System and method for mapping electrophysiology information onto complex geometry

BACKGROUND OF THE INVENTION

1. Field of the Invention

0001The instant invention relates to an electrophysiology apparatus and method used to measure electrical activity occurring in a portion of tissue of a patient and to visualize the electrical activity and/or information related to the electrical activity. In particular, the instant invention relates to three-dimensional mapping of the electrical activity and/or the information related to the electrical activity.

2. Background Art

0002The present invention relates to the creation of electrophysiological maps of the human anatomy, including for example, an electrophysiology map of the human heart.

0003Conventional modeling systems exist for generating a three-dimensional model of the heart utilizing technology such as CT scan, MRI, radar imaging, x-ray imaging, and fluoroscopic imaging. Such data is often processed using a three-dimensional modelling technique. Such imaging technology is often useful in preparing a patient for treatment and/or surgery, and typically, the imaging process is performed hours and in some cases days in advance of the treatment and/or surgery.

0004During the treatment and/or surgery, conventional systems are available that can generate an electrophysiology map for the patient. An electrophysiology map is especially useful in connection with the diagnosis and treatment of atrial fibrillation of a patient's heart. The points at which the electrophysiology data is measured, however, rarely correspond to the data points that define the three-dimensional model prepared in advance of the treatment.

0005Accordingly, a need exists for an improvement that can relate electrophysiology data to a three-dimensional surface model of a patient's anatomy.

0006<patcit id="pcit0001" dnum="US5687737A"><text>US 5,687,737</text></patcit> discloses an electrophysiologic mapping system for map directed arrhythmia surgery and cardiac research. The system can display activation or potential distribution data on an anatomically accurate 3-D model of the heart. The 3-D model of the heart is based on a preliminary excised heart from a dog, a human cadaver, or any other desired species.

0007The abstract "<nplcit id="ncit0001" npl-type="b"><text>Three-dimensional reconstruction of the left ventricle based on the Delaunay triangulation", by N. Souag, Signal Processing and Information Technology, 2004. Proceedings of the fourth IEEE International Symposium, Rome, Italy, December 18-21, 2004, Piscataway, NJ, USA; IEEE, 18 December 2204, pages 539 to 542</text></nplcit> discloses the development of software for three-dimensional reconstruction of the Left Ventricle from two-dimensional echographic images.

0008<nplcit id="ncit0002" npl-type="b"><text>Kuklik P. at al "The reconstruction, from a set of points, and analysis of the interior surface of the heart chamber", Physiological Measurements, Institute of Physics Publishing, Bristol, GB, volume 25, No. 3,1 June 2004, pages 617 to 627</text></nplcit>, discloses a method of reconstruction of the left ventricle of the heart from a measured set of data points and performing an interpolation of the measured voltages over the reconstructed surface. Further, regions are detected with voltage in a specified range and their areas and circumferences are computed. This allows finding geometries of damaged muscle areas, for example.

0009<nplcit id="ncit0003" npl-type="b"><text>SIMPSON E V ET AL: "Three-dimensional visualization of electrical variables in the ventriclar wall of the heart", PROCEEDINGS OF THE FIRST CONFERENCE ON VISUALIZATION IN BIOMEDICAL COMPUTING (CAT. NO. 90TH0311-1) IEEE COMPUT. SOC. PRESS LOS ALAMITOS, CA, USA, 22 May 1990 (1990-05-22), pages 190-194, XP010019012, DOI: 10.1109/VBC.1990.109320, ISBN: 978-0-8186-2039-3</text></nplcit>, relates to three-dimensional visualization of electrical variables in the ventricular wall of the heart.

0010<nplcit id="ncit0004" npl-type="b"><text>SUBHAM GHOSH ET AL: "Accuracy of Quadratic Versus Linear Interpolation in Non invasive Electrocardiographic Imaging (ECGI)", ANNALS OF BIOMEDICAL ENGINEERING, KLUWER, ACADEMIC PUBLISHERS-PLENUM PUBLISHERS,NE, vol. 33, no. 9, 1 September 2005 (2005-09-01), pages 1187-1201, XP019273014, ISSN: 1573-9686</text></nplcit> relates to the accuracy of quadratic versus linear interpolation in non-invasive electrocardiographic imaging.

0011<nplcit id="ncit0005" npl-type="s"><text>LIN ET AL. : "Visualization of Cardiac Dynamics using Physics- based Deformable Model" PROCEEDINGS OF THE SPIE, vol. 3976 (2000) pp. 210-217</text></nplcit>, relates to a deformable heart surface model, with electrophysiological values assigned to the vertices of this model by interpolating the values the three nearest electrodes.

BRIEF SUMMARY OF THE INVENTION

0012The present invention expands the previous capabilities of cardiac electrophysiology mapping systems by providing the ability to map electrophysiology measurements directly to previously obtained three-dimensional images.

0013The present invention provides the ability to utilize high resolution image data together with electrophysiology measurements taken at the time of treatment. Thus, the present invention permits the blending of different technologies for an improved treatment.

0014The foregoing and other aspects, features, details, utilities, and advantages of the present invention will be apparent from reading the following description and claims, and from reviewing the accompanying drawings.

0015According to an embodiment of the present invention, a system for mapping electrophysiological information on a three-dimensional model is providing comprising a modeling processor to obtain a three-dimensional model of at least a portion of a heart comprising position information for a plurality of location points on a surface of the heart; an electrophysiology measurement device for generating a cardiac electrophysiology map comprising position information for a plurality of measurement points and electrophysiology measurements made at each of the plurality of measurement points, said electrophysiology measurements being associated with the respective measurement points at which the electrophysiology measurements were measured; an edge processor to process a subset of the plurality of location points in the three-dimensional model and to determine, for each location point being processed, the two measurement points in the cardiac electrophysiology map that are closest in distance to location point being processed, said processor defining a plurality of edges, each of which comprises the pairs of measurement points determined to be closest to each of the location points being processed; a geometry processor to define a plurality of polygons within the cardiac electrophysiology map based on the plurality of edges; and a projection processor to assign an electrophysiology level to at least one location point located within one of the plurality of polygons based on interpolation using the electrophysiology measurements associated with each of the vertices of the polygons. Optionally, the edges are Delaunay edges and the interpolation is barycentric interpolation.

0016Optionally, the processor is also configured to assign an electrophysiology level to at least one location point located near an edge based on bilinear interpolation using the electrophysiology measurements measured at endpoints of the edge.

0017Optionally, the processor is also configured to assign an electrophysiology level to at least one location point based on the electrophysiology measurements measured at a measurement point that is within a proximity threshold, wherein the electrophysiology level being assigned is the same as that of the measurement point.

