Stimulus-induced critical point. Mechanism for electrical initiation of reentry in normal canine myocardium

Virtual electrode-induced phase singularity: a basic mechanism of defibrillation failure

Delivery of a strong electric shock to the heart remains the only effective therapy against ventricular fibrillation. Despite significant improvements in implantable cardioverter defibrillator (ICD) therapy, the fundamental mechanisms of defibrillation remain poorly understood. We have recently demonstrated that a monophasic defibrillation shock produces a highly nonuniform epicardial polarization pattern, referred to as a virtual electrode pattern (VEP). The VEP consists of large adjacent areas of strong positive and negative polarization. We sought to determine whether the VEP may be responsible for defibrillation failure by creating dispersion of postshock repolarization and reentry. Truncated exponential biphasic and monophasic shocks were delivered from a bipolar ICD lead in Langendorff-perfused rabbit hearts. Epicardial electrical activity was mapped during and after defibrillation shocks and shocks applied at the plateau phase of a normal action potential produced by ventricular pacing. A high-resolution fluorescence mapping system with 256 recording sites and a voltage-sensitive dye were used. Biphasic shocks with a weak second phase (<20% leading-edge voltage of the second phase with respect to the leading-edge voltage of the first phase) produced VEPs similar to monophasic shocks. Biphasic shocks with a strong second phase (>70%) produced VEPs of reversed polarity. Both of these waveforms resulted in extra beats and arrhythmias. However, biphasic waveforms with intermediate second-phase voltages (20% to 70% of first-phase voltage) produced no VEP, because of an asymmetric reversal of the first-phase polarization. Therefore, there was no substrate for postshock dispersion of repolarization. Shocks producing strong VEPs resulted in postshock reentrant arrhythmias via a mechanism of phase singularity. Points of phase singularity were created by the shock in the intersection of areas of positive, negative, and no polarization, which were set by the shock to excited, excitable, and refractory states, respectively. Shock-induced VEPs may reinduce arrhythmias via a phase-singularity mechanism. Strong shocks may overcome the preshock electrical activity and create phase singularities, regardless of the preshock phase distribution. Optimal defibrillation waveforms did not produce VEPs because of an asymmetric effect of phase reversal on membrane polarization.

Progressive depolarization: a unified hypothesis for defibrillation and fibrillation induction by shocks

Experimental studies of defibrillation have burgeoned since the introduction of the upper limit of vulnerability (ULV) hypothesis for defibrillation. Much of this progress is due to the valuable work carried out in pursuit of this hypothesis. The ULV hypothesis presented a unified electrophysiologic scheme for linking the processes of defibrillation and shock-induced fibrillation. In addition to its scientific ramifications, this work also raised the possibility of simpler and safer means for clinical defibrillation threshold testing. Recent results from an optical mapping study of defibrillation suggest, however, that the experimental data supporting the ULV hypothesis could instead be interpreted in a manner consistent with traditional views of defibrillation such as the critical mass hypothesis. This review will describe the evidence calling for such a reinterpretation. In one regard the ULV hypothesis superseded the critical mass hypothesis by linking the defibrillation and shock-induced fibrillation processes. Therefore, this review also will discuss the rationale for developing a new defibrillation hypothesis. This new hypothesis, progressive depolarization, uses traditional defibrillation concepts to cover the same ground as the ULV hypothesis in mechanistically unifying defibrillation and shock-induced fibrillation. It does so in a manner consistent with experimental data supporting the ULV hypothesis but which also takes advantage of what has been learned from optical studies of defibrillation. This review will briefly describe how this new hypothesis relates to other contemporary viewpoints and related experimental results.

The induction of reentry in cardiac tissue. The missing link: How electric fields alter transmembrane potential

This review examines the initiation of reentry in cardiac muscle by strong electric shocks. Specifically, it concentrates on the mechanisms by which electric shocks change the transmembrane potential of the cardiac membrane and create the physiological substrate required by the critical point theory for the initiation of rotors. The mechanisms examined include (1) direct polarization of the tissue by the stimulating current, as described by the one-dimensional cable model and its two- and three-dimensional extensions, (2) the presence of virtual anodes and cathodes, as described by the bidomain model with unequal anisotropy ratios of the intra- and extracellular spaces, (3) polarization of the tissue due to changing orientation of cardiac fibers, and (4) polarization of individual cells or groups of cells by the electric field ("sawtooth potential"). The importance of these mechanisms in the initiation of reentry is examined in two case studies: the induction of rotors using successive stimulation with a unipolar electrode, and the induction of rotors using cross-field stimulation. These cases reveal that the mechanism by which a unipolar stimulation induces arrhythmias can be explained in the framework of the bidomain model with unequal anisotropy ratios. In contrast, none of the examined mechanisms provide an adequate explanation for the induction of rotors by cross-field stimulation. Hence, this study emphasizes the need for further experimental and theoretical work directed toward explaining the mechanism of field stimulation. (c) 1998 American Institute of Physics.

Evolving perspectives during 12 years of electrical turbulence

This Focus issue describes a problem in electrical dynamics which has fascinated generations of physiologists. There are today so many views of fibrillation that only the rarest generalization can embrace all of them. Fifty-two prominent investigators collaborate here to present aspects of the problem in these eighteen articles (including this introduction) tailored for readers whose principal expertise lies elsewhere. In "The High One's Lay" (Norse Runes, ca. 800) Odin remarks, "Much too early I came to many places: the beer was not yet ready, or was already drunk em leader " but to this one we come at very nearly the right time in 1998. This introduction attempts to guide newcomers by noting the changed or multiple meanings of novel technical terms while sorting the key facts and ideas into an order that facilitates comparison and contrast with those of a dozen years ago. This Focus issue is authored by some of the foremost innovators of both theory and experiment in this area. By assimilating their presentations the readers of Chaos can become well poised to appreciate and evaluate the definitive evidence expected in the next few years. (c) 1998 American Institute of Physics.

