CN111887981A - Ablation electrode and ablation catheter - Google Patents

Abstract

The invention provides an ablation electrode and an ablation catheter. The ablation electrode is used to generate radio frequency current to perform radio frequency ablation treatment on the lesion. The ablation electrode has a chamber, an injection port communicating with the chamber, and a plurality of cooling holes. The injection port is injected into the chamber and sprayed out from the cooling hole to cool the ablation electrode; the outer surface of the ablation electrode is provided with a cooling hole and a groove, wherein the groove is also provided with a cooling hole. According to the ablation electrode of the present invention, by arranging grooves on the outer surface of the ablation electrode, the effective heat dissipation area of the ablation electrode can be increased without increasing the volume of the ablation electrode, and the heat dissipation and cooling effect of the ablation electrode can be improved. Moreover, the outer surface of the ablation electrode includes a plurality of cooling holes in the groove, and the cooling liquid can be sprayed through the cooling holes to cool the ablation electrode, thereby further improving the cooling effect of the ablation electrode, thereby improving the operation efficiency. reliability and security.

Description

Ablation electrodes and catheters

technical field

The present invention relates to the technical field of medical equipment, in particular to an ablation electrode and an ablation catheter.

Background technique

Catheter radiofrequency ablation is the most commonly used minimally invasive interventional technology for the treatment of arrhythmia. For the abnormal origin of the lesion, the cylindrical ablation electrode at the tip of the catheter is contacted with the lesion tissue with an effective contact force, and then radio frequency current is emitted through the return electrode attached to the skin of the patient's body surface. The radiofrequency current flows through the focal tissue under the electrode through the electrode, and generates heat in the tissue. When the temperature reaches the level of coagulation necrosis, the tissue will permanently lose its electrophysiological activity, and the arrhythmia can be cured.

When the ablation electrode sends an electric current to cause tissue heat generation, it is passively heated due to the heating of the tissue due to the thermally conductive and endothermic properties of the electrode material. Once the electrode is overheated and the blood circulation around it is insufficiently cooled, it is prone to scabbing, carbon deposition, and even knocking of the tissue under the electrode. In this way, on the one hand, the impedance between the electrode and the tissue is increased, which affects the depth and effect of ablation; on the other hand, complications such as embolism and perforation are also caused.

In order to prevent the ablation electrode from overheating, in the related art, the method of unidirectional circulating saline spray cooling is mostly adopted to cool the ablation electrode. At the same time, by controlling the number of spray holes on the electrode surface, the cooling effect and the amount of saline perfusion per unit time can be adjusted. However, the above-mentioned related technical solutions have the problems of large input of cooling brine and poor cooling effect.

SUMMARY OF THE INVENTION

The technical problem to be solved by the present invention is how to improve the cooling effect of the ablation electrode of the ablation catheter. The present invention provides an ablation electrode and an ablation catheter.

According to the ablation electrode of the embodiment of the present invention, the ablation electrode is used for generating radio frequency current to perform radio frequency ablation treatment on the lesion, and the ablation electrode has a chamber, an injection port communicating with the chamber and a plurality of cooling holes, Cooling liquid is injected into the chamber through the injection port and sprayed from the cooling hole to cool the ablation electrode;

The cooling holes and grooves are provided on the outer surface of the ablation electrode, wherein the cooling holes are also provided in the grooves.

According to the ablation electrode of the embodiment of the present invention, by arranging grooves on the outer surface of the ablation electrode, the outer surface area of the ablation electrode can be increased without increasing the volume of the ablation electrode, thereby increasing the effective heat dissipation area of the ablation electrode, The heat dissipation and cooling effect of the ablation electrode is improved. Moreover, the outer surface of the ablation electrode includes a plurality of cooling holes in the groove, and the cooling liquid can be sprayed through the cooling holes to cool the ablation electrode, thereby further improving the cooling effect of the ablation electrode, thereby improving the operation efficiency. reliability and security.

According to some embodiments of the present invention, the ablation electrode is cylindrical, the groove is provided on a side surface of the ablation electrode, and the groove is an annular groove provided along the circumferential direction of the ablation electrode .

In some embodiments of the present invention, along the axial direction of the ablation electrode, a plurality of the annular grooves are provided at intervals.

