Patent Description:
<CIT> relates to the utilization of electrode spatial arrangements for characterizing cardiac conduction conditions, wherein no clique of electrodes is selected from a plurality of electrodes for determining quality of electrophysiology (OIS) signals by analyzing E field data points associated with the selected clique of electrodes. <CIT> relates to the field of electrophysiology for accurate measurement of parameters within body-surface ECG, intracardiac, and EP cardial electrical signals such as heart rates and local activation times. <CIT> relates to medical devices for assessing an anatomical space of a body by generating vector field maps for electrical activity of anatomical structures. <CIT> relates to mapping of organs in a body, in particular mapping electrical activity in a heart. <NPL> discloses quantitative techniques for analyzing high-resolution cardiac-mapping data. <CIT> relates to methods for characterizing cardiac conduction conditions in a catheter orientation independent manner using electrode spatial arrangements in 3D mapping systems.

Electrophysiology (EP) catheters are used in a variety of diagnostic, therapeutic, and/or mapping and ablative procedures to diagnose and/or correct conditions such as atrial or ventricular arrhythmias, including for example, ectopic atrial tachycardia, atrial fibrillation, and atrial flutter. Arrhythmias can create a variety of conditions including irregular heart rates, loss of synchronous atrioventricular contractions and stasis of blood flow in a chamber of a heart which can lead to a variety of symptomatic and asymptomatic ailments and even death.

Typically, a catheter is deployed and manipulated through a patient's vasculature to the intended site, for example, a site within a patient's heart. The catheter carries one or more electrodes that can be used for cardiac mapping or diagnosis, ablation and/or other therapy delivery modes, or both, for example. Once at the intended site, treatment can include, for example, radio frequency (RF) ablation, cryoablation, laser ablation, chemical ablation, high-intensity focused ultrasound-based ablation, microwave ablation, and/or other ablation treatments. The catheter imparts ablative energy to cardiac tissue to create one or more lesions in the cardiac tissue. This lesion disrupts undesirable cardiac activation pathways and thereby limits, corrals, or prevents errant conduction signals that can form the basis for arrhythmias.

To position a catheter at a desired site within the body, some type of navigation may be used, such as using mechanical steering features incorporated into the catheter (or a sheath). In some examples, medical personnel may manually manipulate and/or operate the catheter using the mechanical steering features.

A navigating system may be used for visualization and to facilitate the advancement of catheters through a patient's vasculature to specific locations within the body. Such navigating systems may include, for example, electric and/or magnetic field based positioning and navigating systems that are able to determine the position and orientation of the catheter (and similar devices) within the body.

Conduction disorders in the body can result from abnormal conduction in regions as small as <NUM>-<NUM>. In addition, ablation in these regions must be restricted to the pathological tissue to preserve electrical and mechanical function, particularly with ventricular arrhythmias. Today, many catheters employ electrode pairs spaced greater than <NUM> apart which can make it difficult to reliably allow discrimination or localization of defects. Even when the electrodes are more closely spaced, around <NUM> to around <NUM>, the orientation of the pair of electrodes is a prominent factor in the amplitude and morphology of the resulting signals.

The foregoing discussion is intended only to illustrate the present field and should not be taken as a disavowal of claim scope.

The invention provides a system for analyzing signal quality of a plurality of electrodes according to claim <NUM>. The methods disclosed herein are not claimed as such.

In one embodiment, a system for obtaining an OIS coordinate frame comprises an electronic control unit configured to determine a local 3D electric field loop, create a zero mean version of E(t) over a depolarization interval, compute an Ė value at each of a plurality of time intervals, compute an initial estimate of ŵ from a cross product of E and the Ė value for each of the plurality of time intervals, average the initial estimate of ŵ from each of the plurality of time for a best estimate of ŵ, determine a plurality of â(θ) values and choosing a corresponding n̂(θ) value for each of the plurality of â(θ) values, compute a composite match score, and choose at least one best value for â and a best value for n̂.

In another embodiment, a method for obtaining an OIS coordinate frame comprises determining a local 3D electric field loop, creating a zero mean version ofE(t) over a depolarization interval, computing an Ė value at each of a plurality of time intervals, computing an initial estimate of ŵ from a cross product of E and the Ė value for each of the plurality of time intervals, averaging the initial estimate of ŵ from each of the plurality of time for a best estimate of ŵ, determining a plurality of â(θ) values and choosing a corresponding n̂(θ) value for each of the plurality of â(θ) values, computing a composite match score, and choosing at least one best value for â and a best value for n̂.

In yet another embodiment, a system for obtaining an OIS coordinate frame comprises an electronic control unit configured to determine a local 3D electric field loop, compute a composite match score for how well φ̇ matches an inner product of E and â(θ) and -φ matches an inner product of E and n̂, choose a best value for â and a best value for n̂, and determine a value for ŵ by a right hand rule and a cross product ŵ = n̂ × â.

Cardiac EP mapping today primarily uses bipolar electrograms (EGMs) obtained from electrode pairs. Bipoles are preferred as they have reduced low frequency noise, reduced far-field effects and often produce sharp and well-recognized features when filtered appropriately. Unipolar EGMs on the other hand contain far-field information and less stable baselines that make them less attractive for mapping purposes. A feature of the unipolar signal that makes it useful for mapping is the fact that its morphology and amplitude are independent of catheter orientation. Amplitudes and morphology of bipolar EGM's are dependent on the orientation of the electrode pair from which they are calculated and hence depend on the orientation of the catheter. The dependence on orientation results in inconsistently measured amplitudes and morphology-based measurements like activation times. It therefore also impacts derived quantities like scar boundaries, activation direction, and conduction velocity.

Electrophysiologic information may also be elicited by pacing a tissue or organ and observing the resulting spread of depolarization from immediately adjacent to the site where capture occurs. These observations are difficult with current technology because of pacing artifacts but directional information provided by En, Ea, or v, as described herein, can serve as clues to anatomic or functional conduction blocks. Even without pacing, conduction around obstacles such as valve orifices or blocks is known to become curved and slowed and this can be directly mapped and visualized with the information disclosed herein much more conveniently and reliably than previously possible.

<FIG> illustrates one embodiment of a system <NUM> for mapping electrophysiological information corresponding to an anatomic structure onto a multidimensional (e.g., three-dimensional) geometry surface model of the anatomic structure (each of the terms "electrophysiology" and "electrophysiological" will hereinafter be referred to as "EP"). The system <NUM> comprises, among other components, a medical device <NUM> and a model construction system <NUM>. In one embodiment, the medical device <NUM> comprises a catheter, and the model construction system <NUM> comprises, in part, a processing apparatus <NUM>. The processing apparatus <NUM> may take the form of an electronic control unit, for example, that is configured to obtain a geometry surface model of the cardiac structure, and to construct an EP map corresponding to the cardiac structure using data collected by, for example, the catheter <NUM>. The catheter <NUM> is configured to be inserted into a patient's body <NUM>, and more particularly, into the patient's heart <NUM>. The catheter <NUM> may include a cable connector or interface <NUM>, a handle <NUM>, a shaft <NUM> having a proximal end <NUM> and a distal end <NUM> and one or more sensors <NUM> (e.g., <NUM><NUM>, <NUM><NUM>, <NUM><NUM>) mounted in or on the shaft <NUM> of the catheter <NUM>. In one embodiment, the sensors <NUM> are disposed at or near the distal end <NUM> of the shaft <NUM>. The connector <NUM> provides mechanical, fluid, and electrical connection(s) for cables, such as, for example, cables <NUM>, <NUM> extending to the model construction system <NUM> and/or other components of the system <NUM> (e.g., a visualization, navigation, and/or mapping system (if separate and distinct from the model construction system <NUM>), an ablation generator, irrigation source, etc.).

The sensors <NUM> mounted in or on the shaft <NUM> of the catheter <NUM> are electrically connected to the model construction system <NUM>, and the processing apparatus <NUM> thereof, in particular. The sensors <NUM> may be provided for a variety of diagnostic and therapeutic purposes including, for example and without limitation, EP studies, pacing, cardiac mapping, and ablation. In an embodiment, one or more of the sensors <NUM> are provided to perform a location or position sensing function. Accordingly, in such an embodiment, as the catheter <NUM> is moved along a surface of the cardiac structure and/or about the interior thereof, the sensor(s) <NUM> can be used to collect location data points that correspond to the surface of, or locations within, the cardiac structure. These location data points can then be used by, for example, the model construction system <NUM> in the construction of a geometry surface model of the cardiac structure.

