Keywords: Guinea-pig, Ventricular myocardium, Regional differences. 

In guinea-pig ventricle, unlike those of other species, electrical activities of cells isolated from different regions of ventricular wall show no significant difference in action potential configuration, such as the spike-and-dome morphology, and the resting potential. However, it has been found that the action potential durations at 50% (APD₅₀) and 90% (APD₉₀) repolarization are significantly shorter in subepicardial myocytes than in subendocardial myocytes [12, 13, 14]. In other species, I_to contributed to the differences in the action potential configuration. In guinea-pig ventricular cells, experiments have failed to find evidence for the existence of I_to [15, 16,17]. The difference in APD is assumed to be mainly due to the relative densities of I_Kr and I_Ks, and their associated channel kinetics [13, 14]. To test this hypothesis, we constructed mathematical models for endo- and epi-cardial ventricular cells of guinea-pig heart. These models incorporate the experimental data of regional differences of ionic current densities. The model action potentials show the same characteristics of action potentials and their regional differences as those recorded from cells isolated from epi- and endo-cardial ventricular cells of guinea-pig heart.

In intact ventricle, the recorded electrical activity from different region did not show the same remarkable regional differences as seen in isolated cells [18]. Such a significant quantitative difference has raised a question, whether or not regional differences shown in the electrical activity of epi- and endo-cardial ventricle cells is due to the intrinsic properties of cells, or due to damage of cells in the process of isolation during experiments? If it is an intrinsic property of cells, what is the mechanism underlying such an apparent disagreement between the data obtained from isolated cells and intact ventricle? In other words, what is the reason for the regional difference to disappear in the intact ventricle? We approach this question computationally. Here we constructed a one-dimensional model of a transmural string of ventricular wall, extending from the endo- to epicardium. The one-dimensional model incorporates the heterogeneity in the electrical activity of ventricular cell. It is shown that, due to the electrotonic interactions, the regional differences in action potential characteristics recorded from different sites are reduced.

 
 

Models of electrical activity of epi- and endo-ventricular cells of guinea-pig heart are based on modifications of a standard model of electrical activity of guinea-pig ventricular cell [19, 20]. The models consist of a set of ordinary differential equations derived from the results of extensive electrophysiological experiments on guinea-pig ventricular myocytes. It represents voltage-dependent ionic currents, pump/exchanger currents, time dependent changes in intracellular and extracellular ionic concentrations, and storage and release of Ca²⁺ by intracellular organelles. In the models we incorporated the published experimental data of Bryant et al. [14] on the ionic current densities measured in isolated guinea-pig ventricular endocardial and epicardial cells. The magnitudes of the Na⁺-K⁺ pump and exchange currents were also modified. The equations, together with the parameter values, are listed in the Appendix.
 

Figure 1: Delayed rectifier tail current densities in endo- (circles) and epicardial (squares) cells of guinea-pig ventricle: experimental data (red lines) [14] and computed results (blue lines). Panel A, shows am example of the protocol used to elicit time-dependent and tail currents, which were elicited upon repolarisation to -40 mV after a 1 s step depolarisation to -20 mV, 0 mV, +20 mV, +40 mV, and +60 mV from a holding potential of -40 mV. Panel B, C and D, current-voltage relationship curves for I_K, I_Kr and I_Ks tail currents.
 

Based on the experimental data of Bryant et al. [14], we modified the kinetics of I_Kr and I_Ks, and also incorporated their regional dependent ionic current densities in our epi- and endo-ventricular models. To do that, we simulated voltage clamp experiment with a same protocol as used in experiments. The current-voltage relationship curves were simulated to fit the experimental data by choosing value of the ionic conductance of G_Kr1, G_Kr2 (fast and slow components of I_Kr) and G_Ks and the rates of activation and inactivation of I_Kr and I_Ks for endo- and epicardial ventricular cells.
 