0018Yet another embodiment of the present invention provides a computerized method for mapping electrophysiological information on a three-dimensional model comprising the following steps: A) receiving a three-dimensional model of at least a portion of an anatomy comprising position information for a plurality of location points on a surface of the anatomy; B) receiving an electrophysiology map for the anatomy comprising position information for a plurality of measurement points and electrophysiology measurements made at each of the plurality of measurement points; C) using a computer to determine, for each individual location point of the plurality of location points in the three-dimensional model, the two measurement points from the electrophysiology map that are closest to the individual location point and then defining an edge comprising the determined pair of measurement points; D) using the computer to connecting the edges to form a mesh of closed polygons; E) using the computer to identify location points from the three dimensional model that lie on a surface of a closed polygons whose edges surround the identified location point, wherein the computer assigning an electrophysiology level to the identified location point based on interpolation using the electrophysiology measurements measured at each of the vertices of the polygons whose edges surround the identified location point; and F) outputting an output file comprising position information for a plurality of location points and electrophysiology levels that were assigned to each of the plurality of location points.

BRIEF DESCRIPTION OF THE DRAWINGS

0019<ul id="ul0001" list-style="none" compact="compact"><li><figref idref="f0001">Fig. 1</figref> is a schematic diagram of a system for performing a cardiac electrophysiology examination or ablation procedure wherein the location of one or more electrodes can be determined and recorded.</li><li><figref idref="f0002">Fig. 2</figref> is a schematic representation of a heart investigated by an electrophysiology catheter with several distal electrodes.</li><li><figref idref="f0003">Fig. 3</figref> is a schematic diagram of an exemplary methodology for rendering a surface of a heart cavity using recorded electrode position data points.</li><li><figref idref="f0004">Fig. 4</figref> is a schematic depiction of a graphical user interface for displaying electrocardiograph and related electrophysiological information to a clinician.</li><li><figref idref="f0005">Fig. 5</figref> is an enlargement of the panel 66 depicted in <figref idref="f0004">Fig. 4</figref>.</li><li><figref idref="f0006">Fig. 6</figref> shows side-by-side views of time-varying electrograms collected for various locations along a wall of a heart.</li><li><figref idref="f0007">Fig. 7</figref> shows side-by-side views of time-varying electrograms collected for various locations along a wall of a heart.</li><li><figref idref="f0008">Fig. 8</figref> shows side-by-side comparisons of electrograms for typical compact and fibrillar myocardial muscle tissues in the time-domain and frequency-domain.</li><li><figref idref="f0009">Fig. 9A</figref> shows a side-by-side comparison of time-domain and frequency-domain information for electrograms.</li><li><figref idref="f0010">Fig. 9B</figref> shows a side-by-side comparison of time-domain and frequency-domain information for electrograms with energy in multiple spectral bands shown in cross-hatch.</li><li><figref idref="f0011">Fig. 10</figref> shows a method for collecting electrograms and mapping time-domain and/or frequency-domain electrogram information on a three-dimensional model.</li><li><figref idref="f0012">Fig. 11</figref> illustrates a three-dimensional model of a portion of a heart. An identical color version of <figref idref="f0012">Fig. 11</figref> (without reference numbers) is also submitted herewith.</li><li><figref idref="f0013">Fig. 12</figref> illustrates an electrophysiology data map for the same portion of the heart shown in <figref idref="f0012">Fig. 11</figref>. An identical color version of <figref idref="f0013">Fig. 12</figref> (without reference numbers) is also submitted herewith.</li><li><figref idref="f0014">Fig. 13</figref> contains the three-dimensional model of <figref idref="f0012">Fig. 11</figref> upon which distance lines have been drawn from midpoints that are measured using <figref idref="f0013">Fig. 12</figref>. An identical color version of <figref idref="f0014">Fig. 13</figref> (without reference numbers) is also submitted herewith.</li><li><figref idref="f0015">Fig. 14</figref> shows a voltage map for the same portion of the heart as shown in <figref idref="f0012">Fig. 11</figref>, in which the electrophysiology data map from <figref idref="f0013">Fig. 12</figref> has been projected on to the three-dimensional model of <figref idref="f0012">Fig. 11</figref>. An identical color version of <figref idref="f0015">Fig. 14</figref> (without reference numbers) is also submitted herewith.</li></ul>

DETAILED DESCRIPTION OF THE INVENTION

0020The present invention improves a system's ability to create an improved electrophysiology mapping of an anatomy. The present invention is not limited to creating accurate models of the heart, but for illustrative purposes, reference will often be madeherein to a navigation and localization system used for assessment and treatment of cardiac tissue. The methodology described herein would be equally applicable to modeling other parts of the human anatomy. For purposes of illustrating the present invention, the techniques for creating an electrophysiology map of a cardiac tissue will be described below.

0021Many conventional systems exist for generating a three-dimensional model of the heart, including systems that utilize technology such as CT scanning, MRI, ultrasound imaging, radar imaging, x-ray imaging, and fluoroscopic imaging. The output of such data may be a plurality of x-y-zdata coordinates, spherical coordinates and/or other formats to provide a three-dimensional image. Such imaging technology is often useful in diagnosis as well as preparing for a patient's treatment and/or surgery. Sometimes, the imaging process is performed hours before and in some cases days in advance of the treatment and/or surgery.

0022Of course, the three-dimensional model may utilize a segmented approach, including for example, a segmented CT or MRI scan image. A segmented model indicates that a subregion of a three-dimensional image has been digitally separated from a larger three-dimensional image, e.g., an image of the right atrium separated from the rest of the heart. Other methodologies and techniques for creating a three-dimensional model of a portion of the patient may also be utilized in accordance with the present invention, including for example, the methodologies and techniques disclosed in <patcit id="pcit0002" dnum="US6728562B"><text>U.S. Patent No. 6,728,562</text></patcit> ("the '562 patent").

0023Still other techniques to create a three-dimensional model of the anatomy will be discussed further below.

0024Techniques available to develop an electrophysiology map will now be discussed in connection with <figref idref="f0001">Fig. 1</figref>, which shows a schematic diagram of a localization system 8 for conducting cardiac electrophysiology studies by navigating a cardiac catheter and measuring electrical activity occurring in a heart 10 of a patient 11 and three-dimensionally mapping the electrical activity and/or information related to or representative of the electrical activity. System 8 can be used to help create an anatomical model using one or more electrodes. System 8 can also be used to measure electrophysiology data at a plurality of points along a cardiac surface, and store the measured data in association with location information for each measurement point at which the electrophysiology data was measured.

