US20230329772A1 - Electroporation systems and catheters for electroporation systems - Google Patents

Abstract

The present disclosure provides electroporation systems, methods of controlling electroporation systems to limit electroporation arcs through intracardiac catheters, and catheters for electroporation systems. One method of controlling an electroporation system including a direct current (DC) energy source, a return electrode connected to the DC energy source, and a catheter connected to the DC energy source is disclosed. The catheter has a at least one catheter electrode. The method includes positioning the return electrode near a target location within a body and positioning the catheter electrode adjacent the target location within the body. A system impedance is determined with the return electrode positioned near the target location and the catheter electrode positioned within the body. The system impedance is adjusted to a target impedance to limit arcing from the catheter electrode.

Description

CROSS REFERENCE TO RELATED APPLICATIONS
• This application is a divisional of U.S. application Ser. No. 16/464,738, filed on May 29, 2019, which is the national stage entry of PCT/US2017/063650, filed on Nov. 29, 2017, which claims the benefit of priority to U.S. provisional application Ser. No. 62/427,190, filed Nov. 29, 2016, U.S. provisional application Ser. No. 62/427,195, filed Nov. 29, 2016, and U.S. provisional application Ser. No. 62/431,735, filed Dec. 8, 2016, all of which are incorporated herein by reference in their entirety.
FIELD OF THE DISCLOSURE
• The present disclosure relates generally to medical devices that are used in the human body. In particular, in many embodiments, the present disclosure relates to electroporation systems and methods of controlling electroporation systems to limit electroporation arcs from catheters. Further, the present disclosure relates to systems and methods for identifying such arcs.
BACKGROUND
• It is generally known that ablation therapy may be used to treat various conditions afflicting the human anatomy. One such condition in which ablation therapy finds a particular application in, for example, is the treatment of atrial arrhythmias. When tissue is ablated, or at least subjected to ablative energy generated by an ablation generator and delivered by an ablation catheter, lesions form in the tissue. Electrodes mounted on or in ablation catheters are used to create tissue necrosis in cardiac tissue to correct conditions such as atrial arrhythmia (including, but not limited to, ectopic atrial tachycardia, atrial fibrillation, and atrial flutter). Arrhythmia (i.e., irregular heart rhythm) can create a variety of dangerous conditions including loss of synchronous atrioventricular contractions and stasis of blood flow which can lead to a variety of ailments and even death. It is believed that the primary cause of atrial arrhythmia is stray electrical signals within the left or right atrium of the heart. The ablation catheter imparts ablative energy (e.g., radiofrequency energy, cryoablation, lasers, chemicals, high-intensity focused ultrasound, etc.) to cardiac tissue to create a lesion in the cardiac tissue. This lesion disrupts undesirable electrical pathways and thereby limits or prevents stray electrical signals that lead to arrhythmias.
• One candidate for use in therapy of cardiac arrhythmias is electroporation. Electroporation therapy involves electric-field induced pore formation on the cell membrane. The electric field may be induced by applying a direct current (DC) signal delivered as a relatively short duration pulse which may last, for instance, from a nanosecond to several milliseconds. Such a pulse may be repeated to form a pulse train. When such an electric field is applied to tissue in an in vivo setting, the cells in the tissue are subjected to trans-membrane potential, which opens the pores on the cell wall, hence the term electroporation. Electroporation may be reversible (i.e., the temporally-opened pores will reseal) or irreversible (i.e., the pores will remain open). For example, in the field of gene therapy, reversible electroporation (i.e., temporarily open pores) is used to transfect high molecular weight therapeutic vectors into the cells. In other therapeutic applications, a suitably configured pulse train alone may be used to cause cell destruction, for instance by causing irreversible electroporation.
BRIEF SUMMARY OF THE DISCLOSURE
• The present disclosure generally relates to electroporation systems, methods of controlling electroporation systems, and catheters for electroporation systems. In many embodiments, the electroporation system includes a monophasic direct current (DC) energy source connected to a catheter including several catheter electrodes. Other embodiments and descriptions of the present disclosure are set forth below.
• In one embodiment, the present disclosure is directed to a method of controlling an electroporation system including a direct current (DC) energy source, a return electrode connected to the DC energy source, and a catheter connected to the DC energy source. The catheter has at least one catheter electrode. The method includes positioning the return electrode near a target location within a body and positioning the catheter electrode adjacent the target location within the body. A system impedance is determined with the return electrode positioned near the target location and the catheter electrode positioned within the body. The system impedance is adjusted to a target impedance to limit arcing from the catheter electrode.
• In another embodiment, the present disclosure is directed to an electroporation system including a monophasic energy source, a return electrode, a catheter, and a variable impedance. The return electrode is connected to a return of the monophasic energy source. The catheter is connected to an output of the monophasic energy source and includes at least one catheter electrode. The variable impedance is connected to the monophasic energy source to selectively vary an impedance of the electroporation system.
• In another embodiment, the present disclosure is directed to a method of controlling an electroporation system including a monophasic energy source, a return electrode connected to the monophasic energy source, and a catheter connected to the monophasic energy source. The catheter has an electrode surface area. The method includes determining a system impedance with the patch electrode on a body and the catheter positioned within the body adjacent a target area. The system impedance is adjusted to a target impedance selected to cause the monophasic energy source to produce a current density on the electrode surface area of less than 150 milliamps per square millimeter (mA/mm²). For example, at least one resistor may be connected to the catheter or return electrode to adjust the system impedance. Alternatively, a pulse energy may be modified (e.g., using a knob or other input mechanism included in the electroporation system) to adjust the system impedance.
• In another embodiment, the present disclosure is directed to a catheter including a handle, a shaft, a distal loop subassembly, and a plurality of electrode wires. The handle includes an insulated electrical connector at a proximal end of the handle configured for connection to an electroporation generator and defines an interior channel. The shaft is coupled to and extends from a distal end of the handle. The shaft defines an interior channel. The distal loop subassembly is coupled to a distal end of the shaft and includes a loop having a plurality of catheter electrodes disposed thereon. Each electrode wire of the plurality of electrode wires is coupled to a different catheter electrode of the plurality of catheter electrodes and extends from the distal loop assembly to the connector through the interior channels of the shaft and the handle. Each electrode wire of the plurality of electrode wires is surrounded by an insulator with a thickness of at least about 1.5 thousandths of an inch.
• In another embodiment, the present disclosure is directed to a system including an electroporation subsystem having an electroporation energy source, a second subsystem configured for at least one of diagnostic, mapping, and navigation operations, a catheter and a selection interface. The catheter includes a plurality of catheter electrodes, an electrical connector, and a plurality of electrode wires. Each electrode wire of the plurality of electrode wires is coupled to a different catheter electrode of the plurality of electrodes and the electrical connector. The selection interface is coupled to the electroporation subsystem, the second subsystem, and the catheter's electrical connector. The selection interface is configured for selectively coupling the catheter to a selected one of the electroporation subsystem and the second subsystem.
• In another embodiment, the present disclosure is directed to an electroporation system including a monophasic energy source, a return electrode connected to a return of the monophasic energy source, and a catheter connected to an output of the monophasic energy source. The catheter includes a handle, a shaft, a distal loop subassembly and a plurality of electrode wires. The handle includes an insulated electrical connector at a proximal end of the handle configured for connection to an electroporation generator and defines an interior channel. The shaft is coupled to and extends from a distal end of the handle. The shaft defines an interior channel. The distal loop subassembly is coupled to a distal end of the shaft and includes a loop having a plurality of catheter electrodes disposed thereon. Each electrode wire of the plurality of electrode wires is coupled to a different catheter electrode of the plurality of catheter electrodes and extends from the distal loop assembly to the connector through the interior channels of the shaft and the handle. Each electrode wire of the plurality of electrode wires is surrounded by an insulator with a thickness of at least about 1.5 thousandths of an inch.
• In another embodiment, a method of detecting arcing in an electroporation system is provided. The electroporation system includes a direct current (DC) energy source, a return electrode connected to the DC energy source, and a catheter connected to the DC energy source, the catheter having at least one catheter electrode. The method includes positioning the return electrode near a target location within a body, and positioning the catheter electrode within the body adjacent the target location within the body. The method further includes monitoring a system impedance with the return electrode positioned near the target location and the catheter electrode positioned within the body, detecting a positive deflection in the system impedance, the positive deflection indicative of arcing, and generating an alert, based on the detection, the alert indicating that arcing has occurred.
• The foregoing and other aspects, features, details, utilities and advantages of the present disclosure will be apparent from reading the following description and claims, and from reviewing the accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
• FIG.1 is a schematic and block diagram view of a system incorporating embodiments for electroporation therapy including a variable system impedance to limit electrical arcing.
• FIG.2 is flowchart of a method of controlling an electroporation system, such as the system shown inFIG.1.
• FIG.3 is flowchart of another method of controlling an electroporation system, such as the system shown inFIG.1.
• FIG.4 is a simplified diagram of an example implementation of the system shown inFIG.1.
• FIG.5 graphically presents the current, voltage, calculated resistance, and pressure wave from the tests of the example implementation shown inFIG.4 in saline with the variable resistance at zero ohms.