 

Figure 1 shows the simulation of the voltage clamp experiment, and comparison with the experimental data of Bryant et al. [14]. In Figure 1A, the top panel shows the voltage clamp protocol. The cell membrane potential is clamped from a holding potential of -40 mV to +60 mV for 1 s duration. The bottom panel shows the time trace of I_K. In figure 1B, we plotted the I-V relationship of I_K. The current density of I_K is estimated by the peak tail current at the end of the test pulse. In the figure, filled square with solid line represents the data computed from the epi-cardial cell mode, filled circle with solid line represents the computed data from endo-cardial model; filled square with dash line represents the mean data obtained from epicardial cells, filled circle with dash line represents the mean data obtained from endocardial cells. Our computed data fitted quite well with the experimental data.
 
 

Figure 1C plots the I-V relationship of I_Kr, and comparison with experimental data. In the figure, solid square with solid line is the data from epicardial cell model, filled circle with solid line is the data from endocardial cell model. The computed data for both epi- and endocardial cells are within the experimental range of the mean data obtained from epi- (solid square with dashed line) and endo-cardial cells (solid circle with dashed.).
 
 

In figure 1D, we plotted the computed I-V relationship of I_Ks, and comparison with experimental data. Once again, solid squares represent the data from epicardial cell model (with solid line) and the mean data from epicardial cells (with dashed line); solid circles represents the data from endocardial cell model (with solid line) and the mean data from endocardial cells. For both the epi- and endocardial cell models, the computed data are consistent with the experimental data.

Table 1 lists the experimental data (mean + S.E.M.) of ionic current densities of I_K, I_K,r and I_K,s obtained from n cells isolated from epi-cardial and endo-cardial ventricular cell (n changes from 9 to 12). Our model generated data are also listed. The model generated data are within the range of experimental data.
 
 
 

I_K is tail currents elicited upon repolarisation to -40 mV after 1s step depolarisaton to either -30 mV or +60 mV. I_K is tail current density measured in normal Tyrode. I_Ks = defetilide-insensitive tail current density and I_Kr = defetilide-sensitive tail current density.
 
 

One dimensional model incorporating heterogeneity

A one-dimensional model of a transmural string of ventricular wall takes the form of partial differential equation. In the model we incorporated the heterogeneities of ionic current densities. We assumed that the length of string is 16 mm. In the string, cell capacitance changes linearly from 132 pF at the epicardial to 142 at the endocardial end. The ionic current densities are linear functions of cell capacitance. Electrotonic interactions between cells are through diffusive interactions of membrane potentials. The model takes the form:
 

(1)

in which, V (x,t) is the membrane potential of a node at x distance from the end of epicardium, D is the diffusion coefficient for V, Ñ ² is the Laplacian operator. In numerical simulation, the partial differential equation is solved by a 3-node Laplacian operator, and a time step dt of 0.1 ms, space step dx of 0.32 mm. The diffusion coefficient D was set to 256 mm²s^-1 to give a conduction velocity of 0.3 ms^-1.

Figure 2: Action potentials of the endo- (circle) and epicardial (square) cells of guinea-pig ventricle: (A) simulated result (B) experimental data [14]
 
 

Figure 2A shows the model generated action potentials of epi- and endo-ventricular cells (circle for endocardial cell; square for epicardial cell) in response to a supra-threshold stimulus. The model action potentials are compared with action potentials recorded from epi- and endo-cardial ventricular cells of guinea pig heart (Figure 2B). In both simulation and experimental recording, action potential of epi-cardial cell has significantly shorter APD than that of endocardial cell. However, there is no difference in resting potential. In simulation, there is no difference in the amplitude of action potentials, however, in experimental recording, there is noticeable difference in the amplitude. Difference in the amplitude may result in other ionic currents involved, such as the sustained background sodium current [14].
 
 

Table 2 gives detailed comparison of characteristics of action potentials of epi- and endocardial ventricular cells. In the table, the experimental data are in mean + S.E.M (n changes from 30 to 40) format. From the table we can see that our model generated action potentials of epi- and endo-cardial ventricular cells have the same region characteristics as those recorded experimentally. The model generated action potential duration (APD) is shorter in the epicardial myocytes than in the endocardial myocytes. APD measured at 50% and 90% repolarization were longer in endocardial myocytes than in epicardial myocytes either in the experimental data and computed results: with a stimulation interval of 5000 ms, the action potential duration measured at 50% repolarization (APD₅₀) from the endocardial and epicardial cell models was 261 ms and 198 ms, which are consistent with the experimental results of 250 ± 12 and 185 ± 9 ms, and the APD₉₀ was 284 ms and 228 ms, while the experimental results are 292 ± 12 and 227 ± 9 ms. There is no significant difference in the simulated AP resting potential and amplitude.
 