According to some embodiments of the present invention, the cooling holes include:

a spray cooling hole, the spray cooling hole is located in the groove, and the cooling liquid in the cavity is sprayed out in a mist form through the spray cooling hole;

A jet cooling hole, the jet cooling hole is located on the side surface of the ablation electrode except the groove, and the cooling liquid in the chamber is ejected in a ray shape through the jet cooling hole.

In some embodiments of the present invention, the spray cooling holes and the jet cooling holes are a plurality of uniformly spaced apart along the circumferential direction of the ablation electrode, and the diameter of the spray cooling holes is smaller than that of the jet cooling holes hole diameter.

According to some embodiments of the present invention, the top wall and the side wall of the ablation electrode are provided with a plurality of temperature sensors for detecting the temperature of the ablation electrode.

An ablation catheter according to an embodiment of the present invention includes:

an ablation electrode, the ablation electrode is the ablation electrode described above;

a tube body, and the ablation electrode is connected to the end of the tube body.

According to the ablation catheter of the embodiment of the present invention, grooves are provided on the outer surface of the ablation electrode at the head end of the tube body, which can increase the outer surface area of the ablation electrode without increasing the volume of the ablation electrode, thereby increasing the effective heat dissipation of the ablation electrode area, which improves the heat dissipation and cooling effect of the ablation electrode. Moreover, the outer surface of the ablation electrode includes a plurality of cooling holes in the groove, and the cooling liquid can be sprayed through the cooling holes to cool the ablation electrode, thereby further improving the cooling effect of the ablation electrode, thereby improving the operation efficiency. reliability and security.

According to some embodiments of the present invention, the ablation catheter further comprises:

Piezoelectric component, the piezoelectric component is arranged in the tube body, and when the ablation electrode is in contact with the lesion site, a part of the piezoelectric component is deformed under pressure, and generates a contact for obtaining the tip end of the ablation electrode Force piezo current.

In some embodiments of the present invention, the piezoelectric assembly includes:

a piezoelectric spring disposed adjacent to the ablation electrode;

A piezoelectric reed, the piezoelectric reed is located at one end of the piezoelectric spring away from the ablation electrode, and is in contact with the piezoelectric spring. When the ablation electrode is in contact with the lesion, the Both the piezoelectric spring and the piezoelectric reed are deformed under pressure, and the piezoelectric current is generated;

an insulating heat shield, the insulating heat shield is located between the ablation electrode and the piezoelectric spring;

a base, the base is located at one end of the piezoelectric spring away from the piezoelectric spring, and is used for fixing the piezoelectric spring.

According to some embodiments of the present invention, the ablation catheter further comprises: a flow tube, the flow tube communicates with the injection port, and is used for injecting a cooling liquid into the cavity.

Description of drawings

FIG. 1 is a schematic structural diagram of an ablation electrode according to an embodiment of the present invention;

FIG. 2 is a partial structural cross-sectional view of an ablation electrode according to an embodiment of the present invention;

3 is a top view of an ablation electrode according to an embodiment of the present invention;

4 is a schematic structural diagram of an ablation catheter according to an embodiment of the present invention;

5 is an axial cross-sectional view of a partial structure of an ablation catheter according to an embodiment of the present invention;

6 is a transverse cross-sectional view of an ablation catheter according to an embodiment of the present invention;

7 is an exploded view of a partial structure of an ablation catheter according to an embodiment of the present invention;

8 is a schematic structural diagram of an ablation catheter according to an embodiment of the present invention;

9 is a schematic diagram of the principle of calculating the contact force according to the quadrilateral rule according to an embodiment of the present invention;

FIG. 10 is a schematic diagram of the force of a piezoelectric reed according to an embodiment of the present invention;

FIG. 11 is a schematic diagram of the force of a piezoelectric spring according to an embodiment of the present invention;

12 is a schematic diagram of a process for calculating a contact force according to the quadrilateral rule according to an embodiment of the present invention;

FIG. 13 is a schematic diagram illustrating the calculation principle of the contact force of the tip end of the ablation catheter according to an embodiment of the present invention.

