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Here, we used the modified bidomain model that takes into account the effects of deformation.
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Several scientists have studied how this model, referred to as the bidomain model, can be modified to incorporate the effect of heart infarctions on simulated ECG (electrocardiogram) recordings.
The Bidomain model is a degenerate parabolic set of nonlinear reaction-diffusion equations.
We were able to simulate similar patterns in both a monodomain model of a tilted stack of rings of dipole current and a bidomain model of a tilted stack of spiraled cardiac tissue that was stimulated at the apex.
When using the bidomain model to model the electrical activity of the heart, there are potentially six cardiac conductivity values involved: conductivity values in directions along and normal to the cardiac fibres with a sheet, as well as a conductivity value in the normal direction between the sheets, and these occur for both the extracellular and intracellular domains in the model.
The bidomain model [10], a generalization of the cable equation [11], has been employed in this area avoiding the discrete constructs of tissue, assuming instead a continuum of two domains, intra- and extracellular, connected by a membrane and that occupy the same volume [12].
A bidomain model based boundary element formulation (linear triangular elements) was applied to relate step-like local activation (resting potential: −90 mV; plateau level: 0 mV; rising time: 3 ms) at the endocardial and epicardial source points to the simulated potentials at the electrode locations [7].
See [ 27] for a mathematical analysis of the bidomain model.
From the bidomain model, Geselowitz (8) derived a succinct expression for the UEG.
The values of electrical conductivities for the bidomain model were extracted from the literature [ 26].
In [ 7], we extended the monodomain model that considers deformation to this version of the bidomain model.
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