and the outer ring is wrapped on the shaping framework;

a guide tube, an end of the spiral ring being inserted into a port of the guide tube, the guide tube being for insertion into a catheter handle;

one end of the pull wire is connected with the end part of the shaping framework, and the other end of the pull wire penetrates out of the guide pipe;

the rebound spring is installed in the guide tube and always applies force to the pull wire in the direction of the ablation electrode head.

Preferably, the shaped framework is made of shape memory alloy, and the original shape of the shaped framework is consistent with the shape of the spiral ring in an unstressed state.

Preferably, the ablation electrode head further comprises an electrode, and the electrode is located on the outer peripheral surface of the outer ring.

Preferably, the number of the electrodes is 2N, and N is a natural number of 3-8; the electrodes comprise positive electrodes and negative electrodes, and the positive electrodes and the negative electrodes are arranged in a crossed mode.

Preferably, the number of pulse groups discharged by the pulsed electric field per time is 1-20, such as 3, 5, 8, 10, 15, etc., each pulse group comprises 50-500 pulses, preferably 60-300, more preferably 80-200, such as 100, 130, 150, etc.; the time interval of adjacent pulse groups of the pulsed electric field is 500-3000ms, preferably 600-2500ms, more preferably 800-2000ms, more preferably 1000-1800ms, such as 1200ms, 1500ms, etc.

Preferably, each pulse comprises a positive high pulse, a positive low pulse, further, a negative high pulse and a negative low pulse; the pulse width of the positive high pulse is 4-12 us, the pulse width of the negative high pulse is 4-12 us, the pulse width of the positive low pulse is 2-4 us, and the pulse width of the negative low pulse is 400-3000 us. Preferably, the ablation electrode catheter further comprises an electrode lead, the electrode lead is connected with the electrode, and the electrode lead penetrates through the outer ring and the guide tube.

Preferably, a lead passage is provided in the guide tube, and the electrode lead passes through the lead passage.

Preferably, the ablation electrode catheter further comprises a pull wire sleeve, the shaping framework and the pull wire are fixed at two ends of the pull wire sleeve respectively, the rebound spring is sleeved on the pull wire, one end of the rebound spring is abutted with the pull wire sleeve, and the other end of the rebound spring is abutted to the inner circumferential surface of the guide tube.

Preferably, a stay wire channel is arranged in the guide tube, the stay wire passes through the stay wire channel, and the cross section of the stay wire channel is in an eccentric shape.

Preferably, the guide tube comprises a bending adjusting guide tube and a main guide tube, the bending adjusting guide tube is made of bendable materials, the outer ring of the ablation electrode head is inserted into one end of the bending adjusting guide tube, the other end of the bending adjusting guide tube is fixed with one end of the main guide tube, and the other end of the main guide tube is inserted into a guide tube handle.

Compared with the prior art, the beneficial effect of this application lies in: according to the ablation electrode catheter, the position of the ablation electrode head can be adjusted through the design of the pull wire and the rebound spring, so that the ablation electrode head can be better attached to an ablation target tissue; when the ablation electrode catheter is used for ablation operation, the operation time is greatly shortened, meanwhile, the selective ablation of cardiac muscle cells is realized, the integrity of tissue matrix is kept, surrounding tissues are not damaged, and the efficiency and the success rate of the ablation operation are improved.

Drawings

The technical features and advantages of the present invention are more fully understood by referring to the following detailed description in conjunction with the accompanying drawings.

Fig. 1 is a schematic structural view of an ablation electrode catheter assembly according to the present invention.

Fig. 2 is a schematic view of another angle configuration of the ablation electrode catheter assembly of fig. 1.

Fig. 3 is a schematic structural view of an ablation electrode tip of the ablation electrode catheter assembly of fig. 1.

Fig. 4 shows a top view of the ablation electrode tip of fig. 3.

Fig. 5 is a schematic illustration of electrode pulses for the ablation electrode tip of fig. 3.

Fig. 6 shows a schematic diagram of a single pulse of the electrode pulses shown in fig. 5.

Fig. 7 is a schematic view showing a structure of an ablation electrode catheter of the ablation electrode catheter assembly shown in fig. 1.