• FIG.6 graphically presents the current, voltage, calculated resistance, and pressure wave from the tests of the example implementation shown inFIG.4 in bovine blood with the variable resistance at zero ohms.
• FIG.7 graphically presents the results from a test in an in vivo pig model with the variable resistance at zero ohms.
• FIG.8 graphically presents the calculated resistance for two hundred joule shocks in a saline tank, a blood tank, and in an in vivo pig model with the variable resistance at zero ohms and increased to limit arcs.
• FIG.9 is a graph of the system impedance at the arc threshold for a saline tank, a blood tank, and in vivo pig.
• FIG.10 shows saline tank data indicating arcing for a two hundred joule shock with zero added variable resistance, and indicating no arcing for a two hundred joule shock with a ten ohm added variable resistance.
• FIG.11 is a graph of results from a test performed to determine the current density at which arcing occurs when using a monophasic defibrillator as an electroporation generator.
• FIG.12 is a variable diameter hoop catheter in an expanded configuration.
• FIG.13 is the variable diameter hoop catheter ofFIG.12 in a contracted configuration.
• FIG.14 is a variable diameter, high output hoop catheter in an expanded configuration.
• FIG.15 is a distal loop subassembly of the hoop catheter ofFIG.14
• FIG.16 is a top view of the distal loop subassembly ofFIG.15.
• FIG.17 is a cross-sectional view of a portion of the distal loop subassembly ofFIG.15 taken along the lone A-A.
• FIG.18 is another example embodiment of a variable diameter, high output hoop catheter.
• FIG.19 is another example embodiment of a variable diameter, high output hoop catheter.
• FIG.20 is another example embodiment of a variable diameter, high output hoop catheter.
• FIG.21 is a block diagram of an example diagnostic and treatment system using a single catheter for diagnostic procedures and electroporation.
• FIG.22 shows graphs plotting data from an arcing shock and a non-arcing shock.
• Corresponding reference characters indicate corresponding parts throughout the several views of the drawings. It is understood that that Figures are not necessarily to scale.
DETAILED DESCRIPTION OF THE DISCLOSURE
• The present disclosure relates generally to medical devices that are used in the human body. In particular, in many embodiments, the present disclosure relates to electroporation systems and methods of controlling electroporation systems to limit electroporation arcs from catheters. In some embodiments, the catheters are intracardiac catheters. Electroporation arcs can occur from catheter electrodes to a blood pool when an insulating layer of gas covers the catheter electrode. The insulating layer of gas may be created by the electrical pulse output by an electroporation generator and the volume of gas is proportional to the energy of the pulse. The disclosed embodiments may lead to more consistent and improved patient outcomes with less chance of undesired electrical arcing. In many embodiments, the present disclosure also relates to catheters for electroporation systems. The disclosed embodiments may lead to more consistent and improved patient outcomes with less chance of undesired electrical arcing. It is contemplated, however, that the described features and methods of the present disclosure as described herein may be incorporated into any number of systems as would be appreciated by one of ordinary skill in the art based on the disclosure herein.
• Referring now to the drawings,FIG.1 is a diagrammatic and block diagram view of asystem10 for electroporation therapy. In general, the various embodiments include an electrode assembly disposed at the distal end of a catheter. As used herein, “proximal” refers to a direction toward the end of the catheter near the clinician and “distal” refers to a direction away from the clinician and (generally) inside the body of a patient. The electrode assembly includes one or more individual, electrically-isolated electrode elements. Each electrode element, also referred to herein as a catheter electrode, is individually wired such that it can be selectively paired or combined with any other electrode element to act as a bipolar or a multi-polar electrode.
• System10 may be used for irreversible electroporation to destroy tissue. In particular,system10 may be used for electroporation-induced primary necrosis therapy, which refers to the effects of delivering electrical current in such manner as to directly cause an irreversible loss of plasma membrane (cell wall) integrity leading to its breakdown and cell necrosis. This mechanism of cell death may be viewed as an “outside-in” process, meaning that the disruption of the outside wall of the cell causes detrimental effects to the inside of the cell. Typically, for classical plasma membrane electroporation, electric current is delivered as a pulsed electric field in the form of short-duration direct current (DC) pulses (e.g., 0.1 to 20 ms duration) between closely spaced electrodes capable of delivering an electric field strength of about 0.1 to 1.0 kV/cm. As described in greater detail below,system10 may be used with a high output hoop catheter for high output (e.g., high voltage and/or high current) electroporation procedures.
• In one embodiment, all electrodes of the hoop catheter deliver an electric current simultaneously. That is, the electrodes are electrically connected in parallel during the application. Delivering electric current simultaneously using a plurality of electrodes arranged in a circular fashion facilitates creating a sufficiently deep lesion for electroporation. To facilitate activating electrodes simultaneously, the electrodes may be switchable between being connected to a 3D mapping system and being connected to EP amplifiers.
• When using a circular hoop catheter, the current density in surrounding tissue decays linearly with distance from the electrodes when all electrodes deliver an electric current simultaneously. If, however, less than all the electrodes delivery an electric current simultaneously, the current density near electrodes that do not participate in current delivery will decay exponentially, instead of linearly. The exponential decay in current may result in insufficient lesion depth, gaps in an ablation line, and undesired procedural outcomes. Accordingly, in at least some of the embodiments described herein, current is delivered simultaneously by all electrodes (e.g., even those with low or no tissue contact). Simultaneous delivery of all electrodes in a circular arrangement may also be used for other types of electrical energy. For example, for RF ablation, simultaneous delivery (i.e., with an in-phase electrical RF current) via all electrodes (instead of a phased array or sequential delivery) may result in improved outcomes.
• For a hoop catheter (e.g., as shown inFIGS.12 and13), when the hoop diameter is minimized, multiple electrodes will overlap, such that a subset of the electrodes form a circle by themselves (see, e.g.,FIG.13). Accordingly, in such a configuration, current can be simultaneously delivered using the subset of the electrodes without using the remaining electrodes, as the remaining electrodes overlap the subset of electrodes. In such an embodiment, determining which electrodes to use may be accomplished by determining which electrodes have the best tissue contact. By using less than all electrodes, the total energy delivered by the hoop catheter is reduced.
• Irreversible electroporation through a multielectrode hoop catheter may enable pulmonary vein isolation in as few as one shock per vein, which may produce much shorter procedure times compared to sequentially positioning a radiofrequency (RF) ablation tip around a vein.
• It should be understood that while the energization strategies are described as involving DC pulses, embodiments may use variations and remain within the spirit and scope of the invention. For example, exponentially-decaying pulses, exponentially-increasing pulses, and combinations may be used.
• It should be understood that the mechanism of cell destruction in electroporation is not primarily due to heating effects, but rather to cell membrane disruption through application of a high-voltage electric field. Thus, electroporation may avoid some possible thermal effects that may occur when using radio frequency (RF) energy. This “cold therapy” thus has desirable characteristics.
• With this background, and now referring again toFIG.1,system10 includes acatheter electrode assembly12 including at least one catheter electrode configured to be used as briefly outlined above and as described in greater detail below.Electrode assembly12 is incorporated as part of a medical device such as acatheter14 for electroporation therapy oftissue16 in abody17 of a patient. In the illustrative embodiment,tissue16 comprises heart or cardiac tissue. It should be understood, however, that embodiments may be used to conduct electroporation therapy with respect to a variety of other body tissues.
• FIG.1 further shows a plurality of return electrodes designated18,20, and21, which are diagrammatic of the body connections that may be used by the various sub-systems included in theoverall system10, such as anelectroporation generator26, an electrophysiology (EP) monitor such as anECG monitor28, a localization andnavigation system30 for visualization, mapping and navigation of internal body structures. In the illustrated embodiment, returnelectrodes18,20, and21 are patch electrodes. It should be understood that the illustration of a single patch electrode is diagrammatic only (for clarity) and that such sub-systems to which these patch electrodes are connected may, and typically will, include more than one patch (body surface) electrode. In other embodiments, returnelectrodes18,20, and21 may be any other type of electrode suitable for use as a return electrode including, for example, one or more catheter electrodes. Return electrodes that are catheter electrode may be part ofelectrode assembly12 or part of a separate catheter (not shown).System10 may further include a main computer system32 (including anelectronic control unit50 and data storage—memory52), which may be integrated withsystem30 in certain embodiments.System32 may further include conventional interface components, such as various user input/output mechanisms34aand a display34b,among other components.
• Electroporation generator26 is configured to energize the electrode element(s) in accordance with an electroporation energization strategy, which may be predetermined or may be user-selectable. For electroporation-induced primary necrosis therapy,generator26 may be configured to produce an electric current that is delivered viaelectrode assembly12 as a pulsed electric field in the form of short-duration DC pulses (e.g., a nanosecond to several milliseconds duration, 0.1 to 20 ms duration, or any duration suitable for electroporation) between closely spaced electrodes capable of delivering an electric field strength (i.e., at the tissue site) of about 0.1 to 1.0 kV/cm. The amplitude and pulse duration needed for irreversible electroporation are inversely related. As pulse durations are decreased, the amplitude must be increased to achieve electroporation.