Reference number:

ablation catheter 100,

Ablation electrode 10, chamber V1, injection port 110, cooling hole 120, spray cooling hole 121, jet cooling hole 122, groove 130, temperature sensor 140,

Tube body 20, marking surface S1, piezoelectric spring 30, insulating sheet 40, base 50, piezoelectric reed 60, flow tube 70, handle 80, tail wire 90,

The first annular electrode 101 , the second annular electrode 102 , the third annular electrode 103 , the positioning chip 104 , the pulling wire 105 , the three-dimensional visual electrode 106 , and the lead wire 107 .

Detailed ways

In order to further illustrate the technical means and effects adopted by the present invention to achieve the predetermined purpose, the present invention will be described in detail below with reference to the accompanying drawings and preferred embodiments.

In the related art, the use of saline irrigation to cool the radiofrequency ablation catheter has the following disadvantages:

Limited by the size of the side area of the cylindrical ablation electrode at the catheter tip, although the number of holes for external saline spray is continuously increased, the cooling efficiency is still not high. Under the premise of a certain side area of the cylindrical ablation electrode, in order to achieve a better cooling effect, it is necessary to increase the flow rate of saline perfusion. The current perfusion flow of the 12-hole radiofrequency ablation catheter is 17ml/min, and the perfusion flow of the 56-hole radiofrequency ablation catheter is 8ml/min. In this way, 1000-3000ml of saline is required for the 3-hour surgical procedure. Significantly increase the burden on the patient's heart, there is a risk of induced heart failure.

In view of the above-mentioned defects of the ablation catheter in the related art, the present invention provides an ablation electrode and an ablation catheter.

According to the ablation electrode 10 of the embodiment of the present invention, the ablation electrode 10 is used to generate radio frequency current, so as to perform radio frequency ablation treatment on the lesion. As shown in FIG. 1 and FIG. 2 , the ablation electrode 10 has a chamber V1, an injection port 110 communicating with the chamber V1, and a plurality of cooling holes 120. The cooling liquid is injected into the chamber V1 through the injection port 110 and sprayed from the cooling holes 120 to The ablation electrode 10 is cooled. The outer surface of the ablation electrode 10 is provided with a cooling hole 120 and a groove 130 , wherein the cooling hole 120 is also provided in the groove 130 .

According to the ablation electrode 10 of the embodiment of the present invention, by providing the groove 130 on the outer surface of the ablation electrode 10, the outer surface area of the ablation electrode 10 can be increased without increasing the volume of the ablation electrode 10, thereby increasing the ablation electrode The effective heat dissipation area 10 improves the heat dissipation and cooling effect of the ablation electrode 10 . Moreover, the outer surface of the ablation electrode 10 includes a plurality of cooling holes 120 in the groove 130 , and the cooling liquid can be sprayed through the cooling holes 120 to cool the ablation electrode 10 , thereby further improving the cooling effect of the ablation electrode 10 , thereby improving the reliability and safety of the operation.

According to some embodiments of the present invention, as shown in FIGS. 1 and 2 , the ablation electrode 10 is cylindrical, the grooves 130 are provided on the side surface of the ablation electrode 10 , and the grooves 130 are provided along the circumferential direction of the ablation electrode 10 . Annular groove 130 . It should be noted that, by arranging the circumferential annular groove 130 on the outer surface of the ablation electrode 10 , the processing and manufacture of the groove 130 is facilitated, and the production cost of the ablation electrode 10 is reduced. Moreover, the area of the groove 130 can be increased, and the cooling and heat dissipation effect of the ablation electrode 10 can be improved.

In some embodiments of the present invention, along the axial direction of the ablation electrode 10, a plurality of annular grooves 130 are provided at intervals. It can be understood that, by providing a plurality of annular grooves 130 , the effective heat dissipation area of the ablation electrode 10 can be further increased, thereby further improving the cooling and heat dissipation effect of the ablation electrode 10 .

According to some embodiments of the present invention, as shown in FIG. 1 , the cooling holes 120 include: spray cooling holes 121 and jet cooling holes 122 .

The spray cooling hole 121 is located in the groove 130 , and the cooling liquid in the chamber V1 is sprayed out through the spray cooling hole 121 in the form of a mist. The jet cooling hole 122 is located on the side surface of the ablation electrode 10 except for the groove 130 , and the cooling liquid in the chamber V1 is ejected in a ray-like manner through the jet cooling hole 122 .

