Methods and apparatus for performing renal neuromodulation via catheter apparatuses having inflatable balloons

Abstract

Methods and apparatus are provided for non-continuous circumferential treatment of a body lumen. Apparatus may be positioned within a body lumen of a patient and may deliver energy at a first lengthwise and angular position to create a less-than-full circumferential treatment zone at the first position. The apparatus also may deliver energy at one or more additional lengthwise and angular positions within the body lumen to create less-than-full circumferential treatment zone(s) at the one or more additional positions that are offset lengthwise and angularly from the first treatment zone. Superimposition of the first treatment zone and the one or more additional treatment zones defines a non-continuous circumferential treatment zone without formation of a continuous circumferential lesion. Various embodiments of methods and apparatus for achieving such non-continuous circumferential treatment are provided.

Description

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication or patent application was specifically and individually indicated to be incorporated by reference.

TECHNICAL FIELD

The present invention relates to methods and apparatus for performing a non-continuous circumferential treatment of a body lumen. Several embodiments of such methods and apparatus are directed to circumferential treatments of the body lumen that apply energy in one or more discrete treatment areas to form one or more lesions that are not contiguous or continuous about any complete circumference of a cross-section normal to a longitudinal axis of the body lumen.

BACKGROUND

Applicants have described methods and apparatus for treating a variety of renal and cardio-renal diseases, such as heart failure, renal disease, renal failure, hypertension, contrast nephropathy, arrhythmia and myocardial infarction, by modulating neural fibers that contribute to renal function, e.g., denervating tissue containing the neural fibers that contribute to renal function. This is expected to reduce renal sympathetic nervous activity, which increases removal of water and sodium from the body, and returns renin secretion to more normal levels. Normalized renin secretion causes blood vessels supplying the kidneys to assume a steady state level of dilation/constriction, which provides adequate renal blood flow. See, for example, Applicants' U.S. Pat. Nos. (a) 7,162,303; (b) 7,653,438; (c) 8,145,316; (d) 7,620,451; (e) 7,617,005; and (f) 6,978,174. All of these applications and the patent are incorporated herein by reference in their entireties.

Applicants also have previously described methods and apparatus for intravascularly-induced neuromodulation or denervation of an innervated blood vessel in a patient or any target neural fibers in proximity to a blood vessel, for example, to treat any neurological disorder or other medical condition. Nerves in proximity to a blood vessel may innervate an effector organ or tissue. Intravascularly-induced neuromodulation or denervation may be utilized to treat a host of neurological disorders or other medical conditions, including, but not limited to, the aforementioned conditions including heart failure and hypertension, as well as pain and peripheral arterial occlusive disease (e.g., via pain mitigation). The methods and apparatus may be used to modulate efferent or afferent nerve signals, as well as combinations of efferent and afferent nerve signals. See, for example, Applicants' co-pending U.S. Patent Application Publication No. US 2007/0129760, which is incorporated herein by reference in its entirety.

Although the foregoing methods are useful by themselves, one challenge of neuromodulation and/or denervation is sufficiently affecting the neural tissue from within the vessel. For example, intravascular neuromodulation should avoid increasing the risk of acute and/or late stenosis. Therefore, it would be desirable to provide methods and apparatus that further address these challenges.

BRIEF DESCRIPTION OF THE DRAWINGS

Several embodiments of the present invention will be apparent upon consideration of the following detailed description, taken in conjunction with the accompanying drawings, in which like reference characters refer to like parts throughout, and in which:

FIG. 1 is a schematic isometric detail view showing a common location of neural fibers proximate an artery.

FIGS. 2A-2J are schematic side views, partially in section, and cross-sectional views illustrating an example of methods and apparatus for a non-continuous circumferential treatment of a body lumen.

FIG. 3 is a schematic side view, partially in section, illustrating an alternative embodiment of the methods and apparatus of FIG. 2.

FIG. 4 is a schematic side view, partially in section, illustrating further alternative methods and apparatus for non-continuous circumferential treatments.

FIGS. 5A and 5B are schematic side views, partially in section, illustrating still further alternative methods and apparatus for non-continuous circumferential treatments.

FIGS. 6A and 6B are schematic side views, partially in section, illustrating additional alternative methods and apparatus for non-continuous circumferential treatments.

FIGS. 7A and 7B are schematic side views, partially in section, illustrating alternative embodiments of the apparatus and methods of FIG. 6.

FIG. 8 is a schematic side view, illustrating a non-continuous circumferential treatment that is oblique to the lengthwise axis of the patient's vasculature.

FIGS. 9A and 9B are schematic side views, partially in section, illustrating intravascular methods and apparatus for oblique circumferential treatment.

FIGS. 10A and 10B are schematic side views, partially in section, illustrating extravascular embodiments of methods and apparatus for non-continuous circumferential treatment of a body lumen, illustratively oblique circumferential treatment.

DETAILED DESCRIPTION

A. Overview

The applicants have discovered that it may be desirable to perform a circumferential treatment of a body lumen to positively affect a medical condition by applying energy to discrete zones that are non-continuous along the complete circumference of a radial cross-section generally normal to the lumen wall. For example, in the treatment of atrial fibrillation or other arrhythmia, a circumferential treatment may be achieved by forming a continuous circumferential lesion that is continuous completely about a normal cross-section of the pulmonary vein to disrupt aberrant electrical signals. In the treatment of heart failure, a circumferential treatment may be achieved by forming a similar continuous circumferential lesion that is continuous completely about a normal cross-section of a renal artery to reduce renal sympathetic neural activity. However, continuous circumferential lesions that extend continuously about a full 360° of the circumference of a cross-section normal to the body lumen or tissue in proximity to the body lumen may increase a risk of acute and/or late stenosis formation within the blood vessel. Therefore, many of the embodiments described below are directed to forming discrete, non-continuous lesions normal of a lumen without adversely affecting the vessel.