• Electroporation generator26, sometimes also referred to herein as a DC energy source, is amonophasic electroporation generator26 configured to generate a series DC energy pulses that all produce current in the same direction. In other embodiments, electroporation generator is biphasic or polyphasic electroporation generator configured to produce DC energy pulses that do not all produce current in the same direction. In some embodiments,electroporation generator26 is a monophasic defibrillator. The defibrillator is configured to output energy in DC pulses at selectable energy levels, such as fifty joules, one hundred joules, two hundred joules, and the like. Other embodiments may have more or fewer energy settings and the values of the available setting may be the same or different. For successful electroporation, some embodiments utilize the two hundred joule output level.Electroporation generator26 may output a DC pulse having a peak magnitude of about between about negative one kilovolt (kV) and about negative two kV at the two hundred joule output level. In some embodiments,electroporation generator26 outputs a DC pulse having a peak magnitude of about between about negative 1.5 kV and about negative 2.0 kV. Other embodiments may output any other suitable voltage, including a positive voltage. In some embodiments, the monophasic defibrillator is a Lifepak 9 defibrillator available from Physio-Control, Inc., of Redmond, Washington, USA.
• Avariable impedance27 allows the impedance of the system to be varied to limit arcing from the catheter electrode ofcatheter14. Moreover,variable impedance27 may be used to change one or more characteristics, such as amplitude, duration, pulse shape, and the like, of an output ofelectroporation generator26. Although illustrated as a separate component,variable impedance27 may be incorporated incatheter14 orgenerator26.Variable impedance27 includes one or more impedance elements, such as resistors, capacitors, or inductors (not shown) connected in series, parallel, or combinations of series and/or parallel. In the illustrated embodiment,variable impedance27 is connected in series withcatheter14. Alternatively, the impedance elements ofvariable impedance27 may be connected in parallel withcatheter14 or in a combination of series and parallel withcatheter14. Moreover, in other embodiments, the impedance elements ofvariable impedance27 are connected in series and/or parallel withreturn electrode18. Some embodiments include more than onevariable impedance27, each of which may include one or more impedance elements. In such embodiments, eachvariable impedance27 may be connected to a different catheter electrode or group of catheter electrodes to allow the impedance through each catheter electrode or group of catheter electrodes to be separately varied.
• In the illustrative embodiment, the variable impedance is a variable resistance. In some embodimentsvariable impedance27 includes one or more resistors (not shown) removably connected betweengenerator26 andcatheter14. The resistors may be connected in series, parallel, or any combination of series and parallel connections to produce a desired system impedance. Some or all of the resistors may be added, removed, or connected differently to vary the system impedance. In some other embodiments,variable impedance27 is variable resistor, such as a rheostat or a potentiometer. In still other embodiments,variable impedance27 includes resistors coupled together by one or more switches to allow the resistors to be selectively switched in and out of the connection betweengenerator26 andcatheter14. Such avariable impedance27 may also be configured to allow some or all of the resistors to be selectively connected together in series or in parallel with each other. In some embodiments,variable impedance27 is variable in response to an appropriate control signal fromcomputer system32. The resistors may be any suitable type of resistor. In all embodiments, the resistors (or other impedance elements) have relatively high energy ratings sufficient to handle the output ofgenerator26 without being damaged. In some embodiments,variable impedance27 includes Ohmite PulsEater resistors available from Ohmite Mfg. Co. of Warrenville, IL, USA. With continued reference toFIG.1, as noted above,catheter14 may comprise functionality for electroporation and in certain embodiments also an ablation function (e.g., RF ablation). It should be understood, however, that in those embodiments, variations are possible as to the type of ablation energy provided (e.g., cryoablation, ultrasound, etc.).
• In the illustrative embodiment,catheter14 includes a cable connector orinterface40, ahandle42, and a shaft44 having aproximal end46 and a distal48 end.Catheter14 may also include other conventional components not illustrated herein such as a temperature sensor, additional electrodes, and corresponding conductors or leads. Theconnector40 provides mechanical and electrical connection(s) forcable56 extending fromgenerator26. Theconnector40 may comprise conventional components known in the art and as shown is disposed at the proximal end ofcatheter14.
• Handle42 provides a location for the clinician to holdcatheter14 and may further provide means for steering or the guiding shaft44 withinbody17. For example, handle42 may include means to change the length of a guidewire extending throughcatheter14 todistal end48 of shaft44 or means to steer shaft44. Moreover, in some embodiments, handle42 may be configured to vary the shape, size, and/or orientation of a portion of the catheter.Handle42 is also conventional in the art and it will be understood that the construction ofhandle42 may vary. In an alternate exemplary embodiment,catheter14 may be robotically driven or controlled. Accordingly, rather than a clinician manipulating a handle to advance/retract and/or steer or guide catheter14 (and shaft44 thereof in particular), a robot is used to manipulatecatheter14. Shaft44 is an elongated, tubular, flexible member configured for movement withinbody17. Shaft44 is configured to supportelectrode assembly12 as well as contain associated conductors, and possibly additional electronics used for signal processing or conditioning. Shaft44 may also permit transport, delivery and/or removal of fluids (including irrigation fluids and bodily fluids), medicines, and/or surgical tools or instruments. Shaft44 may be made from conventional materials such as polyurethane and defines one or more lumens configured to house and/or transport electrical conductors, fluids or surgical tools. Shaft44 may be introduced into a blood vessel or other structure withinbody17 through a conventional introducer. Shaft44 may then be advanced/retracted and/or steered or guided throughbody17 to a desired location such as the site oftissue16, including through the use of guidewires or other means known in the art.
• In some embodiments,catheter14 is a hoop catheter having catheter electrodes (not shown) distributed about one or more hoops at the distal end of shaft44. The diameter of the hoop(s) may be variable. In some embodiments, the hoop catheter has a maximum diameter of about twenty-seven millimeters (mm). In some embodiments, the hoop diameter is variable between about fifteen mm and about twenty eight mm. Alternatively, the catheter may be a fixed diameter hoop catheter or may be variable between different diameters. In some embodiments,catheter14 has fourteen catheter electrodes. In other embodiments,catheter14 includes ten catheter electrodes, twenty catheter electrodes, or any other suitable number of electrodes for performing electroporation. In some embodiments, the catheter electrodes are ring electrodes, such as platinum ring electrodes. Alternatively, the catheter electrodes may be any other suitable type of electrodes, such as single sided electrode or electrodes printed on a flex material. In various embodiments, the catheter electrodes have lengths of 1.0 mm, 2.0 mm, 2.5 mm, and/or any other suitable length for electroporation.
• FIGS.12 and13 show the distal end of an example variablediameter hoop catheter1200 usable ascatheter14.Hoop catheter1200 includes fourteencatheter electrodes1202.Catheter electrodes1202 are ring electrodes. InFIG.12,hoop catheter1200 is shown in its fully expanded configuration with adiameter1204 of about twenty-eight millimeters (mm). InFIG.13,hoop catheter1200 is shown in its fully contracted configuration with a diameter of about fifteen mm. In other embodiments,catheter1200 may be variable between different diameters and/or may include any other suitable number of electrodes for performing electroporation. Additional catheters that may be suitable for use ascatheter14 are discussed below with respect toFIGS.14-20.
• The localization andnavigation system30 may be provided for visualization, mapping and navigation of internal body structures.System30 may comprise conventional apparatus known generally in the art (e.g., an EnSite NAVX™ Navigation and Visualization System, commercially available from Abbott Laboratories. and as generally shown with reference to commonly assigned U.S. Pat. No. 7,263,397 titled “Method and Apparatus for Catheter Navigation and Location and Mapping in the Heart,” the entire disclosure of which is incorporated herein by reference). It should be understood, however, that this system is exemplary only and not limiting in nature. Other technologies for locating/navigating a catheter in space (and for visualization) are known, including for example, the CARTO navigation and location system of Biosense Webster, Inc., the AURORA® system of Northern Digital Inc., commonly available fluoroscopy systems, or a magnetic location system such as the gMPS system from Mediguide Ltd. In this regard, some of the localization, navigation and/or visualization system would involve a sensor be provided for producing signals indicative of catheter location information, and may include, for example one or more electrodes in the case of an impedance-based localization system, or alternatively, one or more coils (i.e., wire windings) configured to detect one or more characteristics of a magnetic field, for example in the case of a magnetic-field based localization system.
• Several factors may influence the formation of electrical arcs from catheter electrodes in an electroporation system, such assystem10. In general, the various factors combine to define in a maximum energy that can be delivered by an electroporation generator to a catheter in a single pulse without causing arcing from the catheter. The total electrode surface area is a strong determinant of the maximum allowable energy which can be safely delivered in a single pulse without arcing from the catheter electrode(s). The total electrode surface area is the sum of all individual electrode surface areas. The catheter shape is another determinant of the maximum allowable pulse energy. For example when a catheter hoop is deployed in the minimum possible diameter, the threshold for arcing is lower than when the hoop is deployed in the maximum diameter. The time between individual energy applications is another determinant of the maximum allowable pulse energy. For example when one pulse is “followed quickly” by a second pulse, the arc threshold on the second pulse is lower than the threshold for the first pulse, because some of the gas bubbles which were created on the electrode by the first pulse are still present when the second pulse is applied. The formation of the insulating gas layer on the electrode is cumulative, and if/when the layer forms a complete insulator an arc can occur. This effect has been observed in pulses applied about 30 seconds apart (i.e. it is not only a short-duration phenomenon).
• FIG.2 is a flowchart of amethod200 of controlling an electroporation system, such assystem10 shown inFIG.1. Althoughmethod200 will be described with reference tosystem10, it should be understood thatmethod200 may be performed using any suitable electroporation system including a DC energy source, a return electrode connected to the DC energy source, and a catheter including a catheter electrode connected to the DC energy source. The method includes positioning, at202, returnelectrode18 near a target location withinbody17. As used herein, a return electrode is near a target location when positioned on or in a body sufficiently close to the target location to allow electroporation to be performed. For example, areturn electrode18 that is part of a catheter (whether thecatheter14 or a separate catheter) may be positioned in the body adjacent the target location. In embodiments in which returnelectrode18 is a patch electrode, the return electrode is positioned on an external surface ofbody17 near the target location. In other embodiments, the return electrode is positioned withinbody17 near the target location. At204, the method includes positioning the catheter's catheter electrode withinbody17 adjacent the target location, e.g.,adjacent tissue16.