Fig. 8 is a schematic view showing the internal structure of the ablation electrode catheter shown in fig. 7.

Fig. 9 is a schematic view of a catheter handle of the ablation electrode catheter assembly of fig. 1.

Fig. 10 is an exploded view of the structure of the catheter handle of fig. 9.

Fig. 11 is an enlarged view of a portion of the area a of the catheter handle shown in fig. 10.

Fig. 12 is a cross-sectional view of the catheter handle of fig. 9.

FIG. 13 is a cross-sectional view of the catheter gripping structure of the catheter handle of FIG. 12.

Figure 14 is a schematic view of the conduit gripping device shown in figure 13 in the conduit gripping configuration.

Fig. 15 is a schematic view of another angle of the catheter clip of fig. 13.

Fig. 16 shows a cardiac stromal map of a patient prior to ablation.

FIG. 17 is a graph of cardiac electrical signals of the patient of FIG. 16 prior to ablation.

Fig. 18 shows a map of the cardiac stroma after ablation of the patient shown in fig. 16.

FIG. 19 is a graph of cardiac electrical signals of the patient of FIG. 16 after ablation.

Description of the reference numerals

The ablation electrode comprises an ablation electrode catheter 100, an ablation electrode head 101, a guide tube 102, a spiral ring 103, an electrode 104, a central end 105, a free end 106, a shaping framework 107, an outer ring 108, a pressure sensor 109, a temperature sensor 110, a pull wire 111, a rebound spring 112, a pull wire sleeve 113, a bending guide tube 114, a main guide tube 115 and an electrode lead 116;

the catheter comprises a catheter handle 200, a catheter clamping structure 201, a handle shell 202, a catheter clamping piece 203, a catheter pushing piece 204, a pushing piece head 205, a first connecting pipe 206, a clamping piece 207, a first insertion hole 208, a first connecting hole 209, a second insertion hole 210, an inclined surface 211, a matching surface 212, an outer expanding surface 213, a second connecting hole 214, a limiting groove 215, a limiting hole 216, an electrode lead perforation 217, a first groove 218, a second groove 219, a first sealing ring 220, a second sealing ring 221, an outer expanding opening 222, a supporting fixing disc 223, a wire drawing port 224, a wire drawing fixing port 225 and a generator connecting part 226.

Detailed Description

Unless otherwise defined, technical or scientific terms used herein shall have the ordinary meaning as is understood by those of ordinary skill in the art to which the invention belongs.

In the description of the present invention, it is to be understood that the terms "center", "longitudinal", "lateral", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", and the like, indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings, and are used merely for convenience of description and for simplicity of description, and do not indicate or imply that the device or element being referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore, should not be construed as limiting the present invention.

Furthermore, the terms "first", "second", etc. are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first," "second," etc. may explicitly or implicitly include one or more of that feature. In the description of the present invention, "a plurality" means two or more unless otherwise specified.

Fig. 1-2 are schematic views of an ablation electrode catheter assembly according to the present invention. The ablation electrode catheter assembly includes an ablation electrode catheter 100 and a catheter handle 200. Wherein, the ablation electrode catheter 100 includes an ablation electrode tip 101 and a guide tube 102, the ablation electrode tip 101 is inserted into a port of the guide tube 102, and the guide tube 102 is used to be inserted into the catheter handle 200. During treatment, the ablation electrode catheter 100 is extended into the blood vessel, leaving the catheter handle 200 outside the body. When the ablation electrode tip 101 reaches the target region, the shape of the ablation electrode tip 101 can be changed by manipulating the pull wire on the catheter handle 200 to cause the electrode of the ablation electrode tip 101 to conform to the ostium of the pulmonary vein to ablate the target tissue.

