Objective To examine how epicardial activation and repolarisation patterns change in the course of ischaemia, and how these changes are related to the underlying histological structures.
Methods Langendorff perfused isolated rabbit hearts were submitted to 30 minutes of left anterior descending coronary artery occlusion followed by 30 minutes of reperfusion. A 256 channel epicardial map was plotted during the various experimental phases. Activation time points were determined as t(dU/dtmin) and repolarisation time points as t(dU/dtmax). From these data the local activation–recovery interval (ARI), its dispersion (SD of ARI), and the geometry of the activation spread could be analysed. After the experiments the hearts were processed histologically and the mapping data were projected onto histological slides.
Results There was elevation of the ST segment within the occluded area, which recovered during reperfusion. Within this area, ARI was significantly shortened and its dispersion was maximally enhanced. The enhancement of dispersion was pronounced at sites of histological inhomogeneity like fat, connective tissue, or vessels. There was also a change in the preferential direction of activation spread within the occluded zone with a marked transverse propagation of the activation wavefront, whereas under normal conditions the activation followed the longitudinal fibre axis. In addition, the total activation time in the occluded area was significantly prolonged.
Conclusions Ischaemia alters the local activation pattern with enhanced dispersion, especially at sites of histological irregularity, transverse shift of the activation waves, and a general slowing of conduction, which may explain the increased susceptibility to arrhythmia in hearts with enhanced histological irregularities—for example, an infarct or in multi-infarcted hearts, or after myocarditis.
- epicardial activation–recovery interval
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One of the most striking problems with cardiac ischaemia and reperfusion is the occurrence of severe arrhythmias, especially ventricular fibrillation. Although the underlying pathophysiological mechanisms are heterogeneous, a major role has been attributed to the rise in [K+]e 1-3 and to rises in [Ca2+]i, which seem to be associated with certain types of early afterdepolarisation.4 Furthermore, besides initiating the flow of the so called injury current5 generated by current sources and sinks, which can also induce arrhythmia, hypoxia leads to an increase in longitudinal resistance, which is believed to be caused by closure of gap junction channels.6 ,7 This cellular uncoupling may play an important role in the genesis of some forms of reentrant arrhythmia after 15 to 20 minutes of ischaemia (type Ib arrhythmia).8-12 This uncoupling is also caused by the rise in [Ca2+]i,13 ,14 metabolic acidification,15 ATP depletion,16LTB4 released from activated leucocytes,8diacylglycerols,17 and accumulation of long chain acylcarnitines.18 Uncoupling, however, is known to result in an increase in dispersion of action potential duration.19-21 From these computer simulation studies it was predicted that dispersion can be enhanced at sites of tissue inhomogeneity—for example non-excitable tissues such as vessels, fat, and connective tissue—owing to inhomogeneous current flow from excited to not yet excited tissue, but not to non-excitable sites, if conduction is slowed or uncoupling occurs. Since such a condition could occur in regional cardiac ischaemia, we tried to determine whether regional ischaemia enhances dispersion, especially in regions of inhomogeneity and at non-excitable sites.
Male New Zealand White rabbits (Fortkamp, Lengerich, Germany; fed ad libitum, body weight: 2000 to 2500 g) were killed by a sharp blow on the neck and subsequently exsanguinated. Blood clotting was prevented by intravenous administration of heparin (1000 IU/ml/kg) five minutes before the animals were killed. The heart was transferred to a Langendorff apparatus and perfused at a constant pressure of 70 cm H2O with Tyrode solution (composition (mmol/l): Na+ 161.02, K+ 5.36, Ca2+ 1.8, Mg2+ 1.05, Cl− 147.86, HCO3 − 23.8, PO4 2−0.42, glucose 11.1, equilibrated with 95% O2 and 5% CO2, 37°C). Left ventricular pressure was measured by an intraventricular balloon and coronary flow was determined volumetrically by collecting the coronary effluent. After a 45 minute equilibration period a branch of the left anterior descending coronary artery was ligated for 30 minutes followed by 30 minutes of reperfusion. The branch was chosen so that the resulting ischaemic zone was located in the centre of the electrode grid.