• At206, the system impedance is determined withreturn electrode18 positioned near the target location and the catheter electrode positioned withinbody17. The system impedance may be determined using any suitable method for determining the system impedance. In some embodiments, the catheter electrodes are shorted together and a known (non-electroporation) signal is output bygenerator26 tocatheter14. The response ofsystem10 is measured and the system impedance is calculated. In some embodiments, the system impedance is measured at 485 kilohertz (kHz) using an RF ablation generator. The RF ablation generator may be part ofgenerator26, or may be a separate RF ablation generator. An example suitable RF ablation generator is an IBI-1500T11 ablation generator available from Abbott Laboratories. In some embodiments, a small (relative to the electroporation voltage) DC voltage is applied to the catheter and the output voltage and current are measured. The resistive impedance is determined according to Ohm's law by dividing the voltage by the current.
• The system impedance is adjusted, at208, to a target impedance to limit arcing from the catheter electrode. The system impedance is adjusted usingvariable impedance27. In the example embodiment, the variable impedance is a resistance and resistance may be added or removed as needed to adjust the system impedance to the target impedance. In some embodiments, the target impedance is a range of impedances, such as a resistance between about seventy and eighty ohms. In some embodiments, adjusting the system impedance includes adjusting the system capacitance, inductance, resistance, or a combination thereof. In the example embodiment, the target impedance is a determined resistance that will limit the likelihood of electrical arcing between the catheter electrodes and returnelectrode18 when system is used for electroporation. The target impedance is selected primarily based on the particular settings and characteristics ofgenerator26, characteristics ofcatheter14, and a desired maximum (or threshold) current density on the catheter electrodes. The value of the target impedance is selected to keep the current density on the catheter electrodes below a threshold current density to prevent arcing. In various embodiments, the target resistance is selected to keep the current density on the catheter electrodes below about one hundred fifty milliamps per square millimeter (mA/mm²), below about one hundred thirty mA/mm², below about one hundred twenty mA/mm², below about one hundred mA/mm², between about one hundred mA/mm²and one hundred twenty mA/mm², or below any threshold current density or in any current density range that is suitable to limit the likelihood of arcing. Multiplying the threshold current density by the surface area of the catheter electrodes produces a desired peak current. If the peak voltage output of the generator at a particular energy setting and in the particular environment (e.g., in body17) is known, the target impedance to produce that desired peak current can be calculated using Ohm's law. Accordingly, the target system impedance may be determined by:
• $\begin{array}{cc}{R}_{target}=\frac{V_{\mathrm{peak}}}{\mathrm{Current}\mathrm{Density}\mathrm{Threshold}\times \mathrm{Catheter}\mathrm{Electrode}\mathrm{SA}}& \left(1\right)\end{array}$
• Where R_targetis the target system impedance, V_peakis the peak output voltage ofgenerator26 under current conditions and settings, Current Density Threshold is the target current density to limit arcing, and Catheter Electrode SA is the surface area of the catheter electrodes.
• FIG.3 is flowchart of amethod300 of controlling an electroporation system, such assystem10 shown inFIG.1. Althoughmethod300 will be described with reference tosystem10, it should be understood thatmethod300 may be performed using any suitable electroporation system including a DC energy source, and a catheter connected to the DC energy source and having an electrode surface area. At302, the system impedance is determined with the patch electrode on a body and the catheter positioned within the body adjacent a target area. At304, the system impedance is adjusted, e.g., with the variable impedance, to a target impedance. The target impedance is selected to cause the DC energy source to produce a current density on the electrode surface area of less than one hundred fifty mA/mm². In other embodiments, the target impedance is selected to cause the DC energy source to produce a current density on the electrode surface area of less than one hundred twenty mA/mm².
EXAMPLE 1
• An example implementation ofsystem10 was constructed and tested.FIG.4 is a simplified diagram of theexample system400. In theexample system400,generator26 is the Lifepak 9 defibrillator described above. Ajunction box402 is used to connect generator26 (and variable impedance27) tocatheter14 and returnelectrode18.Catheter14 is a fifteen mm diameter hoop catheter with ten electrodes of two mm length. The surface area of the electrodes is about one hundred forty six square millimeters.Return electrode18 is a four cm square stainless steel mesh with a much larger surface area than that of the catheter electrodes. The voltage and current supplied tocatheter14 are detected atjunction box402 and monitored by acomputing device404.
• Some tests of this implementation were performed withcatheter14 and thereturn18 in atank406 having a diameter of eleven centimeters (cm). Other tests were performed with thecatheter14 and return18 in an in vivo pig model (not shown) rather than intank406. Apressure transducer408 is attached to wall oftank406 with the sensor approximately six cm from the catheter hoop.Tank406 was filled with 6.7 millisiemens per cm (mS/cm) saline for one set of tests and heparinized bovine blood with conductivity approximately 6.2 mS/cm for a second set of tests. Shocks of fifty, one hundred, and two hundred joules were applied fromgenerator26 tocatheter14.
• FIGS.5 and6 are graphs of the current, voltage, calculated resistance, and pressure wave from the tests in saline and bovine blood with the variable resistance at zero ohms. In saline (FIG.5), the fifty and one hundred joule shocks produced smooth waveforms, but the two hundred joule shocks produced a slight deflection in the recovery slope of the current trace and a more obvious deflection at a similar point in the voltage trace. These deflections manifest as the large deflection in the calculated resistance trace. The pressure wave shows large oscillations that correspond to the resulting explosion from an electric arcing event. In blood (FIG.6), the fifty joule shocks produced smooth waveforms and showed no signs of arcing. The one hundred and two hundred joule shocks, however, have apparent deflections in the current, voltage, and calculated resistance traces, indicating arcing occurred.
• FIG.7 presents the results from a repeat of the test in an in vivo pig model (rather than in tank406) withvariable impedance27 at zero ohms. The results also show no arcing with fifty and one hundred joule shocks, and arcing during two hundred joule shocks.
• The saline, bovine blood, and in vivo pig tests were repeated with the system impedance increased usingvariable impedance27. Shocks were delivered at two hundred joule and the impedance increased in ten ohm increments until no arc was detected. The delivered current and voltage are measured between the catheter and return.FIG.8 presents calculated resistance for representative two hundred joule shocks in the saline tank, the blood tank, and in vivo (top to bottom). The left column clearly demonstrates that shocks withvariable impedance27 at zero arced in each model. The right column is the corresponding threshold for a shock with no arcing for each trial. The resistance added byvariable impedance27 in each trial is labelled. The absence of arcing is evidenced by the smooth calculated medium resistance trace.
• FIG.9 summarizes the arc threshold findings as system resistance (y axis=medium resistance+added resistance) for each of the three models (binned on the x axis). Shocks that arced without added resistance are represented by Xs and threshold resistances (system resistance that prevented arcs for each trial) are represented by +s. The blood data set was in better agreement with the in vivo data than was the saline data, which underestimated the system resistance required to prevent shocks. Reframed to mean +/− standard deviation of joules delivered to the test medium, the saline threshold was ninety nine joules +/− nineteen joules (n=10), the blood threshold was one hundred and six joules (n=1), and in vivo threshold was one hundred fifty five joules +/− thirty five joules (n=8).
• To limit arcing in the implementation of Example 1, the target impedance to which the system impedance should be adjusted may be set at about one hundred fifty ohms.
EXAMPLE 2
• A second example implementation ofsystem10 was constructed and tested. The second implementation is the same as theexample system400, but uses adifferent catheter14. In the second implementation,catheter14 is a fourteen electrode hoop catheter with 2.5 mm ring electrodes and a 15-28 mm adjustable hoop size. The electrodes have a surface area of about two hundred fifty six square millimeters.
• FIG.10 shows saline tank data with evidence of arcing (the bump in the impedance trace) when a two hundred joules shock is applied bygenerator26 withvariable impedance27 at zero. When the system impedance is increased by ten ohms usingvariable impedance27, the traces (right side) do not show any sign of arcing when a two hundred joule shock is applied. The tests were repeated multiple times to collect multiple current, voltage, and calculated resistance traces from two hundred joule shocks in the saline tank. Based on test data, a target impedance for the system impedance for the system in Example 2 is about seventy ohms. In vivo testing was performed using the Example 2 implementation ofsystem10 set at two hundred joules.Variable impedance27 was used to adjust the system impedance to about 70 for the trials and no arcing was observed.
• FIG.11 is a graph of results from a test performed to determine the current density at which arcing occurs when using a monophasic defibrillator asgenerator26, such as in the systems of Examples 1 and 2. A length of a stainless steel rod was positioned in a saline tank and connected to the defibrillator as the shock anode. A hoop catheter with ten 2.0 mm length electrodes was connected to the defibrillator as the cathode and positioned in the saline tank. Multiple trials of two hundred joule shocks by the defibrillator were conducted. The amount of the stainless steel rod submerged in the tank was varied during the trials to vary the electrode surface area. The collected data is plotted inFIG.11 and shows a transition from arcing shocks to non-arcing shocks occurred when the total current density dropped below about two hundred mA/mm².
• Various additional experiments were performed to determine threshold current densities below which arcing was unlikely to occur. A first set of experiments were performed using a ten electrode catheter with 2.0 mm ring electrodes and a twenty electrode catheter with 1.0 mm ring electrodes in blood, in vivo pig, and in saline. Table 1, below, presents the mean of the largest current density (in mA/mm²) achieved without arcing.

