Patent Grant
10842572
The embodiments described herein relate generally to medical devices for therapeutic electrical energy delivery, and more particularly to systems, apparatuses, and methods for tracking ablation devices (e.g., ablation catheters) and generating lesion lines using such devices.
Pulsed field ablation using application of high voltage pulses has been demonstrated to be suitable for the rapid and effective generation of lesions in cardiac tissue as well as other target anatomy. In the cardiac context, pulsed field ablation has been used for focal ablation or the generation of discrete local lesions. For example, an ablation catheter configured for focal ablation can be used to delivered pulsed field ablation via irreversible electroporation to cardiac tissue.
In a clinical catheter laboratory, electroanatomical mapping systems that use impedance tracking or impedance-based localization systems can be used to provide three-dimensional visualization feedback of devices positioned in patient anatomy. Additionally or alternatively, electromagnetic tracking sensors can be integrated into devices and used to track those devices within patient anatomy.
It can be desirable during an ablation procedure to track properties of an ablation device and use such information to assess ablation characteristics, e.g., to assist with ablation procedure planning.
Described herein are systems, devices, and methods for visualizing and generating focal tissue ablation using an ablation catheter. In some embodiments, the ablation devices used in these systems may be deployed epicardially or endocardially in cardiac applications.
In some embodiments, an apparatus may include a memory; and a processor operatively coupled to the memory, the processor configured to: activate a field generator to generate an electric or magnetic field such that signals are received by a receiver coupled to an ablation device disposed adjacent to a tissue surface; obtain processed data associated with the signals; determine a position and an orientation of the ablation device based on the processed data; determine an expected ablation zone of the ablation device in the tissue surface based on the position and the orientation of the ablation device; and display, via an output device, a map of the tissue surface and a visual representation of the expected ablation zone in the map of the tissue surface.
In some embodiments, a method may include receiving, at a processor, data representative of signals received by a receiver coupled to an ablation device disposed adjacent to a tissue surface, the receiver receiving the signals in response to an electric or magnetic field being generated by a field generator; determining, at the processor, a position and an orientation of the ablation device based on the data representative of the signals; determining, at the processor, an expected ablation zone of the ablation device in the tissue surface based on the position and the orientation of the ablation device; and displaying, via an output device operatively coupled to the processor, a map of the tissue surface and a visual representation of the expected ablation zone in the map of the tissue surface.
In some embodiments, a system may include a field generator configured to generate an electric or magnetic field; a signal generator configured to generate a pulse waveform for ablating tissue; an output device; and a processor operatively coupled to the field generator, the signal generator, and the output device, the processor configured to: activate the field generator to generate the electric or magnetic field such that signals are received by a receiver coupled to an ablation device disposed adjacent to a tissue surface; obtain processed data associated with the signals; determine a position and an orientation of the ablation device based on the processed data; determine an expected ablation zone of the ablation device in the tissue surface based on the position and the orientation of the ablation device; cause the output device to display a map of the tissue surface and a visual representation of the expected ablation zone in the map of the tissue surface; and in response to the expected ablation zone corresponding to a desired ablation zone, activate the signal generator to generate the pulse waveform to be delivered to the ablation device such that the ablation device produces an ablated zone corresponding to the expected ablation zone.
Described herein are systems, devices, and methods for selective and rapid application of pulsed electric fields to ablate tissue by irreversible electroporation. Generally, the systems, devices, and methods described herein may be used to generate lesion lines with an ablation device (e.g., a focal ablation device).
In some embodiments, the systems, devices, and methods described herein provide spatial tracking of an ablation device (e.g., catheter) in a body cavity to aid tissue ablation, such as the generation of contiguous and transmural lesion lines with a focal ablation catheter. Such spatial tracking can, for example, provide real-time tracking of the spatial location and orientation of the ablation device. Systems, devices, and methods incorporating spatial tracking functionality may enable real-time procedure planning and may be applied to the context of pulsed electric field ablation procedures with delivery of high voltage pulse waveforms to generate lesions using irreversible electroporation.