0025The patient 11 is depicted schematically as an oval for simplicity. Three sets of surface electrodes (e.g., patch electrodes) are shown applied to a surface of the patient 11 along an X-axis,, a Y-axis, and a Z-axis. The X-axis surface electrodes 12, 14 are applied to the patient along a first axis, such as on the lateral sides of the thorax region of the patient (e.g., applied to the patient's skin underneath each arm) and may be referred to as the Left and Right electrodes. The Y-axis electrodes 18, 19 are applied to the patient along a second axis generally orthogonal to the X-axis, such as along the inner thigh and neck regions of the patient, and may be referred to as the Left Leg and Neck electrodes. The Z-axis electrodes 16,22 are applied along a third axis generally orthogonal to the X-axis and the Y-axis, such as along the sternum and spine of the patient in the thorax region and may be referred to as the Chest and Back electrodes. The heart 10 lies between these pairs of surface electrodes. An additional surface reference electrode (e.g., a "belly patch") 21 provides a reference and/or ground electrode for the system 8. The belly patch electrode 21 is an alternative to a fixed intra-cardiac electrode 31. It should also be appreciated that, in addition, the patient 11 will have most or all of the conventional electrocardiogram (ECG) system leads in place. This ECG information is available to the system 8 although not illustrated in the <figref idref="f0001">Fig. 1</figref>.

0026In a preferred embodiment, the localization/mapping system is the EnSite NavX™ navigation and visualization system of St. Jude Medical, Atrial Fibrillation Division, Inc. Other localization systems, however, may be used in connection with the present invention, including for example, the CARTO navigational and location system of Biosense Webster, Inc. and the LOCALISA intracardiac navigation system of Medtronic, Inc. The localization and mapping systems described in the following patents can be used with the present invention: United States Patent Nos. <patcit id="pcit0003" dnum="US6990370B"><text>6,990,370</text></patcit>; <patcit id="pcit0004" dnum="US6978168B"><text>6,978,168</text></patcit>; <patcit id="pcit0005" dnum="US6947785B"><text>6,947,785</text></patcit>; <patcit id="pcit0006" dnum="US69339309B"><text>6,9339,309</text></patcit>; <patcit id="pcit0007" dnum="US6728562B"><text>6,728,562</text></patcit>; <patcit id="pcit0008" dnum="US6640119B"><text>6,640,119</text></patcit>; <patcit id="pcit0009" dnum="US5983126A"><text>5,983,126</text></patcit>; and <patcit id="pcit0010" dnum="US5697377A"><text>5,697,377</text></patcit>.

0027A representative catheter 13 having at least one electrode 17 (e.g., a distal electrode) is also shown. This representative catheter electrode 17 is referred to as the "roving electrode" or "measurement electrode" throughout the specification. Typically, multiple electrodes on catheter 13, or on multiple such catheters, will be used. In one embodiment, for example, the system 8 may comprise up to sixty-fotir electrodes on up to twelve catheters disposed within the heart and/or vasculature of the patient. Of course, this embodiment is merely exemplary, and any number of electrodes and catheters may be used within the scope of the present invention.

0028An optional fixed reference electrode 31 (e.g., attached to a wall of the heart 10) is also shown on a second catheter 29. For calibration purposes, this electrode 31 may be stationary (e.g., attached to or near the wall of the heart) or disposed in a fixed spatial relationship with the roving electrode 17. The fixed reference electrode 31 may be used in addition or alternatively to the surface reference electrode 21 described above. In many instances, a coronary sinus electrode or other fixed electrode in the heart 10 can be used as a reference for measuring voltages and displacements.

0029Each surface electrode is coupled to the multiplex switch 24 and the pairs of electrodes are selected by software running on a computer 20, which couples the electrodes to a signal generator 25. The computer 20, for example, may comprise a conventional general-purpose computer, a special-purpose computer, a distributed computer, or any other type of computer. The computer 20 may comprise one or more processors, such as a single central-processing unit, or a plurality of processing units, commonly referred to as a parallel processing environment.

0030Generally, three nominally orthogonal electric fields are generated by a series of driven and sensed electric dipoles in order to realize catheter navigation in a biological conductor. Alternately, these orthogonal fields can be decomposed and any pairs of surface electrodes can be driven as dipoles to provide effective electrode triangulation. Additionally, such nonorthogonal methodologies add to the flexibility of the system. For any desired axis, the potentials measured across an intra-cardiac electrode 17 resulting from a predetermined set of drive (source-sink) configurations are combined algebraically to yield the same effective potential as would be obtained by simply driving a uniform current along the orthogonal axes.

0031Thus, any two of the surface electrodes 12, 14, 16, 18, 19,22 may be selected as a dipole source and drain with respect to a ground reference, e.g., the belly patch 21, while the unexcited electrodes measure voltage with respect to the ground reference. The measurement electrode 17 placed in the heart 10 is exposed to the field from a current pulse and is measured with respect to ground, e.g., the belly patch 21. In practice the catheters within the heart may contain multiple electrodes and each electrode potential may be measured. As previously noted, at least one electrode may be fixed to the interior surface of the heart to form a fixed reference electrode 31, which is also measured with respect to ground. Data sets from each of the surface electrodes, the internal electrodes, and the virtual electrodes may all be used to determine the location of the measurement electrode 17 or other electrodes within the heart 10.

0032One of skill in the art will readily appreciate that the measurement electrode 17 can also be used to measure electrophysiology data and system 8 can be used to store the electrophysiology data (e.g., voltage readings, including without limitation, voltage variations over a period of time) in association with location information for the measurement point at which the electrophysiology data was measured.

0033For example, all of the raw electrode voltage data is measured by the A/D converter 26 and stored by the computer 20 under the direction of software. This electrode excitation process occurs rapidly and sequentially as alternate sets of surface electrodes are selected and the remaining non-driven electrodes are used to measure voltages. This collection of voltage measurements is referred to herein as the "electrode data set." The software has access to each individual voltage measurement made at each electrode during each excitation of each pair of surface electrodes.

0034The raw electrode data is used to determine the "base" location in three-dimensional space (X, Y, Z) of the electrodes inside the heart, such as the roving electrode 17, and any number of other electrodes located in or around the heart and/or vasculature of the patient 11. <figref idref="f0002">Fig. 2</figref> shows a catheter 13, which may be a conventional electrophysiology catheter (sometimes referred to as an "EP catheter"), extending into the heart 10. In <figref idref="f0002">Fig. 2</figref>, the catheter 13 extends into the left ventricle 50 of the heart 10. The catheter 13 comprises the distal electrode 17 discussed above with respect to <figref idref="f0001">Fig. 1</figref> and has additional electrodes 52, 54, and 56. Since each of these electrodes lies within the patient (e.g., in the left ventricle of the heart), location data may be collected simultaneously for each of the electrodes. In addition, when the electrodes are disposed adjacent to the surface, although not necessarily directly on the surface of the heart, and when the current source 25 is "off" (i.e., when none of the surface electrode pairs is energized), at least one of the electrodes 17, 52, 54, and 56 can be used to measure electrical activity (e.g., voltage) on the surface of the heart 10.

