Method and apparatus for radiofrequency ablation with increased depth and/or decreased volume of ablated tissue
A method of ablating a tissue site includes at least two stages. A first stage involves conducting bipolar ablation between a first pair of electrodes situated in an opposing arrangement on opposing sides of the tissue site to form a pair of opposing first stage ablation regions extending from respective sides of the tissue towards the center. A second stage involves conducting bipolar ablation between a second pair of electrodes situated in a diametrical arrangement with respect to the first stage ablation regions, which forms a second stage ablation region intermediate the pair of first stage ablation regions. The second stage completes the ablation through the entire depth of the tissue site. Since the overall process can accommodate incomplete ablation during the first stage, lower power, reduced ablation times or both may be used during the first stage, avoiding overheating and with a decrease in ablated tissue volume.
This application is a continuation of U.S. application Ser. No. 12/428,173, filed 22 Apr. 2009, now ______, which is hereby incorporated by reference as though fully set forth herein.
BACKGROUND OF THE INVENTIONa. Field of the Invention
The present disclosure relates generally to ablation systems, and more particularly, to a method and apparatus for radiofrequency ablation with increased depth and/or decreased volume of ablated tissue.
b. Background Art
It is known to deliver radiofrequency (RF) energy to a desired target area through an electrode assembly to ablate tissue at the target site. RF ablation may generate significant heat, which if not controlled can result, generally, in undesired or excessive tissue damage. It is particularly difficult to achieve successful RF ablation of live, relatively thick biological tissue, for a number of reasons. The cross-sectional profile (Le., depth) of ablation is often too shallow, in part because most of the Ohmic heat is generated near the RF electrodes, i.e., at the surface of the tissue. Furthermore, the rate at which heat diffuses deep into the tissue layer(s) is extremely slow, and may be counteracted by the cooling effects due to blood perfusion, for example, during epicardial ablation. As the tissue surrounding the electrodes is being ablated, its Ohmic resistivity increases. This increase in resistivity further exacerbates the problem of non-uniform heating, because at a given current density, the heating intensity experienced by the tissue is proportional to its then-existing Ohmic resistivity.
Moreover, the goals of thick layer RF cardiac ablation are often at odds. It is often necessary to ablate all the way through the thickness of the tissue, while at the same time avoiding tissue overheating and minimizing the volume of ablated tissue. However, the thicker the tissue layer, the less possible it is to achieve adequate ablation through its thickness without overheating the tissue near the RF electrodes (i.e., damaging the tissue in an unacceptable way) and without ablating an undesirable excess volume of tissue.
There are a number of two-electrode or multi-electrode RF ablating devices known in the art, for example as seen by reference to U.S. Pat. No. 7,241,292 entitled CARDIAC ABLATION DEVICE WITH MOVABLE HINGE issued to Hooven. Hooven discloses a transmural RF ablation device. However, Hooven does not address the problems of inadequate ablation depth or excessive ablated tissue volume described above, particularly for a relatively thick biological tissue layer.
There is therefore a need to minimize or eliminate one or more of the problems set forth above.
BRIEF SUN/MARY OF THE INVENTIONOne advantage of the methods and apparatus described, depicted and claimed herein relates to increased depth of RF ablation lesions while at the same time reducing the overall volume of ablated tissue as compared to known approaches.
This disclosure is directed to methods of ablating tissue site between diverse electrode pairs and the methods include at least two discrete ablation procedure stages. During a first stage, an embodiment of the inventive method involves conducting radiofrequency (RF) energy (e.g., bipolar or unipolar RF energy) ablation between a first pair of electrodes situated in an opposing arrangement on opposing sides of the tissue site. The first stage ablation forms a pair of opposing first stage ablation regions extending from respective sides of the tissue towards the center of the site. However, the first stage may not completely ablate the site through its depth. During a second stage in one form of the invention, the methods involve conducting bipolar ablation but between a second pair of electrodes situated in a diametrical arrangement with respect to the first stage ablation regions. The second stage ablation forms a second stage ablation region intermediate the first stage ablation regions, effectively bridging the pair of first stage ablation regions. To the extent an un-ablated channel, region or gap exists between the pair of opposing ablation regions after the first stage, the second stage completes the ablation through the entire depth of the tissue site. Since the invention can accommodate incomplete ablation or non-transmural ablation lesions (i.e., a lesion due to ablation that does not penetrate the entire depth of the tissue site) during the first stage, lower power, reduced ablation times or both may be used during such first stage, with a resultant decrease in ablated tissue volume. The second stage completes the ablation process throughout the tissue depth, providing increased depth. As note, unipolar or bipolar electrical configurations can be used, or combinations of each type of energy delivery.