Pulsed electric field ablation for cardiac tissue ablation has been demonstrated recently to be a suitable modality for the rapid and effective generation of ablation lesions. In the cardiac context, focal ablation, or the creation of discrete local lesions, is a relevant application of pulsed electric field ablation. In a clinical catheter laboratory, electroanatomical mapping systems (e.g., the CARTO® system manufactured by Biosense Webster Inc., or the NavX™ system manufactured by Abbott Laboratories) can be used to provide three-dimensional visualization feedback for a catheter device positioned in the cardiac anatomy or chambers.
An electromagnetic tracking sensor may be integrated into a catheter device using electrodes configured to track the device position (e.g., in real time) within a three-dimensional volume of interest. Suitable electromagnetic tracking or localization systems for some medical applications include, for example, systems and sensors manufactured by Northern Digital Inc. Using a catheter endowed with such a sensor endocardially to navigate to different locations within a cardiac chamber, location data of a catheter electrode, and/or ECG signals recorded from the electrodes may be used to reconstruct the surface anatomy of a cardiac chamber.
Additionally or alternatively, a device location tracking system may determine a location of a device (e.g., a catheter) using an electric field or voltage gradients generated by a set of surface electrode patches on a patient, e.g., with potential differences set up between the surface electrode patches. With at least three such independently paired potential differences not all in the same plane, the three-dimensional location of an electrode may be estimated based on the voltage potentials measured by an electrode or sensor relative to one or more of the surface patches, or equivalently, impedance measurements may be estimated based on measured currents and/or voltages. Suitable techniques and methods of estimating spatial locations using such potential differences or voltage gradients of a set of electrodes, also termed impedance tracking or impedance-based localization systems, are incorporated in electroanatomical mapping systems such as the NavX™ system manufactured by Abbott Laboratories, the Rhythmia™ system manufactured by Boston Scientific Inc., or the CARTO® system manufactured by Biosense Webster Inc. In some embodiments, when a catheter device includes an electromagnetic sensor for electromagnetic tracking and is further used with an impedance tracking system, the locations of electrodes on the catheter may be more accurately estimated than by the use of impedance tracking without electromagnetic tracking.
Given a focal catheter configured to deliver pulsed field ablation lesions (e.g., lesions produced by irreversible electroporation) with a high voltage pulse waveform, the characteristics of a lesion (e.g., spatial extent and geometry) delivered using such a catheter with a given pulsed field ablation waveform and at given voltages may be determined using computational modeling and/or lesion data from studies or past procedures (e.g., preclinical or animal studies and/or procedures). Depending on the electrode geometry of the focal catheter, the lesion geometry generated by such an ablation generally depends at least in part on device orientation with respect to a local tissue surface or wall.
Systems and methods described herein relate to displaying expected lesion geometries or ablation zones on anatomical maps or surface renderings, which can enable a series of lesions (e.g., contiguous and/or transmural) to be efficiently generated in a predetermined anatomical region. In some embodiments, a focal ablation catheter configured to generate pulsed electric field ablation lesions can take a variety of geometric forms. In some embodiments, the methods, systems, and devices disclosed herein may comprise one or more of the methods, systems, and devices described in U.S. application Ser. No. 16/375,561, filed on Apr. 4, 2019, and titled “SYSTEMS, DEVICES, AND METHODS FOR FOCAL ABLATION,” the contents of which are hereby incorporated by reference in its entirety.
The term “electroporation” as used herein refers to the application of an electric field to a cell membrane to change the permeability of the cell membrane to the extracellular environment. The term “reversible electroporation” as used herein refers to the application of an electric field to a cell membrane to temporarily change the permeability of the cell membrane to the extracellular environment. For example, a cell undergoing reversible electroporation can observe the temporary and/or intermittent formation of one or more pores in its cell membrane that close up upon removal of the electric field. The term “irreversible electroporation” as used herein refers to the application of an electric field to a cell membrane to permanently change the permeability of the cell membrane to the extracellular environment. For example, a cell undergoing irreversible electroporation can observe the formation of one or more pores in its cell membrane that persist upon removal of the electric field.