Fig. 3 to 4 show an embodiment of the ablation electrode tip 101, the ablation electrode tip 101 includes a spiral ring 103 and a plurality of electrodes 104, the electrodes 104 are located on the outer circumferential surface of the spiral ring 103, the center end 105 of the spiral ring 103 is used for fixing, the end of the spiral ring 103 away from the guide tube 102 is a free end 106, and the spiral ring 103 is spirally bent under an unstressed state. The distance from the spiral ring 103 to the central end 105 of the spiral ring 103 gradually increases in a direction approaching the free end 106 of the spiral ring 103, i.e. the spiral ring 103 has a tendency to gradually flare from the central end 105 to the free end 106. Due to the structural design of the spiral ring 103, the adjacent electrodes can be prevented from contacting after expansion, and particularly, the problem of contact between the positive electrode and the negative electrode can be avoided. When the pulmonary vein opening is attached, the free end 106 can be attached firstly, and the spiral ring 103 is gradually pressed on the pulmonary vein opening, so that the effect of attaching to the pulmonary vein opening is better.

The spiral ring 103 comprises a shaping framework 107 and an outer ring 108, wherein the shaping framework 107 is made of shape memory alloy, and the original shape of the shaping framework 107 is consistent with that of the spiral ring 103 in an unstressed state; the outer ring 108 is wrapped on the shaping framework 107, and the electrode 104 is positioned on the outer peripheral surface of the outer ring 108. The shaping framework 107 is made of shape memory alloy, which can ensure that the spiral ring 103 always keeps a gradually outward-expanding shape under an unstressed state.

As shown in fig. 3, the number of the electrodes 104 is 2N, N being a natural number of 3 to 8; the electrodes 104 include positive electrodes and negative electrodes arranged in a crossing manner. The number of electrodes 104 ensures optimal ablation.

As shown in fig. 3, the ablation electrode tip 101 further includes a plurality of pressure sensors 109, the pressure sensors 109 are disposed on the outer peripheral surface of the spiral ring 103 at a side facing the pulmonary vein ostium, and the pressure sensors 109 are configured to detect a pressure value and output the pressure value to a pressure monitoring device. The pressure sensor 109 can measure the pressure of the ablation electrode tip 101 on an ablation site at any time; the pressure monitoring device can monitor the pressure of the ablation site at any time and display the pressure in real time so as to better detect whether the electrode 104 is attached to the ablation site.

Wherein, the number of the pressure sensors 109 is M, and M is 3 or 4; the spiral ring 103 is divided equally into M segments and the pressure sensors 109 are located on the side of each segment remote from the free end 106. By the evenly arranged pressure sensors 109, it is ensured that the pressure values of the respective ablation sites can be measured comprehensively.

The ablation electrode head 101 further comprises a plurality of temperature sensors 110, the temperature sensors 110 are disposed on one side of the outer peripheral surface of the spiral ring 103 facing the pulmonary vein ostium, and the temperature sensors 110 are used for detecting temperature and outputting the temperature to a temperature monitoring device. By providing the temperature sensor 110, the temperature of the ablation site can be monitored at any time, allowing for real-time adjustment of the treatment regimen.

As shown in fig. 3, the helical ring 103 is rotated more than 360 ° around the central end 105. Spiral ring 103 is greater than 360 around the rotation angle of central point 105, like 380, 400 etc, can melt bigger area or ring at every turn, can improve and melt efficiency, avoids rotatory pipe many times, and this is because at the operation in-process, the resistance that the pipe received is great, during twist grip, and the distal end electrode is hardly kept in step with the handle, does not change even, the utility model discloses a enlarge the electrode angle, can once only melt the tissue of bigger area, also correspondingly reduced the operation time. The distance in the axial direction parallel to the overlapping region of the spiral rings 103 is h, and the diameter D = (2 to 8) h of the spiral rings 103. The overlapped areas of the spiral rings 103 keep a certain distance, so that the spiral rings 103 are staggered to form two layers, and one-time ablation can be more complete.