It should be noted that, when the ablation electrode 10 is cooled and cooled, the cooling liquid in the chamber V1 can be sprayed from the spray cooling hole 121 in a mist form, so as to increase the spray range of the cooling liquid and improve the cooling and cooling effect; The cooling liquid in the chamber V1 can also be ejected in a ray-like manner through the jet cooling holes 122 to drive the surrounding blood to flow and accelerate the cooling and heat dissipation efficiency of the ablation electrode 10 .

In some embodiments of the present invention, as shown in FIG. 1 and FIG. 2 , the spray cooling holes 121 and the jet cooling holes 122 may be multiple evenly spaced along the circumferential direction of the ablation electrode 10 , thereby improving the The uniformity of the cooling liquid injection can improve the uniformity of the heat dissipation of the ablation electrode 10 . The diameter of the cooling hole 120 of the spray cooling hole 121 is smaller than that of the jet cooling hole 122 . For example, the diameter of the spray cooling hole 121 may be less than 50um, and the diameter of the jet cooling hole 122 may be less than 100um.

According to some embodiments of the present invention, as shown in FIG. 3 , the top wall and the side wall of the ablation electrode 10 are provided with a plurality of temperature sensors 140 for detecting the temperature of the ablation electrode 10 . Thus, the temperature of each part of the ablation electrode 10 can be acquired in real time, so that when the temperature reaches a preset value, the ablation electrode 10 is cooled by spraying cooling liquid.

As shown in FIGS. 4-7 , an ablation catheter 100 according to an embodiment of the present invention includes an ablation electrode 10 and a tubular body 20 .

The ablation electrode 10 is the ablation electrode 10 described above, and the ablation electrode 10 is connected to the end of the tube body 20 .

According to the ablation catheter 100 of the embodiment of the present invention, the groove 130 is provided on the outer surface of the ablation electrode 10 at the head end of the tube body 20 , which can increase the outer surface area of the ablation electrode 10 without increasing the volume of the ablation electrode 10 , thereby increasing the The effective heat dissipation area of the ablation electrode 10 is increased, and the heat dissipation and cooling effect of the ablation electrode 10 is improved. Moreover, the outer surface of the ablation electrode 10 includes a plurality of cooling holes 120 in the groove 130 , and the cooling liquid can be sprayed through the cooling holes 120 to cool the ablation electrode 10 , thereby further improving the cooling effect of the ablation electrode 10 , thereby improving the reliability and safety of the operation.

According to some embodiments of the present invention, the ablation catheter 100 further includes: a piezoelectric component, the piezoelectric component is arranged in the tube body 20 , when the ablation electrode 10 is in contact with the lesion site, part of the piezoelectric component is deformed under pressure, and produces a The piezo-variable current is used to obtain the contact force of the tip end of the ablation electrode 10 .

It should be noted that, in the related art, the display of the magnitude and direction of the contact force at the tip of the ablation catheter is inaccurate and intuitive, and the arrow indication of the contact force at the tip of the catheter can only indicate the direction of the contact force, neither the magnitude nor the contact force. changes and warning values, which affect the conduct of surgery. In the ablation catheter 100 proposed by the present invention, when the ablation electrode 10 is in contact with the lesion during the ablation operation, the piezoelectric component will be deformed under pressure to generate a piezocurrent. According to the magnitude of the piezocurrent, the ablation electrode 10 and the lesion can be obtained by calculation. Therefore, it is convenient for the operator to control the contact state of the ablation catheter 100 .

In some embodiments of the present invention, as shown in FIG. 5 and FIG. 7 , the piezoelectric assembly includes: a piezoelectric spring 30 , a piezoelectric spring 60 , an insulating heat shield 40 and a base 50 .

The piezoelectric spring 30 is disposed adjacent to the ablation electrode 10, and the piezoelectric spring 60 is located at one end of the piezoelectric spring 30 away from the ablation electrode 10, and offsets with the piezoelectric spring 30. When the ablation electrode 10 offsets the lesion, the piezoelectric Both the spring 30 and the piezoelectric reed 60 are compressed and deformed, and a piezo-variable current is generated.