• TABLE 1
  Current Density (No Arc)

  	Ten Electrodes	Twenty Electrodes
  	(2.0 mm length)	(1.0 mm length)

  	Mean	Std Dev	n	Mean	Std Dev	n

  blood	141	NA	1	129	NA	1
  in vivo pig	151	20	7	195	20	6
  saline	209	13	10	208	40	8

• Table 2, below, was compiled from data similarly comparing a fourteen electrode catheter with 2.5 mm ring electrodes to a ten electrode catheter with 2.0 mm long ring electrodes. It shows the mean of largest current density (in mA/mm²) observed without arc. The saline data was collected with the catheter hoop in saline and contact with bovine heart tissue.

• TABLE 2
  Current Density (No Arc)

  	Ten Electrodes	Fourteen Electrodes
  	(2.0 mm length)	(2.5 mm length)

  	Mean	Std Dev	n	Mean	Std Dev	n

  blood	133	6	15	138	19	17
  Saline + tissue	179	24	2	156	6	2

• Peak current (in amperes) for the data set in the Table 2 is shown in Table 3 below. The electrode surface area of the fourteen electrode catheter is about two hundred fifty six square millimeters. The ten electrode catheter had a surface area of about one hundred forty six square millimeters.

• TABLE 3
  Peak Current

  	Ten Electrodes	Fourteen Electrodes
  	(2.0 mm length)	(2.5 mm length)

