Patient Specific Modeling of Internal Defibrillation


Fig.1 Solid model of the heart muscle and major blood vessels.

Daniel Mocanu, M.S. Department of Biomedical Engineering, Boston University
Joachim Kettenbach, M.D. Division of Radiology, University Hospital of Vienna, Austria
Michael O. Sweeney, M.D. Division of Cardiology, Brigham and Womens Hospital, Boston
Solomon R. Eisenberg, Sc.D. Department of Biomedical Engineering, Boston University

Ventricular fibrillation is a condition marked by unsynchronized contraction of cardiac muscle cells. The resulting lack of blood flow can cause damage or death if not promptly treated. With the advent of smaller defibrillation generators, catheter electrodes and “active can” technologies, implantable defibrillators (AICD) employing high-energy biphasic shocks have become the treatment of choice for patients with arrhythmias that do not respond to drug therapy. Recent computer modeling studies in our laboratory of myocardial current distribution during defibrillation [1] have shown a good correlation with the overall mean of reported clinical defibrillation metrics. These findings suggest a possible use for computational models in the presurgical planning of AICD implantation. The goal of this research is to investigate the predictive capacity of such computational models by comparing patient-specific simulated and clinical defibrillation metrics.


Fig.2 Voxel-based control volume mesh (lungs and bones).

Ten patients with implanted AICD have been recruited for this study. Patient specific models are constructed from segmented cross-sectional computerized tomographic (CT) images obtained post-implant from Brigham and Women’s Hospital. The segmented data is imported into a computer-aided engineering package (I-DEAS) and the finite volume method is used to simulate internal defibrillation episodes.

Two methods are used to generate the finite volume models. In the first method, the 3-D model of the patient’s conductive anatomy is reconstructed using NURBS surfacing techniques (fig.1) and the resulting geometry is discretized using tetrahedral volume elements. In the second, the 3-D model is constructed with a structured meshing algorithm, in which each voxel in the segmented image data set is defined as a volume element (fig.2).

Fig.3 Electric potential distribution in the heart and blood vessels.

In the quasistatic limit, the electric potential distribution associated with the defibrillation shock is governed by an elliptic partial differential equation subject to Dirichlet (electrodes) and Neumann (thorax surface) boundary conditions. The linear system generated by the finite volume method is solved for the electric potential using the conjugate gradient method. Electric potential and derived current density distributions are shown in fig.3 and fig.4.


Fig.4 Virtual reality rendering of current density distribution.


[1] Kinst T.F., Michael O. Sweeney, Lehr, J.L., Eisenberg, S.R. “Simulated internal defibrillation in humans using an anatomically realistic three-dimensional finite element model of the thorax.” J. Cardiovasc. Electrophysio. 8:537-547 (1997).