Reentrant waves and their elimination in a model of mammalian ventricular tissue

The vulnerability to reentrant wave propagation, its characteristics (period, meander, and stability), the effects of rotational transmural anisotropy, and the control of reentrant waves by small amplitude perturbations and large amplitude defibrillating shocks are investigated theoretically and numerically for models based on high order, stiff biophysically derived excitation equations.

Vortex dynamics in three-dimensional continuous myocardium with fiber rotation: Filament instability and fibrillation

Wave propagation in ventricular muscle is rendered highly anisotropic by the intramural rotation of the fiber. This rotational anisotropy is especially important because it can produce a twist of electrical vortices, which measures the rate of rotation (in degree/mm) of activation wavefronts in successive planes perpendicular to a line of phase singularity, or filament. This twist can then significantly alter the dynamics of the filament. This paper explores this dynamics via numerical simulation. After a review of the literature, we present modeling tools that include: (i) a simplified ionic model with three membrane currents that approximates well the restitution properties and spiral wave behavior of more complex ionic models of cardiac action potential (Beeler-Reuter and others), and (ii) a semi-implicit algorithm for the fast solution of monodomain cable equations with rotational anisotropy. We then discuss selected results of a simulation study of vortex dynamics in a parallelepipedal slab of ventricular muscle of varying wall thickness (S) and fiber rotation rate (theta(z)). The main finding is that rotational anisotropy generates a sufficiently large twist to destabilize a single transmural filament and cause a transition to a wave turbulent state characterized by a high density of chaotically moving filaments. This instability is manifested by the propagation of localized disturbances along the filament and has no previously known analog in isotropic excitable media. These disturbances correspond to highly twisted and distorted regions of filament, or "twistons," that create vortex rings when colliding with the natural boundaries of the ventricle. Moreover, when sufficiently twisted, these rings expand and create additional filaments by further colliding with boundaries. This instability mechanism is distinct from the commonly invoked patchy failure or wave breakup that is not observed here during the initial instability. For modified Beeler-Reuter-like kinetics with stable reentry in two dimensions, decay into turbulence occurs in the left ventricle in about one second above a critical wall thickness in the range of 4-6 mm that matches experiment. However this decay is suppressed by uniformly decreasing excitability. Specific experiments to test these results, and a method to characterize the filament density during fibrillation are discussed. Results are contrasted with other mechanisms of fibrillation and future prospects are summarized. (c)1998 American Institute of Physics.

Vulnerability to ventricular fibrillation

One of the factors that favors the development of ventricular fibrillation is an increase in the dispersion of refractoriness. Experiments will be described in which an increase in dispersion in the recovery of excitability was determined during brief episodes of enhanced sympathetic nerve activity, known to increase the risk of fibrillation. Whereas in the normal heart ventricular fibrillation can be induced by a strong electrical shock, a premature stimulus of moderate intensity only induces fibrillation in the presence of regional ischemia, which greatly increases the dispersion of refractoriness. One factor that is of importance for the transition of reentrant ventricular tachycardia to ventricular fibrillation during acute regional ischemia is the subendocardial Purkinje system. After selective destruction of the Purkinje network by lugol, reentrant tachycardias still develop in the ischemic region, but they do not degenerate into fibrillation. Finally, attempts were made to determine the minimal mass of thin ventricular myocardium required to sustain fibrillation induced by burst pacing. This was done by freezing of subendocardial and midmural layers. The rim of surviving epicardial muscle had to be larger than 20 g. Extracellular electrograms during fibrillation in both the intact and the "frozen" left ventricle were indistinguishable, but activation patterns were markedly different. In the intact ventricle epicardial activation was compatible with multiple wavelet reentry, in the "frozen" heart a single, or at most two wandering reentrant waves were seen. (c) 1998 American Institute of Physics.

Self-organization and the dynamical nature of ventricular fibrillation

This article reviews recent data supporting the conjecture that, in the structurally and electrophysiologically normal heart, cardiac fibrillation is not a totally random phenomenon. Experimental and numerical studies based on the theory of excitable media suggest that fibrillation in the mammalian ventricles is the result of self-organized three-dimensional (3-D) electrical rotors giving rise to scroll waves that move continuously (i.e., drift) throughout the heart at varying speeds. A brief review of studies on the dynamics of rotors in two-dimensional (2-D) and 3-D excitable media is presented with emphasis on the experimental demonstration of such dynamics in cardiac muscle of various species. The discussion is centered on rotor dynamics in the presence and the absence of structural heterogeneities, and in the phenomena of drifting and anchoring, which in the electrocardiogram (ECG) may manifest as life-threatening cardiac rhythm disturbances. For instance, in the rabbit heart, a single electrical rotor that drifts rapidly throughout the ventricles gives rise to complex patterns of excitation. In the ECG such patterns are indistinguishable from ventricular fibrillation. On the other hand, a rotor that anchors to a discontinuity or defect in the muscle (e.g., a scar, a large artery or a bundle of connective tissue) may result in stationary rotating activity, which in the ECG is manifested as a form of so-called "monomorphic" ventricular tachycardia. More recent data show that ventricular fibrillation occurs in mammals irrespective of size or species. While in small hearts, such as those of mice and rabbits, a single drifting or meandering rotor can result in fibrillation, in larger hearts, such as the sheep and possibly the human, fibrillation occurs in the form of a relatively small number of coexisting but short-lived rotors. Overall, the work discussed here has paved the way for a better understanding of the mechanisms of fibrillation in the normal, as well as diseased human heart. (c) 1998 American Institute of Physics.