In one embodiment, the model construction system <NUM>, and the processing apparatus <NUM> thereof, in particular, is configured to obtain a geometry surface model of the cardiac surface (or at least a portion thereof), and to map EP information corresponding to that cardiac structure onto the geometry surface model. The processing apparatus <NUM> is configured to use, at least in part, data (location data and/or EP data/information) collected by the catheter <NUM> in the construction of one or both of a geometry surface model and an EP map.

In an embodiment wherein the model construction system <NUM> is configured to construct the geometry surface model, the model construction system <NUM> is configured to acquire location data points collected by the sensor(s) <NUM> corresponding to the cardiac structure. The model construction system <NUM> is configured to then use those location data points in the construction of the geometry surface model of the cardiac structure. The model construction system <NUM> is configured to construct a geometry surface model based on some or all of the collected location data points. In addition to constructing a geometry surface model of a structure, the model construction system <NUM> is configured to function with the sensor(s) <NUM> to collect location data points that are used in the construction of the geometry surface model. In such an embodiment, the model construction system <NUM> may comprise an electric field-based system, such as, for example, the EnSite NavX™ system commercially available from St. Jude Medical, Inc. , and generally shown with reference to <CIT> entitled "Method and Apparatus for Catheter Navigation and Location and Mapping in the Heart". In other exemplary embodiments, however, the model construction system <NUM> may comprise other types of systems, such as, for example and without limitation: a magnetic-field based system such as the Carto™ System available from Biosense Webster, and as generally shown with reference to one or more of <CIT> entitled "Intrabody Measurement," <CIT> entitled "Medical Diagnosis, Treatment and Imaging Systems," and <CIT> entitled "System and Method for Determining the Location and Orientation of an Invasive Medical Instrument," or the gMPS system from MediGuide Ltd. , and as generally shown with reference to one or more of <CIT> entitled "Medical Positioning System," <CIT> entitled "System for Determining the Position and Orientation of a Catheter," and <NUM>,<NUM>,<NUM> entitled "Medical Imaging and Navigation System," a combination electric field-based and magnetic field-based system such as the Carto <NUM>™ System also available from Biosense Webster.

In one embodiment, the sensor(s) <NUM> of the catheter <NUM> comprise positioning sensors. The sensor(s) <NUM> produce signals indicative of catheter location (position and/or orientation) information. In an embodiment wherein the model construction system <NUM> is an electric field-based system, the sensor(s) <NUM> may comprise one or more electrodes. In such an embodiment, each of the electrodes may comprise one of a number of types of electrodes, such as, for example, tip electrodes, ring electrodes, button electrodes, coil electrodes, brush electrodes, flexible polymer electrodes, and spot electrodes. Alternatively, in an embodiment wherein the model construction system <NUM> is a magnetic field-based system, the sensor(s) <NUM> may comprise one or more magnetic sensors configured to detect one or more characteristics of a low-strength magnetic field. For instance, in one exemplary embodiment, the sensor(s) <NUM> may comprise magnetic coils disposed on or in the shaft <NUM> of the catheter <NUM>.

For purposes of clarity and illustration, the model construction system <NUM> will hereinafter be described as comprising an electric field-based system, such as, for example, the EnSite NavX™ system identified above. It will be appreciated that while the description below is primarily limited to an embodiment wherein the sensor(s) <NUM> comprise one or more electrodes, in other exemplary embodiments, the sensor(s) <NUM> may comprise one or more magnetic field sensors (e.g., coils). Accordingly, model construction systems that include positioning sensor(s) other than the sensors or electrodes described below remain within the scope of the present disclosure.

With reference to <FIG>, in addition to the processing apparatus <NUM>, the model construction system <NUM> may include, among other possible components, a plurality of patch electrodes <NUM>, a multiplex switch <NUM>, a signal generator <NUM>, and a display device <NUM>. In another exemplary embodiment, some or all of these components are separate and distinct from the model construction system <NUM> but that are electrically connected to, and configured for communication with, the model construction system <NUM>.

The processing apparatus <NUM> may comprise a programmable microprocessor or microcontroller, or may comprise an application specific integrated circuit (ASIC). The processing apparatus <NUM> may include a central processing unit (CPU) and an input/output (I/O) interface through which the processing apparatus <NUM> may receive a plurality of input signals including, for example, signals generated by patch electrodes <NUM> and the sensor(s) <NUM>, and generate a plurality of output signals including, for example, those used to control and/or provide data to, for example, the display device <NUM> and the switch <NUM>. The processing apparatus <NUM> may be configured to perform various functions, such as those described in greater detail above and below, with appropriate programming instructions or code (i.e., software). Accordingly, the processing apparatus <NUM> is programmed with one or more computer programs encoded on a computer storage medium for performing the functionality described herein.

With the exception of the patch electrode 188B called a "belly patch," the patch electrodes <NUM> are provided to generate electrical signals used, for example, in determining the position and orientation of the catheter <NUM>. In one embodiment, the patch electrodes <NUM> are placed orthogonally on the surface of the body <NUM> and are used to create axes-specific electric fields within the body <NUM>.

In one embodiment, the sensor(s) <NUM> of the catheter <NUM> are electrically coupled to the processing apparatus <NUM> and are configured to serve a position sensing function. More particularly, the sensor(s) <NUM> are placed within electric fields created in the body <NUM> (e.g., within the heart) by exciting the patch electrodes <NUM>. For purposes of clarity and illustration only, the description below will be limited to an embodiment wherein a single sensor <NUM> is placed within the electric fields. It will be appreciated, however, that in other exemplary embodiments that remain within the scope of the present disclosure, a plurality of sensors <NUM> can be placed within the electric fields and then positions and orientations of each sensor can be determined using the techniques described below.

When disposed within the electric fields, the sensor <NUM> experiences voltages that are dependent on the location between the patch electrodes <NUM> and the position of the sensor <NUM> relative to tissue. Voltage measurement comparisons made between the sensor <NUM> and the patch electrodes <NUM> can be used to determine the location of the sensor <NUM> relative to the tissue. Accordingly, as the catheter <NUM> is swept about or along a particular area or surface of interest, the processing apparatus <NUM> receives signals (location information) from the sensor <NUM> reflecting changes in voltage levels on the sensor <NUM> and from the non-energized patch electrodes <NUM>. Using various known algorithms, the processing apparatus <NUM> may then determine the location (position and orientation) of the sensor <NUM> and record it as a location data point corresponding to a location of the sensor <NUM> on the surface of, or within, the cardiac structure in a memory or storage device associated with, or accessible, by the processing apparatus <NUM>, such as the memory <NUM>. In one embodiment, prior to recording the location as a location data point, the raw location data represented by the signals received by the processing apparatus <NUM> may be corrected by the processing apparatus <NUM> to account for respiration, cardiac activity, and other artifacts using known or hereafter developed techniques. The system described in <FIG> and <FIG> is further described in <CIT>.

One aspect described herein addresses a unique way to combine the benefit of orientation independence of the unipolar signals with the other benefits of bipolar signals that were highlighted previously. The disclosure utilizes closely spaced electrodes on high-density diagnostic catheters to derive local "pseudo bipolar", "equivalent bipole", or "omnipolar" signals that are catheter orientation independent and are free of low-frequency noise and far-field effects. The closely spaced electrodes can be located on a single high-density diagnostic or other catheter or in some embodiments can be located on multiple catheters where electrodes on the catheters are located near or adjacent each other. Furthermore, the equivalent bipolar EGMs so derived possess characteristic shapes and relationships that reflect physiologic and anatomic directions which enable better contact maps by virtue of more consistent activation timing directions. The presence of closely spaced electrodes also helps to characterize the substrate in the immediate vicinity (e.g., a few mm) of the catheter. The omnipolar electrogram signal's amplitude and morphology would only be a function of the local substrate's electrophysiology and hence lends itself to the creation of better, consistent, and more useful contact maps. Examples of high-density catheters that can be used for the purpose include (but are not limited to) the catheters shown in <FIG>, and basket catheters like the catheters shown in <FIG> and <FIG>.