A system for RF ablation according to the invention is also presented. In such a system a pair of opposing substantially resilient elongate members couple electrodes for RF energy delivery therebetween. The elongate members can comprise clamping members actuated via a pivot such a scissor-like unit or a pair of members slideably coupled so that one is fixed and the other moveable toward the fixed member. Suitable elongate conductors, switches couple the electrodes to an RF generator. In one form the members are designed and fabricated of biocompatible material and of dimension providing ease of pericardial access via, for example, a sub-xiophoid incision to access one or more pulmonary veins of a subject. In another form, the elongate members comprise at least two pairs of opposing members so that both pairs can engage a target tissue site in a compressive state and at least one can be relaxed in a non-compressive state thereby not engaging the target tissue site. In another form an insulative sheath can be advanced over one or more of the electrodes to selectively insulate same from the target tissue site during subsequent ablation procedures. The electrodes can be coupled to only an RF generator or one or more electrodes can also couple to a cardiac pacing circuit and/or a cardiac sensing circuit or impedance measuring circuit according to various forms of the invention. The pacing and/or sensing circuitry can be used to confirm transmurality of a particular lesion set (e.g., a continuous transmural lesion around a plurality of pulmonary veins) whether or not the set was produced by a system according to the foregoing or in part by another apparatus. That is, pacing or sensing “above” the lesion set (above natural sinus rhythm) should not conduct or capture the myocardium thus indicating continuity of the lesion set. Likewise, sensing above the lesion set should not detect cardiac activity (or at least not at typical amplitude(s)).
These and other benefits, features, and capabilities are provided according to the structures, systems, and methods depicted, described and claimed herein.
Referring now to the drawings wherein like reference numerals are used to identify identical components in the various views,
With continued reference to
The ablation generator 14 may include a main controller 18, a user interface 20, an RF power source 22 and optionally an impedance detection circuit 24. The main controller 18 may be configured to control the operation of the RF power source 22 in accordance with various inputs (e.g., power setting, ablation duration (time), etc.) received from a user thereof through the user interface 20. The controller 18 may be further configured interact with the impedance detection circuit 24 to obtain data indicative of an impedance value measured through or using one or more of the electrodes within electrode blocks 161, 162 and to communicate and/or control the user interface 20 to display or otherwise communicate the measured impedance to a user. The RF power source 22 may typically produce RF signals in the frequency range of between about 50 kHz and 500 kHz. The controller 18 may be still further configured to control a switching function block 26 to make the connections between the RF power source 22 and the plurality of electrodes contained in the electrode blocks 161, 162, in a manner that will become more apparent from the detailed description below. The controller 18, user interface 20, RF power source 22, impedance detection circuit 24 and switching function block 26 may each comprise conventional components known to those of ordinary skill in the art, except as may be otherwise noted herein. For example, the RF ablation generator 14 may comprise conventional apparatus, such as a commercially available unit sold under the model number IBI-1500T Cardiac Ablation Generator, available from Irvine Biomedical, Inc. Of course, the RF ablation generator 14 can also comprise other known energy sources. The art is replete with RF ablation generator configurations, designs, implementations and the like, and will therefore not be described in any further detail.
Additional components (not shown) may also be integrated into the system 10, such as visualization, mapping and navigation components known in the art, including among others, for example, an EnSite™ Electro Anatomical Mapping System commercially available from St. Jude Medical, Inc., and as also seen generally by reference to U.S. Pat. No. 7,263,397 entitled “METHOD AND APPARATUS FOR CATHETER NAVIGATION AND LOCATION AND MAPPING IN THE HEART” to Hauck et al., owned by the common assignee of the present invention, and hereby incorporated by reference in its entirety. Additionally, an electrophysiological (EP) monitor or display such as an electrogram signal display, or other systems conventional in the art may also be integrated into the system 10. It should he understood that embodiments consistent with the present invention may, and typically will, include other features not shown or described herein in
In step 28, the method involves conducting, during a first stage, bipolar ablation between a first pair of electrodes situated in an opposing arrangement on opposing sides of the tissue site so as to form a pair of opposing first stage ablation regions. This step may or may not achieve complete transmural ablation (i.e., complete through the depth of the tissue site), and accordingly may leave a channel of un-ablated tissue between the first stage ablation regions. Since the two stage process can accommodate ablation that does not, during the first stage alone, achieve ablation through the complete depth of the tissue, the method contemplates that reduced power levels, reduced ablation durations (e.g., time) or other variations may be used, which has the desirable result of avoiding overheating and yielding a reduced volume of ablated tissue. The method proceeds to step 30.
