Atrioventricular Valve Tissue Ablation Catheter and Method

This application is related to U.S. patent application Ser. No. 08/429,429 filed May 1, 1995 for DUAL CURVE ABLATION CATHETER AND METHOD and now abandoned, the disclosure of which is incorporated by reference.

It has long been known that the action of the heart depends upon electrical signals carried within the heart tissue. Sometimes these electrical signals become faulty. It has been found that ablating (burning) these cardiac conduction pathways in the region of the problem destroys the tissue to eliminate the faulty signal.

Electrophysiology (EP) catheters are catheters having one or more electrodes at their tips and are used for both diagnosis and therapy. The electrodes at the tips of EP catheters allow the physician to measure electrical signals along the surface of the heart (called mapping) and then, when necessary, ablate certain tissue using, typically, radio frequency (RF) energy directed to one or more high energy capable ablation electrodes.

The present invention is directed to an EP ablation catheter especially suited for ablating heart tissue on either side of the annulus of an atrioventricular (AV) valve. This technique could be useful to terminate a tachycardia caused by an accessory pathway from atrial to ventricular tissue. Some of these accessory pathways fall into the group "Mahaim fibers," commonly found on the right side of the heart at the right atrioventricular valve, also known as the tricuspid valve. However, the catheter could also be useful at the left side of the heart at the left atrioventricular valve, also called the mitral valve. The electrodes are potentially useful for mapping Mahaim fibers along the ventricular wall, or for mapping other regions of the heart. The catheter is designed to remain in place and provide firm electrode contact during mapping and ablation despite respiratory, cardiac or blood motion during the ablation.

The ablation catheter includes a shaft having proximal and distal ends with a deflectable tip at the distal end and a handle at the proximal end. Pulling on a manipulator wire, passing through a lumen in the shaft and attached to the distal end of the shaft, causes the proximal segment of the tip to curve. The distal segment can be preformed to create the desired hook or lip-shaped curvature; the distal end can also be curved using a manipulator wire as well. The proximal and distal segments curve in opposite directions so that when properly positioned, the proximal curve segment is passed through the AV valve to help stabilize the catheter and to place mapping electrodes against ventricular tissue. The distal segment engages the tissue at the annulus of the AV valve to be ablated. Ablation energy is preferably supplied through two ablation electrodes, preferably one at a time, to ablate the tissue on either side of the annulus of the AV valve without the need for moving the catheter back and forth across the valve, once in position.

A rotatable core wire, passing the central lumen and secured to the tip of the shaft, may be used to permit a torquing force to be applied to the distal end of the shaft without rotating the entire catheter. The temperature of the ablation electrodes is preferably monitored, such as using thermocouple wires, to permit enhanced control over the ablation temperatures.

One of the advantages of the invention is achieved when a series of ablation electrodes instead of one long electrode is used to ablate the cardiac tissue. Making the ablation electrodes electrically isolated from one another and allowing them to be individually powered permits a lower power ablation energy source to be used than would be required if the multiple ablation electrodes were replaced by one long electrode or if the multiple ablation electrodes were all powered simultaneously. Also, the use of multiple electrodes allows bipolar recording to be conducted. Of course, if a power source has sufficient capacity to simultaneously power more than one ablation electrode, this can be done also.

Other features and advantages of the invention will appear from the following description in which the preferred embodiment has been discussed in detail in conjunction with the accompanying drawings.

FIG. 1 is an overall view of an atrioventricular valve tissue ablation catheter made according to the invention;

FIG. 1A is a simplified view of the tip of the catheter showing the movement of the proximal segment from the straight, dashed line position to the curved, solid line position;

FIG. 1B is similar to FIG. 1A but shows the movement of the distal segment from the straight, dashed line position to the curved, solid line position;

FIG. 1C shows the lateral deflection of the catheter tip of FIG. 1B from the solid line position to the dashed line positions;

FIG. 2 is a simplified view showing placement of the tip of the catheter of FIG. 1 with the curved proximal segment extending from the right atrium through the tricuspid valve and into the right ventricle, and with the recurved distal segment extending from the right ventricle to engage the annulus of the tricuspid valve;

FIGS. 3A and 3B are enlarged longitudinal cross-sectional views of a portion of the tip of the catheter of FIG. 1 omitting the electrical conductor and thermocouple wires passing through the central lumen of the body of the catheter shaft and showing one ablation-capable tip electrode in FIG. 3A and one ablation-capable band electrode and two mapping electrodes in FIG. 3B;

FIG. 3C is an enlarged transverse cross-sectional view of a segment of the catheter shaft taken along line 3C--3C of FIG. 1;