<FIG> show embodiments of catheters that can be used for high-density (HD) mapping applications. <FIG> illustrates one embodiment of a catheter <NUM> comprising a catheter body <NUM> coupled to a paddle <NUM>. The catheter body <NUM> can further comprise a first body electrode <NUM> and a second body electrode <NUM>. The paddle <NUM> can comprise a first spline <NUM>, a second spline <NUM>, a third spline <NUM>, and a fourth spline <NUM> that are coupled to the catheter body <NUM> by a proximal coupler <NUM> and coupled to each other by a distal connector <NUM> at a distal end of the paddle <NUM>. In one embodiment the first spline <NUM> and the fourth spline <NUM> can be one continuous segment and the second spline <NUM> and the third spline <NUM> can be another continuous segment. In other embodiments the various splines can be separate segments coupled to each other. The plurality of splines can further comprise a varying number of electrodes <NUM>. The electrodes in the illustrated embodiment can comprise ring electrodes evenly spaced along the splines. In other embodiments the electrodes can be evenly or unevenly spaced and the electrodes can comprise point or other types of electrodes. <FIG> illustrates another embodiment of a catheter <NUM> that can be used for HD mapping applications. The catheter <NUM> can comprise a catheter body <NUM> coupled to a paddle <NUM>. The catheter body <NUM> can further comprise a first body electrode <NUM> and a second body electrode <NUM>. The paddle <NUM> can comprise a first spline <NUM>, a second spline <NUM>, a third spline <NUM>, and a fourth spline <NUM> that are coupled to the catheter body <NUM> by a proximal coupler <NUM> and coupled to each other by a distal connector <NUM> at a distal end of the paddle <NUM>. In one embodiment, the proximal coupler <NUM> can further comprise an electrode.

Electrode placement along splines is controlled by the good mechanical stability of electrodes on splines. As a result, spacing along splines is best determined not by the mapping system, but by design and manufacturing. But spacing between splines is variable as a result of the forces and torques experienced as a catheter is maneuvered to a desired location. Electrodes located in spline midsections are most vulnerable to displacement. <FIG> shows incorporating slender tensile elements configured to join the splines near their centers to limit the maximal displacement from one another. One means to accomplish this is to use slender mono or multifilament nylon thread or suture like material, fastened at the ends, and looping around splines in the middle. A pass through a reflow oven during production allows the threads to become incorporated into the spline's polymer insulation, securing the thread to each spline and minimizing protuberances.

<FIG> illustrates one embodiment of a catheter <NUM> using tethers to limit the maximal spread between splines and thus enforce a more consistent electrode spacing when in use. The catheter <NUM> can comprise a catheter body <NUM> coupled to a paddle <NUM>. The catheter body <NUM> can further comprise a first body electrode <NUM> and a second body electrode <NUM>. The paddle <NUM> can comprise a first spline <NUM>, a second spline <NUM>, a third spline <NUM>, and a fourth spline <NUM> that are coupled to the catheter body <NUM> by a proximal coupler <NUM> and coupled to each other by a distal connector <NUM> at a distal end of the paddle <NUM>. The paddle <NUM> can further comprise a first support member <NUM> and a second support member <NUM> to limit displacement of the splines from each other. These support members can be slender tensile elements (like threads or suture material) that collapse during insertion of the catheter <NUM> into a sheath. The catheters shown in <FIG> are further described in international application no. <CIT> and published in English on <NUM> July <NUM> under international publication no. <CIT> (the '<NUM> application) and <CIT> ('the '<NUM> application).

Illustrates an embodiment of a basket catheter <NUM> which can be considered to be a 2D array of electrodes distributed over an ellipsoid surface. The basket catheter <NUM> can comprise a catheter body <NUM> coupled to a basket <NUM>. The basket <NUM> can be coupled to the catheter body with a proximal connector <NUM>. The basket <NUM> can comprise a plurality of splines <NUM>, a distal coupler <NUM>, and an irrigation tubing <NUM>. Each of the plurality of splines <NUM> can comprise at least one electrode <NUM>. In the illustrated embodiment, each of the plurality of splines comprises <NUM> electrodes. The exact number of electrodes can be varied based on the desired characteristics. The basket catheter shown in <FIG> is further described in <CIT>.

Current techniques to estimate conduction velocity and the direction of activation generally rely on the precise determination of activation times over precise distances. The techniques to assign times to signal locations can result in predictions that are not accurate under certain conditions. The method below utilizes the fundamental concept of wave propagation and does not rely on LAT (local activation time) detection algorithms. This approach is more robust and consistent. Certain extensions are also described that specialize and enhance the application to <NUM>- and <NUM>-dimensional arrangements of electrodes on cardiac surfaces. With each depolarization, the local electric field vector, E, sweeps out a loop like trajectory governed by anatomic and physiologic factors adjacent to these arrangements of electrodes. Two dimensional electrode arrangements allow the resolution of Et, the "tangent bipole vector", which is a useful orientation independent signal to which wave propagation principles can be applied and can be used to introduce a scalar version of Et along the unit activation direction â, and call it Ea. Three dimensional electrode arrangements allow the resolution of a second equivalent bipole component of E along the surface normal direction denoted n̂ called En. Finally, both <NUM>- and <NUM>-dimensional electrode arrangements allow determination of the E field along the direction ŵ = n̂ × â called Ew which for a wave traveling in direction â is a very small signal.

<FIG> illustrates the unit activation vector <NUM>, wavecrest vector <NUM>, surface normal vector <NUM>, wavefront crest <NUM>, and conduction velocity direction <NUM>. A single depolarization wavefront <NUM> is depicted based on a unipolar traveling wave voltage signal, φ(x,y,z,t). Propagation of the depolarization wavefront <NUM> occurs from left to right in the view. The depolarization wavefront <NUM> does not have to conform to a specific shape for the discussion within this disclosure to be valid, but a benefit can be found from physiologic unipolar morphology.

The catheter orientation independent omnipole signals En and Ea possess characteristic shapes and amplitudes in normal myocardium. This can be further seen in <FIG>. These permit more robust determinations of EP characteristics such as electrogram amplitude, activation timing, and conduction velocity by traditional means.

The next section explains the derivation of the omnipole or "equivalent bipole" signal Ea using a high density catheter such as one of the catheters <NUM>, <NUM>, <NUM> shown in <FIG>. The paddle catheter, basket catheter, or other high density catheter is presumably maneuvered such that some or all adjacent electrodes lie flat on the surface/substrate. For convenience the following will use language indicating all catheter electrodes lie on the surface (i.e. the catheter lies on the surface) but the language refers to those electrodes that do lie on the surface or are sufficiently close to be indistinguishable from those that do.

The E-field (E) in the plane of the surface can be calculated using electrode locations X and the potentials measured at the electrodes φ using the following equations (where dφ and dX have been derived from X, φ, and subtraction matrix F, as described in international application no. <CIT> and published in English on <NUM> November <NUM> under international publication no. <CIT> (the '<NUM> application) and <CIT> ('the '<NUM> application). The information is also further described in international application no. <CIT> (the '<NUM> application) and <CIT> ('the '<NUM> application). The equations have the same form for both 2D and 3D situations: <MAT> <MAT> where.

However, for the 2D case where electrodes lie almost exactly in a single plane, the resulting E-field can be constrained to that plane. This may be done, for example, by fitting a plane to locations X, and by denoting a unit normal vector to this plane as n̂, eliminating any contribution in direction n̂ and thus obtaining Et = E - (E · n̂) n̂.

Illustrates one embodiment of a paddle catheter <NUM> showing <NUM> electrodes and some of the sets of electrodes that can be used to determine Et. In the illustrated embodiment, the paddle catheter <NUM> can comprise four splines with each spline comprising four electrodes. Any 2D electrode set with at least three adjacent non-colinear electrodes forms a clique and can be used for the calculations. A three electrode clique <NUM>, a four electrode clique <NUM>, and a five electrode clique <NUM> is illustrated on the paddle catheter <NUM> in <FIG>. The three electrode clique <NUM> can comprise electrodes D <NUM>, two <NUM>, and five <NUM>. The four electrode clique <NUM> can comprise electrodes six <NUM>, seven <NUM>, ten <NUM>, and eleven <NUM>. The five electrode clique <NUM> can comprise electrodes six <NUM>, nine <NUM>, ten <NUM>, eleven <NUM>, and fourteen <NUM>. As can be seen by the above illustration, the same electrode on the catheter can be used for multiple cliques.