In step 30, the method involves determining whether first stage termination conditions have been met. This step may be expressed in a number of different embodiments. In one embodiment, the user (e.g., practitioner) may set an initial power level (e.g., constant power level in watts) and duration, based on, for example, experience, patient/tissue site assessment and/or other factors known in the art. Accordingly, when the manually-set duration expires, the first stage ablation is complete. Alternatively, the termination conditions may involve assessment of the impedance between different pairs of electrodes, for example, when an impedance value is determined to saturate (i.e., increase to a certain level or by a certain amount or by a certain factor and then substantially level off). This impedance assessment may be made manually (i.e., by the user), or may be automated, in which case the main controller 18 is configured to monitor the impedance, as determined by the impedance detection circuit 24, and when the impedance saturation condition is detected, generating a control signal to the RF power source to automatically discontinue power (i.e., or otherwise discontinue application of power, such as by disconnecting the power source via opening of the switching devices in the switching function block 26, or in other ways known in the art). This impedance assessment feature will be described in greater detail below with respect to specific electrodes in specific embodiments. In any event, if the termination conditions have not been met (“NO”), then the method branches back to step 28, where the first stage ablation continues. However, if the first stage termination conditions are met (“YES”), then the method proceeds to step 32.
In step 32, the method involves further bipolar ablation, during a second stage, but now between a second pair of electrodes situated in a diametrical arrangement with respect to the first stage ablation regions (i.e., not the opposing arrangement described above). Because of the increased impedance exhibited by the first stage ablation regions, the tissue that may remain unablated after the first stage (i.e., the region between the first stage ablation regions) constitutes the proverbial “path of least resistance” for the ablation energy to be delivered and focused into during this second stage, given the diametrical arrangement of electrodes. The second stage is thus operative to form a second stage ablation region intermediate the opposing first stage ablation regions. The second stage ablation completes the ablation process, ensuring that the tissue site is ablated completely through its depth, without undesired, excessive volume of tissue being ablated.
With continued reference to
For such unipolar component embodiments, the electrode configuration described herein would further include an indifferent or reference electrode, disposed either within the body or affixed to the body surface of the subject (i.e., skin patch electrode). The activation for the unipolar component (first stage) may involve, in one embodiment, sequential activation of the electrodes 1A and 1B of the electrode pair 34 (i.e., each electrode being vectored to the indifferent/reference electrode). Thus, while one electrode (e.g., electrode 1A) is activated, the opposing, non-activated electrode (e.g., electrode 1B) is electrically isolated from the tissue site, such as, for example, by removing the non-activated electrode from contact with the tissue site (i.e. spaced from the tissue—myocardium) or otherwise selectively electrically insulating the electrode from the tissue. In another unipolar component embodiment, both electrodes are electrically driven at the same time; however, not in counter-phase but rather with a phase offset greater than 0 degrees and less than 180 degrees (again, a reference/indifferent electrode is used). It bears emphasizing that to the extent unipolar ablation components are used, it would be used during the first stage ablation. The second stage ablation would continue to involve bipolar ablation.
In the embodiment of
In addition, to better concentrate RF current between the first stage ablation regions 441, 442, in one variation, the first pair of electrodes 34 (1A/1B) may be electrically isolated from the tissue site 12 so that these electrodes (1A/1B) will not partially shunt current via the first stage ablation regions 441, 442. Electrical isolation may be accomplished by physically removing the first pair electrodes 34 from electrical contact with the tissue site 12 or alternatively interposing a relatively high impedance material, such as an insulative sheath movable between a first conductive position and a second insulating position, between the first electrode pair 34 (1A/1B) and the RF power source 22 of the ablation generator 14.