Disclosed herein are systems and devices configured for generating focal ablation lesions in tissue. Generally, a system described here for ablating tissue with high voltage pulse waveforms may include a device tracking or localization component, ECG recording or monitoring component, cardiac stimulator, and ablation component. The systems, methods and implementations described in the present disclosure apply to synchronous or asynchronous ablation delivery. Furthermore, as described herein, the systems and devices may be deployed endocardially and/or epicardially to treat cardiac fibrillation.
The ablation device (110) can be operatively coupled to a mapping system (140). The mapping system (140) can include components that are functionally and/or structurally similar to the ablation mapping system (10), as described above with respect to
Memory (144) can be, for example, a random access memory (RAM), a memory buffer, a hard drive, an erasable programmable read-only memory (EPROM), an electrically erasable read-only memory (EEPROM), a read-only memory (ROM), Flash memory, etc. The memory may store instructions to cause the processor (142) to execute modules, processes and/or functions, such as field generation and/or location and orientation determination.
Input/output device (148) can be used to present information and/or receive information from a user and/or other compute devices (e.g., remote compute devices that are operatively coupled to the electroporation system (100) via a wired and/or wireless connection. In some embodiments, the processor (142) (or another processor) can be configured to generate information and control the input/output device (148) to present that information, e.g., using a display, audio device, projector, etc. The input/output device (148) can include, for example, a user interface, e.g., a display, an audio device, etc. that enables presentation of outputs to a user and/or receipt of input from the user. In some embodiments, the input/output device (148) can display a visual representation of specific anatomy (e.g., cardiac anatomy) along with a visual representation of a tracked device (e.g., the ablation device (110)) within that anatomy. In operation (e.g., during an ablation procedure), the visual representation can display the position, orientation, and/or configuration of the tracked device as it moves through target anatomy, e.g., in real-time (e.g., within fractions of a second). In some embodiments, the input/output device (148) can be used to receive inputs from a user that specify pulse waveform parameters (e.g., voltages, durations, delays, etc.), properties or characteristics of the ablation device (e.g., type of ablation device, deployment state, etc.) and/or other information that may assist in determining an expected ablation zone. In some embodiments, input/output device (148) can be configured to display expected ablation zones and/or ablated zones, e.g., in real time during an ablation procedure. In some embodiments, input/output device (148) can be configured to display different features or components (e.g., surrounding anatomical structure, ablation device, expected ablation zone, and/or ablated zone) using different markings, patterns, visual renderings, and/or colors to show during components as overlaying other components.
The pulse waveform generator (130) may be configured to generate ablation pulse waveforms for irreversible electroporation of tissue, such as, for example, pulmonary vein ostia. For example, the pulse waveform generator (130) may generate and deliver a pulse waveform to the ablation device (110), which generates a pulsed electric field that can ablate tissue. In some embodiments, the pulse waveform generator (130) is configured to generate the ablation pulse waveform in synchronization with a cardiac cycle of a heart (e.g., within a common refractory window of an atrial pacing signal and a ventricular pacing signal). For example, in some embodiments, the common refractory window may start substantially immediately following a pacing signal (or after a very small delay) and last for a duration of approximately 250 milliseconds (ms) or less thereafter. In some embodiments, an entire pulse waveform may be delivered within this duration, while in other embodiments, portions of the pulse waveform may be delivered within this duration with other portions being delivered during common refractory windows of a subsequent cardiac cycle. In such embodiments, the synchronization with the cardiac cycle can be achieved through the use of pacing or by appropriate gating of ablation delivery to R-wave detection based on an ECG recording.
In some embodiments, a cardiac stimulator (180) can be configured to generate pacing signal(s) and provide these to an optional pacing device (120) disposed near the target anatomy. Pacing device (120) can include a set of electrode(s) 122 that can receive the pacing signals and deliver them the cardiac anatomy, e.g., to pace the heart. One or both of atrial and/or ventricular pacing signals can be generated or delivered to the heart. In some embodiments, pacing device (120) can be configured to sense and/or analyze information (e.g., cardiac signals) regarding the patient, and provide this information to one or more of the mapping system (140) and/or pulse waveform generator (130) to further assist with controlling operation of those devices (e.g., initiating or interrupting pulse waveform delivery, determining expected ablation zones and/or ablated zones, etc.).