Computerized mapping of fibrillation in normal ventricular myocardium

It is well known that the ability to fibrillate is intrinsic to a normal ventricle that exceeds a critical mass. The questions we address are how is ventricular fibrillation (VF) initiated and perpetuated in normal myocardium, and why is VF not seen more often in the general population if all ventricles have the ability to fibrillate. To study the mechanisms of VF, we used computerized mapping techniques with up to 512 channels of simultaneous multisite recordings for data acquisition. The data were then processed for dynamic display of the activation patterns and for mathematical analyses of the activation intervals. The results show that in normal ventricles, VF can be initiated by a single strong premature stimulus given during the vulnerable period of the cardiac cycle. The initial activations form a figure-eight pattern. Afterward, VF will perpetuate itself without any outside help. The self-perpetuation itself is due to at least two factors. One is that single wave fronts spontaneously break up into two or more wavelets. The second is that when two wavelets intersect perpendicular to each other, the second wavelet is broken by the residual refractoriness left over from the first wavelet. Mathematical analyses of the patterns of activation during VF revealed that VF is a form of chaos, and that transition from ventricular tachycardia (VT) to VF occurs via the quasiperiodic route. In separate experiments, we found that we can convert VF to VT by tissue size reduction. The physiological mechanism associated with the latter transition appears to be the reduction of the number of reentrant wave fronts and wandering wavelets. Based on these findings, we propose that the reentrant wave fronts and the wandering wavelets serve as the physiological equivalent of coupled oscillators. A minimal number of oscillators is needed for VF to perpetuate itself, and to generate chaotic dynamics; hence a critical mass is required to perpetuate VF. We conclude that VF in normal myocardium is a form of reentrant cardiac arrhythmia. A strong electrical stimulus initiates single or dual reentrant wave fronts that break up into multiple wavelets. Sometimes short-lived reentry is also generated during the course of VF. These organized reentrant and broken wavelets serve as coupled oscillators that perpetuate VF and maintain chaos. Although the ability to support these oscillators exists in a normal ventricle, the triggers required to generate them are nonexistent in the normal heart. Therefore, VF and sudden death do not happen to most people with normal ventricular myocardium. (c) 1998 American Institute of Physics.

Lidocaine's effect on defibrillation threshold are dependent on the defibrillation electrode system: epicardial versus endocardial

INTRODUCTION

Epicardial and endocardial defibrillation electrode systems affect myocardial electrophysiology and sympathetic function differently. Thus, we postulate that antiarrhythmic drugs will interact with these electrode systems differently.

METHODS AND RESULTS

Defibrillation energy requirements (DER) at 20% (ED20), 50% (ED50), and 80% (ED80) success were measured at baseline and during lidocaine (10 mg/kg per hour) or D5W treatment for epicardial and endocardial electrodes. Pigs were randomized to treatment (lidocaine or D5W) and electrode system, which resulted in four experimental groups: (1) epicardial electrode + D5W; (2) epicardial electrode + lidocaine; (3) endocardial electrode + D5W; and (4) endocardial electrode + lidocaine. ED50 DER (mean +/- SEM) values at baseline for groups 1-4 were 10.6+/-1, 8.5+/-1, 12.6+/-1, and 12.3+/-1 J, respectively. DER values for groups 1 and 3 during D5W were similar to baseline. Conversely, lidocaine increased ED50 DER values from 8.5+/-1 to 13.5+/-2 J (P < 0.05) in group 2 animals (epicardial electrodes). When lidocaine was administered to group 4 animals (endocardial electrodes), however, ED50 DER values remained similar to baseline values (12.3+/-1 to 14.3+/-2 J, P = NS). Lidocaine increased ED50 DER values by 59% with the epicardial electrode system, which was significantly greater than the 16% increase with the endocardial electrode system (P < 0.05). Electrophysiologic response and electrode impedance were similar between electrode systems.

CONCLUSION

Lidocaine increases DER values to a greater extent when using epicardial versus endocardial electrode system. Thus, drug-device interactions are dependent on the electrode system. These data suggest that the electrophysiologic milieu created by endocardial defibrillation mitigates the effects that lidocaine has on DER values.

Two forms of spiral-wave reentry in an ionic model of ischemic ventricular myocardium

It is well known that there is considerable spatial inhomogeneity in the electrical properties of heart muscle, and that the many interventions that increase this initial degree of inhomogeneity all make it easier to induce certain cardiac arrhythmias. We consider here the specific example of myocardial ischemia, which greatly increases the electrical heterogeneity of ventricular tissue, and often triggers life-threatening cardiac arrhythmias such as ventricular tachycardia and ventricular fibrillation. There is growing evidence that spiral-wave activity underlies these reentrant arrhythmias. We thus investigate whether spiral waves might be induced in a realistic model of inhomogeneous ventricular myocardium. We first modify the Luo and Rudy [Circ. Res. 68, 1501-1526 (1991)] ionic model of cardiac ventricular muscle so as to obtain maintained spiral-wave activity in a two-dimensional homogeneous sheet of ventricular muscle. Regional ischemia is simulated by raising the external potassium concentration ([K(+)](o)) from its nominal value of 5.4 mM in a subsection of the sheet, thus creating a localized inhomogeneity. Spiral-wave activity is induced using a pacing protocol in which the pacing frequency is gradually increased. When [K(+)](o) is sufficiently high in the abnormal area (e.g., 20 mM), there is complete block of propagation of the action potential into that area, resulting in a free end or wave break as the activation wave front encounters the abnormal area. As pacing continues, the free end of the activation wave front traveling in the normal area increasingly separates or detaches from the border between normal and abnormal tissue, eventually resulting in the formation of a maintained spiral wave, whose core lies entirely within an area of normal tissue lying outside of the abnormal area ("type I" spiral wave). At lower [K(+)](o) (e.g., 10.5 mM) in the abnormal area, there is no longer complete block of propagation into the abnormal area; instead, there is partial entrance block into the abnormal area, as well as exit block out of that area. In this case, a different kind of spiral wave (transient "type II" spiral wave) can be evoked, whose induction involves retrograde propagation of the action potential through the abnormal area. The number of turns made by the type II spiral wave depends on several factors, including the level of [K(+)](o) within the abnormal area and its physical size. If the pacing protocol is changed by adding two additional stimuli, a type I spiral wave is instead produced at [K(+)](o)=10.5 mM. When pacing is continued beyond this point, apparently aperiodic multiple spiral-wave activity is seen during pacing. We discuss the relevance of our results for arrythmogenesis in both the ischemic and nonischemic heart. (c) 1998 American Institute of Physics.