EPICARDIAL POTENTIAL MAPPING
To assess the electrocardiological alterations in the spontaneously beating hearts during the entire experiment, we performed epicardial potential mapping using HAL3, developed in cooperation with ELSA, Aachen, Germany, providing 256 channels with spatial resolution of 1 mm, temporal resolution 4 kHz/channel, amplitude resolution 0.04 mV, and interchannel coupling < −60 dB (further details in22-24 and fig1).
Four concave electrode grids consisting of 64 AgCl electrodes arranged in an 8×8 orthogonal fashion were each attached smoothly to the epicardium. The mapping data were processed for determination of the activation time points and repolarisation time points of each electrode as t(dU/dtmin) and t(dU/dtmax), respectively. These time points were calculated by computer and thereafter controlled by the experimenter. From these data the activation–recovery interval (ARI, corresponding to the epicardial potential duration) was calculated for all electrodes. ARI were only calculated if the QRS complex showed both a positive and a negative component and if there was a well defined T wave. Other ARI were excluded from the analysis. It has been shown by Millar and coworkers25 that changes in the ARI of unipolar epicardial potentials reflect changes in local refractory period. In addition the Qtc time was calculated as Qtc = ARI/BCL (basic cycle length). The standard deviation of the ARI, designated as ARI dispersion, was determined for each electrode grid (front, left, right and back). In order to allow a quantitative and comparative description of the activation process, an activation vector was calculated for each electrode from the activation times and the locations of the surrounding electrodes, which were activated after the central electrode.22-24 These vectors gave direction and apparent velocity of local activation. We also calculated the ST segment elevation by summing all the deviations from the isoelectric level at the 50% mean ARI time point. An increase in ST segment elevation indicates an efflux of positively charged ions during the action potential and can be used to determine the ischaemic area.26 The total activation time of each electrode grid was determined as the latency between the activation time point of the first and the last electrode activated on that grid.
After the experiment the positions of the electrode grids were marked by injection of ink and afterwards the heart was fixed and embedded in Technovit 7100. Acrylate sections 5 μm thick were cut and stained with haematoxylin and eosin. All visual fields of the ink marked tissue were scanned photographically and a histological image of the complete area was composed (yielding a 1 m2 image). Vector fields were printed on transparencies at the same scale as the histological photographs, oriented using the ink marks and overlayed on the histological image. This microscopic image with the projection of the electrode pattern and vectors was reproduced photographically. At each electrode the longitudinal fibre axis was determined and the angle between the local vector and the underlying fibre axis of the tissue could be measured, as shown schematically in fig 1. The cut depth used for graphic reproduction of the tissue was located 100 to 300 μm deep in the epicardium.
All reagents used in this study were purchased from Sigma (St Louis, Missouri, USA) and were of analytical grade unless otherwise indicated. Heparin was purchased from Serva (Heidelberg, Germany). Technovit 7100 was obtained from Heraeus-Kulzer (Wehrheim, Germany). Formaldehyde (37%) was purchased from Baker (Deventer, The Netherlands).
All values are given as means (SEM) of seven experiments. Statistical analysis was performed using analysis of variance with subsequent Student t test at a level of significance of p < 0.05.
Occlusion of the left anterior descending coronary artery resulted in a reduction of coronary flow from 21.5 (1.8) ml/min during the equilibration period to 11.2 (0.6) ml /min after 30 minutes of ischaemia (54.2(5.4)%, p = 0.02). Ischemia reduced left ventricular pressure from 81.3 (3.7) to 42 (1.3) mm Hg, a decrease of 51.7(3.1)% (p = 0.02). The ST segment elevation and the extent of ischaemia (as indicated by the ST segment elevation) were increased by ischaemia: ST—as the integral of the local ST elevations at each site—was increased from 33.2 (10.7) to 284 (42) arbitrary units (au) (p = 0.01) and the area of ST elevation was found to be 39.31 (12.75) mm2 after 30 minutes of ischaemia.