In some embodiments, the cardiac stimulator (180) and pulse waveform generator (130) may be in communication with one another (e.g., for coordinating timing of the pulse waveform delivery, pacing signal delivery). In some embodiments, the cardiac stimulator (180) may be integrated with the pulse waveform generator (130) in a single console. In some embodiments, the cardiac stimulator (180) and the pulse waveform generator (130) may be in communication with other devices, e.g., mapping system (140) or remote compute devices, directly or via, for example, one or more networks, each of which may be any type of network. A wireless network may refer to any type of digital network that is not connected by cables of any kind. However, a wireless network may connect to a wireline network in order to interface with the Internet, other carrier voice and data networks, business networks, and personal networks. A wireline network is typically carried over copper twisted pair, coaxial cable or fiber optic cables. There are many different types of wireline networks including, wide area networks (WAN), metropolitan area networks (MAN), local area networks (LAN), campus area networks (CAN), global area networks (GAN), like the Internet, and virtual private networks (VPN). Hereinafter, network refers to any combination of combined wireless, wireline, public and private data networks that are typically interconnected through the Internet, to provide a unified networking and information access solution.
In some embodiments, the pulse waveform generator (130) and/or cardiac stimulator (180) can be operatively coupled to the mapping system (140) such that information regarding the pulse waveform, pacing signals, and/or sensed signals (e.g., sensed cardiac signals from the pacing device (120)) can be provided to the mapping system (140), e.g., to assist with device localization and/or expected ablation determination. In some embodiments, the mapping system (140) and/or processor(s) associated with the pulse waveform generator (130) and/or cardiac stimulator (180) can be integrated into one or more controllers that can function to control the component(s) of each of these devices.
While not depicted, the cardiac stimulator (180) and the pulse waveform generator (130) can include one or more processor(s), which can be any suitable processing device configured to run and/or execute a set of instructions or code, similar to processor (142).
While not depicted, the cardiac stimulator (180) and the pulse waveform generator (130) can include one or more memory or storage device(s), similar to memory (144). The memory may store instructions to cause the processor of any one of the cardiac stimulator (180) and the pulse waveform generator (130) to execute modules, processes and/or functions, such as pulse waveform generation and/or cardiac pacing.
In some embodiments, one or more of the splines (230) may include one or more of a set of proximal electrodes (232, 234) and distal electrodes (236, 238). In some embodiments, a spline of the set of splines (230) may include between about 1 and about 8, inclusive, proximal electrodes (232, 234) and between about 1 and about 8, inclusive, distal electrodes (236, 238). In some embodiments, the device (200) may include between about 2 and about 12 splines, including all ranges and sub-values in-between.
In some embodiments, an ablation device (e.g., ablation device (110, 200)) may incorporate a receiver (e.g., receiver (118)) implemented as an electromagnetic tracking sensor for tracking a position or orientation of the ablation device. Along with the device configuration calculations as described herein, the electromagnetic localization data may provide refined (e.g., improved) spatial locations of all the device electrodes. In such embodiments, the ablation device can be used to endocardially navigate to different locations within a cardiac camber while collecting location data and/or cardiac data (e.g., recorded using one or more electrodes of the ablation device), which in turn can be used to construct a virtual representation of a surface anatomy of the cardiac camber.
Additionally or alternatively, in some embodiments, an ablation catheter (e.g., ablation device (110)) can include a receiver implemented as an electrode that is configured to measure voltage and/or current induced by electric fields generated by a set of surface patches. In such embodiments, the set of surface patches can be configured to generate electric fields in multiple planes, with voltage and/or current signals being measured by the electrode of the ablation catheter (or impedance estimated using such measurements).