The local E-field at a position on the surface can be calculated from sets of sufficient nearby electrodes (also referred to as a clique) on the catheter as illustrated in <FIG>. As indicated generally by dashed lines in <FIG>, for example, a <NUM>-dimensional clique may comprise a set of three or more electrodes (e.g., electrodes D, <NUM>, <NUM>) located along a plane of the catheter. When only a unipole or bipole is present, the clique can be referred to as a degenerate clique. A degenerate clique is unable to be used to determine orientation independent assessments of directional quantities. A unipole degenerate clique, while orientation independent, has no real directional information. When, for example, more than <NUM> electrodes are used in a clique, the bipolar signals over-determine the 2D field, e.g. Et. In such an instance, where the clique has more electrodes than strictly necessary for its 2D or 3D role, the clique is overdetermined and admits "subcliques. " Subcliques are themselves cliques which may or may not be minimal depending on how overdetermined the original clique was to start with and what subclique is being reviewed. Cliques that are not degenerate allow omnipoles and subcliques allow a unique direct demonstration of orientation independent sensing (OIS) superiority over traditional bipoles. OIS can be uniformly better than bipoles in determining many EP characteristics, including amplitude, timing, conduction velocity direction and magnitude. Although <FIG> only illustrates cliques comprising three (electrodes D, <NUM>, <NUM>) <NUM>, four (electrodes <NUM>, <NUM>, <NUM>, <NUM>) <NUM>, and <NUM> (electrodes <NUM>, <NUM>, <NUM>, <NUM>, <NUM>) <NUM> neighboring electrodes, the method can be extended to other cliques with more electrodes on the catheter. Since the catheter is assumed to lie flat on the substrate, the full 3D vector E at any clique is also expected to have components in the 2D tangent plane of the endocardial or epicardial surface. As a result, the term Et is used to describe the component of the E-field in the tangent plane.

One method of determining the local E field is to choose one electrode from the clique as a reference electrode and determine n-<NUM> bipolar potentials (dφ) and displacements (dX) with respect to the reference electrode. Another method of determining the local E field is to determine all possible distinct bipoles (n*(n-<NUM>)/<NUM>) from the clique's n electrodes to compute dφ and dX. Determining all possible distinct bipoles can lead to a more robust determination of the E-field as it reduces "2nd order" orientation effects that result from the electrode distribution with respect to wavefront.

Let â and ŵ be unit vectors in the tangent plane along the activation and wavefront directions as illustrated in <FIG>. For an ideal, homogenous wavefront, Et is expected to be either parallel or anti-parallel to the activation direction (â) with very little component along the wavefront direction (ŵ). The scalar Ea (also the equivalent bipole or omnipole activation signal) can be defined using the inner or dot product as <MAT> Ea is the equivalent bipolar EGM that would be measured on the cardiac surface if one were to place a pair of bipoles separated by <NUM> along the activation direction. By definition, Ea is catheter and clique orientation independent and hence its morphology and amplitude should purely be a function of the local substrate. By virtue of it being a bipolar signal, it is also expected that it would be largely free of far-field artifacts and can possess a stable isoelectric baseline.

The two signals thus resolved (En and Ea) are significantly independent of each other, opening the possibility of learning more from local EGM signals. The algorithm to determine â from Et will be explained below.

The conduction velocity can be derived from the E-field using traveling wave concepts. The potential is recognized to be a function of space and time. Propagation of a traveling wave with velocity v = (vx, vy, vz) implies that the wave at time t<NUM> matches exactly the wave at a time t<NUM> + t at coordinates x+vxt, y+vyt, and z+vzt. As a result <MAT> for all initial times and locations t<NUM>, x<NUM>, y<NUM>, z<NUM> and for all times t. Taking the total derivative of both sides of the above equation with respect to time leads to <MAT> which we note is equivalent to <MAT> where v is a vector representing cardiac conduction velocity. Recognizing that E = -∇φ and that only the component of E-field in the tangent plane contributes to the inner product, we get <MAT> <MAT> The conduction velocity vector v can then expressed as <MAT>.

The magnitude of conduction velocity, a presumed constant during local depolarization, is recognized to be the ratio of the time derivative to the spatial derivative along the direction of activation in the tangent plane of the potential. It is then expected that under ideal conditions, the morphology of Ea would be similar to that of φ̇ with the only difference being a scale factor which would be the velocity magnitude. The activation direction (â) can be determined to be the direction in the tangent plane that results in the maximum correlation between φ̇(t) and Ea(t). Although the expression (<NUM>) above holds in principle at every time point during local depolarization and location within the clique, when signal levels are sufficiently small or isoelectric, the ratio of φ̇ to Ea cannot be meaningfully determined.

The analysis can be expected to be more robust when the electrodes that form a clique are in good contact with the surface. This can be checked and enforced a priori using some or all of the criteria below. The criteria to check whether a clique is in good contact with the surface can be applied together or separately as determined by the user or process. Automatic application of the first six criteria can form an important component of the disclosure as getting uniform contact of all electrodes is generally difficult for any catheter, particularly so for small basket catheters.

The first criteria looks at the angular deviation between a 3D mapping systems determined surface normal near the clique and the normal to the plane that best fits the electrodes on the clique and determines whether they are below a threshold. The second criteria looks at the angular deviation between the normal corresponding to the clique of interest and the normal corresponding to the neighboring cliques and determines whether they are below a threshold. The third criteria looks at the distance between the electrode locations that form the clique and the surface and determines whether they are below a threshold. In one embodiment, the second criteria further includes ensuring that the local curvature is not above a threshold. The fourth criteria looks at the amplitudes of the unipolar signals obtained from the electrodes on the clique and determines whether they exceed the noise level and are within a typical range. The fifth criteria looks at the morphologies of the unipolar signals obtained from the electrodes on the clique and determines whether they are typical (e.g. modest upstroke followed by a dominant down deflection and fairly prompt return) and reasonably consistent. In another embodiment, an additional criteria can be used by looking at the morphologies of φ̇ to determine whether they are typical and reasonably consistent. Unipolar signals φ(t) can also sufficiently resemble omnipole signal -En(t). The sixth criteria looks at the amplitudes, shapes, and morphologies of Et, and Ea obtained from the clique and determines whether they are typical. Omnipole signal Ea(t) can sufficiently resemble φ̇(t). The seventh criteria looks at the visual cues for good contact such as fluoro, ICE, etc. as well as tactile sensations and maneuvering history on the part of a catheter operator. While seven criteria are listed herein to check whether a clique is in good contact with the surface, not all seven of the criteria listed have to be used to make that determination. Further, other criteria can also be used to determine whether a clique has made good contact with a surface.

Conduction velocity once derived can be displayed with a 3D mapping system on the chamber geometry using, for example, arrows, with the direction of the arrow indicating the activation direction and the color, length, or width of the arrow showing the magnitude. In another embodiment an interpolated color map can also be used to display conduction velocity magnitude with or without arrows of uniform length showing the direction. In another embodiment, conduction velocity vector maps can also be coupled with voltage amplitude or LAT maps. Generally, the display is updated immediately following each local depolarization and persisting or gradually fading out until the next local depolarization. Finally, some or all isochrones may be displayed as curved lines on the cardiac surface, for instance at specific intervals since the start of depolarization such as <NUM>, <NUM>, <NUM>, and <NUM>. This reduces visual clutter and allows a more interpretable superposition of conduction velocity arrows. In another embodiment, some or all isochrones may be displayed as curved lines on the cardiac surface, for instance at specific intervals since the start of depolarization such as <NUM>, <NUM>, <NUM>, and <NUM>.