As shown in FIGS. 5 to 6, taking an electrode with a spiral ring diameter of 13 to 15mm as an example, the high and low voltages applied to the two ends of the electrode are + -600V to + -1500V; the number of pulse groups discharged by the pulse electric field each time is 1-20, and each pulse group comprises 60-200 pulses; the time interval of adjacent pulse groups of the pulse electric field is 500-3000ms. The time interval of the pulse group of the electrode is 500ms, 800ms, 1000ms, 1500ms, 2000ms, 2500ms or 3000ms and the like; each pulse comprises a positive high pulse, a positive low pulse, a negative high pulse and a negative low pulse; the pulse width of the positive high pulse is 4-12 us, the pulse width of the negative high pulse is 4-12 us, the pulse width of the positive low pulse is 2-4 us, and the pulse width of the negative low pulse is 400-3000 us. The discharge time of a single pulse is the sum of the pulse widths of the above 4 pulses; the pulse width of the positive high pulse of the single pulse is 4-12 us, the pulse width of the negative high pulse is 4-12 us, the pulse width of the positive low pulse is 2-4 us, and the pulse width of the negative low pulse is 400-3000 us. When the parameters of the electrode 104 are set within the above ranges, the cells of the tissue causing abnormal electrical potential may be broken down and the normal function of other tissues may not be affected when the ablation electrode catheter 100 is used for surgery.

When the ablation electrode catheter 100 is used for surgery, firstly, electrodes are used for mapping intracavitary electrocardiosignals of a patient, then the ablation electrode catheter 100 is used for respectively carrying out pulsed electric field ablation on four pulmonary veins of a Left Superior Pulmonary Vein (LSPV), a Left Inferior Pulmonary Vein (LIPV), a left superior pulmonary vein (RSPV) and a left superior pulmonary vein (RIPV) of the patient, ablation parameters shown in table 1 are used, pulmonary vein isolation is successfully realized only in 50 seconds, and finally CS S1S1 (S1S 2) is used for pacing stimulation, so that no atrial fibrillation is induced, and the good surgery effect is proved. After completion of the pulsed electric field ablation procedure, the matrix-mapped pulmonary vein low voltage indicates that the four pulmonary veins have been completely isolated. By adopting the ablation electrode catheter 100, the operation time is greatly shortened, meanwhile, the selective ablation of cardiac muscle cells is realized, the integrity of tissue matrix is maintained, surrounding tissues are not damaged, and the efficiency and the success rate of ablation operation are improved.

TABLE 1 intraoperative ablation parameter setting table

The ablation effect of the patient in the operation 3 is selected to illustrate the ablation effect of the electrode catheter provided by the invention. Parameters before and after the operation are shown in fig. 16-fig. 19, before the ablation, obvious electric signals are detected at 730ms of 4 Pulmonary Veins (PV), and after the ablation, the electric signals at the pulmonary veins are weak or even have no electric signals, which indicates that the ablation has successfully blocked the transmission of the electric signals, the original feeling of palpitation disappears, and the electrocardiogram of the reexamination of the patient after the operation shows that the sinus rhythm is obtained.

As shown in fig. 7 to 8, when the ablation electrode tip 101 is mounted on the guide tube 102, the ablation electrode catheter 100 further includes an adjustment assembly mounted in the guide tube 102 for adjusting the position of the ablation electrode tip 101.

The adjusting assembly comprises a pull wire 111 and a rebound spring 112, the outer ring 108 of the ablation electrode head 101 is inserted into a port of the guide tube 102, and the guide tube 102 is used for being inserted into the guide handle 200; one end of a pull wire 111 is connected with the end part of the shaping framework 107, and the other end of the pull wire 111 penetrates out of the guide pipe 102; a resilient spring 112 is mounted within the guide tube 102, the resilient spring 112 always applying a force to the pull wire 111 in a direction toward the ablation electrode tip 101.

Pulling the pull wire 111 can bend one end of the guide tube 102 close to the ablation electrode tip 101, thereby adjusting the direction of the ablation electrode tip 101 to facilitate treatment. The resilient spring 112 can provide a restoring force to the pulling wire 111, so that the guide tube 102 is restored to the original state when the pulling wire 111 is not stressed.

As shown in fig. 8, the ablation electrode catheter 100 further includes a pull wire sleeve 113, the fixed framework 107 and the pull wire 111 are respectively fixed at two ends of the pull wire sleeve 113, the resilient spring 112 is sleeved on the pull wire 111, one end of the resilient spring 112 abuts against the pull wire sleeve 113, and the other end of the resilient spring 112 abuts against the inner circumferential surface of the guide tube 102. When the pull wire 111 is pulled, the rebound spring 112 is compressed, and the guide tube 102 is bent; when the pull wire 111 is not stressed, the rebound spring 112 is restored, and the guide tube 102 is restored to the original state.