While an ablation device (110) having a basket shape is depicted in
Also described here are methods for determining an expected ablation zone during a tissue ablation process performed in or near one or more heart chamber(s) using the systems and devices described herein. In an embodiment, the heart chamber(s) may be the left atrial chamber and include its associated pulmonary veins, while the devices and methods described herein can also be used in other cardiac chambers. Generally, one or more catheters may be advanced in a minimally invasive fashion through vasculature to a target location. For example, an ablation device may be advanced through vasculature over a guidewire and through a deflectable sheath. The sheath may be configured for deflection and aid in guiding a focal ablation catheter through vasculature and one or more predetermined targets (e.g., pulmonary vein ostia). A dilator may be advanced over a guidewire and configured for creating and dilating a transseptal opening during and/or prior to use. The methods described here include introducing and disposing an ablation device (e.g., ablation device (110, 200)) in contact with one or more pulmonary vein ostial or antral regions. A pacing signal may be delivered to the heart using a cardiac stimulator (e.g., cardiac stimulator (180)) and/or measure cardiac activity. Spatial characteristics (e.g., position, orientation, configuration) of the ablation device and tissue may be determined and used to generate an expected ablation zone and/or tissue map for display. A pulse waveform may be delivered by one or more electrodes of the ablation device to ablate tissue. In some embodiments, ablation energy may be delivered in synchrony with cardiac pacing. In some embodiments, the voltage pulse waveforms described herein may be applied during a refractory period of the cardiac cycle so as to avoid disruption of the sinus rhythm of the heart. The tissue map including ablated tissue and the expected ablation zone may be updated in real-time on the display as the device is navigated through tissue and additional pulse waveforms are delivered to the tissue.
A pulse waveform may be generated and delivered to one or more electrodes of the device to ablate tissue. In some embodiments, the pulse waveform may be generated in synchronization with a pacing signal of the heart to avoid disruption of the sinus rhythm of the heart. In some embodiments, the electrodes may be configured in anode-cathode subsets. Additionally or alternatively, the pulse waveforms may include a plurality of levels of a hierarchy to reduce total energy delivery, e.g., as described in International Application Serial No. PCT/US2019/031135, filed on May 7, 2019, and titled “SYSTEMS, APPARATUSES AND METHODS FOR DELIVERY OF ABLATIVE ENERGY TO TISSUE,” the disclosure of which is incorporated herein by reference. In some embodiments, the ablation devices (e.g., ablation device (110, 200)) described herein may be used for epicardial and/or endocardial ablation. Examples of suitable ablation catheters are described in International Application Serial No. PCT/US2019/014226, incorporated by reference above.
In some embodiments, spatial information associated with the ablation device and tissue may be determined, at (908). For example, signals may be received at a receiver (e.g., sensor, electrode, etc.) coupled to or integrated into the ablation device in response to electric and/or magnetic fields generated by a field generator. Data representative of signals received by the receiver may be received at a processor (e.g., processor (42, 142)), which can further process and/or analyze such information. Based on such analysis, spatial information (e.g., position, orientation, configuration) of the ablation device may be determined at the processor.
For example, such analysis can involve determining one or more geometric parameters that characterize the distal end of the ablation device. In some embodiments, with a known distal geometry of a distal portion of an ablation device (e.g., focal ablation catheter), for a given configuration of the splines, the shape of the ablation device may be characterized by a set of geometric parameters. For example, as shown in
In some embodiments, an impedance-based localization system may be configured to generate spatial coordinates of proximal and distal electrodes of an ablation device. Conventional impedance-based localization systems can be prone to error due to tissue inhomogeneities. The localization systems as described herein may generate improved (or refined) spatial coordinate estimates of a distal portion of a focal ablation device. Given the coordinates of the proximal electrodes of an ablation device obtained from an impedance-based localization system, a centroid of the proximal electrodes on each spline may be determined. From this set of centroids on each spline, the centroid x1 of these centroids of the proximal electrodes can be determined. The centroid x1 may be used to calculate a center for a best-fit circle C1 (corresponding to the proximal electrodes) having a diameter d1 that may be calculated using, for example, a least-squares fit. Likewise, the centroids of the distal electrodes of the set of splines can be determined, and a centroid x2 of the centroids of the distal electrodes can be determined. The centroid x2 can be used to calculate a center for a best-fit circle C2 (corresponding to the distal electrodes) having a diameter d2. A diameter d1 of the centroid x1 and a diameter d2 of the centroid x2 may be determined. A distance b between the centroids x1 and x2 may be calculated.