Such non-continuous treatments may, for example, be conducted from an intravascular or intraluminal position, which can include treatment utilizing elements passed from an intravascular location to an extravascular location, i.e., intra-to-extravascular treatment. However, it should be understood that extravascular treatment apparatus and methods in accordance with the present invention also may be provided.

The treatments can be applied relative to nerves, including nervous tissue in the brain, or other target structures within or in proximity to a blood vessel or other body lumen that travel at least generally parallel or along a lengthwise dimension of the blood vessel (body lumen). The target structures can additionally or alternatively comprise a rotational orientation relative to the blood vessel (body lumen). Several disclosed embodiments of non-continuous circumferential treatments may reduce the risk of acute and/or late stenosis formation by treating neural matter along portions of multiple radial planes or cross-sections that are normal to, and spaced apart along, the lengthwise or longitudinal axis of the blood vessel (body lumen).

The treatment area at each radial plane or cross-section defines a treatment zone that is not completely continuous along a normal circumference, i.e., defines a treatment zone without a continuous circumferential lesion normal to the longitudinal axis. However, superimposition of the multiple treatment zones along the multiple radial planes or normal cross-sections defines a non-continuous, overlapping circumferential treatment zone along a lengthwise or longitudinal segment of the blood vessel (body lumen). In some embodiments, this overlapping treatment zone may provide a non-continuous, but substantially fully circumferential treatment without formation of a continuous circumferential lesion normal to the vessel (lumen). In other embodiments, the overlapping treatment zone may provide a non-continuous, partial circumferential treatment.

In this manner, a non-continuous circumferential treatment is performed over a lengthwise segment of the blood vessel (body lumen), as compared to a continuous circumferential treatment at a single normal cross-section or radial plane. Target structures substantially traveling along the lengthwise dimension of the blood vessel (body lumen) are thus circumferentially affected in a non-continuous fashion without formation of the continuous circumferential lesion along any normal cross-section or radial plane of the blood vessel (body lumen). This may reduce a risk of acute or late stenosis formation within the blood vessel (body lumen). A non-continuous circumferential treatment can thus comprise a treatment conducted at multiple positions about the lengthwise dimension of a body lumen, wherein the treatment zone at any one lengthwise position does not comprise a continuous circumferential lesion completely about a radial plane or normal cross-section, but wherein a superimposition of the treatment zones at all or some of the lengthwise positions may define an overlapping circumferential treatment zone.

The non-continuous circumferential treatment optionally may be achieved via apparatus positioned within a body lumen in proximity to target neural fibers for application of energy to the target neural fibers. The treatment may be induced, for example, via electrical and/or magnetic energy application, via thermal energy application (either heating or cooling), via mechanical energy application, via chemical energy application, via nuclear or radiation energy application, via fluid energy application, etc. Such treatment may be achieved, for example, via a thermal or non-thermal electric field, via a continuous or pulsed electric field, via a stimulation electric field, via localized drug delivery, via high intensity focused ultrasound, via thermal techniques, via athermal techniques, combinations thereof, etc. Such treatment may, for example, effectuate irreversible electroporation or electrofusion, necrosis and/or inducement of apoptosis, alteration of gene expression, action potential blockade or attenuation, changes in cytokine up-regulation, ablation and other conditions in target neural fibers. All or a part of the apparatus optionally may be passed through a wall of the body lumen to an extraluminal location in order to facilitate the treatment. The body lumen may, for example, comprise a blood vessel, and the apparatus may be positioned within the blood vessel via well-known percutaneous techniques.

Treatment may be achieved via either direct alteration of the target structures (e.g., target neural structures) or at least in part via alteration of the vascular or other structures that support the target structures or surrounding tissue, such as arteries, arterioles, capillaries, veins or venules. In some embodiments, the treatment may be achieved via direct application of energy to the target or support structures. In other embodiments, the treatment may be achieved via indirect generation and/or application of the energy, such as through application of an electric field or of high-intensity focused ultrasound that causes resistive heating in the target or supporting structures. Alternative thermal techniques also may be utilized.

In some embodiments, methods and apparatus for real-time monitoring of the treatment and its effects on the target or support structures, and/or in non-target tissue, may be provided. Likewise, real-time monitoring of the energy delivery apparatus may be provided. Power or total energy delivered, impedance and/or the temperature, or other characteristics of the target or non-target tissue, or of the apparatus, additionally or alternatively may be monitored.

When utilizing an electric field to achieve desired circumferential treatment, the electric field parameters may be altered and combined in any combination, as desired. Such parameters can include, but are not limited to, frequency, voltage, power, field strength, pulse width, pulse duration, the shape of the pulse, the number of pulses and/or the interval between pulses (e.g., duty cycle), etc. For example, suitable field strengths can be up to about 10,000 V/cm, and may be either continuous or pulsed. Suitable shapes of the electrical waveform include, for example, AC waveforms, sinusoidal waves, cosine waves, combinations of sine and cosine waves, DC waveforms, DC-shifted AC waveforms, RF waveforms, microwaves, ultrasound, square waves, trapezoidal waves, exponentially-decaying waves, and combinations thereof.