0035The data used to determine the location of the electrode(s) within the heart is measured while the surface electrode pairs impress an electric field on the heart. A number of electrode locations may be collected by either sampling a number (e.g., sixty-two electrodes spread among up to twelve catheters) simultaneously or in sequence (e.g., multiplexed) and/or by sampling one or more electrodes (e.g., the roving electrode 17) being moved within the patient (e.g., a chamber of the heart). In one embodiment, the location data for individual electrodes are sampled simultaneously, which allows for collection of data at a single stage or phase of a heartbeat. In another embodiment, location data may be collected either synchronously with one or more phases of the heartbeat or without regard for any particular stage of the heartbeat. Where the data is collected across the phases of the heartbeat, data corresponding to locations along the wall of the heart will vary with time. In one variation, the data corresponding to the outer or inner locations may be used to determine the position of the heart wall at the maximum and minimum volumes, respectively. For example, by selecting the most exterior points it is possible to create a "shell" representing the shape of the heart at its greatest volume.

0036The electrode data may also be used to create a respiration compensation value used to improve the raw location data for the electrode locations as described in <patcit id="pcit0011" dnum="US20040254437A" dnum-type="L"><text>U.S. Patent Application Publication No. 2004/0254437</text></patcit>. The electrode data may also be used to compensate for changes in the impedance of the body of the patient as described in co-pending <patcit id="pcit0012" dnum="US22758005A" dnum-type="L"><text>U.S. Patent Application No. 11/227,580, filed on 15 September 2005</text></patcit>.

0037In summary, the system 8 first selects a set of surface electrodes and then drives them with current pulses. While the current pulses are being delivered, electrical activity, such as the voltages measured at least one of the remaining surface electrodes and in vivo-electrodes are measured and stored. At this point, compensation for artifacts, such as respiration and/or impedance shifting may be performed as indicated above. As described above, various location data points are collected by the system 8 that are associated with multiple electrode locations (<i>e.g.,</i> endocardial electrode locations). Each point in the set has coordinates in space. In one embodiment, the system 8 collects location data points for up to sixty-four electrodes that may be located on up to twelve catheters simultaneously or in close proximity to one another. However, smaller or larger data sets may be collected and result in less complex and lower resolution or more complex and higher resolution representations of the heart, respectively.

0038A three-dimensional model of a portion of the patient, e.g., a region of the patient's heart or surrounding vasculature, may be created from the location data points, e.g., during the same or a previous procedure, or a previously generated three-dimensional model, e.g., a segmented CT or MRI scan image, may be used. A segmented model indicates that a subregion of a three-dimensional image has been digitally separated from a larger three-dimensional image, e.g., an image of the right atrium separated from the rest of the heart. Exemplary segmentation applications include ANALYZE (Mayo, Minneapolis, MN), Verismo (St. Jude Medical, Inc., St. Paul, MN), and CardEP (General Electric Medical Systems, Milwaukee, WI). Where the three-dimensional model is created from the location data points collected by the system 8, for example, during a single procedure by sweeping one or more electrodes over the surface of the heart, the exterior-most location points in the data can be used to determine a shape corresponding to the volume of a region of the patient's heart.

0039Other methodologies and techniques for creating three-dimensional models of a portion of the patient may also be utilized in accordance with the present invention. For example, a convex hull may be generated using standard algorithms such as the Qhull algorithm. The Qhull algorithm, for example, is described in <nplcit id="ncit0006" npl-type="s"><text>Barber, C.B., Dobkin, D.P., and Huhdanpaa, H.T., "The Quickhull algorithm for convex hulls," ACM Trans: on Mathematical Software, 22(4):469-483, Dec 1996</text></nplcit>. Other algorithms used to compute a convex hull shape are known and may also be suitable for use in implementing the invention. This surface may then be re-sampled over a more uniform grid and may be interpolated to give a reasonably smooth surface stored as a three-dimensional model for presentation to the physician during the same or a later procedure. The re-sampled surface generally may have a greater number of data points. The re-sampled surface may also be processed using a smoothing algorithm, which will give the geometry a much smoother appearance. Such a three-dimensional model, for example, provides an estimated boundary of the interior of the heart region from the set of points.

0040<figref idref="f0003">Fig. 3</figref> schematically depicts another exemplary method for creating a shell corresponding to the shape of a heart chamber. The location data identifying position data points 40 of one or more electrodes within the heart chamber over a period of time is accessed. The location data may be represented as a cloud of points within the heart chamber. The most distant position data points 40 will thus correspond to the interior wall of the heart chamber in a relaxed or diastole state corresponding to its greatest volume. A shell or surface is rendered from this location data by fitting an array of "bins" 44 around groups of the position data points 40. The bins 44 are constructed by determining a mean center point 42 within the cloud of position data points 40 and then extending borders radially outward from the center point 42. The bins 44 extend to the furthest position data point 40 within the slice encompassed by the bin 44. It should be noted that even though <figref idref="f0003">Fig. 3</figref> is schematically presented in two dimensions, the bins 44 are three-dimensional volumes. The radial end faces 46 of the bins 44 thus approximate the surface of the heart chamber wall. Common graphic shading algorithms can then be employed to "smooth" the surface of the shell thus created out of the radial end faces 46 of the bins 44.

0041Another example of creating a three-dimensional map using a cloud of points is described in United States application no. <patcit id="pcit0013" dnum="US11647275B"><text>11/647,275, filed 29 December 2006</text></patcit>, which claims the benefit of United States provisional application no. <patcit id="pcit0014" dnum="US60800858B"><text>60/800,858, filed 17 May 2006</text></patcit>. Yet another technique for creating a three-dimensional map of a tissue surface is described in United States application no. <patcit id="pcit0015" dnum="US11647298B"><text>11/647,298, filed 29 December 2006</text></patcit>, which claims the benefit of United States provisional application no. <patcit id="pcit0016" dnum="US60851042B"><text>60/851,042, filed 12 October 2006</text></patcit>, and which is a continuation-in-part of United States application no. <patcit id="pcit0017" dnum="US11139908B"><text>11/139,908, filed 27 May 2005</text></patcit>, which claims the benefit of United States provisional application no. <patcit id="pcit0018" dnum="US60575411B"><text>60/575,411, filed 28 May 2004</text></patcit>.

0042Various electrophysiology data may be measured and presented to a cardiologist through the display 23 of the system 8 shown in <figref idref="f0001">Fig. 1</figref>. <figref idref="f0004">Fig. 4</figref> depicts an illustrative computer display that may be displayed via the computer 20. The display 23, for example, may be used to show data to a user, such as a physician, and to present certain options that allow the user to tailor the configuration of the system 8 for a particular use. It should be noted that the contents on the display can be easily modified and the specific data presented is illustrative only and not limiting of the invention. An image panel 60 shows a three-dimensional model of a heart chamber 62 identifying regions that received a depolarization waveform at the same time, i.e., "isochrones," mapped to the model in false color or grayscale. The isochrones are, in one variation, mapped to three-dimensional coordinates (e.g., X, Y, Z) corresponding to the electrogram from which they were obtained. The isochrones are also shown in guide bar 64 as a key, identifying information associated with a particular color or grayscale mapped to the three-dimensional model. In this image, the locations, of multiple electrodes on a pair of catheters are also mapped to the three-dimensional model. Other data that may be mapped to the heart surface model include, for example, the magnitude of a measured voltage and the timing relationship of a signal with respect to heartbeat events. Further, the peak-to-peak voltage measured at a particular location on the heart wall may be mapped to show areas of diminished conductivity and may reflect an infarcted region of the heart.