In order to better realize the bending of one end of the guide tube 102 close to the ablation electrode head 101, the guide tube 102 comprises a bending adjusting guide tube 114 and a main guide tube 115, the bending adjusting guide tube 114 is made of bendable material, the outer ring 108 of the ablation electrode head 101 is inserted into one end of the bending adjusting guide tube 114, the other end of the bending adjusting guide tube 114 is fixed with one end of the main guide tube 115, and the other end of the main guide tube 115 is used for being inserted into the catheter handle 200. When the material of the bending adjusting catheter 114 is selected, the material which is easier to bend is selected, so that the ablation electrode head 101 can be bent better.

As shown in fig. 8, the ablation electrode catheter 100 further includes an electrode lead 116, the electrode lead 116 is connected to the electrode 104, and the electrode lead 116 passes through the outer ring 108 and the guide tube 102. Electrode leads 116 are used to connect the electrodes 104 to the electrode control elements.

The guide tube 102 is divided into at least two independent channels, the two independent channels are a lead channel and a pull line channel respectively, the electrode lead 116 passes through the lead channel, and the pull line 111 passes through the pull line channel. The cross section of the wire passage is eccentric, which can provide eccentric force for the wire 111.

As shown in fig. 9 to 12, when the ablation electrode catheter 100 is attached to the catheter handle 200, the guide tube 102 is held by the catheter holding structure 201 and then attached to the handle housing 202. Specifically, the catheter clamping structure 201 comprises a catheter clamping element 203, a catheter pushing element 204 and a pushing element head 205, wherein the catheter clamping element 203 comprises a first connecting pipe 206 and a plurality of clamping sheets 207 arranged on the end surface of the first connecting pipe 205, and a first insertion hole 208 is formed in the middle of the plurality of clamping sheets 207; the end face of the catheter pusher 204 forms a first connection hole 209, and the first connection tube 205 is inserted into the first connection hole 209; the pusher head 205 is fitted over the end of the catheter pusher 204, the pusher head 205 surrounds the catheter clamp 203, the pusher head 205 is provided with a second insertion hole 210 communicating with the first insertion hole 208, and the second insertion hole 210 and the first insertion hole 208 are used for accommodating the guide tube 102.

Wherein, the catheter pusher 204 and the pusher head 205 can be connected by threads. When the guide tube 102 needs to be installed, the guide tube 102 passes through the second insertion hole 210 of the pushing element head 205 and the first insertion hole 208 of the catheter clamping element 203 in sequence, and then the pushing element head 205 is rotated to connect the pushing element head 205 with the catheter pushing element 204. The plurality of gripping tabs 207 of the catheter crimp 203 are tightened under compression by the pusher head 205, thereby gripping the guide tube 102.

As shown in fig. 14 to 15, in order to better grip the guide tube 102, the free end of the gripping tab 207 remote from the first connection tube 205 forms an inclined surface 211, the inclined surface 211 being at an acute angle to the axis of the first connection tube 205; the inner peripheral surface of the pusher head 205 has a mating surface 212 that contacts the inclined surface 211. When the pinching pieces 207 are pressed by the pusher head 205, the pinching pieces 207 are drawn toward the center by the inclined surface 211, so that the first insertion hole 208 becomes small, and the guide tube 102 is clamped.

The outer peripheral surface of the snap tab 207 remote from the free end of the first connecting tube 205 is flared outwardly to form a flared surface 213, and the flared surface 213 intersects the inclined surface 211. The flared surface 213 and the inclined surface 211 constitute a convex reinforcing portion which secures the strength of the free end of the clamping tab 207 so that the clamping tab 207 can more stably clamp the guide tube 102.

