ABLATION CATHETER AND METHOD FOR ELECTRICALLY ISOLATING CARDIAC TISSUE

Abstract

Ablation catheter comprising an elongate member with proximal and distal ends, wherein the distal end is arranged to apply a high energy electrical shock from a plurality of locations along the length of said distal end and wherein said distal end is curved. Preferably the distal end of the elongate member extends in a circle segment.

Claims

1.-38. (canceled)

39. A system for electrically isolating cardiac tissue, comprising: an ablation catheter comprising an elongate member, wherein the elongate member comprises a proximal end and a distal end, wherein the distal end comprises a plurality of electrodes and is configured to apply a high energy electrical shock across a plurality of the plurality of electrodes to a cardiac tissue, and wherein each of the plurality of the plurality of electrodes is configured to contact the cardiac tissue and to deliver a shock sufficient for ablation of the cardiac tissue; and a measurement device electrically coupled to the ablation catheter, wherein the measurement device is configured to monitor a heart rhythm, wherein the high energy electrical shock is configured to be applied in dependence of the heart rhythm, wherein the high energy electrical shock is applied at a predetermined time in the heart rhythm on or before the QRS-complex of the ECG.

40. The system according to claim 39, wherein the distal end comprises the plurality of electrodes, and wherein the plurality of electrodes have the same polarity.

41. The system according to claim 40, wherein the high energy electrical shock comprises shocks with different voltages from at least two adjacent electrodes of the plurality of electrodes along the length of the distal end.

42. The system according to claim 40, wherein the high energy electrical shock is configured to simultaneously apply a shock from the plurality of electrodes.

43. The system according to claim 39, wherein the elongate member comprises one electrode extending along substantially the whole length of the distal end.

44. The system according to claim 39, wherein the distal end of the elongate member is configured to be contacted with the tissue along a path, and wherein the high energy electrical shock is configured to form a closed path of electrically non-conducting tissue.

45. The system according to claim 39, wherein a curvature of the distal end of the elongate member is configured to be adjusted to a surface of the cardiac tissue to be isolated.

46. The system according to claim 45, wherein the distal end of the elongate member extends in a circle segment, and wherein a diameter of the circle segment is configured to be adjusted.

47. The system according to claim 39, wherein the distal end of the ablation catheter is curved and wherein a plane of the curved segment is configured to be adjusted.

48. The system according to claim 39, further comprising a sheath, wherein the ablation catheter is configured to be advanced through the sheath, wherein the elongate member is configured to be moveable between a first position wherein the elongate member extends substantially rectilinear and a second position wherein the distal end of the elongate member is curved, and wherein the elongate member is configured to move from the first to the second position by advancing the elongate member out of the sheath.

49. The system according to claim 39, wherein one of the plurality of electrodes comprises an indifferent electrode.

50. The system according to claim 39, wherein the cardiac tissue comprises pulmonary vein ostia of a pulmonary vein near an entrance to a left atrium.

51. The system according to claim 50, wherein the high energy electrical shock is configured to be applied radially outward from the distal end of the ablation catheter along a cross-section of the pulmonary vein.

52. The system according to claim 51, further comprising a sheath, wherein the sheath comprises a coil configured to be an indifferent electrode.

53. The method according to claim 39, wherein the high energy electrical shock comprises a shock between 250 and 400 Joule.

54. The system according to claim 53, wherein the high energy electrical shock comprises a shock of 350 Joule.

55. The system according to claim 39, wherein the predetermined period of time is less than 5 ms.

56. The system according to claim 55, wherein the predetermined period of time is approximately 1 ms.

57. The system according to claim 39, wherein the distal end of the ablation catheter is configured to be inserted into a pulmonary vein.

58. The system according to claim 39, wherein the distal end of the elongate member comprises a radially expanding circle segment, and wherein the radially expanding circle segment is configured to be placed within a pulmonary vein.