Characteristics of the temporal and spatial excitable gap in anisotropic reentrant circuits causing sustained ventricular tachycardia

The excitable gap of a reentrant circuit has both temporal (time during the cycle length that the circuit is excitable) and spatial (length of the circuit that is excitable at a given time) properties. We determined the temporal and spatial properties of the excitable gap in reentrant circuits caused by nonuniform anisotropy. Myocardial infarction was produced in canine hearts by ligation of the left anterior descending coronary artery. Four days later, reentrant circuits were mapped in the epicardial border zone of the infarcts with a multielectrode array during sustained ventricular tachycardia induced by programmed stimulation. During tachycardia, premature impulses were initiated by stimulation at sites around and in the reentrant circuits, and their conduction characteristics in the circuit were mapped. All circuits had a temporal excitable gap in at least part of the circuit, which allowed premature impulses to enter the circuit. Completely and partially excitable segments of the temporal gap were identified by measuring conduction velocity of the premature impulses; conduction was equal to the native reentrant wave front in completely excitable regions and slower than the reentrant wave front in partially excitable regions. In some circuits, a temporal gap existed throughout the circuit, permitting the entire circuit to be reset over a range of premature coupling intervals, although the size of the gap varied at different sites. In other circuits, the gap became so small at local sites that even though premature impulses could enter the circuit, the circuit could not be reset. Premature impulses could terminate reentry in circuits that could be reset or not. We also found a significant spatial gap, which was identified by determining the distance between the head of the circulating wave front, which could be located on the activation map, and its tail, which was the site most distal from the head as located by the site of entry of the premature wave front into the circuit. The spatial gap could also vary in different parts of the circuit. Therefore, nonuniform anisotropic reentrant circuits have both a temporal and spatial excitable gap with fully and partially excitable components that change in different parts of the circuit.

Catheter ablation for patients with atrial tachycardia

Although atrial tachycardias are relatively rare, their poor response to standard therapies, the suboptimal hemodynamic results of complete atrioventricular node ablation and pacer implantation, and their potential for serious hemodynamic effects make management difficult. Although their mechanisms are complex and divergent, catheter ablation has proven to be highly effective in management of atrial tachycardias. This article discusses arrhythmia mechanisms and therapeutic approaches by catheter ablation.

Cellular electrophysiologic mechanisms of cardiac arrhythmias

Cardiac arrhythmias are caused by alterations in the electrophysiologic properties of the cardiac cells, which affect the characteristics of the transmembrane potentials. The electrophysiologic properties that cause arrhythmias are automaticity, triggered activity, and reentrant excitation. Each of these mechanisms is described in terms of the characteristics of the transmembrane potentials and how these influence the appearance of the arrhythmia on the electrocardiogram.

Internal cardioversion of chronic atrial fibrillation in patients

Transvenous internal cardioversion of chronic AF using a right atrium (RA) coronary sinus (CS) vector requires more energy than cardioversion of paroxysmal AF. Chronic AF is not terminated in 25% of patients using biphasic shocks up to 10 J. We therefore evaluated efficacy, safety, and tolerability of internal cardioversion using a "unipolar" configuration (RA to skin patch) and biphasic shocks in patients with long-lasting AF and different heart disease. In each patient, biphasic R wave synchronous shocks were delivered between a large defibrillating surface area electrode in the RA and a skin patch in the left prepectoral position. Defibrillation protocol started with a test shock of 0.4 J. Shocks were repeated and increased until termination of AF or a maximum of 34 J. Sedation was used when the patient described the shock as painful. This study included 11 patients with a mean age of 67 +/- 8 years (range 56-83). AF duration was > or = 1 month in all patients with a mean duration of 11 +/- 11 months (range 2-36). Underlying heart disease was present in all patients and the mean left atrial dimension was 43 +/- 9 mm (range 26-57). AF was terminated in 10 of 11 patients (91%) with a mean delivered energy of the successful shocks of 18.7 +/- 8.7 J (median energy 16.9 J; range 7.3-32.5) and a mean leading edge voltage of 564 +/- 129 V. The mean shock impedance at the defibrillation threshold was 71 +/- 13 omega (range 59-103). A total of 131 shocks were delivered without any complication and proarrhythmia episodes. We conclude that low energy "unipolar" internal cardioversion is a simple, safe, and effective technique for termination of chronic AF in patients with heart disease. The procedure is often tolerated under light sedation.