As can be readily appreciated from equations <NUM> and <NUM> listed above, it is important to have reasonably accurate electrode displacements (dX) and electrode positions (X) to judge contact and the local surface tangent plane so as to portray the signals and resulting EP characteristics including conduction velocity accurately. It has been suggested that impedance based mapping system locations are more robustly determined from tip or circumferential ring electrodes than from small surface area electrodes on portions of a catheter shaft. Nevertheless, the issue can remain significant in catheter designs with small ring electrodes on flexible splines. Small electrodes, owing to their high electrode-electrolyte impedance can be difficult to locate accurately-they are more susceptible to artifact and can be biased toward the system reference "belly patch" electrode. Compensation algorithms can be used to correct for the positions. However, they rely on a priori knowledge of the construction and inter-electrode distances. Flexible splines can deform, bunch up, or become separated (splayed) in vivo under certain conditions resulting in important deviations from their nominal design. When that happens, the compensation algorithms referred to above may not be able to effectively correct electrode location errors. Means to prevent the deformations, bunching, and separation of catheter splines and electrodes from becoming severe enough to significantly disturb assessments of EP characteristics are also disclosed above in relation to <FIG>.

<FIG> illustrates a flowchart showing a step-by-step approach to acquire, determine, and output orientation independent information. The method illustrated in the flowchart can comprise the following steps:.

At step <NUM> acquire electrophysiology signals from a plurality of electrodes.

At step <NUM> determine the location of the plurality of electrodes in step <NUM>.

At step <NUM> determine whether the plurality of electrodes are on or near the target surface.

At step <NUM> form cliques from the electrodes that fit within defined characteristics for inclusion in cliques.

At step <NUM> process the electrophysiology signals to determine En, Ea, Et, conduction velocity, and other orientation independent characteristics such as amplitude or timing.

At step <NUM> output the derived information to a display.

Helical basket catheters have been proposed as a means to achieve more uniform coverage of electrodes over the extent of a basket. This can be a desirable characteristic for this disclosure on its own, but also for the increased stiffness (and thus resistance to displacement) that results. Increased stiffness can allow for reliance on the spacing as determined by design and manufacturing rather than the mapping system location for each electrode.

<FIG> illustrates a helical catheter design of a catheter <NUM> with non-uniform electrode spacing along splines but achieves a nearly uniform electrode dispersal over the outer surface of the basket. Each point <NUM> in the figure represents an electrode. The catheter illustrated in <FIG> is further described in <CIT>, (the '<NUM> application).

Beam buckling theory suggests compliance goes as the length dimension squared so half the length translates to <NUM> times stiffer. With small size, then, come the benefits of: (a) interelectrode spacing more consistent under varying use conditions, (b) more dense sampling and thus better spatial resolution, and (c) the capacity to be maneuvered into full contact positions and orientations.

As discussed earlier, conventional mapping techniques suffer from bipole orientation induced amplitude and morphology uncertainty which also adversely affects activation timing. Challenging arrhythmias in clinical EP today may involve features such as channels with low amplitudes and slow conduction that are only of the order of <NUM> in width. Detailed maps are often not required over an entire cardiac chamber but confined to certain locations where pathology often appears or other diagnostic tests such as surface ECGs, ultrasound, MRI, or even basic EP catheter signals indicate. What is important is that the information reliably reflect the state of the myocardium locally and that it do so with adequate resolution.

The algorithm discussed in the invention can be used to derive local E-fields (including E and Et), and equivalent bipolar signals (En and Ea) with orientation independent amplitudes and reliable morphology/timing, and instantaneous conduction velocity vectors. Such characterization can permit improved maps of substrate amplitude (using En, Ea, or measures of E or Et loop size such as maximal dimension also known as Espan), activation times (LAT), conduction velocity (magnitude and direction), as well as an index of inhomogeneous conduction derived from Ew or the eccentricity of Et. Bipolar-like omnipole signals of consistent morphology may be understood from the fundamentals of cell depolarization and unipolar EGM signals when in proximity to active tissue.

One or more of these characteristics can also enable clinicians to perform more reliable scar border delineation (known to contribute to VT and other arrhythmias). Also, local determinations of low amplitude and/or slow conduction velocity can help identify critical pathways such as isthmuses for arrhythmias that are amenable to ablation therapy. More reliable EGM amplitudes and morphologies can also allow better measures of EGM reduction measures, lesion characterization, or the local assessment of conduction velocity as a critical isthmus is affected or a lesion gap approached.

OIS technology can also be utilized with implanted medical devices. Implanted medical devices responsible for rhythm discrimination currently rely primarily on depolarization event timing. Timing alone however can fail to distinguish between important rhythms as the times of occurrence can be similar, and multi-chamber algorithms are not sufficiently specific. The application of OIS to an implanted device's catheter or lead can establish a baseline direction and speed (using OIS characterizations) for healthy rhythms.

Implanted devices already perform elementary mapping system functions, but with OIS technology as discussed herein, can better track the number and degree of abnormality of beats and can group them by similarity in detection criteria. For example, a non-physiologic heart rate increase typically would cause the conduction velocity to decrease, while a physiologic cause for heart rate increase, like exercise, would not result in a decrease in conduction velocity. Hence the decision to treat this tachycardia can be based not only on changes in heart rate and other traditional ICD metrics such as timing but based on noting the conduction velocity vector's direction and magnitude are consistent with a VT. Some of the detection criteria that can be used by the implanted device can include combinations of rate, number consecutive abnormal beats, frequency "x of y beats", etc..

Observations from one or more sites on implanted leads can also be used to track rate or ischemia induced functional block occurrences with greater accuracy than inferences drawn from timing changes. This in turn can enable patient or health care provider alerts to potential problems with brady or tachy arrhythmias before deciding on treatments with pacing or cardioversion shocks.

<FIG> illustrates a paddle catheter <NUM> and the cliques used for the computations discussed herein. The paddle catheter <NUM> can comprise a first spline <NUM>, a second spline <NUM>, a third spline <NUM>, and a fourth spline <NUM>. Each of the splines can comprise four electrodes. For the purpose of validation, cliques comprising four electrodes (two from each pair of adjacent splines as seen in <FIG> can be used. In some instances some of the rectangular cliques can be considered to not be in contact with the cardiac surface.

The determination of whether a clique can be considered to be in contact with the cardiac surface can be accomplished in a variety of ways. There are a variety of methods that can be used to determine whether a high quality OIS signal is present.

In one method, the peak-to-peak amplitude ratio of Ew/Espan can be used. A low ratio of the peak-to-peak amplitudes of Ew/Espan can lead to a finding of a high quality OIS signal. Ew is the signal that remains when En and Ea are accounted for and, for an ideal homogeneous wavefront traveling linearly with ideal OIS coordinates should be zero. Espan is a term to describe what is the peak-to-peak equivalent amplitude for the entire E field loop. Espan is the maximum over all of the depolarization's E field point pairs of |Ei - Ej| at time points i and j. Importantly, it does not require ideal wavefronts or coordinates and will be greater than or equal to Ea peak-to-peak and En peak-to-peak.

In another method, the cross correlation lags between Ea and φ̇ can be used. A low cross correlation lag between Ea and φ̇ can lead to a finding of a high quality OIS signal. In one embodiment, a low cross correlation lag can be defined as typically less than <NUM> for a catheter designs with <NUM>-<NUM> between electrodes. In other embodiments, a different value can be used to define a low cross correlation lag. In another method, the conduction velocity can be used to determine the OIS signal quality. A physiologically plausible conduction velocity determination can be used to determine the signal quality at a given location. In one embodiment, a conduction velocity of healthy tissue can be set in the range of <NUM>-<NUM>/ms and the conduction velocity in or near scar tissue can be set in the range of <NUM>-<NUM>/ms. In yet other embodiments other velocities can be used by the system to determine the quality of any OIS signals. A user of the system can further set a different value for the system to use to determine a signal quality.

In yet another method, the amplitude of a unipolar signal can be used. In on embodiment, a unipolar signal amplitude can be determined to be adequate to give a quality OIS signal can be set as <NUM>-<NUM> mV in healthy tissue. In another method, the unipolar morphology can be used to determine the quality of an OIS signal. A plausible unipolar morphology can be determined by looking for a unipolar morphology that comprises a main portion that either contains a small to moderate sized upward deflection followed by a moderate to large downward deflection or a unipolar morphology that comprises a moderate to large downward one. In another method, the cross correlation between clique unipoles can be used. A good maximal cross correlation between clique unipoles can suggest that the clique unipoles reflect a locally homogeneous assessment of conduction.