Description

[0050] The present invention is further illustrated by the following Figures, which show a preferred embodiment of the device according to the invention, and are not intended to limit the scope of the invention in any way, wherein:

[0051] FIG. 1 schematically shows a ablation catheter according to the invention;

[0052] FIG. 2 schematically shows the catheter in the left atrium;

[0053] FIG. 3 schematically shown the catheter in a vessel in cross section;

[0054] FIG. 4 schematically shows a curved tissue area in perspective;

[0055] FIG. 5 schematically shows the distribution of the electrical energy from the electrodes.

[0056] FIG. 6 schematically shows a heart of a pig, and;

[0057] FIGS. 7A, 7B, 8A, and 8B show the results of a test conducted on a pig.

[0058] In FIG. 1 a catheter 1 according to the invention is shown. The catheter 1 comprises an elongate member 2 with a proximal end (not shown) and a distal end 21. The distal end 21 of the elongate member is curved. In this example the distal end 21 extends in a circle segment, wherein the distal end 21 forms a loop or a lasso. The distal end 21 extends in a plane II under an angle with respect to the longitudinal axis I of the elongate member 2. The distal end 21 is provided with a plurality of electrodes 6, in this case ten. The electrodes 6 extend on mutually distances of 5 mm.

[0059] The distal end 21 of elongate member 2 is steerable which allows the practitioner to adjust the plane II of the electrodes 6. This facilitates the placement of the electrodes on the tissue to be treated as will be explained in more detail below. Also shown is a steerable sheath 3, which allows an efficient advancement of the catheter 1 through the vasculature. In this embodiment the sheath 3 is provided with an indifferent electrode in the form of a coil 7. The coil 7 is disposed coaxially to the sheath.

[0060] The distal end 21 forming the loop is preferably manufactured from a deflectable material. When the elongate member 2 is drawn into the sheath 3 in a direction indicated with III, the distal end 21 will deform such that the distal end 21 will extend substantially rectilinear. In this first position the distal end 21 is contained in the sheath 3. This results in a compact composition. In the first position, the elongate member 2 can be advanced through the sheath 3 to the tissue to be treated. When the catheter 1 is advanced to the tissue, the elongate member 21 is advanced out of the sheath 3, and the distal end 21 deflects back to the second position, as shown in FIG. 1.

[0061] In FIG. 2 the catheter 1 is shown in place in the left atrium 8 of the heart. The sheath 3 advanced through the septum 81. The coil 7 hereby extends in the right atrium. In order to isolate a tissue area from the pulmonary vein 82, the distal end 21 of the elongate member 2 is advanced in said vein 82 such that the electrodes 6 contact the wall along a cross section of said vein 82.

[0062] In order to facilitate the placement of the electrodes 6 onto the wall of the vein 82, the most distal end 22 is steerable, allowing the plane of the electrodes 6, indicated with II in FIG. 1, to be adjusted in directions indicated with V and VI.

[0063] Using the steerable most distal end 22 it is also possible to adjust the diameter of the circle segment wherein the electrodes 6 extend, as is shown schematically in FIG. 3. When the distal end 21 is advanced in a vein 82 it is possible that the electrodes 6 do not contact the tissue closely, as the case in FIG. 3. In order to achieve a close fit of the distal end 21 provided with the electrodes 6 to the wall, the diameter can be adjusted. The electrodes 6 are moved in a direction indicated with VI to achieve a close contact between the wall of the vein 82 and the electrodes 6.

[0064] As is shown in FIG. 3, the distal end 21 provided with the electrodes 6 forms a closed loop over a cross section of the vein 82. The electrodes 6 extend over a closed loop over the inner wall of the vein, isolating the tissue areas extending adjacent the distal end 21 (below and above the plane of FIG. 3).