  	Mean	Std Dev	n	Mean	Std Dev	n

  blood	19	1	15	35	5	17
  Saline +tissue	26	4	2	40	0	2

• Based on the data presented above, a current density threshold may be established for use with systems and methods described herein. The data suggests electroporation pulse arcs require a current density in excess of one hundred fifty to two hundred mA/mm²in animals. Thus, in some embodiments, a current density threshold is set at one hundred fifty mA/mm². In some embodiments, the current density threshold is set between about one hundred and about one hundred twenty mA/mm²to maintain therapy while preventing arcs. In some embodiments, the current density threshold is set at about one hundred twenty mA/mm²to provide about a twenty percent margin of safety from the one hundred fifty mA/mm²current density above which arcing seems to occur. In other embodiments, the current density threshold is set at any other suitable value high enough to allow irreversible electroporation to occur and low enough to prevent arcing.
• As discussed above, the target system impedance can then be determined for any particular implementation ofsystem10 based on the selected current density threshold, the surface area of the catheter electrodes, and the peak output voltage ofgenerator26.
• In some embodiments, a variable diameter, high output hoop catheter may be used for electroporation procedures. Such a catheter may be used with the systems and methods described above, such as, for example, withsystem10 and/or with other electroporation generators and systems. Several example embodiments of variable diameter, high output hoop catheters are described below with reference toFIGS.14-20.
• FIGS.14-17 illustrate an example variable diameter, highoutput hoop catheter1400 usable, in some embodiments, ascatheter14. As described in greater detail below,hoop catheter1400 is configured to safely handle an electrical input in the range of ten amperes and/or one thousand volts.
• Referring first toFIG.14,hoop catheter1400 includes ahandle1402, ashaft1404, adistal loop subassembly1406, and aconnector1408.Hoop catheter1400 has aproximal end1410 and adistal end1412. As used herein, “proximal” refers to a direction toward the portion of thecatheter12 near the clinician, and “distal” refers to a direction away from the clinician and (generally) inside the body of a patient.
• Connector1408 provides mechanical, fluid, and electrical connection(s) for cables, such as, for example, electrical cables (not shown) and/or other components of system10 (e.g., a visualization, navigation, and/or mapping system, an ablation generator, irrigation source, etc.).Connector1408 is disposed at aproximal end1410 ofhoop catheter1400, and handle1408 thereof, in particular. In the example embodiment,connector1408 is a waterproof connector. In other embodiments, connector is water resistant connector. In some embodiments,connector1408 is not itself waterproof, but includes a waterproof element to protect the connector from liquids and moisture, such as a waterproof or water resistant sheath.Connector1408 further includes an insulator or insulating material (not shown), such thatconnector1408 is suitable for conducting voltages in the range of one thousand volts and electrical current in the range of ten amps. In the example embodiment,connector1408 is used to couplecatheter1400 to an electroporation generator, such aselectroporation generator26.
• Handle1402, which is disposed atproximal end1410 ofshaft1404, provides a location for the clinician to holdcatheter1400 and may further provide means for steering or guidingshaft1404 within the body of the patient.Handle1402 may include means to change the length of a steering wire extending throughcatheter1400 todistal end30 ofshaft1404 to steershaft1404. In other embodiments,catheter1400 may be robotically driven or controlled. Accordingly, rather than a clinician manipulating a handle to steer or guidecatheter1400 andshaft1404 thereof, in such an embodiments, a robot is used to manipulatecatheter1400. In various embodiments, handle1402 is a FLEXABILITY Uni-D handle with modifications configured to increase pull wire travel.Handle1402 may further include an 8F shaft lug and flush port plug.Handle1402 is at least partially hollow to define an interior channel (not shown) therethrough.
• Shaft1404 is an elongate, tubular, flexible member configured for movement withinbody18. A pull wire (not shown inFIG.14) for adjusting the diameter of the hoop and electrical conductors (not shown inFIG.14) connected between electrodes atdistal end1412 andconnector1408 are disposed within an interior channel (not shown) defined byshaft1404.Shaft1404 may also permit transport, delivery, and/or removal of fluids (including irrigation fluids, cryogenic ablation fluids, and bodily fluids), medicines, and/or surgical tools or instruments.Shaft1404 may be made from conventional materials such as polyurethane, and defines one or more lumens configured to house and/or transport electrical conductors, fluids, or surgical tools.Shaft1404 may be introduced into a blood vessel or other structure within thebody18 through a conventional introducer.Shaft1404 may then be steered or guided throughbody18 to a desired location, such asheart20, using means well known in the art.Shaft1404 houses electrode wires (not shown inFIG.14) for carrying electrical current toelectrodes1414. Electrode wires extend betweenhandle1402 andelectrodes1414 within an interior portion ofshaft1404. To this end,shaft1404 may include an insulator or insulating material. For example,shaft1404 may be packed with an insulation material and/or a cylindrical layer of insulation material may be circumferentially disposed within an interior portion ofshaft1404. The thickness and material characteristics of such insulation are selected to configureshaft1404 for safe use with voltage and current in the range of one thousand volts and/or ten amperes.
• Catheter electrodes1414 mounted ondistal loop subassembly1406 may be used for a variety of diagnostic and therapeutic purposes including, for example and without limitation, electroporation, electrophysiological studies, pacing, cardiac mapping, and ablation. In a preferred embodiment,catheter electrodes1414 are configured for use as electroporation electrodes. In some embodiments,catheter electrodes1414 may be configured for additional uses. For example, one or more ofcatheter electrodes1414 may perform a location or position sensing function. More particularly, one or more ofcatheter electrodes1414 may be configured to be a positioning sensor(s) that provides information relating to the location (position and orientation) ofcatheter1400, anddistal end1412 ofshaft1404 thereof, in particular, at certain points in time. Accordingly, ascatheter1400 is moved along a surface of a structure of interest ofheart20 and/or about the interior of the structure, the sensor(s) can be used to collect location data points that correspond to the surface of, and/or other locations within, the structure of interest. These location data points can then be used by, for example,model construction system14, in the construction of a three-dimensional model of the structure of interest. In other embodiments, separate catheter electrodes are used for electroporation and positioning.
• FIGS.15 and16 are views ofdistal loop subassembly1406. Specifically,FIG.15 is a side view ofdistal loop subassembly1406 with avariable diameter loop1500 atdistal end1412.FIG.15 is a top view ofvariable diameter loop1500 ofdistal loop subassembly1406.
• Variable diameter loop1500 is variable between an expanded (also referred to as “open”) diameter1600 (shown inFIG.16) and a retracted (also referred to as “closed”) diameter1600 (not shown). In the example embodiment, the expandeddiameter1600 is twenty seven mm and a retracteddiameter1600 of fifteen mm. In other embodiments,diameter1600 may be variable between any suitable open andclosed diameter1600.
• Variable diameter loop1500 includes fourteencatheter electrodes1414 evenly spaced around the circumference ofvariable diameter loop1500.Catheter electrodes1414 are platinum ring electrodes configured to conduct and/or discharge electrical current in the range of one thousand volts and/or ten amperes. In other embodiments,variable diameter loop1500 may include any suitable number ofcatheter electrodes1414 made of any suitable material.Catheter electrodes1414 may comprise any catheter electrode suitable to conduct high voltage and/or high current (e.g., in the range of one thousand volts and/or ten amperes). Eachcatheter electrode1414 is separated from each other catheter electrode by aninsulated gap1502. In the example embodiment, eachcatheter electrode1414 has a same length1604 (shown inFIG.16) and eachinsulated gap1502 has asame length1606 as eachother gap1502.Length1604 andlength1606 are both about 2.5 mm in the example embodiment. In other embodiments,length1604 andlength1606 may be different from each other. Moreover, in some embodiments,catheter electrodes1414 may not all have thesame length1604 and/orinsulated gaps1502 may not all have thesame length1606. In some embodiments,catheter electrodes1414 are not spaced evenly around the circumference ofvariable diameter loop1500.
• Diameter1600 andcatheter electrode1414 spacing may be developed to provide a targeted range of energy density to tissue, as well as to provide sufficient electroporation coverage for different human anatomic geometries. In general, a sufficient number ofelectrodes1414 withappropriate lengths1604 are desired to provide substantially even and continuous coverage around the circumference ofvariable diameter loop1500, while still allowing enough flexibility to allowvariable diameter loop1500 to expand and contract to varydiameter1600 to the desired extremes. As mentioned above,length1604 of catheter electrodes141 may be varied. Increasinglength1604 ofcatheter electrodes1414 may increase coverage ofelectrodes1414 around the circumference ofloop1500 while also decreasing current density (by increasing the surface area) onelectrodes1414, which may help prevent arcing during electroporation operations. Increasinglength1604 too much, however, may preventvariable diameter loop1500 from forming a smooth circular shape and may limit theclosed diameter1600 ofvariable diameter loop1500. Additionally, too great alength1604 may increase the surface area ofcatheter electrodes1414 to a point that the current density applied tocatheter electrodes1414 by a power source is below the minimum current density needed for successful therapy. Conversely, decreasinglength1604 decreases the surface area, thereby increasing the current density (assuming no other system changes) oncatheter electrodes1414. As discussed above, greater current densities may lead to increased risk of arcing during electroporation, and may result in larger additional system resistances needing to be added to prevent electroporation. Moreover, in order to get a desired, even coverage about the circumference ofvariable diameter loop1500,more catheter electrodes1414 may be needed iflength1604 is decreased. Increasing the number ofcatheter electrodes1414 onvariable diameter loop1500 may preventvariable diameter loop1500 from being able to be contracted to a desiredminimum diameter1600.
• FIG.17 is across-section1700 ofvariable diameter loop1500 taken along the line A-A shown inFIG.16.Cross-section1700 includes ashape memory wire1702, apull wire1704,electrode wires1706, andtubing1708,1710,1712,1714, and1716.
• Shape memory wire1702 is pre-shaped to a loop configuration at aparticular diameter1600 to shapevariable diameter loop1500 into its circular shape of the expandeddiameter1600. After a change in shape ofvariable diameter loop1500, such as a change indiameter1600 or a straightening for insertion into a patient's body,shape memory wire1702 will substantially returnvariable diameter loop1500 to its initial shape anddiameter1600. In the example embodiment,shape memory wire1702 is a nitinol wire. In other embodiments,shape memory wire1702 may be any other suitable shape memory alloy.