When utilizing a pulsed electric field, suitable pulse widths can be of any desired interval, for example, up to about 1 second. The field includes at least one pulse, and in many applications the field includes a plurality of pulses or is continuously applied, e.g., for up to several minutes. Suitable pulse intervals include, for example, intervals less than about 10 seconds. These parameters are provided as suitable examples and in no way should be considered limiting.

When utilizing thermal mechanisms to achieve the desired treatment, protective elements optionally may be provided to protect the non-target tissue, such as the smooth muscle cells, from thermal damage during the thermally-induced non-continuous circumferential treatment. For example, when heating target nerves or support structures, protective cooling elements, such as convective cooling elements, may be provided to protect the non-target tissue. Likewise, when cooling target nerves or support structures, protective heating elements, such as convective heating elements, may be utilized to protect the non-target tissue. Thermal energy may be applied either directly or indirectly for a brief or a sustained period of time in order to achieve, for example, desired neuromodulation or denervation. Feedback, such as sensed temperature and/or impedance, along target or non-target tissue or along the apparatus, optionally may be used to control and monitor delivery of the thermal energy.

The non-target tissue optionally may be protected during, e.g., the neuromodulation or denervation, by utilizing blood flow as a conductive and/or convective thermal sink that absorbs excess thermal energy (hot or cold). For example, when blood flow is not blocked, the circulating blood may provide a relatively constant temperature medium for removing the excess thermal energy from the non-target tissue during the procedure. The non-target tissue additionally or alternatively may be protected by focusing the thermal (or other) energy on the target or support structures, such that an intensity of the energy is insufficient to induce thermal damage in the non-target tissue distant from the target or support structures.

Additional and alternative methods and apparatus may be utilized to achieve a non-continuous circumferential treatment without formation of a continuous circumferential lesion, as described hereinafter. To better understand the structures of devices of the present invention and the methods of using such devices for non-continuous circumferential treatment, it is instructive to examine a common neurovascular anatomy in humans.

B. Neurovascular Anatomy Summary

FIG. 1 illustrates a common anatomical arrangement of neural structures relative to body lumens or vascular structures, typically arteries. Neural fibers N generally may extend longitudinally along the lengthwise dimension L of an artery A about a relatively small range of positions along the radial dimension r, often within the adventitia of the artery. The artery A has smooth muscle cells SMC that surround the arterial circumference and generally spiral around the angular dimension θ of the artery, also within a relatively small range of positions along the radial dimension r. The smooth muscle cells of the artery accordingly have a lengthwise or longer dimension generally extending transverse (i.e., non-parallel) to the lengthwise dimension of the blood vessel. The misalignment of the lengthwise dimensions of the neural fibers and the smooth muscle cells is defined as “cellular misalignment.”

The cellular misalignment of the nerves N and the smooth muscle cells SMC may be exploited to selectively affect the nerve cells with reduced effect on the smooth muscle cells. More specifically, a non-continuous circumferential treatment may be achieved by superimposing treatments undertaken along multiple radial or cross-sectional planes of the artery A that are separated along the lengthwise dimension L of the artery, rather than performing a continuous circumferential treatment along a single radial plane or cross-section of the artery. In this manner, due to the cellular misalignment, the lengthwise-oriented neural fibers may experience a full, non-continuous circumferential treatment, while the angularly-oriented smooth muscle cells may experience only a partial circumferential treatment. Monitoring elements optionally may be utilized to assess an extent of treatment induced in the nerves and/or in the smooth muscle cells, as well as to adjust treatment parameters to achieve a desired effect.

C. Embodiments of Apparatus and Methods for Non-Continuous Circumferential Treatment of a Body Lumen

FIGS. 2-7 and 9 illustrate examples of intravascular systems and methods for performing non-continuous circumferential treatments. The applicants have described intravascular and intra-to-extravascular systems for neuromodulation or denervation, for example, in Applicants' U.S. Pat. Nos. 7,653,438 and 7,620,451, both of which have been incorporated herein by reference. The applicants also have described extravascular systems for neuromodulation or denervation (see, for example, U.S. Pat. No. 8,145,316, incorporated herein by reference), and it should be understood that non-continuous circumferential treatments may be performed using extravascular (or extraluminal) systems, in addition to intravascular (intraluminal) or intra-to-extravascular (intra-to-extraluminal) systems (see FIGS. 10A and 10B). Applicants also have previously described thermal systems for neuromodulation or denervation, for example, in Applicants' U.S. Pat. No. 7,617,665.

Referring now to FIGS. 2A-2J, the embodiment of an apparatus 300 comprises a catheter 302 having an optional positioning element 304 (e.g., a balloon, an expandable wire basket, other mechanical expanders, etc.) and expandable electrode element 306 positioned along the shaft of the catheter and illustratively located over the positioning element. The electrode element 306 can have one or more electrodes 307 electrically coupled to a field generator 50 for delivery of an electric field to the target neural fibers. In an alternative embodiment, one or more of the electrode(s) 307 of the electrode element 306 may comprise Peltier electrodes for heating or cooling the target neural fibers to modulate the fibers. The electrode(s) 307 optionally may be individually assignable and may be utilized in a bipolar fashion, and/or may be utilized in a monopolar fashion with an external ground pad attached to the exterior of the patient.

The field generator 50, as well as any of the electrode embodiments described herein, may be utilized with any embodiment of the present invention for delivery of an electric field with desired field parameters. The field generator 50 can be external to the patient. It should be understood that electrodes of embodiments described hereinafter may be electrically connected to the generator even though the generator is not explicitly shown or described with each embodiment. Furthermore, the field generator optionally may be positioned internal to the patient, and the electrodes and/or the field generator optionally may be temporarily or permanently implanted within the patient.