Shock-induced dispersion of ventricular repolarization: implications for the induction of ventricular fibrillation and the upper limit of vulnerability

INTRODUCTION

Shock-induced dispersion of ventricular repolarization (SIDR) caused by an electrical field stimulus has been suggested as a mechanism of ventricular fibrillation (VF) induction; however, this hypothesis has not been studied systematically in the intact heart. Likewise, the mechanism underlying the upper (ULV) and lower (LLV) limit of vulnerability remains unclear.

METHODS AND RESULTS

In eight Langendorff-perfused rabbit hearts, monophasic action potentials were recorded simultaneously from ten different sites of both ventricles. Truncated biphasic T wave shocks were randomly delivered at various coupling intervals and strengths, exceeding the vulnerable window, ULV, and LLV, SIDR, defined as the difference between the longest and shortest postshock repolarization times, was 64 +/- 15 msec for shocks inducing VF. SIDR was 41 +/- 17 msec for shocks delivered above the ULV, and 33 +/- 14 and 27 +/- 8 msec for shocks delivered 10 msec before and after the vulnerable window, respectively (all P < 0.01 vs VF-inducing shocks). Although SIDR was larger for shocks delivered below the LLV (93 +/- 24 msec, P < 0.01 vs VF-inducing shocks), the repolarization extension was significantly smaller for shocks below the LLV (10.3% +/- 3.9% vs 16.3% +/- 4.9%, P < 0.01).

CONCLUSION

SIDR is influenced by the shock timing and intensity. Large SIDR within the vulnerable window and an SIDR decrease toward its borders suggest that SIDR is essential for VF induction. The decrease in SIDR toward greater shock strengths may explain the ULV. Small repolarization extension for shocks below the LLV may explain why these shocks, despite producing large SIDR, fail to induce VF.

Can catheter ablation in cardiac arrest survivors prevent ventricular fibrillation recurrence?

Ventricular tachyarrhythmias are the most common cause for sudden cardiac death. The success of catheter ablation for supraventricular tachycardias led to the supposition that ablation could also be used in the treatment of ventricular tachycardias. Despite the promising results in bundle branch reentry and some forms of idiopathic ventricular tachycardia, the success rate in patients with coronary artery disease is still low. There is hope that new approaches to reliably localize the critical region of the tachycardia and new ablation techniques to create larger areas of injury may lead to a wider application of ablation therapy in the treatment of ventricular tachycardia. Survivors of cardiac arrest typically have more rapid and unstable arrhythmias than patients with sustained ventricular tachycardia, and these rapid arrhythmias frequently degenerate into ventricular fibrillation. The instability of the arrhythmia makes it impossible to localize the arrhythmia origin with current mapping techniques. Experimental and clinical data, however, suggest that these arrhythmias also frequently start from a localized area of electrical activation. With developments in mapping techniques and energy delivery, catheter ablation may soon become a feasible therapeutic approach in some patients with unstable arrhythmias. The article discusses the prerequisites for this approach and suggests the patients who may be appropriate candidates for this technique.

Technical features of a CCD video camera system to record cardiac fluorescence data

A charge-coupled device (CCD) camera was used to acquire movies of transmembrane activity from thin slices of sheep ventricular epicardial muscle stained with a voltage-sensitive dye. Compared with photodiodes, CCDs have high spatial resolution, but low temporal resolution. Spatial resolution in our system ranged from 0.04 to 0.14 mm/pixel; the acquisition rate was 60, 120, or 240 frames/sec. Propagating waves were readily visualized after subtraction of a background image. The optical signal had an amplitude of 1 to 6 gray levels, with signal-to-noise ratios between 1.5 and 4.4. Because CCD cameras integrate light over the frame interval, moving objects, including propagating waves, are blurred in the resulting movies. A computer model of such an integrating imaging system was developed to study the effects of blur, noise, filtering, and quantization on the ability to measure conduction velocity and action potential duration (APD). The model indicated that blurring, filtering, and quantization do not affect the ability to localize wave fronts in the optical data (i.e., no systematic error in determining spatial position), but noise does increase the uncertainty of the measurements. The model also showed that the low frame rates of the CCD camera introduced a systematic error in the calculation of APD: for cutoff levels > 50%, the APD was erroneously long. Both noise and quantization increased the uncertainty in the APD measurements. The optical measures of conduction velocity were not significantly different from those measured simultaneously with microelectrodes. Optical APDs, however, were longer than the electrically recorded APDs. This APD error could be reduced by using the 50% cutoff level and the fastest frame rate possible.

Cellular graded responses and ventricular vulnerability to reentry by a premature stimulus in isolated canine ventricle

BACKGROUND

The cellular mechanism by which a point strong premature stimulus (S2) induces reentry is unknown. We hypothesized that cellular graded responses induced by an S2 mediate and control tissue vulnerability to reentry.

METHODS AND RESULTS

Reentry is induced in normal canine ventricular epicardial slices (30x38x2 mm, n=30) by an S2 at intervals shorter than the effective refractory period. The S1 is applied at the edge and the S2 at the center of the tissue. The line connecting the S1-S2 sites is parallel to the long axis of the fiber orientation. Isochronal activation maps were constructed with 56 to 480 bipolar electrodes, and the activation pattern was visualized dynamically. Reentry induced by an S2 is mediated by the graded responses as follows: The induced graded responses propagate with decrement toward recovered cells. When the amplitude of the propagated depolarizing graded responses reaches threshold relative to the recovering cells, an action potential is initiated along the fiber 2 to 3 mm away from the cathode of the S2. The distally initiated activation wave front blocks near the S2 site because the same S2-induced graded response prolongs the refractory period. The "broken" wave front then circulates around both sides of the block and reenters when the site of block recovers its excitability, completing the first figure-eight reentry cycle. Reentry cannot be induced when the S2 strength is >72+/-21 mA (upper limit of vulnerability) because these strong S2-induced graded responses convert the unidirectional block to bidirectional block by excess prolongation of the refractoriness.