The insulating and heat insulating sheet 40 is located between the ablation electrode 10 and the piezoelectric spring 30. By disposing the insulating heat insulating sheet 40, the temperature conduction of the ablation electrode 10 and the radio frequency current of the ablation electrode 10 can be isolated and blocked, and the piezoelectric spring 30 can be fixed. . The base 50 is located at one end of the piezoelectric reed 60 away from the piezoelectric spring 30 for fixing the piezoelectric reed 60 .

It should be noted that there are many factors affecting the ablation effect and efficiency of the ablation catheter 100 , mainly including: energy, time parameters, surface area of the ablation electrode 10 , and contact force between the ablation electrode 10 and the tissue. The energy and time parameters can be adjusted by controlling the radio frequency instrument, and the surface area of the ablation electrode 10 can be adjusted by controlling the outer diameter of the ablation catheter 100 and the length of the ablation electrode 10 . However, the adjustment of the contact force between the ablation electrode 10 and the tissue is more difficult. The current solution is to set a pressure sensor at the head end of the ablation catheter to sense the magnitude and direction of the contact force at the head end of the ablation catheter. The advantage of these sensors is that the measurement of the magnitude and direction of the axial contact force of the catheter is relatively accurate, but the measurement accuracy of the magnitude and direction of the lateral contact force is poor.

In the present invention, when calculating the contact force of the ablation electrode 10 by the piezoelectric component, the quadrilateral rule shown in FIG. 9 can be used. Combined with Figures 10-13, the calculation principles and methods are as follows:

The calculation principle of the magnitude and direction of the contact force of the ablation catheter 100 is calculated according to the pressure bearing of the piezoelectric reed 60:

As shown in Fig. 10, the forces of the four piezoelectric reeds 60 A, B, C, and D are f1, f2, f3 and f4, respectively. As shown in Fig. 12, the magnitude and direction of the resultant force are calculated in sequence to obtain f1. The resultant force of +f2+f3+f4 is added to the axial force f5 of the piezoelectric spring 30 shown in FIG. 11 to obtain the total resultant force f1+f2+f3+f4+f5 of the ablation catheter 100 . A display connected to the ablation catheter 100 can display the magnitude and direction of the total resultant force f1+f2+f3+f4+f5 in real time.

The calculation and display principle of the contact force angle is shown in Figure 13:

Taking the plane of the head end of the ablation electrode 10 as the reference plane to calculate the axial angle a, the plane of the head end of the ablation catheter 100 is 0 degrees, the axial extension line of the ablation catheter 100 is 90 degrees, and the axial angle ranges from 0 to 90 degrees. Taking the marking surface S0 of the head end of the ablation catheter 100 as a reference to calculate the circumferential angle b, the reference plane of the head end of the ablation catheter 100 is 0 degrees, and it is rotated in a clockwise direction until it returns to the reference plane by 360 degrees.

According to some embodiments of the present invention, as shown in FIG. 4 and FIG. 5 , the ablation catheter 100 further includes: a flow tube 70 , and the flow tube 70 communicates with the injection port 110 for injecting the cooling liquid into the chamber V1 . It should be noted that one end of the circulation pipe 70 is connected to the injection port 110 of the chamber V1, and the other end extends out of the body to communicate with the cooling liquid supply device. The cooling liquid supply device can inject the cooling liquid into the chamber V1 through the circulation pipe 70.

The ablation catheter 100 according to the present invention will be described in detail below with reference to the accompanying drawings in a specific embodiment. It should be understood that the following description is only an exemplary description, rather than a specific limitation of the present invention.

As shown in FIGS. 4-7 , the ablation catheter 100 includes: a tube body 20 , an ablation electrode 10 , a piezoelectric component, a flow tube 70 , a positioning chip 104 , a first annular electrode 101 , a second annular electrode 102 , and a third annular electrode 102 . The ring electrode 103 , the traction wire 105 , the handle 80 , the three-dimensional visual electrode 106 , the lead 107 and the tail wire 90 .

Wherein, the ablation electrode 10 is a cylindrical electrode, which is located at the head end of the tube body 20 and is used to emit radio frequency current for ablation. The ablation electrode 10 can be self-cooled by spraying cooling saline. The diameter of the ablation electrode 10 can be 6F (2.00mm), 8F (2.67mm), 10F (3.34mm), 12F (4.00mm), which is convenient for the operator to choose according to the actual application.