The positioning element 304 optionally may position or otherwise drive the electrode(s) 307 into contact with the vessel wall. The positioning element 304 may also comprise an impedance-altering element that alters the impedance within the vessel during the therapy to direct the electric field across the vessel wall. This may reduce an energy required to achieve desired neuromodulation or denervation and may reduce a risk of injury to non-target tissue. Applicants have previously described use of an impedance-altering element, for example, in Applicants' U.S. Pat. No. 7,756,583, which is incorporated herein by reference in its entirety. When the positioning element 304 comprises an inflatable balloon, as in FIGS. 2A-J, the balloon may serve as both a centering and/or expansion element for the expandable electrode element 306, and as an impedance-altering electrical insulator for directing an electric field delivered via the electrode(s) 307 into or across the vessel wall for modulation of target neural fibers. Electrical insulation provided by the element 304 may reduce the magnitude of applied energy or other parameters of the electric field necessary to achieve desired modulation of the target fibers, up to and including full denervation of tissue containing the target fibers.

Furthermore, element 304 optionally may be utilized as a thermal element. For example, it may be inflated with a chilled fluid that serves as a heat sink for removing heat from tissue that contacts the element. Conversely, element 304 may be inflated with a warmed fluid that heats tissue in contact with the element. The thermal fluid within the element optionally may be circulated and/or exchanged within the positioning element 304 to facilitate more efficient conductive and/or convective heat transfer. Thermal fluids also may be used to achieve thermal neuromodulation via thermal cooling or heating mechanisms, as described in greater detail herein below.

The electrode(s) 307 can be individual electrodes (i.e., independent contacts), a segmented electrode with commonly connected contacts, or a single continuous electrode. Furthermore, the electrode(s) 307 may be configured to provide a bipolar signal, or the electrode(s) 307 may be used together or individually in conjunction with a separate patient ground pad for monopolar use. As an alternative or in addition to placement of the electrode(s) 307 along the expandable electrode element 306, as in FIG. 2, the electrode(s) 307 may be attached to the positioning element 304 such that they contact the wall of the artery upon expansion of the positioning element. In such a variation, the electrode(s) may, for example, be affixed to the inside surface, outside surface or at least partially embedded within the wall of the positioning element (see FIGS. 5A and 5B). In another embodiment, the electrode(s) do not contact the vessel wall, and may be positioned at any desired location within the vessel.

The electrode(s) 307 or any other portion of the apparatus 300, such as catheter 302 or element 304, additionally or alternatively may comprise one or more sensors, such as thermocouples 310, for monitoring the temperature or other parameters of the target tissue, the non-target tissue, the electrodes, the positioning element and/or any other portion of the apparatus 300 or of the patient's anatomy. The treatment regime may be controlled using the measured parameter(s) as feedback. This feedback may be used, for example, to maintain the parameter(s) below a desired threshold, for example, a threshold that may cause injury to the non-target tissues. Conversely, the feedback may be used to maintain the parameter(s) at or above a desired threshold, for example, a threshold that may induce a desired effect in the target tissues, such as neuromodulation of target neural fibers or denervation of tissues innervated by the target neural fibers. Furthermore, the feedback may be used to keep the parameter(s) within a range that will induce the desired effect in the target tissues without injuring the non-target tissues to an unacceptable extent. Multiple parameters (or the same or multiple parameters at multiple locations) optionally may be used as control feedback for ensuring the desired effects while mitigating the undesired effects while mitigating the undesired effects.

As seen in FIG. 2A, the catheter 302 may be delivered to a treatment site within the artery A (or within a vein or any other vessel in proximity to target neural fibers) in a low profile delivery configuration, for example, through the guide catheter or sheath 303. Alternatively, catheters may be positioned in multiple vessels for neuromodulation, e.g., within both an artery and a vein. Multi-vessel techniques for electric field neuromodulation have been described previously, for example, in Applicant's U.S. Pat. No. 7,853,333, which is incorporated herein by reference in its entirety.

Once positioned within the vasculature as desired, the optional positioning element 304 may be expanded to display the electrode element 306 and bring the electrode(s) 307 into contact with an interior wall of the vessel, as seen in FIG. 2B. An electric field then may be generated by the field generator 50, transferred through the catheter 302 to the electrode element 306 and the electrodes 307, and delivered via the electrode(s) 307 across the wall of the artery. The electric field modulates the activity along neural fibers within the wall of the artery or in proximity to the artery, e.g., at least partially denervates tissue or organ(s) innervated by the neural fibers. This may be achieved, for example, via ablation or necrosis or via non-ablative injury or other changes to the target neural fibers or supporting structures. The electric field also may induce electroporation in the neural fibers.

As seen in the cross-sectional view of FIG. 2C taken along the radial plane I-I of FIG. 2B, the apparatus 300 illustratively comprises four electrodes 307 equally spaced about the circumference of the electrode element 306 and the positioning element 304. As seen in FIG. 2D, when utilized in a monopolar fashion in combination with an external ground (not shown; per se known), the circumferential segments treated by each electrode overlap to form discrete treatment zones TZ_I that are not continuous completely around the circumference of the artery in a radial plane normal to the vessel wall. As a result, there are discrete untreated zones UZ_I about the circumference of the artery.