CONCLUSIONS

We conclude that the magnitude and the propagation of S2-induced cellular graded responses mediate and control vulnerability to reentry in the ventricular epicardium.

Optical mapping of drug-induced polymorphic arrhythmias and torsade de pointes in the isolated rabbit heart

OBJECTIVES

This study sought to 1) test the hypothesis that in the setting of bradycardia and drug-induced action potential prolongation, multiple foci of early afterdepolarizations (EADs) result in beat to beat changes in the origin and direction of the excitation wave front and are responsible for polymorphic arrhythmias; and 2) determine whether EADs may initiate nonstationary reentry, giving rise to the typical torsade de pointes (TDP) pattern.

BACKGROUND

In the past, it has been difficult to associate EADs or reentry with the undulating electrocardiographic (ECG) patterns of TDP.

METHODS

A voltage-sensitive dye was used for high resolution video imaging of electrical waves on the epicardial and endocardial surface of the Langendorff-perfused rabbit heart. ECG and monophasic action potentials from the right septal region were also recorded. Bradycardia was induced by ablation of the atrioventricular node.

RESULTS

Perfusion of low potassium chloride Tyrode solution plus quinidine led to prolongation of the action potential and the QT interval. Eventually, EADs and triggered activity ensued, giving rise to intermittent episodes of polymorphic arrhythmia. In one experiment, triggered activity was followed by a long episode of vortex-like reentry with an ECG pattern characteristic of TDP. However, in most experiments, focal activity of varying origins and propagation patterns was observed. Triggered responses also showed varying degrees of local block. Similar results were obtained with E-4031. Burst pacing both at control conditions and in the presence of quinidine consistently led to vortex-like reentry whose ECG pattern resembled TDP. However, the cycle length of the arrhythmia with quinidine was longer than that for control ([mean +/- SEM] 194 +/- 12 vs. 132 +/- 8 ms, p < 0.03).

CONCLUSIONS

Drug-induced polymorphic ventricular arrhythmias may result from beat to beat changes in wave propagation patterns initiated by EADs or EAD-induced nonstationary reentrant activity. In contrast, burst pacing-induced polymorphic tachycardia in the presence or absence of drugs is the result of nonstationary reentrant activity.

[Mechanisms of electrical defibrillation]

Ventricular fibrillation has been described as a "chaotic, random, asynchronous electrical activity of the ventricles due to repetitive reentrant excitation and/or rapid focal discharge". Reentrant and non-reentrant mechanisms are responsible for the initiation of ventricular fibrillation. After fibrillation has been induced, it is thought that multiple, disorganized, wandering wavelets follow constantly changing reentrant pathways. Electrical defibrillation is the only valid therapeutic approach for ventricular fibrillation. A successful defibrillation shock must be of sufficient strength to stop fibrillation but must not be so strong that damage to the myocardium occurs. The clinical use of the implantable cardioverter/defibrillator device has significantly stimulated research in the field of cardiac defibrillation. In order to develop more efficient shock waveforms and electrode configurations for smaller, and also longer lasting devices, we need a better understanding of the basic mechanisms of defibrillation. The development of computerized electrical mapping systems, capable of recording before, during and after a defibrillation shock, optical recording systems and microelectrodes, for action potential recording before and after the shock application and mathematical models have contributed much to the understanding of defibrillation mechanisms.An electrical shock hits the cardiac cells in different phases of their action potential. This results in 1) direct activation, 2) a "graded response", or 3) no effect. "Graded response" produces prolongation of the action potential and prolongs refractoriness without giving rise to a propagated activation front. Refractory period prolongation in an area that is still refractory at the time of the shock is critical for successful defibrillation. Mapping studies have shown that for successful defibrillation with monophasic shocks a minimal potential gradient of 5-7 V/cm is necessary (the exact value depends on the waveform and the orientation of the cells with respect to the electric field).Several hypotheses have been developed in order to explain the mechanisms that underlie successful defibrillation shocks. This paper will discuss the various theories. The "upper limit of vulnerability" hypothesis for defibrillation states that a successful defibrillation shock must stop existing activation fronts by directly exciting or by prolonging refractoriness just in front of the upcoming activation fronts and must not give rise to new activation fronts at the border of the directly excited area. Shocks slightly weaker then necessary to defibrillate stop fibrillation activation fronts, but give rise to new activation fronts that reinitiate fibrillation. These new activation fronts arise at a "critical point," where a critical shock potential gradient interferes with a critical degree of tissue refractoriness. Mappping studies support the "upper limit of vulnerability" hypothesis of defibrillation but not all defibrillation failures, however, can be explained by this hypothesis.Clinical data and experimental results have shown that biphasic shocks may have lower defibrillation thresholds than monophasic shocks. The advantage of defibrillation with a biphasic waveform is not yet clearly understood. We discuss some possible reasons why some biphasic waveforms have lower defibrillation thresholds than monophasic waveforms.

