BACKGROUND:Manometry is commonly used for diagnosis of esophageal and anorectal motility disorders. In the colon, manometry is a useful tool, but clinical application remains uncertain. This uncertainty is partly based on the belief that manometry cannot reliably detect non-occluding colonic contractions and, therefore, cannot identify reliable markers of dysmotility. This study tests the ability of manometry to record pressure signals in response to non-lumen-occluding changes in diameter, at different rates of wall movement and with content of different viscosities.METHODS:A numerical model was built to investigate pressure changes caused by localized, non-lumen-occluding reductions in diameter, similar to those caused by contraction of the gut wall. A mechanical model, consisting of a sealed pressure vessel which could produce localized reductions in luminal diameter, was used to validate the model using luminal segments formed from; (i) natural latex; and (ii) sections of rabbit proximal colon. Fluids with viscosities ranging from 1 to 6800 mPa s(-1) and luminal contraction rates over the range 5-20 mmHg s(-1) were studied.KEY RESULTS:Manometry recorded non-occluding reductions in diameter, provided that they occurred with sufficiently viscous content. The measured signal was linearly dependent on the rate of reduction in luminal diameter and also increased with increasing viscosity of content (R(2) = 0.62 and 0.96 for 880 and 1760 mPa s(-1), respectively).CONCLUSIONS & INFERENCES:Manometry reliably registers non-occluding contractions in the presence of viscous content, and is therefore a viable tool for measuring colonic motility. Interpretation of colonic manometric data, and definitions based on manometric results, must consider the viscosity of luminal content.

The effect of stenting on blood flow is investigated using a model of the coronary artery network. The parameters in a generic non-linear pressure–radius relationship are varied in the stented region to model the increase in stiffness of the vessel due to the presence of the stent. A computationally efficient form of the Navier–Stokes equation is solved using a Lax–Wendroff finite difference method. Pressure, vessel radius and flow velocity are computed along the vessel segments. Results show negative pressure gradients at the ends of the stent and increased velocity through the middle of the stented region. Changes in local flow patterns and vessel wall stresses due to the presence of the stent have been shown to be important in restenosis of vessels. Local and global pressure gradients affect local flow patterns and vessel wall stresses, and therefore may be an important factor associated with restenosis. The model presented in this study can be easily extended to solve flows for stented vessels in a full, anatomically realistic coronary network. The framework to allow for the effects of the deformation of the myocardium on the coronary network is also in place.

Results from recent experiments undertaken on tissue from the gastrointestinal (GI) tract suggests that the interstitial cells of cajal (ICC) are the pacemaker cells responsible for slow wave propagation. The pace-making mechanism of ICC networks is strongly dependant on intracellular spatial dynamics of Ca/sup 2+/. A modeling framework has being developed to test the hypothesis of voltage-dependant Ca channels being responsible for the pace-making mechanism of ICC. The model consists of a coupled system of ordinary differential equations. Regional calcium conservation equations were applied to intra-cellular pools within the ICC framework. Future work with the model will fit parameters from experimental data. This model will also be used to form the basis of a GI tract slow wave computational model.

Simulations of cardiac electrical activity are generally computed in idealized or generic domains. We have developed a semi-automated technique for imaging an extended volume of cardiac ventricular tissue at a resolution of approximately 1 microm, and constructing from those images a geometric and structural model with 10 microm resolution suitable for solving the bidomain equations. This technique enables experimental modeling and computer simulation to be integrated by constructing a tissue-specific structural model in less than one week. We demonstrate the use of this procedure applied to a sample of rat ventricle.

We present source formulations and computational/validation strategies currently in vogue for non–invasive imaging of cardiac electrophysiology.

This paper reports on some problems that can arise with the use of regularized derivative boundary integral equations. It concentrates on developing a formulation for the simple Laplace equation using a cubic Hermite interpolation and shows how certain combinations, of derivative and conventional boundary integral equations can result in a solution scheme severely lacking in stability. With some simple two- and three-dimensional geometries, the derivative equations on their own do not provide enough information to solve a Dirichlet problem. Even combinations of the conventional and derivative equations fail for some simple geometries, We conclude that the only consistently successful combination is that of the conventional equation with the tangential derivative equation, which showed cubic convergence of results with mesh refinement. Numerical results are presented for this scheme in both two and three dimensions.