In yet another method, a unipolar temporal dispersion over the clique can be used to determine a high quality OIS signal. A unipolar temporal dispersion over the clique, in the range of <NUM>-<NUM> for a catheter design with <NUM>-<NUM> between electrodes can show a high quality OIS signal. The unipolar temporal dispersion may be determined by conventional dV/dt threshold crossing techniques or by maximal cross correlations. In another method, the derived OIS omnipole signals can be compared to idealized En and Ea signals. The closer the OIS signal is to the idealized values, the better the OIS signal. A comparative value can be set within the system or can be set by a user to state the amount of resemblance desired to determine whether a high quality OIS signal is present. In another method, the loop-derived n̂ can be compared to the surface normal from an electroanatomical mapping system. In one embodiment, a good match between a NavX mapping system determined n̂ direction and a loop derived n̂ direction can show a high quality OIS signal. The NavX mapping system can determine an n̂ direction from surface shape and catheter clique electrode locations. In yet another embodiment, electrogram signals with isoelectric intervals can be used to determine whether a high quality OIS signal is present. An isoelectric interval with no baseline drift and no large offset over an OIS analysis interval can be used to determine a high quality OIS signal. In one embodiment the OIS analysis interval can comprise <NUM>-<NUM>. In other embodiments, the OIS analysis interval can be longer or shorter or of an interval chosen by a user of the system.

There are also a variety of methods that can be used to determine whether a poor quality OIS signal is present. In one method, the magnitude of the conduction velocity can be used to determine whether a poor quality OIS signal is present. If the conduction velocity magnitudes are larger than would otherwise be expected the system or user can determine that poor quality OIS signals are present. Abnormally large conduction velocity magnitudes can be caused by far field signals since these can often produce very small peak-to-peak Ea values. In one embodiment, if the conduction velocity magnitude is greater than <NUM>-<NUM>/ms a poor quality OIS signal can be determined. In other embodiments other values for excessively large conduction velocity magnitudes can be used. In another method, a unipolar EGM signal can be analyzed to determine whether a poor quality OIS signal is present. A unipolar EGM signal that shows a prominent positive deflection persisting for <NUM>-<NUM> or more ms following depolarization can indicate an injury current component to the unipolar EGM signals. In another method, a saturation of one or more EGM channels can reflect pacing polarization and amplifier recovery. This can also lead to a finding of a poor quality OIS signal.

In yet another embodiment, several different methods can be used to determine whether far field artifact could be causing low quality indices. The methods to determine whether far field artifact is causing low quality indices could include one or more of: "beats" where the tentative detections on all unipolar clique electrodes are virtually simultaneous; if the timing of En and/or Ea in the atria is sufficiently close to that of the surface QRS and thus suggests a probable ventricular unipolar artifact; and at least one small E-field loop. A small E-field loop can be caused by far field signals that result in E-field loops with very small Espan. According to the invention, when the Espan value is less than <NUM> mV/mm the system determines that far field artifact is causing low quality indices.

<FIG> shows the loop trajectory of vector Et <NUM> in the tangent plane over <NUM> of the cardiac cycle when the catheter clique electrodes see atrial depolarization action. If the wavefront passes the clique electrodes progressing uniformly in a homogeneous medium (as seen in <FIG>), then vector Et <NUM> should comprise voltage swings along a dominant axis aligned with the activation direction. The activation direction, calculated using the method described in the previous section is shown using the arrow. The plot shows the trajectory of vector Et <NUM> over a single beat. The tail of the vector is anchored at the isoelectric origin and the plurality of dots <NUM> indicate the path of the head of the E field vector. The vector sweeps a loop around the origin with maximum and minimum excursions along the activation direction (indicated with the arrow).

<FIG> shows the EGM's, their time derivative φ̇ (phi-dot) and the "equivalent bipole" Ea plotted as a function of time for two beats. Note that the morphology and amplitude of the signal is consistent from one beat to the other and that the far-field ventricular signal that we see in the unipolar EGM's is largely absent. The exemplary Ea has a negative deflection followed by a prominent sharp positive deflection. Also, its amplitude is expected to be solely a function of the substrate that is being investigated (and not catheter or bipole orientation). <FIG> shows the stylized shape of an exemplary Ea with a negative deflection followed by a sharp positive deflection.

Due to various factors that contribute to non-ideal conditions, including finite spatial separation of electrodes, the morphologies of φ̇ and Ea do not match exactly but they are very close to proportional. As a result the ratio (velocity magnitude in ideal conditions) is not uniform over the time interval of the beat. Also, when one or both of φ̇ and Ea of Equation <NUM> approaches zero, the algorithm fails to produce meaningful results. Under ideal conditions, φ̇ and Ea would tend to zero at the same instant in time and in the limit when they both tend to zero the ratio could be meaningfully evaluated to be the conduction velocity magnitude. In practice zero crossings of the denominator and numerator play havoc with this ratio.

The practical limitations can be overcome by realizing that a classic unipolar signal recorded at an electrode includes contributions from depolarizing tissue upstream and downstream of the electrode location. The information about depolarizing tissue immediately under the electrode is contained within the region of maximal -dv/dt, peak negative deflection, and the immediate up stroke following the unipolar peak negative. This corresponds to the region contained within the peak negative and the subsequent positive peak in φ̇ and Ea. This region can be seen as time interval <NUM> in <FIG>. Conduction velocity is calculated using information from the signals within this region.

Listed below are some practical ways to calculate the velocity of activation or propagation. One way is to calculate the velocity as the ratio of the peak-to-peak values of φ̇ and Ea. The conduction velocity estimations shown in this section have been evaluated using this method. An equivalent mathematical way to represent a ratio of peak-to-peak values is shown with definite integrals below.

In another embodiment the conduction velocity can be calculated by applying different weights to the information contained within the interval (ta < t' < tb) as follows <MAT> where w(t) is a weighting function. The weighting function can be used to ensure that more importance is given to certain regions within the time interval as shown in <FIG> and discussed below.

<FIG> illustrates a plot showing the time interval (from a to b) <NUM> that holds the most information about depolarizing tissue under a particular clique of electrodes. This generally corresponds to times around when the unipolar voltage is most negative which is when the inward current of depolarization is maximum under the electrodes of the clique. This introduces a practical and improved means to derive velocity from local φ̇ and Ea signals.

<FIG> depicts a weighting function w vs. time. W <NUM> is shown between time ta <NUM> and time tb <NUM>. In this illustration w is chosen to ensure more importance is given to the region corresponding to the zero-crossing of Ea following its pk-neg.

In some embodiments, determining the activation direction from the E field loop data can be overly sensitive to data taken when the loop is small and nearly isoelectric. OIS signals and derived quantities may reflect artifacts due to filtering, offsets, far field effects, or waveform complexity when good information also exists. The artifacts can be minimized by weighting the loop points in calculations, including activation direction cross correlation, not equally by time, but proportional to, or as a monotonic function of, |E(t)| or |d/dt(E(t))| as seen in <FIG>. This can ensure that the E field data points that lie close to the origin or are changing slower than the depolarization, as seen in <FIG>, are given less weight. Only the major deflections, which provide the necessary and key information about the underlying substrate, are then used for deriving OIS quantities, including the OIS coordinate frame (n̂, â, ŵ) and omnipole signals En and Ea. This can concentrate OIS results on the information containing part of the loop when the E field changes rapidly. This weighting can further be used in deriving OIS coordinate directions entirely from the E field loop, which could also lead to more accurate determination of En peak-to-peak, Ea peak-to-peak, and conduction velocity magnitude. In another embodiment, when d/dt(Et) is determined to be too high, this can be due to artifacts and can be used in addition to the set of OIS quality criteria discussed above.

<FIG> illustrates an E-field loop showing regions of large and small |d/dt(E(t))|. The points <NUM> are EGM derived E-field points equally spaced in time. As discussed above, closely spaced points contain little information and contain artifacts that can affect OIS derived signals and EP characteristics. The area around the origin <NUM> has a small |d/dt(E(t))|, while the area with a large |d/dt(E(t))| <NUM> corresponds to strong EGM signal amplitudes and deflections. The area with a large |d/dt(E(t))| is of more interest. As a result, in one embodiment, those areas with a small |d/dt(E(t))| can be removed or deemphasized.