[0065] Referring back to FIG. 2, when the electrodes are placed in close contact with the tissue 83 to be treated, a high energy electrical shock of approximately 350 Joule is applied to the electrodes 6 during approximately 5 ms. Since ten electrodes 6 are used, each of the electrodes 6 delivers a shock of approximately 35 Joule. It was discovered that this is sufficiently to permanently make the tissue 83 extending in the proximity of the electrode nonconductive, isolating the vein 82 from the left atrium 8.

[0066] In order to achieve a good isolation between the tissue areas, the distance between two electrodes 6 is sufficiently small to ensure that all tissue 83 extending between electrodes 6 is subjected to electrical energy sufficiently high to induce non-conductivity. This ensures a proper isolation.

[0067] As an example, a curved surface of tissue 8 is shown in FIG. 4. In order to provide close contact between the electrodes 6 and the tissue 83 to be treated, the distal end 21 is curved complementary to the curvature of the tissue 8. All of the electrodes 6 shown therefore make contact with the tissue 83. Due to the application of the shock through the electrodes 6, the tissue indicated with 83 is made nonconductive. This isolates the tissue indicated with 84a from the tissue indicated with 84b.

[0068] To enhance the distribution of the electrical energy from the electrodes 6 to the tissue, the polarity of all the electrodes 6 is the same. Furthermore, the catheter 1 is arranged to synchronously deliver a shock from the electrodes 6. Each of the electrodes is hereto provided with a separate power source known in the art. This results in a radially outwardly distribution of the electrical energy indicated with E1 in FIG. 5. The term radial must be interpreted with respect to the longitudinal axis I of the elongate member in the case where the distal end 21 extends in the plane II perpendicular to the axis I as shown in FIGS. 1 and 2.

[0069] In FIG. 5, the electrodes 6 are arranged to deliver a shock of an alternating voltage between the electrodes. The electrodes 6a are arranged to deliver a shock with a voltage of 3500V, while the electrodes 6b are arranged to deliver a shock of 3000V. This difference in voltage between adjacent electrodes results in a flow of electrical energy E2 between the adjacent electrodes 6a and 6b. This ensures that tissue extending near the region 21a between the electrodes 6 is also sufficiently subjected to electrical energy E2.

[0070] The present invention is not limited to the embodiment shown, but extends also to other embodiments falling within the scope of the appended claims. It will be understood that although an embodiment is shown using a plurality of electrodes, it is also possible to use one single elongate electrode which can be placed in close contact with the tissue to be treated.

EXAMPLE

[0071] The invention will now further be elucidated using an example.

[0072] In FIG. 6 a sketch of the reconstructed geometry of the left atrium of a pig is shown. The left atrium (LA), three pulmonary vein ostia (RPV, IPV and LPV) and part of the left atrial appendage (LAA) are shown. DC ablations according to the invention were performed in the ostia of the right RPV and left pulmonary veins LPV.

[0073] The intention of the ablation procedure is to destroy all vital atrial myocardium inside the ostium of the pulmonary veins. Such destruction translates into a dramatic reduction of local electrograms, measured using endocardial catheters.

[0074] FIG. 7A shows an electrocardiogram I of the pig's heart prior to ablation. RA and RV are electrograms of the right atrium and the right ventricle. La1-8 are recordings from a lasso catheter in various positions in the atrium.

[0075] A catheter according to the invention had been placed inside the ostium of the right pulmonary vein ostium in four different positions. One of the positions is schematically drawn using a dotted line in FIG. 6. For each position, a DC shock of 200 Joule had been delivered via the ten electrodes of that catheter (20 Joule per electrode). After those shocks, the complete ostium of the right pulmonary vein only shows very small electrogram amplitudes as can be seen from FIG. 7B, indicating the electrically active atrial tissue/muscle has been destroyed by the shocks.

[0076] FIG. 8A are the pre-recordings similar to the recordings shown in FIG. 7A for a second pig. In this case, two subsequent shocks of 200J were applied to the tissue. Also here, as can be seen from FIG. 7B, almost all atrial signals have disappeared, indicating that a lesion has been created in the ostium.