As seen in FIG. 2E, the electrode element 306 may be collapsed about the radial dimension r of the artery such that the electrodes 307 do not contact the vessel wall, e.g., by collapsing the positioning element 304. The electrode element 306 may be rotated about the angular dimension θ of the artery to angularly reposition the electrodes 307 (best shown in FIG. 2G). This rotation may be achieved, for example, by angularly rotating the catheter 302. In FIG. 2E, the electrode element illustratively has been rotated approximately 45° about the angular dimension of the artery. In the embodiment of apparatus 300 shown in FIGS. 2A-G, the electrodes are equally spaced about the circumference of the apparatus such that a 45° angular rotation repositions the electrodes approximately halfway between the initial positions of the electrodes shown in FIG. 2D.

In addition to angular repositioning of the electrodes, the electrodes may be repositioned along the lengthwise or longitudinal dimension L of the artery, which is also shown in FIG. 2E as the longitudinal offset between the electrodes 307 and the radial plane I-I. Such lengthwise repositioning may occur before, after or concurrent with angular repositioning of the electrodes. As seen in FIG. 2F, once repositioned in both the lengthwise and angular dimensions, the electrode element 306 may be re-expanded about the radial dimension to contact the electrodes 307 with the vessel wall. An electric field then may be delivered via the angularly and lengthwise repositioned electrodes 307 along the normal radial plane II-II.

In FIG. 2G, the treatment along radial plane II-II of FIG. 2F creates treatment zone TZ_II and untreated zone UZ_II. As with the treatment zone TZ_I of FIG. 2D, the treatment zone TZ_II of FIG. 2G is not continuous about the complete circumference of the artery. FIGS. 2H and 2I allow comparison of the treatment zone TZ_I and the treatment zone TZ_II. The apparatus 300 is not shown in FIGS. 2H and 2I, e.g., the apparatus may have been removed from the patient to complete the procedure.

As shown, the untreated zones UZ_I and UZ_II along the radial planes I-I and II-II, respectively, are angularly offset from one another about the angular dimension θ of the artery (see FIG. 1). As seen in FIG. 2J, by superimposing the treatment zones TZ_I and TZ_II, which are positioned along different cross-sections or radial planes of the artery A, a composite treatment zone TZ_I-II is formed that provides a non-continuous, yet substantially circumferential treatment over a lengthwise segment of the artery. This superimposed treatment zone beneficially does not create a continuous circumferential lesion along any individual radial plane or cross-section normal to the artery, which may reduce a risk of acute or late stenosis formation, as compared to previous circumferential treatments that create a continuous circumferential lesion.

As discussed previously, non-continuous circumferential treatment by positioning electrodes at different angular orientations along multiple lengthwise locations may preferentially affect anatomical structures that substantially propagate along the lengthwise dimension of the artery. Such anatomical structures can be neural fibers and/or structures that support the neural fibers. Furthermore, such a non-continuous circumferential treatment may mitigate or reduce potentially undesirable effects induced in structures that propagate about the angular dimension of the artery, such as smooth muscle cells. The angular or circumferential orientation of the smooth muscle cells relative to the artery may at least partially explain why continuous circumferential lesions may increase a risk of acute or late stenosis.

Although in FIGS. 2A-J the electrode element 306 is expanded via the positioning element 304, it should be understood that expandable electrode elements or electrodes in accordance with the present invention additionally or alternatively may be configured to self-expand into contact with the vessel wall. For example, the electrodes may self-expand after removal of a sheath or a guide catheter 303 constraining the electrodes in a reduced delivery configuration. The electrodes or electrode elements may, for example, be fabricated from (or coupled to) shape-memory elements that are configured to self-expand. Self-expanding embodiments optionally may be collapsed for retrieval from the patient by re-positioning of a constraining sheath or catheter over the self-expanding elements. Optionally, the electrode element may be shapeable by a medical practitioner, e.g., in order to provide a desired wall-contacting profile.

FIG. 3 illustrates an alternative embodiment of the apparatus 300 having a self-expanding electrode element 306′. Positioning element 304 has been removed from the apparatus. In use, the apparatus 300 is advanced to a treatment site within sheath or guide catheter 303. The sheath is removed, and the element 306′ self-expands to bring the electrodes 307 into contact with the vessel wall. Advantageously, blood continues to flow through the artery A during formation of treatment zone TZ_I. The element 306′ then may be partially or completely collapsed (e.g., within sheath 303), angularly rotated relative to the vessel, laterally repositioned relative to the vessel, and re-expanded into contact with the vessel wall along a different radial plane or cross-section. Treatment may proceed at the new location and in the new angularly orientation in the presence of blood flow, e.g., to form overlapping treatment zone TZ_II that completes a non-continuous circumferential treatment zone TZ_I-II when superimposed with the treatment zone TZ_I. The element 306′ then may be re-collapsed, and the apparatus 300 may be removed from the patient to complete the procedure.

Referring now to FIG. 4, it may be desirable to achieve a non-continuous circumferential treatment without angular and/or lengthwise repositioning of electrodes or other energy delivery elements. To this end, in another embodiment an apparatus 400 comprises catheter 402 having actively-expandable or self-expanding basket 404 having proximal electrodes 406 and distal electrodes 408 spaced longitudinally apart from the proximal electrodes. The proximal electrodes 406 and distal electrodes 408 are also spaced apart radially about the basket and electrically coupled to the field generator 50 (see FIG. 2A). The proximal electrodes 406 can be positioned along different struts or elements of the basket than the distal electrodes. The proximal and distal electrodes are accordingly angularly and laterally offset from one another.