As shown in
One challenge, however, is that this embodiment necessarily involves moving the electrodes and in addition, during the second stage, the tissue site 12 is no longer clamped across the center near the first ablation regions (i.e., where the two electrodes pairs were previously located during the first stage). To address this challenge, in a still further embodiment, an optional mechanical clamping device 60 comprising clamp members 601 and 602 may be used, separable or partially separable from the RF electrodes 1A/1B and 2A/2B. As shown, the mechanical clamping device 60 takes the place vacated by the two electrode pairs after the first stage, thereby ensuring consistent compression through the tissue site 12. This is particularly important where the tissue layer includes multiple, individual layers, such as may exist when conducting epicardial ablation (i.e., “pinching” or “folding” tissue, thereby lapping two individual layers).
In another embodiment, only two movable electrodes (and optionally a clamp) are used. For the first ablation stage, these electrodes are put in the central position (34 in
The ablation process may be effectively monitored by checking the impedance between one or more different pairs of electrodes. Taking the first embodiment (i.e.,
It should be understood that the system 10, particularly the RF ablation generator 14, as described above may include conventional processing apparatus known in the art, capable of executing pre-programmed instructions stored in an associated memory, all performing in accordance with the functionality described herein. Certain aspects of the methods described herein may be programmed (as indicated), with the resulting software being stored in an associated memory and where so described, may also constitute the means for performing such methods. Implementation in software, in view of the foregoing enabling description, would require no more than routine application of programming skills by one of ordinary skill in the art. Such a system may further be of the type having both ROM, RAM, a combination of non-volatile and volatile (modifiable) memory so that the software can be stored and yet allow storage and processing of dynamically produced data and/or signals.
In addition, the ablation electrodes described herein may be coupled to only an RF generator or one or more electrodes can also couple to a cardiac pacing circuit and/or a cardiac sensing circuit or impedance measuring circuit (as described above) according to various forms of the invention. The pacing and/or sensing circuitry can be used to confirm transmurality of a particular lesion set (e.g., a continuous transmural lesion around a plurality of pulmonary veins) whether or not the set was produced by a system according to the foregoing or in part by another apparatus. That is, pacing or sensing “above” the lesion set (above natural sinus rhythm) should not conduct or capture the myocardium thus indicating continuity of the lesion set. Likewise, sensing above the lesion set should not detect cardiac activity (or at least not at typical amplitude(s)).
Although numerous embodiments of this invention have been described above with a certain degree of particularity, those skilled in the art could make numerous alterations to the disclosed embodiments without departing from the spirit or scope of this invention. All directional references (e.g., plus, minus, upper, lower, upward, downward, left, right, leftward, rightward, top, bottom, above, below, vertical, horizontal, clockwise, and counterclockwise) are only used for identification purposes to aid the reader's understanding of the present invention, and do not create limitations, particularly as to the position, orientation, or use of the invention. Joinder references (e.g., attached, coupled, connected, and the like) are to be construed broadly and may include intermediate members between a connection of elements and relative movement between elements. As such, joinder references do not necessarily infer that two elements are directly connected and in fixed relation to each other. It is intended that all matter contained in the above description or shown in the accompanying drawings shall be interpreted as illustrative only and not limiting. Changes in detail or structure may be made without departing from the spirit of the invention as defined in the appended claims.
Claims
1.-21. (canceled)
22. An apparatus, comprising:
- means for conducting bipolar ablation between a first pair of electrodes in an opposing arrangement on opposing sides of the tissue site so as to form a pair of opposing first stage ablation regions in the site during a first stage; and
- means for conducting bipolar ablation between a second pair of electrodes in a diametrical arrangement with respect to the first stage ablation regions to form a second stage ablation region intermediate said first stage ablation regions during a second stage.
23. An apparatus according to claim 22, wherein the diametrical arrangement comprises a first diametrical arrangement, and further comprising:
- means for conducting bipolar ablation during the second stage between a third pair of electrodes in a second diametrical arrangement with respect to the first stage ablation regions.
24. An apparatus according to claim 22, wherein the second pair of electrodes comprises a different pair from the third pair of electrodes.
25. An apparatus according to claim 22, wherein the second stage comprises a first interval and a second interval and wherein said means for conducting bipolar ablation during the second stage further comprises:
- means for conducting bipolar ablation during the first interval using the second pair of electrodes in the diametrical arrangement;
- means for moving the second pair of electrodes to a second diametrical arrangement; and
- means for conducting bipolar ablation during the second interval using the second pair of electrodes in the second diametrical arrangement.