FIGS. 3D and 3E are transverse cross-sectional views taken along lines 3D--3D and 3E--3E in FIG. 3A;

FIGS. 3F and 3G are transverse cross-sectional views taken along lines 3F--3F and 3G--3G in FIG. 3B;

FIG. 4 is a simplified view similar to FIG. 1B and used, in conjunction with FIGS. 5A-5D, to describe how the passage of the manipulator wires through the central and satellite lumens create the various curves;

FIGS. 5A-5D are simplified cross-sectional views taken along lines 5A--5A through 5D--5D of FIG. 4;

FIGS. 6A and 6B illustrate sections of an alternative embodiment of the catheter shown in FIGS. 3B and 3F;

FIG. 7 illustrates the tip of an alternative embodiment of the invention using a coil ablation electrode; and

FIG. 7A illustrates a section of the catheter tip of FIG. 7 including the coil ablation electrode.

FIG. 1 illustrates an anatomically-conforming, dual curve ablation catheter, in particular an atrioventricular (AV) valve tissue ablation catheter 2, including a catheter shaft 4 having a distal end 6 and a proximal end 8. Shaft 4 has an outside diameter of about 0.052 inch (1.32 mm) to 0.1040 inch (2.64 mm) and a length of about 50 mm to 110 mm. Proximal end 8 is mounted to a handle 10 having axially slidable manipulator rings 12, 13 and a rotatable lateral deflection ring 14 operably connected to proximal and distal manipulator wires 17, 16 and a core wire 18, respectively, the wires shown in FIGS. 3A and 3B. Sliding manipulator rings 12, 13 cause a deflectable tip 20 of catheter shaft 4 to deflect as shown in FIGS. 1A and 1B between, for example, the solid-line and dashed-line positions of FIG. 1B. Rotating ring 14 causes lateral deflection of tip 20 through the torquing action of core wire 18, as shown in FIG. 1C.

Handle 10 also includes an electrical connector 21 connected to seven electrical conductors 22 and two pairs of thermocouple wires 24, 25, conductors 22 and wires 24, 25 being shown in FIG. 3C. Handle 10 may be of a conventional design, or as shown in U.S. Pat. No. 5,318,525 or in U.S. Pat. No. 5,545,200, the disclosures of which are incorporated by reference.

The portion of shaft 4 proximal of deflectable tip 20, see FIG. 3C, is capable of good torque transmission to permit controlled placement of tip 20 at the target site as discussed below. Such proximal portion of the shaft 4 includes an outer jacket 26, preferably made of higher durometer Pebax.RTM., such as 55-75D, reinforced by braided stainless steel wires 28. Pebax.RTM. is a polyamide polyether block copolymer made by Elf Atochem, Inc. of Philadelphia, Pa. A polyimide or ULTEMM tubular layer 26A, such as that sold by Hudson or General Electric, is positioned within the proximal central lumen 30 of shaft 4 and houses core wire 18, electrical conductors 22, thermocouple wires 24, 25 and manipulator wires 16, 17.

If desired, one or more axially slidable core wires could be used, the distal ends of the core wires being positionable at different axial positions along tip 20; doing so would permit the size of the curves of tip 20 to be changed. An example of a catheter with a variable curve tip is described in U.S. Pat. No. 5,565,200 for Steerable Electrophysiology Catheter, the disclosure of which is incorporated by reference.

The distal end 32 of shaft 4, see FIG. 3B, lies adjacent an insulator 34 made of PEEK (poly-ether-ether-keytone) or other hard, temperature-resistant material. Insulator 34 is bonded to distal end 32 of shaft 4 by heat fusing or adhesive.

FIG. 3G illustrates a cross-sectional view of catheter shaft 4 adjacent distal end 32 passing through a band mapping electrode 38, five mapping electrodes 38 being positioned along catheter shaft 4 adjacent distal end 32. Each electrode 38 is connected to an electrical conductor 22, typically by soldering or welding techniques. In FIG. 3C all the wires and conductors are housed within proximal central lumen 30. In FIG. 3G some of these elements are housed within one of four satellite lumens 40 formed in outer jacket 26. For example, proximal manipulator wire 17, one pair of thermocouple wires 25 and one of the electrical conductors 22 pass within one of satellite lumens 40 at the position of FIG. 3G; the remainder of the wires and conductors pass within distal central lumen 31.