0043In the variation shown in <figref idref="f0004">Fig. 4</figref>, for example, the guide bar 64 is graduated in milliseconds and shows the assignment of each color or grayscale to a particular time relationship mapped to the three-dimensional model. The relationship between the color or grayscale on the three-dimensional model image 62 and the guide bar 64 can also be determined by a user with reference to the information shown in panel 66. <figref idref="f0005">Fig. 5</figref> shows an enlargement of the panel 66 depicted in <figref idref="f0004">Fig. 4</figref>. The panel 66, in this variation, shows timing information used to generate isochrones mapped on the three-dimensional model 62 shown in <figref idref="f0004">Fig. 4</figref>. In general, a fiducial point is selected as the "zero" time. In <figref idref="f0005">Fig. 5</figref>, for example, the inflection point 70 of a voltage appearing on a reference electrode is used as the primary timing point for the creation of isochrones. This voltage may be acquired from either a virtual reference or a physical reference (e.g., the roving electrode 17 shown in <figref idref="f0001">Fig. 1</figref>). In this variation, the voltage tracing corresponding to the fiducial point is labeled "REF" in <figref idref="f0005">Fig. 5</figref>. The roving electrode signal is depicted in <figref idref="f0005">Fig. 5</figref> and is labeled "ROV." The inflection point 72 of the voltage signal ROV corresponds to the roving electrode 31. The color guide bar 65 shows the assignment of color or grayscale tone for the timing relationship seen between inflection points 70 and 72 of the reference and roving voltage signals REF and ROV, respectively.

0044The amplitude of the voltage signal ROV corresponding to the roving electrode 17 is also shown on panel 66 of <figref idref="f0005">Fig. 5</figref>. The amplitude of the time-varying signal ROV is located between two adjustable bands 74 and 76, which can be used to set selection criteria for the peak-to-peak voltage of the signal ROV. In practice, regions of the heart with low peak-to-peak voltage are the result of infarcted tissue, and the ability to convert the peak-to-peak voltage to grayscale or false color allows identification of the regions that are infarcted or ischemic. In addition, a time-varying signal "V1" is also shown and corresponds to a surface reference electrode, such as a conventional ECG surface electrode. The signal V 1, for example, may orient a user, such as a physician, to the same events detected on the surface of the patient.

0045Various time-domain information related to the EP activity in and/or around the heart of a patient may be mapped to the three-dimensional model. For example, the time difference of an action potential measured at a roving electrode and a reference electrode, the peak-to-peak voltage of an action potential measured at the roving electrode, and/or the peak negative voltage of an action potential measured at the roving electrode may be mapped to a three-dimensional model. In one embodiment, EP activity from up to sixty-two roving electrodes may be collected and mapped to the three-dimensional model.

0046Complex fractionated electrogram (CFE) and frequency-domain information may also be mapped to the three-dimensional model. CFE information, for example, may be useful to identify and guide ablation targets for atrial fibrillation. CFE information refers to irregular electrical activation (e.g., atrial fibrillation) in which an electrogram comprises at least two discrete deflections and/or perturbation of the baseline of the electrogram with continuous deflection of a prolonged activation complex (e.g., over a 10 second period). Electrograms having very fast and successive activations are, for example, consistent with myocardium having short refractory periods and micro-reentry. <figref idref="f0006">Fig. 6</figref>, for example, shows a series of electrograms. (<figref idref="f0006">Figure 6</figref> is associated with an article by NADEMANEE, <nplcit id="ncit0007" npl-type="s"><text>Koonlawee, M.D., FACC, et. al., A new approach for catheter ablation of atrial fibrillation: Mapping of the electrophysiologic substrate, Journal of the American College of Cardiology, (2004) Vol. 43, No. 11, 20.44-53</text></nplcit>.) The first two electrograms, RAA-prox and RAA-dist, comprise typical electrograms from the right atrium of a patient such as from a proximal roving electrode and a distal roving electrode in the right atrium of a patient, respectively. The third electrogram, LA-roof, comprises a CFE electrogram, such as from the roof of the patient's left atrium. In this third electrogram, LA-roof, the cycle lengths indicated by the numbers shown in the electrogram are substantially shorter than the cycle lengths indicated by the numbers shown in the first two electrograms, RAA-prox and RAA-dist. In another example shown in <figref idref="f0007">Fig. 7</figref>, a first electrogram RA-Septum comprises fast and successive activations indicated by the arrows compared to the second electrogram RA. The fast and successive activations, for example, can be consistent with myocardial tissue having short refractory periods and micro-reentry, e.g., an atrial fibrillation "nest."

0047The presence of CFE information can be detected from the EP information (e.g., electrograms) collected by an electrode, for example, by monitoring the number of deflections within an electrogram segment; calculating the average time between deflections within an electrogram segment; monitoring the variation of time between deflections within a cycle length of an electrogram; and calculating slopes, derivatives, and amplitudes of electrograms. For example, discrete activations have an associated peak-to-peak value measured over a specified time period. This peak-to-peak value mary be used to quantify a discrete activation. As shown in <figref idref="f0005">Fig. 5</figref>, a time instant of the discrete activations can be marked on the electrogram on the user display. The time instant and/or other quantifications of the fractionation of the electrogram may be used to determined the presence and/or absence of CFE information. The mean interval between discrete activations within a predetermined time period may, for example, be used as an index to quantify the degree of fractionation of a given electrogram. In this example, a value of one may be assigned to the electrogram if there is only one discrete activation within the given time period, and a lesser or higher value may be assigned if more than one discrete activation is present in the given time period. Another quantification may comprise, for example, quantifying the variance in time between discrete activations of an electrogram. These or other quantifications of the time-domain correlate with the morphology of the electrogram and are, in turn, based upon the underlying physiology of the region from which the electrogram was sampled.

0048In diagnosing atrial fibrillation and guiding an ablation catheter, the electrograms corresponding to physiological mechanisms for initiating and sustaining atrial fibrillation may be identified by quantifying the fractionation of the electrograms. These quantifications, in turn, may be used to identify regions to be ablated to eliminate the atrial fibrillation. Mid-diastolic potentials within an ischemic area of the cardiac chamber may also be identified by quantifying the fractionation of the electrograms collected in a region of the heart. Healthy tissue would correspond to non-fractionated electrograms (i.e., a single discrete activation), while unhealthy tissue (e.g., ischemic tissue) would correspond to fractionated electrograms (i.e., multiple discrete activations and/or perturbations of the baseline). The time instant or other quantifications of CFE information in electrograms may then be mapped to a three-dimensional model as described above.