The ablation electrode 10 has a chamber V1, an injection port 110 communicating with the chamber V1 and a plurality of cooling holes 120. A temperature sensor 140 is provided on the top of the chamber V1 for sensing the temperature change of the head end of the ablation electrode 10 during ablation.

The side surface of the ablation electrode 10 is provided with a plurality of annular grooves 130 at intervals along the axial direction.

A plurality of spray cooling holes 121 are evenly spaced in the groove 130 with a diameter of less than 50um, which are used to spray cooling saline to the surface of the ablation electrode 10 in a cloudy mist shape, and form a circulating cooling with the blood around the ablation electrode 10 to enhance the one-way circulation cooling effect.

The cooling saline injection port 110 is located at the tail of the ablation electrode 10 , and communicates with the chamber V1 of the ablation electrode 10 , and is used to deliver the cooling saline into the ablation electrode 10 . According to the number (more than 120) and distribution of the cooling holes 120 , the cooling saline is injected into the chamber V1 at a saline flow rate within 5 ml/min to ensure the cooling effect on the ablation electrode 10 .

A jet cooling hole 122 is provided on the side of the ablation electrode 10 except for the groove 130, with a diameter of 100 μm or less. Regularly distributed on the surface of the ablation electrode 10 , it is used to spray cooling saline into the surrounding blood to form a circulating cooling with the blood around the ablation electrode 10 .

As shown in FIG. 5 and FIG. 7 , the piezoelectric assembly includes: a piezoelectric spring 30 , an insulating heat shield 40 , a piezoelectric spring 60 and a base 50 .

Wherein, the piezoelectric spring 30 is located between the ablation electrode 10 and the piezoelectric spring 60 , and an insulating and heat insulating sheet 40 is provided between the piezoelectric spring 30 and the ablation electrode 10 . The insulating and heat-insulating sheet 40 is in the shape of a ring, and there is a cooling salt water injection hole in the middle. The insulating and heat insulating sheet 40 is used to insulate the radio frequency current of the ablation electrode 10 , block the heat conduction of the ablation electrode 10 , and fix the piezoelectric spring 30 . The surface of the piezoelectric spring 30 is insulated to sense the fine pressure change in the axial direction of the ablation electrode 10 .

As shown in FIG. 10 , the piezoelectric reed 60 is composed of four polygonal reeds in an array, and the four reeds are arranged axially symmetrically along the axis of the tube body 20 . There is a perfusion hole in the center of the piezoelectric reed 60, and a perfusion slot is formed between two adjacent reeds. The base 50 is used to support and fix the array of piezoelectric reeds 60 . The surface of the piezoelectric spring 60 is insulated for sensing the axial and lateral pressures conducted by the piezoelectric spring 30 .

As shown in Figure 9-12, the resultant force of the pressure on each two reeds can be calculated using the parallelogram rule. The final resultant force is used together with the axial pressure of the piezoelectric spring 30 to calculate the contact vector, which guides the tissue contact of the ablation electrode 10 and the execution of the ablation procedure.

The positioning chip 104 is disposed near the base 50, and the positioning chip 104 is used for three-dimensional spatial positioning of the catheter tip.

The first annular electrode 101 is located on the surface of the tube body 20 near the piezoelectric spring 30. The width of the first annular electrode 101 is within 2 mm and the thickness is within 0.3 mm. The first annular electrode 101 cooperates with the ablation electrode 10 to record the ablation catheter. 100 distal bipolar potential.

The second annular electrode 102 and the third annular electrode 103 are located at the head end of the tube body 20 to form a proximal electrode pair. The widths of the second annular electrodes 102 and the third annular electrodes 103 are both within 2 mm, and the thicknesses are both within 0.3 mm. The distance between the second annular electrode 102 and the third annular electrode 103 is within 5 mm, and is used to record the bipolar potential of the proximal end of the ablation catheter 100 .

The tube body 20 includes a flexible section of the tube body, which is located between the ablation electrode 10 and the first annular electrode 101 , and is used to control the lateral deformation of the head end of the ablation catheter 100 .