Proximal insulator 34 has five bores or lumens which generally align with the corresponding lumens 30, 40 formed in outer jacket 26 of shaft 4. Proximal insulation 34 is preferably mounted to outer tubing 27 and inner tubing 27A by means of thermal bond or adhesive. Proximal insulator 34 is preferably mounted to electrode 46 by means of mechanical interlock and/or adhesive. Manipulator wire 17 passes through one of the lumens in insulator 34 as shown in FIG. 3B and is secured therein by a large ball end 42 formed at the distal end of wire 17 so that pulling on manipulator wire 17 using manipulator ring 12 creates the curve in the proximal segment 44 of tip 20. See FIG. 1A. FIG. 3F illustrates the passing core wire 18, manipulator wire 16, one pair of thermocouple wires 24 and one electrical connector 22 within tubing 27A separated from cylindrical ablation-capable electrode 46. One of the electrical conductors 22 is soldered or welded to electrode 46 while one of the pairs of thermocouple wires 24 is positioned adjacent electrode 46 using a thermally conductive but electrical insulating tube 50, such as polyimide, to permit the temperature of electrode 46 to be monitored.

An insulator 52, also preferably made of PEEK, is mounted to the distal end of electrode 46 preferably using a mechanical interlock and/or adhesive. The distal end 54 of tube 27A is housed within and bonded to insulator 52 through the use of appropriated adhesive, thermal bond, or other appropriate methods. The distal end 56, see FIG. 3A, of insulator 52 is secured to a tubing segment 58 made of 35D Pebax.RTM.. Segment 58 has two major lumens, a central lumen 60, through which core wire 18, the second pair of thermocouple wires 24 and electrical conductor 22 pass, and an offset lumen 62, through which distal manipulator wire 16 passes. Note that only core wire 18 is shown passing within central lumen 60 in FIG. 3A. Segment 58 terminates at and is bonded thermally or adhesively to an insulator 64, also made PEEK, which serves as a terminus for distal manipulator wire 16 and core wire 18. Manipulation of manipulator ring 13 causes manipulator 16 to be pulled, thus causing the distal segment 66 of tip 22 to be pulled into the reverse curve shown in FIGS. 1 and 1B. The distal end 68 of core wire 18 is doubled back over and inserted back into an opening, not shown, in insulator 64. Manipulation of rotatable lateral deflection ring 14 causes the lateral movement of tip 20 as suggested in FIG. 1B. The final electrical conductor 22 (not shown in FIG. 3A) is electrically connected to tip electrode 70, typically by soldering or welding. The second thermocouple wire pair 24 is housed in a polyimide insulator tubing 72 within a recess 74 formed into electrode 70 and is secured in the recess using a suitable thermally conducting, electrically insulating adhesive, not shown.

Electrodes 38, 46, 70 are preferably made of platinum while manipulator wires 16, 17 and core wire 18 are preferably stainless steel. Manipulator wires 16, 17 are preferably coated with PTFE to reduce sliding friction.

The length of proximal segment 44 of tip 20 is preferably about 3 to 10 times, and more preferably about 5 times, the length of distal segment 66. In one preferred embodiment proximal and distal segments 44, 66 are about 70 mm and 15 mm long, respectively.

FIGS. 4 and 5A-5D illustrate, in simplified form, the way in which catheter 20 is placed into the dual, recurved form shown in FIGS. 1 and 1B. In this simplified form, catheter shaft 4 is shown to have a main or central lumen 30 and four satellite lumens 40. As shown in FIG. 5A, the two manipulator wires 16, 17, which cause catheter 2 to bend, pass through central lumen 30 until the start of tip 20. At about that point, manipulator wire 17 crosses into one of the satellite lumens 40, as shown in FIG. 5B. Manipulator wire 17 terminates and is secured to the catheter at position 76. This is also shown in FIG. 3B. Therefore, by pulling on manipulator wire 17, that portion of a catheter between position 76 and the start of tip 20, that is proximal segment 44, is bent. The length of the catheter between position 76 and a position 78, which corresponds generally with distal end 56 of insulator 52, as shown in FIG. 2A, finds manipulator wire 16 within central lumen 30 as the manipulator wire passes through electrode 46. At position 78, manipulator wire 16 passes into the satellite lumen 40 opposite the lumen through which manipulator wire 17 had passed. See FIG. 5D. Manipulator wire 16 terminates adjacent tip electrode 70. Pulling on manipulator wire 17 causes distal segment 66 of tip 20 to form the reversed curve bend in the distal segment as shown in FIGS. 1, 1B and 4. As can be seen from FIGS. 4-5D, a great variety of curved segments can be created by passing manipulator wires from a central lumen into side or satellite lumens and then terminating the manipulator wire. For example, if manipulator wire 16 were passed into one of the satellite lumens 40 oriented 90 degrees from the satellite lumen through which manipulator wire 16 passed, distal segment 66 would be curved in a plane about 90 degrees to the plane of the figures. Also, distal curve 66 could deflect in the same plane and same direction as proximal curve 44. In an alternative embodiment, distal curve 66 and proximal curve 44 could be actuated by a single manipulator wire and a single handle control.