The total activation time was significantly prolonged, from 9.29 (1.55) to 23.92 (5.52) ms after 30 minutes of ischaemia, and recovered during reperfusion to 11.38 (3.36) ms within 30 minutes of reperfusion. In addition, the ARI was shortened from 159.7 (11.2) to 129.2 (13.2) ms (p = 0.03) up to the end of the ischaemic period. The dispersion—that is, the standard deviation of the epicardial ARI—increased from 7.6 (2.2) to 50.9 (4.5) ms (p = 0.02). The local dispersion was also increased.
Figure 2A shows the schematically reproduced tissue of the left ventricle under the electrode grid (square) in a typical experiment. The upper part of the figure represents the situation under control conditions while the lower shows the situation after 10 minutes of regional ischaemia. The ARI are homogeneously distributed from 190 ms (down right) to 200 ms (top) around the upper vessel section during equilibration, corresponding to a mean local ARI of 196.3 ms and a local dispersion of 2.68 ms. The main orientation of the vectors is from the upper left to bottom right. After 10 minutes of regional ischaemia of the left ventricular wall the ARI are generally shortened, as can usually be observed in ischaemic tissue. However, it can be seen that the ARI is heterogeneously shortened.
In general, we found that ARI in front of inexcitable zones were shortened by 50–60%, while behind these zones (seen in the direction of propagation) the shortening was more pronounced (60–80%) regardless of whether the local inexcitable zone was located at the border or within the centre of the ischaemic zone. While the ARI in the direction of the propagating impulse at some distance in front of the vessel ranged between 76 and 89 ms , the ARI directly in front of the vessel and in the direction of the wavefront were less shortened and varied between 97 and 153 and 97 and 152 ms, respectively. Behind the vessel—seen in the direction of the propagating impulse—the shortening was even more pronounced, with ARI ranging between 44 and 68 ms . An intermediate ARI of 101 ms could be seen to the left of the vessel. The mean local ARI of the 12 electrodes considered under these conditions was 84.6 ms, and the local dispersion increased to 34.6 ms, corresponding to a nearly 13-fold increase in ARI dispersion. Both ARI and QTc were shortened in the course of ischaemia and recovered completely during reperfusion, as shown in fig 2B and fig3. The rise in ARI dispersion starts shortly after the occlusion of the coronary artery (two minutes of ischaemia) and reaches its maximum after 10 minutes of ischaemia (fig 3B). It decreases slightly until the end of the ischaemic period.
After 30 minutes of reperfusion we found a nearly full recovery of the ARI and its dispersion. We observed similar changes in the dispersion of the repolarisation time points as well: control, 2.80 ms; two minutes of ischaemia, 18.11 ms; 10 minutes of ischaemia, 40.5 ms; two minutes of reperfusion, 10.8 ms; and 30 minutes of reperfusion, 5.72 ms. To illustrate the rise of ARI dispersion in the course of regional ischaemia, isochrones were constructed (fig 4). These isochrones encircle areas of ARI within a 10 ms range. In addition, we found dramatic changes in the activation pattern. The number of vectors with a deviation in the range of 65–90° from the fibre axis—that is, with propagation transverse to the fibre axis—increased continuously during ischaemia (p = 0.03) (fig 5) and recovered slowly during reperfusion: thus during ischaemia there was a significant transverse spread of activation.