Spirals, chaos, and new mechanisms of wave propagation

The chaos theory is based on the idea that phenomena that appear disordered and random may actually be produced by relatively simple deterministic mechanisms. The disordered (aperiodic) activation that characterizes a chaotic motion is reached through one of a few well-defined paths that are characteristic of nonlinear dynamical systems. Our group has been studying VF using computerized mapping techniques. We found that in electrically induced VF, reentrant wavefronts (spiral waves) are present both in the initial tachysystolic stage (resembling VT) and the later tremulous incoordination stage (true VF). The electrophysiological characteristics associated with the transition from VT to VF is compatible with the quasiperiodic route to chaos as described in the Ruelle-Takens theorem. We propose that specific restitution of action potential duration (APD) and conduction velocity properties can cause a spiral wave (the primary oscillator) to develop additional oscillatory modes that lead to spiral meander and breakup. When spiral waves begin to meander and are modulated by other oscillatory processes, the periodic activity is replaced by unstable quasiperiodic oscillation, which then undergoes transition to chaos, signaling the onset of VF. We conclude that VF is a form of deterministic chaos. The development of VF is compatible with quasiperiodic transition to chaos. These results indicate that both the prediction and the control of fibrillation are possible based on the chaos theory and with the advent of chaos control algorithms.

The zone of vulnerability to T wave shocks in humans

INTRODUCTION

Shocks during the vulnerable period of the cardiac cycle induce ventricular fibrillation (VF) if their strength is above the VF threshold (VFT) and less than the upper limit of vulnerability (ULV). However, the range of shock strengths that constitutes the vulnerable zone and the corresponding range of coupling intervals have not been defined in humans. The ULV has been proposed as a measure of defibrillation because it correlates with the defibrillation threshold (DFT), but the optimal coupling interval for identifying it is unknown.

METHODS AND RESULTS

We studied 14 patients at implants of transvenous cardioverter defibrillators. The DFT was defined as the weakest shock that defibrillated after 10 seconds of VF. The ULV was defined as the weakest shock that did not induce VF when given at 0, 20, and 40 msec before the peak of the T wave or 20 msec after the peak in ventricular paced rhythm at a cycle length of 500 msec. The VFT was defined as the weakest shock that induced VF at any of the same four intervals. To identify the upper and lower boundaries of the vulnerable zone, we determined the shock strengths required to induce VF at all four intervals for weak shocks near the VFT and strong shocks near the ULV. The VFT was 72 +/- 42 V, and the ULV was 411 +/- V. In all patients, a shock strength of 200 V exceeded the VFT and was less than the ULV. The coupling interval at the ULV was 19+/- 11 msec shorter than the coupling interval at the VFT (P < 0.001). The vulnerable zone showed a sharp peak at the ULV and a less distinct nadir at the VFT. A 20-msec error in the interval at which the ULV was measured could have resulted in underestimating it by a maximum of 95 +/- 31 V. The weakest shock that did not induce VF was greater for the shortest interval tested than for the longest interval at both the upper boundary (356 +/- 108 V vs 280 +/- 78 V; P < 0.01) and lower boundary (136 +/- 68 msec vs 100 +/- 65 msec; P < 0.05).

CONCLUSIONS

The human vulnerable zone is not symmetric with respect to a single coupling interval, but slants from the upper left to lower right. Small differences in the coupling interval at which the ULV is determined or use of the coupling interval at the VFT to determine the ULV may result in significant variations in its measured value. An efficient strategy for inducing VF would begin by delivering a 200-V shock at a coupling interval 10 msec before the peak of the T wave.

Induction of ventricular fibrillation by T-wave field-shocks in the isolated perfused rabbit heart: role of nonuniform shock responses

OBJECTIVES

Single electrical field shocks are able to induce ventricular fibrillation (VF) if applied during the vulnerable period. During this period, a shock can either prolong the action potential duration or induce a new action potential. Whether the occurrence of different shock responses contributes to the induction of VF has not been investigated directly in the intact heart.

METHODS

In 12 isolated Langendorff-perfused rabbit hearts seven monophasic action potentials (MAPs) were recorded simultaneously during the application of 838 T-wave shocks. Post-shock repolarization was assessed by classifying the shock-induced response in each MAP recording either as a full action potential or an action potential prolongation. Heterogeneity of post-shock repolarization was defined if both response patterns were present in different MAP recordings at the same time. The heterogeneity of post-shock activation was measured as the dispersion of the post-shock activation time (PS-AT). The arrhythmogeneity of a shock was quantified as the number of rapid shock-induced repetitive responses.

RESULTS

Shocks inducing nonuniform repolarization were associated with greater arrhythmogeneity than shocks inducing uniform repolarization (17.6 +/- 30.0 versus 1.6 +/- 1.1 shock-induced repetitive responses, p < 0.001). The severity of the induced arrhythmia increased gradually with increasing nonuniformity of repolarization (p < 0.01 for a 10% increase), being maximal when the shock initiated near equal numbers of both full action potentials and action potential prolongations. The induction of severe arrhythmias by T-wave shocks was also associated with a higher dispersion of PS-AT (29 +/- 14 ms for the induction of VF, 19 +/- 12 ms for non-sustained arrhythmia, and 12 +/- 8 ms for no arrhythmic response, all p < 0.001). For VF inducing shocks, an increase in shock strength towards the upper limit of vulnerability decreased the dispersion of PS-AT from 34 +/- 15 ms to 23 +/- 11 ms (p < 0.001).

CONCLUSIONS

Nonuniform post-shock repolarization and dispersed post-shock activation contribute to the induction of VF by T-wave shocks. A decreasing dispersion of PS-AT towards higher shock strengths may contribute to the decreased or abolished inducibility by shocks above the upper limit of vulnerability.

Vortices with linear cores in excitable media

Most naturally occurring excitable media exhibit vortex waves with circular cores. It has been reported that the spiral wave activity in cardiac muscle may revolve around longitudinal or elliptical cores. Here we demonstrate that spiral wave vortices with cores resembling a long line may result from decreasing a small parameter which affects the recovery time in an isotropic and homogeneous excitable reaction-diffusion model. The model results compare well with experimental data in cardiac muscle.