The use of catheter 2 will now be described with reference to FIGS. 1 and 2. FIG. 2 illustrates, in simplified form, a portion of a heart 80 having a superior vena cava 82 and an inferior vena cava 84 opening into a right atrium 86. Also illustrated is a portion of right ventricle 88 separated from right atrium 86 by a tricuspid valve 90. Tricuspid valve 90 is one of two atrioventricular valves of heart 80. Tricuspid valve 90 has an annulus 92 at the region joining the right atrium 86 with the right ventricle 88.

At times it is desired to ablate tissue on either side of annulus 92. Catheter 2 is especially suited for this purpose. After introducing tip 20 into right atrium 86, tip 20 is maneuvered and manipulator rings 12, 13 are moved to place proximal and distal segments 44, 66 of tip 20 into the shape shown in FIGS. 1 and 2 with distal segment 66 aligned with annulus 92 so that ablation-capable electrodes 46, 70 lie generally on either side of annulus 92. Mapping electrodes 38 are used to take appropriate readings of the electrical activity on the heart surface tissue to help ensure the proper placement of distal segment 66 of tip 20. Once the appropriate readings are taken and distal segment 66 is in the proper position, electrodes 46, 70 can be connected to a suitable RF power supply, such as RF generator 93, through connector 21. One such power supply is shown in U.S. patent application Ser. No. 08,179,558, filed Jan. 10, 1994, the disclosure of which is incorporated by reference. Ablation electrodes 46, 70 are preferably electrically isolated from one another so that they can be independently powered from the power supply. Therefore, the power supply need not be as large as would be required if they were electrically connected to one another or the separate ablation electrodes were replaced by a single, extra long ablation electrode. This eliminates the need to move the ablation electrode after each application of power, the "burn-drag-burn" technique used with conventional ablation catheters.

Typically, a switchbox 94 is connected between the ablation catheter 2 and RF generator 93. Switchbox 94, which can also be connected to an indifferent electrode 96, allows RF current to be directed to any available ablation electrode. Thermocouple signals from the particular electrode, used for temperature monitoring or control, are also supplied to switchbox 94. More than one ablation electrode and thermocouple can be connected simultaneously using switchbox 94. Switchbox 94 can also be automatically controlled.

In the above embodiment, distal segment 66 is placed in its desired reverse curve or recurved shape using manipulator wire 17. This can also be done by pre-forming distal segment 66 to the desired recurved shape.

FIGS. 6 and 6A illustrate a section of a catheter similar to that shown in FIGS. 3B and 3F in which cylindrical ablation electrode 46 has been replaced by a sleeve ablation electrode 46A placed about tubing 27 instead of being secured to the distal end of tubing 27 as in the embodiment of FIG. 3D. This eliminates the need to use separate insulators 34, 52 as in the embodiment of FIG. 3D which can result in a simpler and less expensive catheter. In the embodiment of FIGS. 3A-3G, insulators 34, 52, 64 may not be necessary so long as the temperatures of ablation electrodes 46, 70 remain below approximately 100 degrees C. during ablation.

FIGS. 7A and 7B illustrate another alternative embodiment of catheter 2 in which the solid cylindrical ablation electrode 46 is replaced by a coil ablation electrode, having a first or proximal section 46B with closely spaced coils and a second, more flexible section 46C with more loosely spaced coils, partially embedded within a silicone tube 98. As shown in FIG. 7, electrode section 46C is flexible which can permit the use of an ablation electrode in the curved portion of distal segment 66. Coil electrodes, as well as sleeve and cylindrical electrodes, can have their temperatures monitored using appropriate means, such as thermocouples.

Modification and variation can be made to the disclosed embodiments without departing from the subject of the invention as defined in the following claims. For example, materials, diameters and lengths can be changed to suit the particular needs or desires of the user. A single ablation electrode, or more than two ablation electrodes could be present. Mapping electrodes could also be located between the ablation electrodes. The attachment and bonding techniques discussed above are merely exemplary; other chemical, mechanical and/or thermal bonding techniques can be used as well. In some cases it may be desired to apply energy to more than one ablation electrode at the same time; for example, four ablation electrodes could be used and powered two-at-a-time.