The proximal electrodes may be operated independently of the distal electrodes, and/or the proximal and distal electrodes all may be operated at the same polarity, e.g., in a monopolar fashion as active electrodes in combination with an external ground. Alternatively or additionally, the proximal electrodes may be utilized in a bipolar fashion with one another and/or the distal electrodes may be utilized in a bipolar fashion with one another. The proximal and distal electrodes preferably are not utilized together in a bipolar fashion. By treating with the distal electrodes 408, the treatment zone TZ_I of FIG. 2H may be formed about the artery. Treating with the proximal electrodes 406 may create the treatment zone TZ_II of FIG. 2I, which is angularly offset relative to the treatment zone TZ_I. Superimposition of the treatment zones TZ_I and TZ_II creates the non-continuous circumferential treatment zone TZ_I-II over a lengthwise segment of the artery.

The proximal and distal electrodes optionally may be utilized concurrently to concurrently form the treatment zones TZ_I and TZ_II. Alternatively, the electrodes may be operated sequentially in any desired order to sequentially form the treatment zones. As yet another alternative, the treatment zones may be formed partially via concurrent treatment and partially via sequential treatment.

FIGS. 5A and 5B describe additional apparatus and methods for non-continuous circumferential treatment without having to reposition electrodes or other energy delivery elements. As seen in FIGS. 5A and 5B, the apparatus 300 has an electrode element 306″ that comprises a flex circuit coupled to or positioned about the positioning element 304. The flex circuit is electrically coupled to the field generator 50 by wires that extend through or along the catheter 302 or by wireless. In FIG. 5A, the flex circuit comprises a collapsible cylinder positioned about the positioning element 304. In FIG. 5B, the flex circuit comprises individual electrical connections for each electrode 307, which may facilitate collapse of the flex circuit for delivery and retrieval. As with the electrodes of apparatus 400 of FIG. 4, the electrodes 307 of FIG. 7 are spaced at multiple lengthwise positions relative to the positioning element and the blood vessel. The electrodes may be operated as described previously to achieve a non-continuous circumferential treatment. As the electrodes 307 illustratively are positioned at three different lengthwise positions, the non-continuous circumferential treatment may, for example, be formed via superimposition of three treatment zones (one at each lengthwise position within the blood vessel).

With any of the embodiments described herein, during delivery of the electric field (or of other energy), blood within the vessel may act as a thermal sink (either hot or cold) for conductive and/or convective heat transfer for removing excess thermal energy from the non-target tissue (such as the interior wall of the vessel), thereby protecting the non-target tissue. This effect may be enhanced when blood flow is not blocked during energy delivery, for example, as in the embodiments of FIGS. 3 and 4 (it should be understood that a variation of the embodiments of FIG. 5 may provide for blood flow; for example, the electrode(s) may be brought into contact with the vessel wall via an expandable basket rather than via an inflatable balloon). Use of the patient's blood as a thermal sink is expected to facilitate delivery of longer or higher energy treatments with reduced risk of damage to the non-target tissue, which may enhance the efficacy of the treatment at the target tissue, for example, at target neural fibers.

In addition or as an alternative to utilizing the patient's blood as a thermal sink, a thermal fluid (hot or cold) may be injected, infused or otherwise delivered into the vessel to remove excess thermal energy and protect the non-target tissues. This method of using an injected thermal fluid to remove excess thermal energy from non-target tissues to protect the non-target tissues from thermal injury during therapeutic treatment of target tissues may be utilized in body lumens other than blood vessels. The thermal fluid may, for example, comprise chilled or room temperature saline (e.g., saline at a temperature lower than the temperature of the vessel wall during the therapy delivery). The thermal fluid may, for example, be injected through the device catheter or through a guide catheter. The thermal fluid injection may be in the presence of blood flow or with flow temporarily occluded. Occlusion of flow in combination with thermal fluid delivery may facilitate better control over the heat transfer kinetics along the non-target tissues, as well as optional injection of the fluid from a downstream location.

Referring now to FIG. 6, another embodiment of the apparatus 300 is described that comprises optional flow occlusion and thermal fluid injection. The optional occlusion/positioning element 304 illustratively is coupled to the guide catheter 303, and the catheter 302 may be repositioned relative to the guide catheter to reposition the electrode(s) 307, optionally without re-establishing flow through the vessel. In FIG. 6, the alternative electrode element 306′″ is self-expanding, and/or is shapeable (e.g., is formed from a spring steel) by a medical practitioner to provide a desired profile for positioning of the electrode(s) 307 into contact with the vessel wall.

The catheter 302 may be advanced within the renal artery RA in a reduced profile delivery configuration. Once properly positioned, the electrode element 306′″ may self-expand (or may be actively expanded) to bring the electrode(s) 307 into contact with the vessel wall, for example, by removing the electrode element from the lumen of the guide catheter. The element 304 also may be expanded (before, during or after expansion of the electrode element) in order to properly position the electrode within the vessel and/or to occlude blood flow within, e.g., the renal artery. An electric field, such as a monopolar electric field, may be delivered via the electrode(s) 307, e.g., between the electrode(s) and an external ground (not shown; per se known). The electric field may, for example, comprise a pulsed or continuous RF electric field that thermally induces neuromodulation (e.g., necrosis or ablation) in the target neural fibers. The therapy may be monitored and/or controlled, for example, via data collected with thermocouples or other sensors, e.g., impedance sensors.

In order to increase the power or duration of the treatment that may be delivered without damaging non-target tissue of the vessel wall to an unacceptable extent, a thermal fluid infusate I may be injected, e.g., through the guide catheter 303 to cool (heat) the non-target tissue, thereby mitigating damage to the non target tissue. The infusate may, for example, comprise chilled saline that removes excess thermal energy (hot or cold) from the wall of the vessel during thermal RF therapy.