As shown in fig. 15, the included angle α =15 ° to 60 °, such as 20 °, 30 °, 35 °, 40 °, 45 °, 50 °, 55 °, and so on, between the flaring surface 213 and the axis of the first connecting tube 205. The angle β =50 ° -90 °, such as 55 °, 60 °, 65 °, 70 °, 75 °, 80 °, 85 °, etc., between the extended surface of the flared surface 213 and the inclined surface 211, and α < β. The provision of the outwardly extending surface 213 and the inclined surface 211 within the above-mentioned angular range can facilitate the manufacture of the clip sheet 207 while ensuring the strength of the free end of the clip sheet 207.

As shown in fig. 9 to 12, the catheter retaining structure 201 is mounted on the handle housing 202, a second connecting hole 214 is formed in the handle housing 202, the catheter pushing member 204 of the catheter retaining structure 201 is inserted into the second connecting hole 214, and the first connecting hole 209 and the second connecting hole 214 form a passage for the pull wire 111 and the electrode lead 116 to pass through. In this manner, the ablation electrode catheter 100 can be coupled to the handle housing 202. During operation, the handle housing 202 is located outside the body for manipulation by the operator.

As shown in fig. 10 to 14, the outer circumferential surface of the catheter pushing member 204 is formed with a limiting groove 215, and the limiting groove 215 extends in a direction parallel to the axial direction of the catheter pushing member 204; a limiting hole 216 is formed in the handle shell 202, and the limiting hole 216 penetrates through the inner peripheral surface of the second connecting hole 214; the catheter handle 200 also includes a stop pin that can be inserted through the stop hole 216 into the stop slot 215. When the catheter pushing element 204 is inserted into the second coupling hole 214, the retaining pin is inserted through the retaining hole 216 and into the retaining slot 215, which prevents the catheter pushing element 204 from rotating within the handle housing 202.

A first groove 218 and a second groove 219 are formed on the outer peripheral surface of the catheter pushing member 204, the first groove 218 and the second groove 219 are arranged around the circumference of the catheter pushing member 204, and the limiting groove 215 is located between the first groove 218 and the second groove 219; the catheter handle 200 further includes a first sealing ring 220 and a second sealing ring 221, the first sealing ring 220 is mounted in the first groove 218, the second sealing ring 221 is mounted in the second groove 219, and the first sealing ring 220 and the second sealing ring 221 are in contact with the inner circumferential surface of the second connection hole 214. The first sealing ring 220 and the second sealing ring 221 may be made of rubber. Due to the arrangement of the first sealing ring 220 and the second sealing ring 221, a seal is formed between the catheter pushing member 204 and the handle shell 202, and blood in a human body is prevented from overflowing from the handle shell 202 to the outside.

In other embodiments, a groove may be formed at other positions on the outer circumference of the catheter pusher 204, and a sealing ring may be installed in the groove, according to the sealing requirements.

As shown in fig. 12-13, an end of the first connection hole 209 remote from the catheter clamp 203 forms an outer flare 222, and the diameter of the outer flare 222 gradually increases in a direction away from the catheter clamp 203. By providing the outer flare 222 at the end of the first connection hole 209, a larger active space can be provided for the pull wire 111 and the electrode lead 116.

As shown in fig. 12, the catheter handle 200 further includes a support fixing plate 223, and the support fixing plate 223 is fixed in the second coupling hole 214. And a support fixing plate 223 for supporting the drawing wire 111 and the electrode lead 116 so that the drawing wire 111 and the electrode lead 116 can extend to a predetermined position along a predetermined extending direction.

Specifically, the handle housing 202 further includes a wire drawing port 224, the wire drawing port 224 penetrates through the inner circumferential surface of the second connection hole 214, the support fixing plate 223 is disposed around the wire drawing port 224, a wire drawing fixing port 225 axially penetrating through the support fixing plate 223 is disposed on the support fixing plate 223, and a wire drawing passage for extending the wire drawing 111 out of the handle housing 202 is formed between the wire drawing fixing port 225 and the wire drawing port 224. The pull wire 111 passes through the pull wire fixing port 225 and the pull wire port 224 to the outside of the handle housing 202, and the pull wire 111 is limited by the pull wire fixing port 225 and the pull wire port 224 at the corner extending out of the handle housing 202.