The tube body 20 is provided with a traction wire 105. The traction wire 105 is matched with the handle 80 and the sliding handle, and the head end of the catheter is bent in one direction, and the maximum bending degree is 360 degrees. The head end of the ablation catheter 100 has a three-dimensional indication mark of the curved plane, and the head end of the handle 80 has the indication mark of the curved plane.

As shown in FIG. 8 , the tail of the ablation catheter 100 is provided with a tail wire 90 for connecting to the host. A three-dimensional visual electrode 106 is arranged in the tube body 20. Starting from 10 cm from the head end of the ablation catheter 100, more than 1 three-dimensional visual electrode 106 is set at a distance of more than 5 cm, which is used to display the tube body of the catheter head end on the three-dimensional map. .

The bending plane indication mark of the head end of the ablation catheter 100 is located at the head end of the handle 80 , and is used to indicate the bending plane of the head end of the ablation catheter 100 .

As shown in FIG. 13, the calculation and three-dimensional display of the contact vector of the head end of the ablation catheter 100: cooperate with the host to calculate the contact angle between the head end of the ablation catheter 100 and the tissue: (1) the axial angle a, the angle range is 0-90 degrees, to ablate The plane of the head end of the electrode 10 is 0 degrees, and the extension line of the central axis of the head end of the ablation catheter 100 is 90 degrees. (2) Tube circumference angle b: the angle range is 0-360 degrees, and the bending plane of the head end of the ablation catheter 100 is 0 degrees, and the clockwise direction reaches 360 degrees.

The working flow and principle of the ablation catheter 100 of the present invention are as follows:

S1, connect the tail line 90 of the ablation catheter 100, connect the saline irrigation pipe joint, and fully exhaust the gas.

S2, the tip end of the ablation catheter 100 is ablated into the predetermined heart cavity through the pre-placed long sheath.

S3, balance the contact pressure zero point, and display the contact vector arrows of the body of the ablation catheter 100 and the head end of the ablation catheter 100 on the three-dimensional image of the predetermined cardiac cavity.

S4, confirming that the magnitude and direction of the contact vector of the tip end of the ablation catheter 100 are within a preset safe range.

S5, the head end of the ablation catheter 100 is bent through the handle 80, and the ablation catheter 100 is advanced at the same time, so that the ablation electrode 10 at the head end contacts the endocardial tissue.

S6 , the piezoelectric spring 30 at the head end of the ablation catheter 100 is deformed due to the reaction force of the tissue to the electrode, and a weak deformation current is generated. The magnitude of the current is proportional to the contact force, and the axial contact force is calculated by the host computer. At the same time, the axial angle a of the contact force is calculated.

S7, due to the reaction force of the tissue to the electrode, the piezoelectric spring 30 at the head end of the ablation catheter 100 is deformed, and the latter further causes the asymmetric deformation of the piezoelectric spring 60 matrix, generating weak deformation currents of different sizes. The contact force is proportional to the lateral contact force calculated by the host. At the same time, the tube circumference angle b of the contact force is calculated.

S8 , the host computer comprehensively calculates the magnitude and direction of the contact force, and displays it separately in the form of a vector arrow at the head end of the ablation catheter 100 and in the form of a screen display window.

S9 , the operator completely adjusts the positioning and contact quality of the electrode at the head end of the ablation catheter 100 by manipulating the catheter handle 80 according to the vector parameters of the head end of the ablation catheter 100 .

The ablation electrode 10 and the ablation catheter 100 proposed by the present invention solve the following problems:

1. On the premise of keeping the side area of the cylindrical ablation electrode 10 at the tip of the catheter unchanged, increase the heat dissipation area and improve the heat dissipation efficiency.

2. Make jet holes with different diameters on the side of the columnar ablation electrode 10 , and cool the vicinity of the ablation electrode 10 with cloudy saline water and around the ablation electrode 10 with a jet of saline water.

3. Increase the number of apertures on the side of the cylindrical ablation electrode 10 to more than 120, and reduce the diameter of a single aperture by more than 50%, so as to reduce the input of saline by more than 50% without reducing the existing cooling efficiency.

4. Design ablation catheters 100 with different diameters of ablation electrodes 10 and matching cooling holes 120 to increase the operator's selectivity for different patients, different parts, and different ablation efficiencies.