In another embodiment, the loop points can also be weighted based on the magnitude of the E-field (norm(E) or |E|) which is the distance from the isoelectric origin.

<FIG> show the tangent E-field loop points before and after weighting based on the method described herein. <FIG> illustrates the tangent E-field loop <NUM> before weighting. <FIG> illustrates the tangent E-field loop <NUM> after weighting the loop points <NUM> based on the norm of the E-field. As can be seen in the comparison of <FIG>, the part of the loop that contains the most useful EP information is accentuated and hence more meaningful OIS characteristics can be obtained from the weighted loop.

<FIG> show the magnitude of conduction velocity estimated for successive beats on the RA septal wall for two different square cliques. <FIG> shows the magnitude of the conduction velocity for clique <NUM> and <FIG> shows the magnitude of the conduction velocity for clique <NUM>. The velocity magnitude was estimated by taking the ratio of the peak-to-peak values of φ̇ and Ea. The beat-to-beat variation in conduction velocity magnitude is minimal and the values of around <NUM>/ms are roughly what was expected. Conduction velocity magnitude and activation direction (unit vector) estimated for successive beats from the two adjacent cliques were as follows.

The activation direction and velocity calculated were similar and consistent with expected results in atrial tissue.

A split tip OIS catheter is also suitable for bipolar pacing in a manner that is much more tip localized than the conventional D-<NUM> bipolar pacing and free of the concern over variable locational of capture (and variable thresholds) that can occur when the ring (and not the tip) captures myocardium. This is a great advantage when, for example, pacing is being done to establish lesion efficacy. The alternative, unipolar pacing, involves a distant electrode and thus is responsible for a large pacing artifact that complicates use of pacing for assessing blocks. The basic idea is that pacing is accomplished by assigning alternating polarities to the four tip electrodes. This may be accomplished by circuit elements such that the four electrograms and mapping system positions remain distinct and yet the tip appears as a "crossed bipole" from the standpoint of pacing. Alternatively this may be done by employing the stimulator, devoting two simultaneous channels to the four electrodes.

With each local depolarization, a new conduction velocity vector may be generated. The system can be configured to display various information including oriented arrow icons, Matlab quiver-like plots, and ripple maps. The system can further have the option to control the persistence of these direction and/or magnitude renderings. In one embodiment, the default process is to update immediately with each new local depolarization (that meets criteria for a depolarization).

Updates that visually replace prior visual assessments are sometimes preferred over cumulative multi-beat maps because if there is only modest movement of the catheter between repeated similar beats, the map will become cluttered with such representations. As a result, it can be beneficial to include a spatial density criterion (like that currently available with traditional mapping systems). New representation points would be added if none are within say <NUM> of previous points (and from the same mapped rhythm if that is distinguished). If old points lie within <NUM> of a new point, the new points can delete or hide old points. Particularly when playing back recorded segments and focus is on a region of interest where a multi-electrode mapping catheter is, the system can hide/delete prior representations at points in favor of the most recent cardiac cycle's representation since play back began.

In another embodiment, a variable persistence can be given to the point representations based on, a given number of milliseconds duration and observed during slow playback. The visual representations at points can come into existence and disappear in a manner that (similar to a propagation map available on the EnSite Velocity mapping system) suggests the wavefront itself (a region of typically <NUM>-<NUM> or so wide that encompasses the <NUM>-<NUM> or so of primary depolarization current and EGM generation). This can benefit the system by removing clutter and focusing attention on immediate events.

Transmural RF ablation possesses certain EGM characteristics which are exploitable by an orientation independent, OIS catheter electrode design and software. In particular, the unipolar signal (which to a first approximation is just a polarity inverted En signal) may change from an rS pattern preablation to an r' pattern afterward. As a result, En can change from a nice dominant upward deflection to a smaller downward deflection, perhaps a downward deflection that was present previously, but now appears minor in comparison with the upward deflection. This can reflect the fact that activation no longer propagates through the electrode clique but halts as it approaches.

While some implementations require a surface normal direction, n̂, to be supplied by a 3D mapping system's surface geometry model (based on the nearest surface point to a clique) this implementation can be less reliable in some circumstances. In one instance, using data from a 3D mapping system's surface geometry model can be less reliable when a cardiac surface curvature is high and thus imperfect surface models and small clique position errors can strongly influence the resulting n̂. The E field loop and traveling wave approach of OIS, however, can be used to generate n̂ and the other two OIS coordinates, â and ŵ, from EGMs alone. As a result, a live surface normal display can be determined. Such a surface normal can be a valuable reflection of catheter contact and wall distension and can even provide more detailed surface geometry models in the face of highly curved structures and respiratory or cardiac motion artifacts.

<FIG> is a flow diagram outlining the steps for obtaining an OIS coordinate frame.

Step <NUM> comprises determining the local 3D electric field loop in the body or mapping system's coordinate frame. This step comprises having one or more electrode cliques on the cardiac surface and using a 3D mapping system to provide positions of electrodes comprising the clique and unipolar voltages obtained from the electrodes. From this information the 3D electric field loop can be determined.

Step <NUM> comprises matched filtering of all unipolar signals, catheter bipoles, and the resulting 3D E field loop. In another embodiment, for the purpose of OIS coordinate frame determinations and conduction velocity and activation direction, low or band pass filtering can be employed to create a more elliptical E field loop and thereby allow more consistent OIS coordinates as well as conduction velocity and activation direction determinations. Band pass filtering of <NUM>-<NUM> can provide robust estimates of OIS coordinates, conduction velocity, and activation direction. In yet another embodiment, wideband filtering of E(t), e.g. <NUM>-<NUM>, can be maintained for generating OIS signals En, Ea, and Ew by the inner product of E(t) with n̂, â, and ŵ respectively to preserve EGM detail. In other embodiments, the filtering in step <NUM> can be performed in a different order than that shown in <FIG>.

After step <NUM>, there are two possible methods for determining â, n̂, and ŵ. If the system or user desires to first use ŵ then proceed to step <NUM>. If the system or user desires to use â and n̂ first, then proceed to step <NUM>.

Step <NUM> comprises creating a zero mean version of E(t) over the depolarization interval.

Step <NUM> comprises computing at each time point Ė = dE/dt(t).

Step <NUM> comprises computing an initial estimate of ŵ from the cross product of E and Ė at each time point.

Step <NUM> comprises averaging or weighted averaging the initial ŵ estimates over the depolarization interval for a best estimate of ŵ.

After ŵ has been estimated from step <NUM>, the method next performs a <NUM>-D search over angles θ for â and n̂ since â and n̂ have a proscribed <NUM> degree relationship to each other and both are perpendicular to ŵ. Only a half circle, θ(<NUM>-<NUM> degrees), has to be searched as opposing directions will yield the negative in terms of match scores. A search can be performed on a suitably defined grid spacing. In one embodiment, every <NUM>-<NUM> degrees, for a total of only <NUM>-<NUM> evaluations. In other embodiments, other grid spacing can be defined by the system or user. Iterative search techniques may also be used but care can be taken to avoid local minima.

Step <NUM> comprises choosing the corresponding n̂ from the cross product â(θ) × ŵ(θ) for every â(θ).

Step <NUM> comprises computing a composite match score for how well φ̇ matches Ea(θ) = E · â(θ) (using an inner product) and how well - φ matches En(θ) = E · n̂(θ) having determined n̂ from above.

Step <NUM> comprises choosing the best θ and thus the best â and n̂ from the previous steps.

In another embodiment, the method can skip computing Ė from step <NUM> and can instead perform a single cross product from a time point i with a sizable |E(ti)|. This can be performed by letting A(t) = E(t) - mean(E(t)) be a zero mean version of the 3D E field trajectory. If A is assumed to be a 3xn matrix, form (<NUM>/n)*A*AT (this is a 3x3 positive definite covariance matrix). The SVD of this will yield singular values and vectors. The vector associated with the least singular value is ŵ (plus or minus a sign). Then check the loop's direction. The positive direction of ŵ "goes with the thumb using the right hand rule on the loop" and using the vector cross product between A(ti) and A(ti+<NUM>)-A(ti), ŵ's direction may be determined.