Convective or other heat transfer between the non-target vessel wall tissue and the infusate I may facilitate cooling (heating) of the vessel wall at a faster rate than cooling (heating) occurs at the target neural fibers. This heat transfer rate discrepancy between the wall of the vessel and the target neural fibers may be utilized to modulate the neural fibers with reduced damage to the vessel wall. Furthermore, when utilizing a pulsed therapy, the accelerated heat transfer at the wall relative to the neural fibers may allow for relatively higher power or longer duration therapies (as compared to continuous therapies), due to the additional time between pulses for protective cooling at the vessel wall. Also, the interval between pulses may be used to monitor and/or control effects of the therapy.

Referring now to FIG. 6B, treatment at additional angular and lengthwise positions relative to the vessel wall may be achieved by rotation and lengthwise repositioning of the catheter 302. This may be repeated at as many lengthwise and/or angular positions as desired by the medical practitioner. The treatment(s) at each individual lengthwise position preferably do not form a continuous circumferential lesion normal to the vessel wall, while superimposition of the treatments at multiple such lengthwise positions preferably forms a non-continuous, partially or fully circumferential lesion, as described previously.

In the embodiment of the FIG. 6, the apparatus illustratively comprises a single electrode 307. However, multiple such electrodes optionally may be provided at multiple, angularly-offset positions, as in FIG. 7A. This may reduce the number of lengthwise positions where treatment needs to be conducted in order to achieve the non-continuous, substantially circumferential treatment of the present invention. In addition or as an alternative to angular offsetting, the electrodes optionally may be offset lengthwise from one another, such that treatment at the multiple lengthwise positions may be achieved concurrently or sequentially without necessitating lengthwise repositioning of the electrodes. FIG. 7B illustrates an embodiment of apparatus 300 having multiple electrodes that are offset from one another both angularly and lengthwise. In such an embodiment, the relative angular and lengthwise positions of the electrodes may be fixed or may be dynamically alterable by the medical practitioner.

As described herein, a continuous circumferential lesion is a circumferential lesion that is substantially continuous in a radial plane normal to the vessel or luminal wall. Conversely, a non-continuous circumferential lesion may be non-continuous relative to a normal radial plane, but substantially continuous along an oblique plane of the vasculature that is not normal to the vessel wall. For example, as seen in dotted profile in FIG. 8, an oblique circumferential treatment OC may be achieved within the patient's vasculature, e.g., the patient's renal artery RA, without formation of a continuous circumferential treatment relative to a normal radial plane of the vasculature. The previously-described apparatus and methods of FIG. 5 may, for example, form such an oblique circumferential treatment OC.

FIGS. 9A and 9B illustrate additional methods and apparatus for achieving such oblique circumferential treatments. In FIG. 9A, the apparatus 300 comprises a spiral or helical electrode element 307 that contacts the wall of the vasculature along one or more partial or complete oblique circumferences. The electrode element 307 may comprise a single continuous electrode over all or a portion of the spiral for formation of a continuous oblique treatment, and/or may comprise multiple discrete electrodes positioned along the spiral, e.g., for formation of a non-continuous circumferential treatment relative to both oblique and the normal planes of the vessel. Regardless of the form of the electrode element 307, the treatment zone(s) formed with the electrode may form a non-continuous circumferential treatment relative to the normal radial plane of the vasculature.

FIG. 9B illustrates an alternative embodiment of the apparatus and methods of FIG. 9A, in which the electrode element 307 comprises a double helix. This may facilitate formation of multiple, non-continuous treatment zones along one or more normal radial planes of the vessel. Continuous or non-continuous oblique treatments also may be achieved, while non-continuous normal circumferential treatments are achieved via superimposition of treatment at multiple locations (either discrete or continuous) along a lengthwise segment of the vasculature.

Referring now to FIGS. 10A and 10B, extravascular variations are described. FIG. 10A illustrates a percutaneous or transcutaneous extravascular variation having electrode(s) configured for temporary placement about the renal vasculature of the patient. FIG. 10B illustrates an implantable extravascular variation configured for prolonged placement within the patient. As will be apparent to those of skill in the art, a composite extravascular variation also may be provided having some elements configured for temporary placement and some elements configured for prolonged placement. In one such variation, one or more electrodes may be implanted within the patient, and a pulse generator or battery charging unit, etc., may be placed external to the patient and/or may be placed within the patient only temporarily during treatment, diagnostics, charging, etc.

The apparatus and methods of FIG. 10 illustratively are configured for formation of partially or completely continuous oblique circumferential treatments that are non-continuous relative to normal radial planes of the patient's vasculature. However, it should be understood that alternative extravascular embodiments may comprise non-continuous normal circumferential treatments that are non-continuous about both the normal and lengthwise dimensions of the vasculature, as opposed to just the normal dimension, i.e., that are also non-continuous about the oblique section. See, for example, the treatments defined by the apparatus and methods of FIGS. 2-7.

In FIG. 10A, apparatus 500 comprises needle or trocar 503 that forms percutaneous access site P. Catheter 502 is advanced through the trocar into proximity of the patient's renal artery RA. Electrode element 507 spirals about the renal artery for formation of an oblique circumferential treatment, as described with respect to FIG. 9A. Electrode element 507 is electrically coupled to field generator 50 for delivery of a desired electrical treatment. The apparatus 500 optionally may be removed from the patient, and the access site P closed, after formation of the oblique circumferential treatment.

FIG. 10B illustrates an extravascular embodiment that is fully implantable and illustratively is configured for bilateral treatment of nerves innervating both of the patient's kidney. It should be understood that any of the previously described embodiments also may be utilized for bilateral treatment, either concurrently or sequentially. Apparatus 600 comprises first and second spiral electrode elements 607a and 607b that spiral about the patient's renal arteries. The electrode elements are electrically coupled to implantable field generator 650, e.g., via tunneled leads 652, for formation of the previously described oblique circumferential treatment.