A configuration of the ablation device may be determined based on the diameter d1, the diameter d2, and the distance b, and the orientation of the ablation device may be defined using the centroids x1 and x1. In particular, given a set of known deployment configurations {Fi} of the ablation device (with index i labeling the configurations), each with corresponding parameters {d1,i, d2,i, bi}, the closest configuration {F*i} may be calculated, for example, by finding the configuration with minimal error or cost Si using:
Si=(d1,i−d1)2+(d2,i−d2)2+(bi−b)2
In embodiments where a focal ablation catheter device does not incorporate an electromagnetic sensor, the device orientation may be defined in part by the unit vector v as follows:
Furthermore, the unit vector w=(p1−x1)/|p1−x1| from the centroid x1 to the centroid p1 of proximal electrodes on a fiducial spline (for example, a first spline) together with v may fully define the device orientation. The device configuration, as obtained above, and the device orientation may provide improved spatial locations of each of the device electrodes.
Optionally, a surface anatomy of a cardiac chamber may be constructed (e.g., simulated) using the device location and/or tracking systems described herein. For example, as depicted in
A portion of such a representation (e.g., tissue map) is illustrated in
In some embodiments, an anatomical map of the cardiac chamber can be acquired using other devices (e.g., imaging devices, etc.), and the anatomical map can be provided to the mapping and ablation systems described herein. In such embodiments, the ablation device can optionally be used to confirm the accuracy of the anatomical map, e.g., using the method depicted in
Referring back to
In some embodiments, the expected ablation zone can be determined at a processor (e.g., processor (42, 142)) based on the position and the orientation of the ablation device, as further described below. For example, the expected ablation zone can be determined by determining a nearest distance from the ablation device to the tissue surface, identifying a set of points from the plurality of points within a predefined distance from a distal end of the ablation device when the nearest distance is less than a predefined value, determining a centroid of the set of points, determining a local tangent plane to a surface extending through the centroid, and determining a center of the expected ablation zone based on the position and the orientation of the ablation device relative to the local tangent plane, the center representing a location of the tissue surface having a maximum depth of ablation. Furthermore, an expected ablation zone can be based on one or more pulse waveform parameters (e.g., voltage, duration, delays, number of pulses, number of pulse groups, etc.) that may modify, for example, a size and depth of an expected ablation zone.
To illustrate an example of determining the expected ablation zone,
A centroid (1122) of this local set of points may be calculated. A local tangent plane (1110) to the surface passing through the local centroid (1122) is determined. For example, such a plane may be determined by solving an optimization problem. If the local set of points (1120) is the centroid (1122) is xc, and the unit normal to the local tangent plane (1110) is n, then the distance of each local point to the tangent plane (1110) is given by:
qi=(yi−xc)·n
A cost function can be defined as the sum of such squared distances:
where the matrix A is defined as the sum (over the local set of points) of outer products
In some embodiments, it is desired to find the normal n to the local tangent plane that minimizes the cost C. Furthermore, since n is a unit normal, it satisfies the constraint nTn=1. Introducing an appropriate Lagrange multiplier λ, this leads to the constrained cost function:
C′=nTAn−λ(nTn−1)
In some embodiments, C′ may be minimized with respect to n and λ. For example, performing the minimization leads to the eigenvalue equation:
An=λn
The unit eigenvector n* corresponding to the smallest eigenvalue of the matrix A is the desired solution for the normal to the local tangent plane (1110). Thus, the local tangent plane (1110) is determined.