To sum up, the ablation catheter 100 proposed by the present invention has the following advantages:

The annular groove 130 is formed on the side of the ablation electrode 10 to increase the heat dissipation area; the cooling holes 120 with different diameters are formed on the side of the ablation electrode 10, and the adjacent parts of the ablation electrode 10 are respectively cooled with cloudy saline and ablated, and jets are applied around the electrode. Cooling by rinsing salt water improves the heat dissipation efficiency; increasing the number of apertures on the side of the ablation electrode 10 to more than 120, reducing the diameter of a single aperture by more than 50%, and reducing the input volume of saline by more than 50% without reducing the cooling efficiency; ablation catheter 100 The diameter of the ablation electrode 10 includes various models: 6F (2.00mm), 8F (2.67mm), 10F (3.34mm), 12F (4.00mm), which increases the operator's choice for different patients, different parts, and different ablation efficiencies. sex.

Through the description of the specific embodiments, it should be possible to have a more in-depth and specific understanding of the technical means and effects adopted by the present invention to achieve the predetermined purpose. However, the accompanying drawings are only for reference and description, not for the present invention. limit.

Claims (10)

1. An ablation electrode, characterized in that, the ablation electrode is used to generate a radio frequency current to perform radio frequency ablation treatment on a lesion, and the ablation electrode has a chamber, an injection port communicating with the chamber, and a plurality of cooling devices a hole, a cooling liquid is injected into the chamber through the injection port and ejected from the cooling hole to cool the ablation electrode; The cooling holes and grooves are provided on the outer surface of the ablation electrode, wherein the cooling holes are also provided in the grooves. 2 . The ablation electrode according to claim 1 , wherein the ablation electrode is cylindrical, the groove is provided on the side surface of the ablation electrode, and the groove is along the circumference of the ablation electrode. 3 . Circular grooves set in the direction. 3 . The ablation electrode according to claim 2 , wherein a plurality of the annular grooves are provided at intervals along the axial direction of the ablation electrode. 4 . 4. The ablation electrode of claim 2, wherein the cooling hole comprises: a spray cooling hole, the spray cooling hole is located in the groove, and the cooling liquid in the cavity is sprayed out in a mist form through the spray cooling hole; A jet cooling hole, the jet cooling hole is located on the side surface of the ablation electrode except the groove, and the cooling liquid in the chamber is ejected in a ray shape through the jet cooling hole. 5 . The ablation electrode according to claim 4 , wherein the spray cooling holes and the jet cooling holes are a plurality of uniformly spaced apart along the circumferential direction of the ablation electrode, and the spray cooling holes The pore size is smaller than the pore size of the jet cooling hole. 6 . The ablation electrode according to claim 1 , wherein a plurality of temperature sensors are provided on the top wall and the side wall of the ablation electrode for detecting the temperature of the ablation electrode. 7 . 7. An ablation catheter, characterized in that, comprising: an ablation electrode, the ablation electrode is the ablation electrode according to any one of claims 1-6; a tube body, and the ablation electrode is connected to the end of the tube body. 8. The ablation catheter of claim 7, wherein the ablation catheter further comprises: Piezoelectric component, the piezoelectric component is arranged in the tube body, when the ablation electrode is in contact with the lesion site, a part of the piezoelectric component is deformed under pressure, and generates a contact for obtaining the tip end of the ablation electrode Force piezo current. 9. The ablation catheter of claim 8, wherein the piezoelectric assembly comprises: a piezoelectric spring disposed adjacent to the ablation electrode; A piezoelectric reed, the piezoelectric reed is located at one end of the piezoelectric spring away from the ablation electrode, and is in contact with the piezoelectric spring. When the ablation electrode is in contact with the lesion site, the Both the piezoelectric spring and the piezoelectric reed are deformed under pressure, and the piezoelectric current is generated; an insulating heat shield, the insulating heat shield is located between the ablation electrode and the piezoelectric spring; a base, the base is located at one end of the piezoelectric spring away from the piezoelectric spring, and is used for fixing the piezoelectric spring. 10 . The ablation catheter according to claim 8 or 9 , wherein the ablation catheter further comprises: a flow tube, the flow tube communicates with the injection port, and is used for injecting cooling liquid into the cavity. 11 .

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