0049In addition to and/or alternatively to the time-domain information analyzed and mapped from the collected EP information, frequency-domain information may also be mapped to a three-dimensional model. In one embodiment, for example, a fast Fourier transform (FFT) or other method of translating a time-varying signal into frequency-domain information may be used to translate the collected signal into a frequency-domain. The frequency domain depicts a spectrum that represents the energy or power of frequency components of a time-varying electrogram signal. FFTs and other transforms are known in the art and are not discussed in further detail herein.

0050<figref idref="f0008">Fig. 8</figref> shows a side-by-side comparison of compact myocardial muscle and fibrillar myocardial muscle that together form the wall of the heart. Compact myocardial muscle tissue comprises groups of tightly-connected cells that conduct electrical activity during depolarization of the heart in a homogenous fashion by transmitting electrical activity at equal speeds in any direction. Fibrillar myocardial muscle tissue, however, typically comprises loosely connected cells, such as transitions between neural, vascular, and atrial tissue. Fibrillar myocardial muscle tissue may also be formed by stretching and/or degeneration of cells leading to poor connections between such damaged tissue. In row A, the first column shows the homogenous or uniform activation of compact myocardial muscle tissue during depolarization of the heart wall. In the second column, however, the irregular activation of fibrillar myocardial muscle tissue is shown during depolarization in which a wave travels at different rates through different strands or portions of the fibrillar myocardial muscle tissue, thus causing asynchronous contraction in different portions of the myocardium.

0051In row B, time-domain electrogram signals are shown for the compact myocardial muscle tissue and the fibrillar myocardial muscle tissue during a depolarization phase of a heartbeat. As shown in <figref idref="f0008">Fig. 8</figref>, the time-domain electrogram signals typically comprise a biphasic or triphasic shape for compact myocardial muscle tissue (shown in column 1) and a more polyphasic shape for fibrillar myocardial muscle tissue (shown in column 2). Finally, the frequency-domain of the electrogram signals of row B for compact myocardial muscle tissue and fibrillar myocardial muscle tissue is shown in row C. The frequency-domain is obtained by performing an FFT on a time period of the time-varying electrograms shown row B, column 1 for compact myocardial muscle tissue and row B, column 2 for fibrillar myocardial muscle tissue. As shown in row C of <figref idref="f0008">Fig. 8</figref>, the frequency spectrum for compact myocardial muscle tissue typically comprises a higher amplitude at a single peak located around a fundamental frequency, while the frequency spectrum for the fibrillar myocardial muscle tissue typically comprises a lower amplitude at its fundamental frequency due to a right-shift of the frequency caused by a number of harmonic frequency components.

0052As shown in <figref idref="f0008">Fig. 8</figref>, fibrillar myocardial muscle tissue can lead to irregular wavefronts of electrical activity during depolarization of the heart. The greater the ratio of fibrillar myocardial muscle tissue to compact myocardial muscle tissue, the more likely there is a propensity for atrial fibrillation. In such areas "atrial fibrillation nests" (or "AFIB nests") may be identified as potential sources of atrial fibrillation. Thus, by use of frequency-domain information, a physician may be able to further identify potential trouble spots that may lead to atrial fibrillation.

0053Various numerical indices can be obtained from the frequency spectrum of the electrogram signal. Any of these indices can then be mapped to a three-dimensional model of a patient's heart to allow a user such as a physician to identify locations on the wall of the heart that correspond to a particular characteristic. In one exemplary variation of the present invention, a dominant frequency of an electrogram signal can be identified in the frequency spectrum, which has been obtained via a FFT. As can be seen in <figref idref="f0009">Fig. 9A</figref>, for example, a typical normal, or compact, myocardial muscle tissue may have a single peak in the spectrum, while a fibrillar myocardial muscle tissue has more spectral peaks than does a compact myocardial muscle tissue. The number of spectral peaks may be determined for multiple points around the wall of the heart on a three-dimensional model as described above. (<figref idref="f0007 f0008 f0009">Figures 7 - 9a</figref> are associated with an article by PACHON, <nplcit id="ncit0008" npl-type="b"><text>Jose, C., et. al., A new treatment for atrial fibrillation based on spectral analysis to guide the catheter RF ablation, ,Europace, (2004) 6, 590-601, The European Society of Cardiology</text></nplcit>.)

0054In another variation of the present invention, a maximum peak amplitude at the dominant frequency may be determined from the frequency. spectrum of the electrogram signal and may be mapped to a three-dimensional model of the heart. In <figref idref="f0009">Fig. 9A</figref>, for example, the maximum peak amplitude at the dominant frequency of compact myocardial muscle tissue can be seen to be higher at about 175 dB mV, while the maximum peak amplitude at the dominant frequency of fibrillar myocardial muscle tissue is lower at about 80 dB mV. These values may also be mapped onto a three-dimensional model of the heart.

0055In yet another variation, a ratio of energy in one band of the frequency-domain to the energy in a second band of the frequency-domain may be determined and mapped to a three-dimensional model, of the heart. For example, <figref idref="f0010">Fig. 9B</figref> shows the ratio of energy in the passband of 60 to 240 Hz to the energy below 60 Hz is higher for the spectrum of electrograms from fibrillar myocardial muscle tissue than in the spectrum of electrograms from compact myocardial muscle tissue.

0056While examples of time-domain and frequency-domain information have been described herein as able to be translated to a three-dimensional map of a patient's heart, one skilled in the art would recognize that other time- and frequency-domain information may also be determined and mapped to a three-dimensional model. For example, the following information may be determined from the time-domain or frequency-domain and mapped to a three-dimensional model: a low-frequency or high-frequency passband of interest (e.g., in Hz); a frequency with the maximum energy in a passband (e.g., in Hz); a number of peaks within a passband (e.g., a count); an energy, power, and/or area in each peak (e.g., dB); a ratio of energy and/or area in each peak to that in another passband; and a width of each peak in a spectra (e.g., in Hz).

0057<figref idref="f0011">Fig. 10</figref> shows one example of a method for determining information from a time-varying electrogram in the time-domain and/or frequency-domain and mapping that information onto a three-dimensional model (e.g., a heart). In operation 100, a number of electrodes (e.g., contact or non-contact, unipolar or bipolar mapping electrodes) are used to sample a time-varying electrogram signal. The electrogram signal, for example, may be sampled for multiple sites along the wall of the heart and/or the surrounding vasculature.