Once the local tangent plane is known, based on known properties of the ablation zone (and its center) depending on the orientation of the distal device geometry with respect to the local tangent plane and/or deployment configuration, the ablation zone center (1130) may be determined. Thereafter, for a given device positioning or placement at the endocardial surface, the expected ablation zone can be rendered in the local tangent plane. In some embodiments, the expected ablation zone can be projected onto the surface rendering itself and be depicted as one or more of a contour on the surface, colored patch, or other graphical indicator (e.g., be projected or rendered in a map of the tissue, at (914)).
The expected ablation zone can be presented, at (914), according to various methods. For example, a map of the tissue surface and a visual representation of the expected ablation zone in the map of the tissue surface may be displayed via an output device (e.g., input/output device (48, 148) or an output device coupled to an external compute device) operatively coupled to the processor.
In some embodiments, the expected ablation zone can be determined (e.g., at a processor including, for example, processor (42, 142)) by identifying an electrode from the plurality of electrodes that is in contact with the tissue surface (e.g., using ECG data, as described above), identifying an expected ablation zone shape from a plurality of expected ablation zone shapes based on the position and the orientation of the ablation device, and generating the expected ablation zone having a center at a location corresponding to a location of the electrode and based on the expected ablation zone shape, the center representing a location of the tissue surface having a maximum depth of ablation. For example,
The shape, size, and/or orientation of the expected ablation zone (440) can be based on the spatial characteristics or geometry of the ablation device. For example, a linear focal device can have an ablation zone whose shape and size can be generally different from that of a focal ablation device. In some embodiments, ablated zones generated by the ablation device (430) can be recorded for the ablation device (430) when the device is in a plurality of positions, orientations, and/or configurations relative to a tissue surface, and the resulting shapes of the generated ablated zones can be recorded and stored for future reference in generating expected ablation zones. In some embodiments, such ablated zones can be generated in experimental environments, e.g., using test subjects/preclinical animal models.
Further examples of expected ablation zones are depicted in and described with reference to
As shown in
In some embodiments, with an estimated expected shape of the ablation zone (including the approximate center of the ablation zone) and its dependence on one or both of device deployment and device orientation with respect to the local tissue wall, a representation of the ablation zone, for example a minimum expected ablation zone, may be graphically provided when a map of the tissue surface anatomy is available.
Referring back to
In some embodiments, a mapping system (e.g., mapping system (10, 140)) separate from a signal generator (e.g., pulse waveform generator (130)) can send a signal to the signal generator to cause the signal generator to generate a pulse waveform to be delivered to the ablation device, such that the ablation device generates an electric field that produces an ablated zone corresponding to the expected ablation zone. In some embodiments, the mapping system can be integrated with a signal generator, and upon determining that ablation is to proceed, the mapping system can generate and deliver the pulse waveform to the ablation device. As described in more detail herein,
In some embodiments, systems, devices, and methods described herein can base the ablated zone on the expected ablation zone (e.g., have the ablated zone be the same as the expected ablated zone). Accordingly, after ablating the tissue, at (918), such systems, devices, and methods can present the ablated zone by changing the representation of the expected ablation zone to signify that the area has been ablated. For example, the expected ablation zone can be visually depicted using a first set of indicia or coloring before ablation, and the abated zone can be visually depicted using a second set of indicia or coloring different from the first set after ablation.
In some embodiments, systems, devices, and methods can use further methods to detect the tissue area that has been ablated (for example, using signals (e.g., impedances) collected by one or more sensor(s) (e.g., electrode(s) (116, 122), receiver (118)), or using an external device). In such embodiments, systems, devices, and methods can further adapt its methods (e.g., models, algorithms) for determining an expected ablation zone based on the detected ablated area. For example, analysis of the expected ablation zone and how that compared to the actual ablated area, along with parameters associated with the tissue and/or ablation device (e.g., thickness of tissue, tissue type, ablation device geometry and/or positioning, etc.) that may have caused discrepancies between the expected ablation zone and actual ablated area, can be used to improve future determinations of expected ablation zones.