• Pull wire1704 is configured to permit an operator to varydiameter1600 ofvariable diameter loop1500 by moving a proximal end (not shown) ofpull wire1704 toward or away fromproximal end1410.Pull wire1704 is surrounded bytubing1708.Tubing1708 is a polyethylene terephthalate (PET) shrink tubing. In other embodiments,tubing1708 may be any other suitable tubing for insulating and protectingpull wire1708.
• Electrode wires1706 carry electrical current from a power source coupled toconnector1408 tocatheter electrodes1414.Electrode wires1706 are any suitable size and material sufficient to carry the voltage and current required for electroporation, as described herein. Eachelectrode wire1706 is connected to adifferent catheter electrode1414.Electrode wires1706 are isolated from one another and are not electrically connected to each other withincatheter1400. In other embodiments,electrode wires1706 may be connected together, for example in parallel, withinvariable diameter catheter1400.
• Shape memory wire1702 and pullwire1704 are separated from and electrically insulated fromelectrode wires1706 bytubing1710,1712,1714, and1716. In the example embodiment,tubing1710 is a polytetrafluoroethylene (PTFE) tubing,tubing1712 is a polyimide tubing, andtubing1714 and1716 are PET shrink tubing.
• Hoop catheter1400 may further incorporate additional insulation materials to accommodate high voltages and currents. For instance,hoop catheter1400 may include an insulator, such as wire sheathing (not shown), that surrounds eachelectrode wire1706. Such a wire sheathing may, for example, have a thickness of 0.0015 inches. Similarly,hoop catheter1400 may include insulation material (not shown) that is packed or bundled aroundelectrode wires1706 to insulateelectrode wires1706 from one another and/or from other components ofhoop catheter1400.
• FIGS.18-20 illustrate several alternative catheters usable, in some embodiments, ascatheter14.
• For example, with attention toFIG.18, a perspective view of a highoutput hoop catheter1800 is shown. In the example embodiment,hoop catheter1800 is a fixed diameter catheter (rather than a variable diameter catheter) having an fixed diameter of 20 mm.Catheter1800 includes tencatheter electrodes1802, each having a length1804 of approximately 2 mm.Hoop catheter1800 may be used with a Bi-D (Safire) handle and/or a Matrix proximal shaft.Hoop catheter1800 has a circumferential loop/primary shaft orientation and a full circumferential shape in an open loop configuration.
• Similarly,FIG.19 is a perspective view of a highoutput hoop catheter1900. In the example embodiment,hoop catheter1900 is a variable diameter catheter configured for expansion and contraction.Catheter1900 has an open loop diameter of 35 mm and a closed loop diameter of 15 mm.Catheter1900 includes tencatheter electrodes1902, each having a length of approximately 2 mm.Hoop catheter1900 may be used with a Uni-D handle and a Matrix proximal shaft.Hoop catheter1900 has a circumferential loop/primary shaft orientation and a C-shape in an open loop configuration.
• FIG.20 is a perspective view of a highoutput hoop catheter2000. In the example embodiment,hoop catheter2000 is a variable diameter catheter configured for expansion and contraction.Catheter2000 has an open loop diameter of 27 mm and a closed loop diameter of 15 mm.Catheter2000 includes fourteencatheter electrodes2002, each having a length of approximately 2 mm.Hoop catheter2000 may be used with a Uni-D (modified) handle and an MTC proximal shaft.Hoop catheter2000 has a center loop/primary shaft orientation and a full circumferential shape in an open loop configuration.
• FIG.21 is a simplified block diagram of anotherexample system2100 for electroporationtherapy using catheter1400. Except as otherwise described herein,system2100 may be identical to or substantially similar tosystem10. Unlikesystem10,system2100 includes a selection interface2102 coupled betweencatheter1400, anelectroporation subsystem2104, and a diagnostic ormapping subsystem2106. Thus,system2100 may include any element or component shown with respect tosystem10. However, for purposes of illustration,system2100 is shown in simplified format. Electroporation subsystem2204 may includeelectroporation generator26, and diagnostic/mapping subsystem2106 may be identical to or substantially similar to localization andnavigation system30. In other embodiments,electroporation generator2104 and diagnostic/mapping subsystem2106 may be any two suitable subsystems for use withcatheter1400.
• Selection interface2102 is operable to select which ofelectroporation generator2104 and diagnostic/mapping subsystem2106 is coupled tocatheter1400, and more specifically, the catheter electrodes1414 (not shown inFIG.21). Thus, for example, an operator ofsystem2100 may insert the appropriate portion ofcatheter1400 into a patient while coupled by selection interface2102 to diagnostic/mapping subsystem2106 to navigate catheter to a desired electroporation site and/or to map a portion of the patient. Once the catheter is suitably positioned, thesame catheter1400 may be coupled toelectroporation subsystem2104 by the operator making such a selection using selection interface2102, and electroporation may proceed as described herein. Switching betweenelectroporation subsystem2104 and diagnostic/mapping subsystem2106 may be accomplished by any suitable mechanical, electrical or electro-mechanical switches (not shown) within selection interface2102.
• Selection interface2102 also facilitates selection of whichcatheter electrodes1414 are coupled to the selectedelectroporation subsystem2104 or diagnostic/mapping subsystem2106, and in what electrical configuration. Switching betweenelectrodes1414 and electrical configuration of electrodes may be accomplished by any suitable mechanical, electrical or electro-mechanical switches (not shown) within selection interface2102. For example, when connected to diagnostic/mapping subsystem2106, each electrode1414 (or a group of less than all electrodes) may be separately connected to diagnostic/mapping subsystem2106 to allow each electrode to be utilized by diagnostic/mapping subsystem2106 independent of allother electrodes1414. During electroporation, however, it may be desirable to connect allelectrodes1414 in parallel to receive the same electroporation energy fromelectroporation subsystem2104. Thus, when selection interface2102 connectscatheter1400 toelectroporation subsystem1400, it connects all ofcatheters1414 toelectroporation subsystem2104 in parallel. In other embodiments, other electrical configurations and combinations of electrical configurations may be used. For example, selection interface may be used to connect a group of less than allelectrodes1414 in parallel, but not connect the group in parallel to anyother electrodes1414 or other groups ofelectrodes1414.
• In some embodiments, selection interface2102 includes or is included in a variable impedance, such asvariable impedance27. Thus, selection interface2102 may also be used to connectvariable impedance27 toelectrodes1414 when connected toelectroporation subsystem2104 and disconnectelectrodes1414 fromvariable impedance27 whencatheter1400 is connected to diagnostic/mapping subsystem2106. Moreover, selection interface2102 may be used to independently couple a same or different impedance to eachcatheter electrode1414 or subgroups ofelectrodes1414. Thus, in some embodiments, particularly ifelectrodes1414 are not connected to each other in parallel, the impedance may be controlled at anindividual electrode1414 level to control the current density on each electrode (or subgroup of electrodes1414) In some embodiments, selection interface2102 may connect and disconnect one ormore catheter electrodes1414 fromelectroporation subsystem2104 during operation to achieve desirable electroporation patterns and/or electroporation results during operation.
• As described herein, electroporation through catheter, such as a hoop catheter used in cardiac ablation procedures, can creates arcs. These arcs create shockwaves that may cause barotrauma (i.e., pressure wave damage to tissue). Accordingly, the systems and methods described above are directed to limiting or preventing such arcing.
• In the event that arcing does occur, however, it would be desirable to alert a physician or other operator. As described herein, such arcs may coincide with a positive deflection in the calculated impedance between catheter electrodes and the shock return. Various methodologies and processes may be used to identify an arc based on the impedance trace signature. If an electrophysiologist/physician recognizes that electroporation arced in a patient, the physician can act to mitigate harm.
• In one embodiment, an ablation system (such as system10 (shown inFIG.1)) is configured to alert a physician or other operator that an arc occurred during electroporation therapy, and that a pressure wave was inflicted on the treatment region. This knowledge may guide subsequent medical decisions to reduce harm to the patient. In one embodiment, the arc is identified based on impedance signature deflections.
• FIG.22 shows data from an arcing shock and a non-arcing shock. The left column ofFIG.22 shows data from a non-arcing shock, and the right column ofFIG.22 shows data from an arcing shock through the same catheter. In one example, the calculated impedance is about 45 ohms in both cases. All arcs generally exhibit a large positive deflection as shown at 4 ms in the 200J shock impedance trace. The bottom trace (row4) shows the derivative of the impedance to demonstrate one embodiment of an identification algorithm.
• As shown inFIG.22, impedance traces (row3) of non-arcing shocks are more flat, as shown in the first column where 100 Joules of energy is applied, while those of arcing shocks exhibit a large deflection, as shown in the second column where 200 Joules of energy is applied.
• In the exemplary embodiments, identification of arcs in accordance with the disclosure include, but are not limited to, thresholding the impedance value (with electrode impedance prior to shock subtracted out). Another example involves thresholding the derivative (seerow4 ofFIG.22). Another example involves combining the derivative threshold and the impedance threshold. Still another example involves detecting the larger impedance integral compared to that expected without arc (with electrode impedance prior to shock subtracted out). Yet another example involves thresholding the second derivative of impedance. Additionally, methodologies that identify R-waves on the surface ECG (such as Pan-Tompkins) could be modified to detect arc in some embodiments.
• Although certain embodiments of this disclosure 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 disclosure. All directional references (e.g., 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 disclosure, and do not create limitations, particularly as to the position, orientation, or use of the disclosure. 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 disclosure as defined in the appended claims.
• When introducing elements of the present disclosure or the preferred embodiment(s) thereof, the articles “a”, “an”, “the”, and “said” are intended to mean that there are one or more of the elements. The terms “comprising”, “including”, and “having” are intended to be inclusive and mean that there may be additional elements other than the listed elements.
• As various changes could be made in the above constructions without departing from the scope of the disclosure, it is intended that all matter contained in the above description or shown in the accompanying drawings shall be interpreted as illustrative and not in a limiting sense.