26. The apparatus of claim 22 wherein said pair of opposing first stage ablation regions in the site extend from respective sides of said tissue site towards a center of said tissue site, said first stage being conducted in accordance with at least one of a selected power and time duration parameter such that upon termination of said first stage ablation, said pair of opposing first stage ablation regions together extend less than said depth of said tissue site; and
- wherein said second stage ablation region is in the center of said tissue site and is different than said first stage ablation regions wherein said second stage ablation regions completes the ablation through the entire depth of said tissue site.
27. The apparatus of claim 26 wherein said second stage occurs after termination of said first stage.
28. The apparatus of claim 26 wherein said means for conducting bipolar ablation between said first pair of electrodes and said means for conducting bipolar ablation between said second pair of electrodes, comprises a radio frequency (RF) ablation generator including a main controller and an RF power source selectively coupled to said first and second pairs of electrodes, said main controller being configured to control the operation of said RF power source.
29. The apparatus of claim 28 wherein said main controller is configured to control operation of said RF power source in accordance with a plurality of inputs received from a user thereof through a user interface.
30. The apparatus of claim 28 wherein said main controller is configured to interact with an impedance detection circuit to obtain data indicative of an impedance value measured through or using one or more of the electrodes.
31. The apparatus of claim 28 wherein said main controller is further configured to control a switching function block to make connections between said RF power source and said first and second pair of electrodes.
32. The apparatus of claim 28 wherein said main controller is configured to control said RF power source so as to provide power in counter-phase to the electrodes of at least one of said first and second pairs of electrodes.
33. The apparatus of claim 32 wherein said main controller is further configured to control said RF power source so as to apply a first signal to one of the electrodes of said at least one first and second electrode pairs and to apply a second signal to the other one of the electrodes of said at least one first and second electrode pairs, wherein said first and second signals are offset in phase by 180 electrical degrees.
34. The apparatus of claim 33 wherein said first and second signals are alternating current (AC) signals having a predetermined frequency.
35. The apparatus of claim 34 wherein said predetermined frequency is in the radio frequency (RF) range between about 50 kHz and 500 kHz.
36. The apparatus of claim 28 wherein said RF ablation generator is configured to power said first pair of electrodes at a substantially constant power.
37. The apparatus of claim 28 wherein said main controller is configured to monitor an impedance of said tissue site as detected by an impedance detection circuit and discontinue bipolar ablation during said first stage when said monitored impedance satisfies predetermined criteria.
38. The apparatus of claim 37 wherein said predetermined criteria includes a saturation condition.
39. An apparatus, comprising:
- a main controller; and
- an RF power source configured to be coupled to a first pair of electrodes and to a second pair of electrodes;
- wherein said main controller is configured to control the operation of said RF power source for conducting bipolar ablation between said first pair of electrodes in an opposing arrangement on opposing sides of a tissue site so as to form a pair of opposing first stage ablation regions in said site during a first stage and for conducting bipolar ablation between said second pair of electrodes in a diametrical arrangement with respect to said first stage ablation regions to form a second stage ablation region intermediate said first stage ablation regions during a second stage.
40. The apparatus of claim 39 wherein said pair of opposing first stage ablation regions in said site extend from respective sides of said tissue site towards a center of said tissue site, said main controller being configured to conduct said first stage in accordance with at least one of a selected power and time duration parameter such that upon termination of said first stage ablation, said pair of opposing first stage ablation regions together extend less than said depth of said tissue site; and
- wherein said second stage ablation region is in the center of said tissue site and is different than said first stage ablation regions wherein said second stage ablation region completes the ablation through the entire depth of said tissue site.
41. The apparatus of claim 40 wherein said main controller is further configured to control a switching function block to make connections between said RF power source and said first and said second pair of electrodes, said main controller is further configured to control operation of said RF power source in accordance with a plurality of inputs received from a user thereof through a user interface, and wherein said main controller is further configured to monitor an impedance of said tissue site as detected by an impedance detection circuit and discontinue bipolar ablation during said first stage when said monitored impedance satisfies predetermined criteria comprising saturation.
Type: Application
Filed: Jan 4, 2017
Publication Date: Jun 15, 2017
Inventor: Gleb V. Klimovitch (Santa Clara, CA)
Application Number: 15/398,217