When delivery of ablation pulses has not been completed by the ablation device (e.g., when using the ablation device to generate a contiguous lesion line, as further described with reference to
A visual representation of the ablated zone may be displayed by the output device using a first set of indicia and a visual representative of the second expected ablation zone using a second set of indicia different from the first set of indicia. For example,
In some embodiments, a first ablated zone and a second ablated zone may form a portion of a continuous lesion in the tissue surface. For example, the signal generator may be activated to generate the pulse waveform to be delivered to the ablation device such that the ablation device produces a second ablated zone corresponding to the second expected ablation zone when the second expected ablation zone has an area of overlap with the ablated zone that is greater than a predetermined value.
This process can be continued to generate a series of overlapping ablated zones for contiguous lesion line generation. In some embodiments, the size of the depicted expected ablation zones can be illustrated to be smaller than the simulated or pre-clinically determined zone size as a method of prescribing closer placement of adjacent ablations to ensure adequate lesion overlap. Furthermore, the shape and size of the surface rendering of the ablation zone can both generally depend on device orientation with respect to the local tangent plane and/or on device deployment state.
When the ablation is completed, (920—Yes), the ablation device may be withdrawn from the cardiac chamber and the patient, at (922).
It should be understood that the examples and illustrations in this disclosure serve exemplary purposes and departures and variations such as numbers of splines, number of electrodes, and so on, or a variety of focal ablation devices such as linear ablation catheters etc. can be built and deployed according to the teachings herein without departing from the scope of this invention.
As used herein, the terms “about” and/or “approximately” when used in conjunction with numerical values and/or ranges generally refer to those numerical values and/or ranges near to a recited numerical value and/or range. In some instances, the terms “about” and “approximately” may mean within ±10% of the recited value. For example, in some instances, “about 100 [units]” may mean within ±10% of 100 (e.g., from 90 to 110). The terms “about” and “approximately” may be used interchangeably.
Some embodiments described herein relate to a computer storage product with a non-transitory computer-readable medium (also may be referred to as a non-transitory processor-readable medium) having instructions or computer code thereon for performing various computer-implemented operations. The computer-readable medium (or processor-readable medium) is non-transitory in the sense that it does not include transitory propagating signals per se (e.g., a propagating electromagnetic wave carrying information on a transmission medium such as space or a cable). The media and computer code (also may be referred to as code or algorithm) may be those designed and constructed for the specific purpose or purposes. Examples of non-transitory computer-readable media include, but are not limited to, magnetic storage media such as hard disks, floppy disks, and magnetic tape; optical storage media such as Compact Disc/Digital Video Discs (CD/DVDs), Compact Disc-Read Only Memories (CD-ROMs), and holographic devices; magneto-optical storage media such as optical disks; carrier wave signal processing modules; and hardware devices that are specially configured to store and execute program code, such as Application-Specific Integrated Circuits (ASICs), Programmable Logic Devices (PLDs), Read-Only Memory (ROM) and Random-Access Memory (RAM) devices. Other embodiments described herein relate to a computer program product, which may include, for example, the instructions and/or computer code disclosed herein.
The systems, devices, and/or methods described herein may be performed by software (executed on hardware), hardware, or a combination thereof. Hardware modules may include, for example, a general-purpose processor (or microprocessor or microcontroller), a field programmable gate array (FPGA), and/or an application specific integrated circuit (ASIC). Software modules (executed on hardware) may be expressed in a variety of software languages (e.g., computer code), including C, C++, Java®, Ruby, Visual Basic®, and/or other object-oriented, procedural, or other programming language and development tools. Examples of computer code include, but are not limited to, micro-code or micro-instructions, machine instructions, such as produced by a compiler, code used to produce a web service, and files containing higher-level instructions that are executed by a computer using an interpreter. Additional examples of computer code include, but are not limited to, control signals, encrypted code, and compressed code.
The specific examples and descriptions herein are exemplary in nature and embodiments may be developed by those skilled in the art based on the material taught herein without departing from the scope of the present invention, which is limited only by the attached claims.
This application claims the benefit of U.S. Provisional Application No. 62/940,219, filed on Nov. 25, 2019, the entire disclosure of which is incorporated herein by reference in its entirety.
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| Number | Date | Country | |
|---|---|---|---|
| 62940219 | Nov 2019 | US |