FIGS. 2-7 and 9-10 illustratively describe electrical methods and apparatus for circumferential treatment without formation of a continuous circumferential lesion positioned normal to the lengthwise axis of the patient's vasculature. However, it should be understood that alternative energy modalities, including magnetic, mechanical, thermal, chemical, nuclear/radiation, fluid, etc., may be utilized to achieve the desired circumferential treatment without circumferential lesion. Furthermore, although FIGS. 2-7 and 9 illustratively comprise fully intravascular positioning of the apparatus, it should be understood that all or a portion of the apparatus in any of the embodiments may be positioned extravascularly as in FIG. 10, optionally via implantation and/or via an intra-to-extravascular approach.

Although preferred illustrative variations of the present invention are described above, it will be apparent to those skilled in the art that various changes and modifications may be made thereto without departing from the invention. For example, although in the described embodiments of FIGS. 2-4 non-continuous circumferential treatment is achieved via superimposition of treatment at two locations, it should be understood that treatment at more than two locations may be superimposed to achieve the circumferential treatment, as described with respect to FIGS. 5A and 5B. Furthermore, although in the described embodiments the methods are conducted in a blood vessel, it should be understood that treatment alternatively may be conducted in other body lumens. It is intended in the appended claims to cover all such changes and modifications that fall within the true spirit and scope of the invention.

Claims

1. An apparatus for renal denervation, the apparatus comprising: a catheter configured for intravascular placement within a renal artery of a human patient;an inflatable balloon at a distal portion of the catheter, wherein the inflatable balloon is configured to vary between a delivery configuration and a deployed configuration sized and shaped to fit within the renal artery; anda plurality of electrodes attached to the inflatable balloon, wherein each electrode comprises at least one pair of bipolar contacts,wherein, when the inflatable balloon is in the deployed configuration, the electrodes are offset from each other and positioned at different lengthwise positions along the balloon to define, at least in part, a helical pattern about the balloon,wherein the electrodes are configured to deliver thermal radio frequency (RF) energy across an interior wall of the renal artery to target renal nerves to achieve at least partial renal denervation.

2. The apparatus of claim 1 wherein the plurality of electrodes comprises a first electrode and a second electrode, and wherein the first and second electrodes are parts of a flex circuit on a surface of the inflatable balloon.

3. The apparatus of claim 2 wherein the flex circuit terminates proximally of a distal end portion of the inflatable balloon.

4. The apparatus of claim 1 wherein the inflatable balloon is configured to bring the individual electrodes into apposition with an interior wall of the renal artery when the inflatable balloon is in the deployed configuration.

5. The apparatus of claim 1 wherein, in the deployed configuration, the inflatable balloon is sized to occlude the renal artery.

6. The apparatus of claim 1 wherein each of the electrodes is dynamically assignable.

7. The apparatus of claim 1 wherein the electrodes are configured to be energized concurrently.

8. The apparatus of claim 1 wherein the electrodes are configured to be energized sequentially.

9. The apparatus of claim 1 wherein the plurality of electrodes comprises four or more electrodes.

10. The apparatus of claim 1 wherein the individual electrodes are configured to deliver the thermal RF energy through an inner wall of the renal artery to the target renal nerves to reduce renal sympathetic nerve activity.

11. The apparatus of claim 1 wherein the thermal RF energy from the electrodes is sufficient to reduce neural communication to and from a kidney of the patient.

12. The apparatus of claim 1 wherein the thermal RF energy from the electrodes is sufficient to cause at least partial ablation of the target renal nerves of the patient.

13. The apparatus of claim 1, further comprising one or more sensors at the distal portion of the catheter for monitoring and/or controlling effects of the thermal RF energy delivery.

14. The apparatus of claim 13 wherein at least one of the sensors comprises a thermocouple for monitoring temperature.

15. The apparatus of claim 1 wherein the catheter and inflatable balloon are configured for placement within the renal artery over a guidewire.

16. The apparatus of claim 1, further comprising a field generator external to the patient and electrically coupled to the plurality of electrodes.

17. A renal neuromodulation system for treatment of a human patient, the system comprising: an electric field generator configured to deliver a thermal RF field to renal nerves that modulate renal neural activity of the patient; anda catheter comprising (a) a shaft having a lumen therethrough, (b) an inflatable distal balloon, and (c) a plurality of bipolar RF electrodes, wherein each electrode comprises a pair of bipolar contacts, and wherein the catheter is transformable between— a reduced profile delivery configuration for percutaneous intravascular placement within renal vasculature of the patient, andan expanded treatment configuration for delivering the thermal RF field to one or more of the renal nerves,wherein the plurality of bipolar RF electrodes are electrically connectable to the electric field generator and are arranged about the inflatable balloon in a helical configuration for delivering the thermal RF field to one or more of the renal nerves to thermally induce modulation of a function of the one or more renal nerves when the inflatable balloon is at least partially located within the renal vasculature.

18. The system of claim 17 wherein the electric field generator is configured to independently control each electrode.

19. The system of claim 17 wherein, when the catheter is in the expanded treatment configuration, the inflatable balloon is configured to maintain apposition with an interior wall of the renal vasculature throughout treatment.

20. The system of claim 17 wherein the lumen is sized and shaped to receive a guide wire.

21. The system of claim 17 wherein the individual bipolar RF electrodes comprise a plurality of bipolar contacts.