In addition, the rear end of the handle housing 202 is provided with a generator connecting part 226, the support fixing disc 223 is positioned between the generator connecting part 226 and the catheter pushing member 204, the support fixing disc 223 is provided with an electrode lead perforation 217 which penetrates along the axial direction, and the electrode lead perforation 217 is used for enabling the electrode lead 116 to pass through and extend to the generator connecting part 226. A generator connection 226 for mounting an electrode generator, the electrode lead 116 connecting the electrode generator to the electrode 104.

According to the ablation electrode catheter assembly, the ablation electrode head 101 is better attached to the tissues at the pulmonary vein opening through the design of the shape of the ablation electrode head 101; the position of the ablation electrode head 101 can be adjusted by the design of the pull wire 111 and the rebound spring 112; through a series of designs of the catheter handle 200, the catheter handle 200 can be made to better grip the ablation electrode catheter 100 and better position the pull wire 111, the electrode lead 116 within the catheter handle 200.

In the description of the present invention, it should be noted that unless otherwise explicitly stated or limited, the terms "mounted," "connected," and "connected" are to be construed broadly, e.g., as being connected, detachably connected, or integrally connected; can be mechanically or electrically connected; they may be connected directly or indirectly through intervening media, or they may be interconnected between two elements. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art through specific situations.

It is obvious to a person skilled in the art that the invention is not restricted to details of the above-described exemplary embodiments, but that it can be implemented in other specific forms without departing from the spirit or essential characteristics of the invention. The present embodiments are therefore to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein. Any reference sign in a claim should not be construed as limiting the claim concerned.

Claims (10)

1. An ablation electrode catheter, comprising:

the ablation electrode head comprises a spiral ring, the spiral ring comprises a shaping framework and an outer ring, and the outer ring is wrapped on the shaping framework;

a guide tube, an end of the spiral ring being inserted into a port of the guide tube, the guide tube being for insertion into a catheter handle;

one end of the pull wire is connected with the end part of the shaping framework, and the other end of the pull wire penetrates out of the guide pipe;

the rebound spring is installed in the guide tube and always applies a force to the pull wire in the direction of the ablation electrode head.

2. The ablation electrode catheter of claim 1, wherein the shaped skeleton is made of a shape memory alloy, and an original shape of the shaped skeleton conforms to a shape of the helical ring in an unstressed state.

3. The ablation electrode catheter of claim 1, wherein the ablation electrode tip further comprises an electrode located on an outer peripheral surface of the outer ring.

4. The ablation electrode catheter of claim 3, wherein the number of said electrodes is 2N, N being a natural number of 3 to 8; the electrodes comprise positive electrodes and negative electrodes, and the positive electrodes and the negative electrodes are arranged in a crossed mode.

5. The ablation electrode catheter of claim 3, wherein the pulsed electric field discharges between 1 and 20 pulse bursts per discharge, each pulse burst comprising between 60 and 200 pulses; the time interval of adjacent pulse groups of the pulse electric field is 500-3000ms.

6. The ablation electrode catheter of claim 3 further comprising an electrode wire connected to the electrode, the electrode wire passing through the outer ring, guide tube.

7. The ablation electrode catheter of claim 6, wherein a lead passage is provided in the guide tube, the electrode lead passing through the lead passage.

8. The ablation electrode catheter of claim 1, further comprising a wire pulling sleeve, wherein the fixing frame and the wire pulling sleeve are fixed to two ends of the wire pulling sleeve respectively, the rebound spring is sleeved on the wire pulling sleeve, one end of the rebound spring abuts against the wire pulling sleeve, and the other end of the rebound spring abuts against the inner circumferential surface of the guide tube.

9. The ablation electrode catheter of claim 8, wherein a pull wire passage is provided in said guide tube, said pull wire passing through said pull wire passage, said pull wire passage having an eccentric shape in cross section.

10. The ablation electrode catheter of claim 1, wherein the guide tube comprises a bending guide tube and a main guide tube, the bending guide tube is made of a bendable material, the outer ring of the ablation electrode head is inserted into one end of the bending guide tube, the other end of the bending guide tube is fixed with one end of the main guide tube, and the other end of the main guide tube is inserted into the catheter handle.

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