0058An FFT is then performed over a time period of the time-varying electrogram to determine frequency-domain information for that electrogram in operation 102. A real-time display of the time-domain and/or frequency-domain information may be displayed in operation 104. One or more parameters are then determined in operation 106. Exemplary parameters are described above and include, for example, a time difference between a roving electrode and a reference electrode; the peak-to-peak voltage of the roving electrode; the peak negative voltage of the roving electrode; CFE information; a dominant frequency of an electrogram signal; a maximum peak amplitude at the dominant frequency; a ratio of energy in one band of the frequency-domain to the energy in a second band of the frequency-domain; a low-frequency or high-frequency passband of interest; a frequency with the maximum energy in a passband; a number of peaks within a passband; an energy, power, and/or area in each peak; a ratio of energy and/or area in each peak to that in another passband; and a width of each peak in a spectrum. Colors, shades of colors, and/or grayscales are assigned to values of the parameters to be identified in operation 108, and colors, shades of colors, and/or grayscales corresponding to the parameters for the electrograms sampled by the electrodes are updated on a three-dimensional model (e.g., of a heart) continuously and in real time in operation 110.

0059One particular area of interest is the mapping of areas of the heart comprised of autonomic nerve cells. ECG information may be mapped to identify the foci of electrical propagation through the heart. The initiation points for electrical signals will generally be autonomic cell bundles, or ganglia plexi. To the extent that any arrhythmia is caused by a malfunction in autonomic cells, the ability to detect this malfunction can significantly aid in the efficacy of treatment and minimize the scope of treatment. A particular advantage to mapping the complex fractionated electrograms in the frequency-domain is the ability to quickly identify and locate such areas of arrhythmia. For example, if it is determined that a specific autonomic bundle is the source of fibrillation, targeting this area of initial neural input instead of treating multiple areas of fibrillar tissue can substantially reduce the number of lesions required to treat the condition.

0060As discussed above, electrophysiology data can be very useful in locating tissue. that may require treatment. A challenge, however, exists with mapping the electrophysiology data onto the three dimensional model of the heart. A projection process in accordance with the present invention will now be described.

0061As described above, the electrodes of at least one EP catheter are moved over the surface of the heart and while in motion they detect the electrical activation of the heart or other EP signals on the surface of the heart. During each measurement, the real-time location of the catheter electrode is noted along with the value of the EP voltage or signal. The collection of location points and the associated measurements are referred to herein as the "EP data set." This data is then projected onto a surface of the three-dimensional model corresponding to the location of the electrode when the sampled EP data was taken. Since this model was not created while the locating surface electrodes are energized, a projection process may be used to place the electrical information on the nearest heart surfaces represented by the geometry. In one exemplary embodiment, for example, each point on the surface of the three-dimensional model is colored or gray-shaded according to the value of the single nearest location in the EP data set. This new point is used as the "location" for the presentation of EP data in the images presented to the physician.

0062In another embodiment, the EP data is mapped onto the three-dimensional model using a new and improved technique. Because the EP data is measured at points that may not be the same set of physical locations used to generate the three-dimensional model, the EP data must be projected on to a surface of the three-dimensional model. In this preferred embodiment, the EP data is projected onto the three-dimensional model for display purposes. The EP data values (peak voltage, activation time, maximum frequency, or other quantities) must also be interpolated onto the points of the three-dimensional geometry. Once the EP data is projected onto the three-dimensional model, the EP data may be converted into colors and rendered according to standard computer graphics techniques. A way to relate the three-dimensional model to the EP data structure must be determined. For many surface-interpolation problems, it is desirable to generate a good triangulation of the data points-connecting them into triangles which fill the x-y plane (in 2D). Then the data value can be approximated at any point in the plane using a smoothly weighted average of the three endpoints of its triangle. This triangular based interpolation is known as barycentric interpolation, although it is contemplated that other known methods of interpolation could be used. In ordinary 2D space, a particular triangulation called the Delaunay triangulation is commonly used and is known to give optimal results. The Delaunay triangulation is closely related to the Voronoi diagram, the set of regions surrounding each data point that are closer to that data point than any other. In particular, each pair of data points whose Voronoi regions border each other is connected by an edge in the Delaunay triangulation. But. it is believed that there are no known algorithms for computing a Delaunay triangulation on arbitrary and complex surfaces such as the three-dimensional models of the heart as described in connection with this invention. The method of this preferred embodiment computes a good approximation to the Delaunay triangulation as follows. Each EP data point is projected to its closest point on the three-dimensional model, and those projected points are searched to determine Voronoi neighbors. A vertex is selected in the three-dimensional model, and the EP data map is searched for the two EP data points that are closest to the vertex in the three-dimensional model. Generally, the EP data points that are neighboring the selected vertex are searched first, and then generally, the neighbors of neighbors are searched, until the two closest EP data points are found. With high likelihood, those data points have Voronoi regions that border each other, and so the two points are connected with a Delaunay edge. The process is repeated for each of the other vertices in the three-dimensional model. Then, a plurality of triangles are formed out of this set of Delaunay edges, knowing that each edge should be part of exactly two triangles. If the resulting triangulation has any "holes"-cycles of four or more edges not containing any triangles the holes may be filled by recursively adding the shortest new edge connecting two data points of the cycle. This is necessary because the two-closest-data-point algorithm may not discover every Delaunay edge, although nearly all edges it does discover turn out to be Delaunay edges. Once the EP data points have been have been collected into this triangulation, the measured data may be interpolated on to each vertex of the three-dimensional model. Most vertices will be interior to one of the Delaunay triangles, and will be interpolated using EP data measured at each of the triangle's three data points. Some vertices may be sufficiently close to a triangle edge (e.g., it lies on or very close to the triangle edge), such that the value to be assigned will be bi-linearly interpolated from the respective measurements of the two endpoints. Preferably, a threshold may be set to dictate how close the vertex must be to an edge before bilinear interpolation is applied. A few vertices may be closer to a data point than any edge or triangle, in which case, the vertices will be assigned the same EP data as the close data point. Preferably, a threshold may be set to dictate how close the vertex must be to a measurement point before the value of the measurement point will be assigned. Once EP data values have been assigned to a plurality of points in the three-dimensional model, then a robust color map may be generated, and preferably, the color map is smoothed using a smoothing algorithm to provide a clinically reasonable color rendering, one in which the points in the three-dimensional model get their color only from measurements that were taken at nearby measurement points.

0063The embodiment described in the previous paragraph will now be discussed in the context of <figref idref="f0012 f0013 f0014 f0015">Figs. 11 - 14</figref>. <figref idref="f0012">Fig. 11</figref> is a three-dimensional model of a portion of a heart, in which the location points 91 have been connected using triangulation. This surface may be re-sampled over a more uniform grid and further may be interpolated to give a reasonably smooth surface stored as a three dimensional model for presentation to the physician during the same or a later procedure. The re-sampled surface generally has a greater number of data points. The resampled surface may also be processed using a smoothing algorithm, which will give the geometry a smoother appearance. Such a three dimensional model, for example, provides an estimated boundary of the interior of the heart region from the set of points. Markers 92 which represent data measurement points within an EP data set have been superimposed upon the three-dimensional model in <figref idref="f0012">Fig. 11</figref>. As previously explained, the locations of the data measurement points (represented by markers 92) for the EP data set generally are not at the same locations as location points 91. Thus, markers 92 are sometimes located wholly within a triangle, and other times, appear on or near an edge of a triangle.