In another embodiment, the cross product or angular momentum can be used to determine ŵ. Let A(t) = E(t) - mean(E(t)). Over the loop points, compute the average cross product over the n time points A × Ȧ from the point-wise in time cross product of A(ti) with its time derivative Ȧ(ti). Positive ŵ will be a normalized version of this vector. In another embodiment, the loop points can be weighted as discussed above and the average cross product computed as just described.

If the system or user desires to use â and n̂ first, the method proceeds from step <NUM> to step <NUM> and conducts either a <NUM> degree of freedom search to jointly solve for â and n̂ or begins with a 2D search over angles θ and ψ for either â or n̂. Only a hemisphere needs to be searched as opposing directions will yield the negative in terms of match scores. The search can be conducted on a defined grid spacing. Although increments of <NUM>-<NUM> degrees on latitude and longitude can work, this can lead to inefficient results as near the hemisphere's pole evaluations are much closer than <NUM>-<NUM> degrees. In one embodiment, a method employing some <NUM>-<NUM> fold fewer grid points can be used. Briefly, this uses an approximate solution to what is known as the Thompson Problem - distributing points evenly on a sphere. The approximate solution constructs lines of latitude, choosing points on successive lines rotated by π(<NUM> - φ-<NUM>) radians where φ≅<NUM>. This method is more fully described in the '<NUM> application. Having determined â or n̂, the other may be found with a 1D semicircular search. Iterative search techniques can also be used but care taken to avoid local minima.

Step <NUM> comprises computing a composite match score for both how well φ̇ matches the inner product of E and â and - φ matches the inner product of E and n̂.

Step <NUM> comprises choosing the best pair of â and n̂.

Step <NUM> comprises determining ŵ by the right hand rule and cross product ŵ = n̂ × â.

In other embodiments, the method or system can proceed down both paths simultaneously and compare those results to determine the better fit. Whether proceeding down the path of using ŵ first, using n̂ and â first, or using both combined, the method then proceeds to step <NUM> to determine the standard final OIS information.

Step <NUM> comprises using the inner product of OIS coordinate directions with E field to compute the OIS omnipole signals En, Ea, and Ew. As discussed above, in one embodiment, the E-field from which omnipole signals are derived can be wide band filtered once the OIS coordinate frame has been determined from a low pass filtered E-field.

Step <NUM> comprises computing amplitudes from the omnipole signals. In one embodiment, the amplitudes are denoted Vpp for peak-to-peak voltage and local activation timing denoted LAT.

Step <NUM> comprises computing the conduction velocity vector v which consists of the conduction velocity magnitude or speed (from the omnipole signals) times the activation direction â.

<FIG> illustrates an example of an E-field loop <NUM> and OIS coordinates. The 3D mapping system supplied a surface normal n̂ <NUM>. The traditionally derived â <NUM> and traditionally derived ŵ <NUM> are determined by a process similar to that described in step <NUM>. A loop derived OIS coordinate direction n̂ <NUM>, a loop derived OIS coordinate direction â <NUM>, and a loop derived OIS coordinate direction ŵ <NUM> are also shown in <FIG>. In the illustrated embodiment, only minor readjustments were made to the coordinate frame. This minor adjustment reflects a high quality system supplied n̂.

A loop derived surface normal, n̂, opens up a number of potentially useful applications relating to cardiac EP mapping. One of the applications is assessing the adequacy of the existing local surface geometry model. A discrepancy between the derived information and the existing local surface geometry model can suggest additional geometry model acquisition is needed or in one embodiment can be automatically triggered. Another application is detecting a catheter force related surface distension. The catheter force related surface distension can be useful in the absence of a force sensor and can also be useful to suggest that the underlying geometry model has been temporarily altered. Another application of a loop derived surface normal is assessing the adequacy of local surface contact. Assessing the adequacy of local surface contact can benefit ablation formation and can also be used to reflect respiration and cardiac related motions that may not be well rendered by an existing 3D mapping system. Another application is allowing for a more robust surface geometry modeling in areas of highly curved cardiac structures and respiratory motion where other respiratory compensation may not always be effective at suppressing artifact and positional uncertainty. The above method can allow a user or system to recognize the situations described as the method responds in meaningful and reproducible ways as an OIS capable catheter is maneuvered throughout a vasculature or other body cavity or organ.

<FIG> illustrate the application described above of detecting a catheter force related surface distension through a determination of the surface normal, n̂. n̂ is of interest itself to help with catheter positioning and to indicate the adequacy of a 3D mapping system surface geometry. It may also provide a real-time assessment of catheter force related distention of the endocardial or epicardial surface. This can be of particular use in the atria. <FIG> illustrates a catheter <NUM> placed at an initial contact point <NUM> of a myocardial wall <NUM>. The catheter <NUM> is illustrated making contact with the myocardial wall <NUM>, but not significantly distorting the shape of the myocardial wall <NUM>. As a result, the surface normal <NUM> from both loop based means described above, and a 3D mapping system agree and are shown as n̂. <FIG> illustrates the catheter <NUM> being deflected and pushed into the myocardial wall <NUM>. The catheter <NUM> is distending the endocardial surface from the original myocardial wall location <NUM> to a distended myocardial wall location <NUM>. The 3D mapping system supplies surface normal <NUM> is the same as in <FIG>. The catheter clique's center however is now more accurately placed at a location between the initial contact point <NUM> and a second myocardial wall point <NUM>. A proper surface normal <NUM>, as determined through the above loop based method, is shown. By determining and using the proper surface normal <NUM> the system enables OIS signals En, Ea, and Ew to be correctly resolved and thus the other results at the bottom of <FIG> can be correctly obtained. Further, the discrepancy between 3D mapping system supplied surface normal <NUM> and the proper surface normal <NUM> indicates an important surface distension. This surface distension can be undetectable using a standard 3D mapping system and can also often be unrecognizable on fluoro because of view angles, contrast, and shapes present in the fluoro system. Further, this can give a live n̂ display a potential role in lesion monitoring. A live display responding to force and local distension/deformation of the atrial wall can be used to enhance RF lesion quality if observed characteristic responses are seen in response to variations in tip deflection. One such characteristic can be a good degree of contact with the surface targeted for ablation. Surface normal information can inform a user of adequate contact and thus help to provide a sufficiently complete map geometry as well as static multi-beat maps. As geometries may change during a procedure for real or artifact reasons, a recent discrepancy between an OIS loop derived n̂ and an n̂ from surface proximity could trigger a geometry and mapping update.

Various embodiments are described herein to various apparatuses, systems, and/or methods. Numerous specific details are set forth to provide a thorough understanding of the overall structure, function, manufacture, and use of the embodiments as described in the specification and illustrated in the accompanying drawings. It will be understood by those skilled in the art, however, that the embodiments may be practiced without such specific details. In other instances, well-known operations, components, and elements have not been described in detail so as not to obscure the embodiments described in the specification. Those of ordinary skill in the art will understand that the embodiments described and illustrated herein are non-limiting examples, and thus it can be appreciated that the specific structural and functional details disclosed herein may be representative and do not necessarily limit the scope of the invention, the scope of which is defined solely by the appended claims.

Reference throughout the specification to "various embodiments," "some embodiments," "one embodiment," or "an embodiment", or the like, means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment. Thus, appearances of the phrases "in various embodiments," "in some embodiments," "in one embodiment," or "in an embodiment", or the like, in places throughout the specification are not necessarily all referring to the same embodiment. Thus, the particular features, structures, or characteristics illustrated or described in connection with one embodiment may be combined, in whole or in part, with the features structures, or characteristics of one or more other embodiments without limitation given that such combination is not illogical or non-functional.

Claim 1:
A system for analyzing signal quality of a plurality of electrodes in contact with a surface of a heart, the system comprising:
an electronic control unit (<NUM>) configured to:
acquire electrophysiology signals from the plurality of electrodes;
process the electrophysiology signals to derive a plurality of orientation independent local E field data points associated with the plurality of electrodes; and
analyze the E field data points associated with the plurality of electrodes to determine whether a far field artifact is causing low quality indices of the electrophysiology signals when an Espan value is less than <NUM> mV/mm, wherein the Espan value is a maximum dimension |Ei - Ej| over all pairs of the local E field data points at time points i and j.