Claims (20)

What is claimed is:

1. A catheter comprising:

a handle including an insulated electrical connector at a proximal end of the handle configured for connection to an electroporation generator, the handle defining an interior channel;

a shaft coupled to and extending from a distal end of the handle, the shaft defining an interior channel;

a distal loop subassembly coupled to a distal end of the shaft, the distal loop subassembly comprising a loop having a plurality of catheter electrodes disposed thereon; and

a plurality of electrode wires, each electrode wire of the plurality of electrode wires coupled to a different catheter electrode of the plurality of catheter electrodes and extending from the distal loop assembly to the connector, through the interior channels of the shaft and the handle, wherein each electrode wire of the plurality of electrode wires is surrounded by an insulator with a thickness of at least about 1.5 thousandths of an inch.

2. The catheter ofclaim 1, wherein the insulated electrical connector comprises a waterproof electrical connector.

3. The catheter ofclaim 1, wherein each electrode wire of the plurality of electrode wires is sized to carry an electrical current of at least ten amps at a voltage of at least one thousand volts.

4. The catheter ofclaim 1, wherein the loop of the distal loop subassembly comprises a variable diameter loop.

5. The catheter ofclaim 4, wherein the variable diameter loop has an open loop diameter of twenty-seven millimeters and a closed loop diameter of approximately fifteen millimeters.

6. The catheter ofclaim 5, wherein each catheter electrode of the plurality of catheter electrodes is a ring electrode having a length of 2.5 millimeters.

7. The catheter ofclaim 5, wherein each catheter electrode of the plurality of catheter electrodes is a ring electrode having a length of 2.0 millimeters.

8. A catheter comprising:

a handle including an insulated electrical connector at a proximal end of the handle configured for connection to an electroporation generator, the handle defining an interior channel;

a shaft coupled to and extending from a distal end of the handle, the shaft defining an interior channel;

a subassembly coupled to a distal end of the shaft, the subassembly having a plurality of catheter electrodes disposed thereon; and

a plurality of electrode wires, each electrode wire of the plurality of electrode wires coupled to a different catheter electrode of the plurality of catheter electrodes and extending from the subassembly to the connector, through the interior channels of the shaft and the handle, wherein each electrode wire of the plurality of electrode wires is surrounded by an insulator with a thickness of at least about 1.5 thousandths of an inch.

9. The catheter ofclaim 8, wherein the insulated electrical connector comprises a waterproof electrical connector.

10. The catheter ofclaim 8, wherein each electrode wire of the plurality of electrode wires is sized to carry an electrical current of at least ten amps at a voltage of at least one thousand volts.

11. The catheter ofclaim 8, wherein the subassembly comprises a distal loop subassembly comprising variable diameter loop.

12. The catheter ofclaim 11, wherein the variable diameter loop has an open loop diameter of twenty-seven millimeters and a closed loop diameter of approximately fifteen millimeters.

13. The catheter ofclaim 12, wherein each catheter electrode of the plurality of catheter electrodes is a ring electrode having a length of 2.5 millimeters.

14. The catheter ofclaim 12, wherein each catheter electrode of the plurality of catheter electrodes is a ring electrode having a length of 2.0 millimeters.

15. An electroporation system comprising:

an electroporation generator; and

a catheter connected to the electroporation generator, the catheter comprising:

a handle including an insulated electrical connector at a proximal end of the handle, the handle defining an interior channel;

a shaft coupled to and extending from a distal end of the handle, the shaft defining an interior channel;

a subassembly coupled to a distal end of the shaft, the subassembly having a plurality of catheter electrodes disposed thereon; and

a plurality of electrode wires, each electrode wire of the plurality of electrode wires coupled to a different catheter electrode of the plurality of catheter electrodes and extending from the subassembly to the connector, through the interior channels of the shaft and the handle, wherein each electrode wire of the plurality of electrode wires is surrounded by an insulator with a thickness of at least about 1.5 thousandths of an inch.

16. The electroporation system ofclaim 15, wherein the insulated electrical connector comprises a waterproof electrical connector.

17. The electroporation system ofclaim 15, wherein each electrode wire of the plurality of electrode wires is sized to carry an electrical current of at least ten amps at a voltage of at least one thousand volts.

18. The electroporation system ofclaim 15, wherein the subassembly comprises a distal loop subassembly comprising variable diameter loop.

19. The electroporation system ofclaim 18, wherein the variable diameter loop has an open loop diameter of twenty-seven millimeters and a closed loop diameter of approximately fifteen millimeters.

20. The electroporation system ofclaim 19, wherein each catheter electrode of the plurality of catheter electrodes is a ring electrode having a length of 2.5 millimeters.

Images