0064<figref idref="f0013">Fig. 12</figref> shows the EP data set which comprises a series of measurement points 93, each of which has a corresponding voltage level. The voltage level is represented by marker 92, whose color is varied to indicate the voltage level.

0065Understanding that the EP data set depicted in <figref idref="f0013">Fig. 12</figref> is the same overall geometry as that of <figref idref="f0012">Fig. 11</figref>, it may be visualized that the measurement points 93 of the EP data set, though generated using the same region of the same heart, do not correspond to the location points 91 of the three-dimensional model. It is the lack of a one-to-one positional correspondence that generates a need to project the measured EP data onto the three-dimensional model. To assist in the projection process, a location point 91 is selected from the plurality of location points 91 that comprise the three-dimensional model of <figref idref="f0012">Fig. 11</figref>. Next, the location of the selected location point 91 is compared to the location of at least a subset of the plurality of measurement points 93 in order to determined which are the two measurement points 93 that are closest to the selected location point 91. The pair of closest measurement points are deemed to form a Delaunay edge 94 (which is depicted by a green line on <figref idref="f0013">Fig. 12</figref>); it is highly likely that the identified pair of closest measurement points 93 are Voronoi neighbors. The closest measurement points may be identified using any number of algorithms designed to evaluate distances, including, for example, a Kirsanov-Hoppe or Fast Marching geodesic algorithm. The identification of pairs of measurement points based on their proximity to selected location points may be repeated to identify additional Delaunay edges. In the process of assessing closest pairs of measurement points for each location point, a plurality of triangles will likely be formed. If after this algorithm, there remain location points which are not part of a triangle, then triangular relationships may be formed by drawing lines to the other measurement points, giving preference to those measurement points which may be connected using shortest distance lines (with preferences given to the creation of triangle edges that are shorter in length).

0066While the proximity relationships between selected location points 91 and their respective pairs of closest measurement points 93 may be tracked in a variety of ways, the relationship are depicted graphically in both <figref idref="f0013">Fig. 12</figref> and <figref idref="f0014">Fig. 13</figref>. On <figref idref="f0013">Fig. 12</figref>, the midpoints 95 of most Delaunay edges have at least one, and typically, several lines (they appear in dark, red ink) that contact the midpoint 95. These lines represent connections to various location points in the three-dimensional model. The existence of a line to a particular location point means that for that particular location point, it was determined that the pair of closest measurement points was the pair that forms the identified Delaunay edge. The same red lines are shown in <figref idref="f0013">Figs. 12</figref> and <figref idref="f0014">13</figref>, but <figref idref="f0013">Fig. 12</figref> shows them with the Delaunay edges and <figref idref="f0014">Fig. 13</figref> with the three-dimensional model. <figref idref="f0014">Fig. 13</figref> contains the three-dimensional model of <figref idref="f0012">Fig. 11</figref> upon which distance lines have been imposed to identify the associations between selected location points in the three-dimensional model and the Delaunay edges that are closest to the selected location points. These associations are used when the measured data of the EP map is projected onto the location points of the three-dimensional model. These red lines only determine which Delaunay edges are used in the triangulation; they are not used to indicate from which Delaunay edges the various location points of the three-dimensional model are interpolated.

0067The actual projection of EP data values will be described next. Each location point in the three-dimensional model is assessed relative to the triangles that have been used to model the EP data set. Conceptually, if the three-dimensional model is superimposed on the triangulated model of the EP data set, the relationship between the location points and the triangles is much easier to visualize. Most location points 91 will be within the interior of one of the triangles of the triangulated model of the EP data set, and the EP data value to be assigned to such location points 91 may be interpolated using barycentric interpolation based on the measured values of the three vertices (the measurement locations 93) of the triangle. Barycentric interpolation is known in the art, and is a preferred method. However, it is contemplated that other known methods of interpolation could be used as well. Some location points 91 may be so close to a triangle edge (e.g., it lies on or very close to the triangle edge), such that the value to be assigned will be bi-linearly interpolated from the respective measured EP data values of the two endpoints of the edge. A few location points 91 may be closer to a measurement point than any edge or triangle, in which case, the location points 91 will be assigned the same EP data value as was measured at the closest measurement point. Once EP data values have been assigned to a plurality of points in the three-dimensional model (and preferably, all of the location points of the three-dimensional model), then the three-dimensional model (and its corresponding assigned EP data values) may be submitted to a coloring program which can color the three-dimensional model based on its assigned EP data levels (e.g., peak voltage, activation time, maximum frequency, or other quantities). <figref idref="f0015">Fig. 14</figref> represents the output from a coloring program, wherein the coloring represents different voltage levels that were assigned by projecting the EP data map of <figref idref="f0013">Fig. 12</figref> onto the three-dimensional model of <figref idref="f0012">Fig.11</figref>.

0068In yet another embodiment, the EP data is mapped onto the three-dimensional model using a technique involving subdividing the three-dimensional model. Specifically, the three-dimensional model is subdivided using triangulation in such a way as to make all EP data points vertices in a subdivided three-dimensional model. Then, the subdivided three-dimensional model may be processed using a mesh-coarsening or decimation algorithm that allows one to specify the output vertex set-which will be specified as being exactly the set of EP data points. The decimation program may then decide the proper connectivity for the points on the three-dimensional model. It is preferred in this embodiment that each vertex in the EP data be projected onto the closest vertex or edge of the subdivided three-dimensional model using the Kirsanov-Hoppe or Fast Marching geodesic algorithm. The output of the decimation program may then be submitted to a coloring program which can color the three-dimensional model based on its voltage levels: It is also contemplated that Delaunay edges that are longer than a predetermined distance threshold be disallowed.

0069Although multiple embodiments of this invention have been described above with a certain degree of particularity, those skilled in the art could make numerous alterations to the disclosed embodiments without departing from the spirit or scope of this invention. For example, while the description above describes data being mapped to a three-dimensional model, data may be mapped to any map including, but not limited to, a two- or three-dimensional, static or time-varying image or model. All directional references (e.g., upper, lower, upward, downward, left, right, leftward, rightward, top, bottom, above, below, vertical, horizontal, clockwise, and counterclockwise) are only used for identification purposes to aid the reader's understanding of the present invention, and do not create limitations, particularly as to the position, orientation, or use of the invention. Joinder references (e.g., attached, coupled, connected, and the like) are to be construed broadly and may include intermediate members between a connection of elements and relative movement between elements. As such, joinder references do not necessarily infer that two elements are directly connected and in fixed relation to each other. It is intended that all matter contained in the above description or shown in the accompanying drawings shall be interpreted as illustrative only and not limiting. Changes in detail or structure may be made without departing from the scope of the invention as defined in the appended claims.