Since an increase in dispersion is commonly believed to play an important role in the genesis of cardiac arrhythmias10 ,28-32 and since from a theoretical point of view this dispersion might be enhanced at local tissue non-uniformities, we tried to determine whether tissue inhomogeneities such as fat, connective tissue, or vessels may enhance dispersion, especially during an ischaemic period. The main outcome of this study was the finding that dispersion of ARI is enhanced at sites of tissue inhomogeneity during ischaemia, but not—or only slightly—during a normoxic control period. In addition, activation was slowed during ischaemia (that is, total activation time was increased). Moreover, the total number of vectors deviating more than 65° from the fibre axis increased during ischaemia, indicating a transverse shift of the spread of activation with respect to the histological fibre axis. It is supposed that this transverse propagation is in part caused by the gap junctional uncoupling due to ischaemia described by Tan et al.12 Generally, the longitudinal propagation of activation is more sensitive to reduced sodium channel availability, as shown by the experiments of Spach and Dolber,33 whereas transverse propagation is more sensitive to gap junctional uncoupling, as demonstrated by Delmar et al.34 However, it is not certain whether in a complex situation like ischaemia (with both gap junctional uncoupling and reduced sodium channel availability owing to depolarisation) propagation will fail in a longitudinal or a transverse direction. This probably depends on the degree of both uncoupling and depolarisation and may change in the course of ischaemia. In addition, geometric features such as the number of gap junction channels at the intercalated disk in comparison with the number of gap junctions at the lateral cell border will affect the changes in propagation. However, these geometrical features of the tissue show some species variability.
Reduction in sodium channel availability will slow the impulse propagation35 and it can be assumed that this will be enhanced by a concomitant uncoupling of the gap junctions, which are predominantly located at the intercalated disc. The ischaemia induced depolarisation will reduce sodium channel availability and will thus decrease conduction velocity (as indicated by the prolongation of the total activation time), which will result in transverse propagation since the longitudinal conduction depends mainly on sodium channel availability.
With respect to the changes in dispersion, it should be borne in mind that although changes in ARI reflect alterations in local refractory periods,25 in the acutely ischaemic myocardium this variable can also be influenced by other factors—such as, for example, the rise in extracellular potassium concentration. However, Gettes and coworkers recently showed in a very elegant study that ARI from unipolar recordings accurately reflect local action potential duration in ischaemic myocardium,36 if care is taken that only those potentials with a QRS complex with positive and negative component and a well defined T wave are evaluated. The changes in ARI cannot be equated with the postrepolarisation refractory period, but the enhanced ARI interval dispersion may also reflect an enhanced dispersion of this variable.
We propose the following mechanism for the observed enhancement of dispersion at tissue inhomogeneities during slowed conduction: if an activation wavefront approaches an inexcitable zone—for example vessels, connective tissue, or fat—it is only possible to have lateral activation, that is, current flows from the excited zone only to the lateral regions and not to the tissue behind, because this is nearly equipotential and is not in the inexcitable zone. However, behind the inexcitable zone activation propagates in three directions—that is, activation current flows to three sites and to a larger area, and thereby the activated cells behind the inexcitable zone may be exposed to a higher electrical burden and thus have shorter potentials than those in front of the inexcitable zone. If in addition the propagation velocity is reduced—for example, in the course of ischaemia, this allows a longer time for the current to flow to the small area before or the large area behind the hindrance, thereby enhancing these differences in action potential duration.
What does this mean for cardiology? An increase in dispersion is commonly believed to play an important role in the genesis of arrhythmia according to Spach et al.37 This may cause unidirectional block and self sustaining reentry resulting in sustained ventricular fibrillation,11 or result in a leading circle.38 Slowing of conduction has also long been considered a risk factor for the initiation of arrhythmias. Thus our finding of an enhanced dispersion at sites of histological inhomogeneity during ischaemia may help to explain the enhanced incidence of arrhythmia observed in hearts with histological irregularities, with enhanced histological irregularities, for example in old age, after an infarct or in multi-infarcted hearts, or after myocarditis.
We thank the Deutsche Forschungsgemeinschaft (DFG) for support of this study with grant Dh-3/1-4).
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