It is known that characteristics of action potential of guinea-pig ventricular cells are rate dependent. If a second action potential is initiated soon after the first, the second action potential in found considerably shorter in action potential duration. Such rate dependence can been illustrated by a restitution curve [21,22]. Here we investigate a possible regional difference in the rate dependence between epi- and endo-cardial cells, as a result of regional difference in their ionic current densities. In figure 3, we plot the normalized action potential duration against the time interval between two successive stimuli. In the figure, circle represents data computed from epicardial cell model, while square represents data computed from the endocardial cell model. With a slow stimulus rate (a longer time interval), there is no differences. With a high stimulus rate (a small time interval), the difference becomes noticeable.

Figure 3: Computer modelling of restitution curves of the endo- (circle) and epicardial (square) cells of guinea-pig ventricle.
 
 

Propagation of electrical activity in one-dimensional model
 

In one dimensional model of a string of transmural ventricular tissue, intrinsic electrical activity of cells along the string show gradient characteristics as shown in Figure 4A. Action potentials from various points along the string are shown. In numerical simulation we set the cell to cell coupling coefficient to zero, and stimulate all cells in the string simultaneously with a supra-threshold. The excited action potential is displaced from top (0 mm: endocardial) to bottom (16 mm: epicardial). From the endocardial to the epicardial end, the action potential duration decreases gradually. The measured APD₉₀ was 284 ms and 228 ms from isolated endocardial and epicardial cells. The difference in APD₉₀ is significant.

However, when cells are coupled together, the difference in APD₉₀ between endocardial and epicardial cells is reduced. This is shown in figure 4B, in which action potentials along the length of string are shown. In this case, a supra-threshold stimulation is applied at the endocardial end. The evoked excitation wave propagates from endocardium to epicardium. Due to the electronic interactions, the regional differences in action potential duration were partly reduced when electrical activity propagating through the heterogenous guinea-pig ventricular wall: the measured APD₉₀ was 282 ms at the end of endocardium and 271 ms.

In the simulation shown in figure 4B, although electrotonic interaction reduced the difference in action potential duration between the endocardial and epicardial cells, however, the sequence of depolarisation and repolarisation is consistent with experimental observations. In the figure, we can see the depolarisation starts from endocardial side, and moves towards the epicardial side, while repolarisation starts from epicardial side, moves towards the endocardial side.
 
 

Figure 5 illustrates quantitatively the changes of dispersion of action potential duration along the string by the electrotonic interactions between cells. In the figure, squares represent the data of isolated cells, circles represent the data of intact transmural string. Electrotonic coupling decreases the transmural dispersion of action potential duration.

Figure 5: Computed action potential duration measured at 90 % repolarization (APD₉₀) in isolated cells (red) and a string (blue) from endocardium to epicardium in guinea-pig ventricle. Electronic interactions between cells smooth the heterogeneity of the characteristics of action potential duration.

 

 

s	second	time
mm	millimetre	space
mV	millivolt	potential
uF	microfarad	capacitance
uS	microsiemen	conductance
nA	nanoampere	current
mM	mole per litre	concentration

 
V- transmembrane voltage, mV;
x_r1, x_r2, x_s - gating variables, 0 to 1;
[Na⁺]_i, [K⁺]_i, [Ca²⁺]_i - intracellular ion concentrations, mM;
[Na⁺]_o, [K⁺]_o, [Ca²⁺]_o - extracellular ion concentrations, mM.

 

Cm (endo)	142(10)-6 uF
Cm (epi)	132(10)-6  uF
[Na+]o	140 mM
[K+]o	4 mM
GKs (endo)	0.0013 uS
GKs (epi)	0.0020 uS
GKr1 (endo)	0.0008 uS
GKr1 (epi)	0.0010 uS
GKr2 (endo)	0.0004 uS
GKr2 (epi)	0.0008 uS
KNaCa (endo)	0.0003 nA
KNaCa (epi)	0.0001 nA
INaKmax (endo)	0.14 nA
INaKmax (epi)	0.12 nA

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