Atrial fibrillation/flutter induced by implantable ventricular defibrillator shocks: difference between epicardial and endocardial energy delivery

INTRODUCTION

We evaluated the incidence and energy dependence of atrial fibrillation/flutter (AF) induced by implantable ventricular defibrillator shocks in 63 patients tested in the operating room or electrophysiology laboratory.

METHODS AND RESULTS

Defibrillator shocks were epicardial monophasic in 32 patients, and through an Endotak lead endocardial monophasic in 19 and biphasic in 12 patients. The epicardial and endocardial patient groups had similar clinical characteristics. A total of 517 defibrillator shocks were given. The epicardial group received 336 total defibrillator shocks and 10 +/- 6 shocks (mean +/- SD) per patient compared with the endocardial group, which received 181 total shocks and 6 +/- 4 defibrillator shocks per patient (P = 0.004). In the epicardial group, AF occurred in 13 (41%) patients and in 17 (5%) of the 336 shocks. No AF was induced with endocardial defibrillator shocks. The epicardial mean energy was 16 +/- 9 J, lower than the endocardial mean energy of 20 +/- 9 J (P < 0.004). In the epicardial monophasic group, energy correlated with AF induction. Each patient received 7 +/- 6 defibrillator shocks < 15 J and 4 +/- 2 shocks > or = 15 J, yet AF occurred in only 2.3% versus 9.6% (P < 0.05) of defibrillator shocks < 15 J and > or = 15 J, respectively. Of note, AF was not induced with energy < 4 J or > 31 J.

CONCLUSIONS

In the epicardial configuration, AF induction is energy dependent, with an apparent lower and upper limit of vulnerability. AF induction by defibrillator shocks delivered through an Endotak lead is very rare, possibly related to an apparent upper limit of vulnerability of less energy, avoidance of thoracotomy, or different energy field distribution.

Modeling the interaction between propagating cardiac waves and monophasic and biphasic field stimuli: the importance of the induced spatial excitatory response

INTRODUCTION

Biphasic (BP) defibrillation waveforms have been shown to be significantly more efficacious than equivalent monophasic (MP) waveforms. However, when defibrillation fails, it tends to do so first in distal regions of the heart where induced field gradient magnitudes are lowest. We tested the hypothesis that the improved efficacy of BP waveforms results from their enhanced ability to prevent the initiation of new postshock activation fronts behind preexisting wavetails, rather than from any significantly improved ability to terminate preexisting wavefronts.

METHODS AND RESULTS

An idealized computer model of a one-dimensional cardiac strand was used to investigate the spatial and temporal interactions between an underlying propagation front (or tail) and uniform MP or BP field stimuli of various intensities. Axial discontinuities from intercellular junctions induced sawtooth patterns of polarization during such field stimuli, enabling the shocks to interact directly with all cells. MP and BP diastolic thresholds were essentially equal. All suprathreshold MP and BP field stimuli successfully terminated preexisting wavefronts by directly depolarizing tissue ahead of those fronts, thus blocking their continued progression. However, the postshock response at the wavetail was significantly dependent on the shape and strength of the administered field. Low-strength MP stimuli induced an all-or-none excitation response across the wavetail, producing a sharp spatial transmembrane voltage gradient from which a new sustained anterogradely propagating wavefront was initiated. In contrast, low-strength BP field stimuli induced a spatially graded excitatory response whose voltage gradient was insufficient to initiate such a wavefront. Higher-strength MP and BP stimuli both produced graded excitatory responses with no subsequent propagation.

CONCLUSIONS

Shock-induced spatial "all-or-none" excitatory responses facilitate, and graded excitatory responses prevent, the postshock initiation of new propagating wavefronts. Moreover, BP field stimuli can induce such graded excitatory responses at significantly lower stimulus strengths than otherwise equivalent MP stimuli. Therefore, these results support an alternative "graded excitatory response" mechanism for the improved efficacy of BP over MP field stimuli in low gradient regions.

Comparative reproducibility of defibrillation threshold and upper limit of vulnerability

The upper limit of vulnerability (ULV) is the strength at or above which VF is not induced when a stimulus is delivered during the vulnerable phase of the cardiac cycle. Previous studies have demonstrated a statistically significant correlation between the ULV and the defibrillation threshold (DFT) in groups of patients. However, the correlation between ULV and DFT may not be close in individual patients. This imperfect correlation may be due to physiological factors or to limitations of the measurement methods. The reproducibility of either DFT or ULV has not been studied critically. The purpose of this study was to compare the reproducibility of clinically applicable methods for determination of DFT and ULV. We prospectively studied 25 patients with a transvenous implantable cardioverter defibrillator (Medtronic 7219D) at postoperative electrophysiological study. DFT was defined as the lowest energy that defibrillated after 10 seconds of VF. The ULV was defined as the lowest energy that did not induce VF with three shocks at 0, 20, and 40 ms before the peak of the T wave in ventricular paced rhythm at a cycle length of 500 ms. Both the DFT and the ULV were determined twice for biphasic pulses using a three-step, midpoint protocol. There was no significant difference between the two determinations of DFT (10.1 +/- 5.9 J vs 10.4 +/- 5.8 J), the two determinations of ULV (13.4 +/- 6.8 J vs 13.8 +/- 6.6) or the DFT-ULV Pearson correlation coefficients for each determination (0.84, P < 0.001 vs 0.75, P < 0.001). To analyze reproducibility, Lin concordance coefficients for second determination versus first determination were constructed for both ULV and DFT. This coefficient is similar to the Pearson correlation coefficient, but measures closeness to the line of identity rather than the line of regression. The Lin concordance coefficient for ULV was higher than that for DFT (0.93, 95% CI 0.85-0.97 vs 0.64, 95% CI 0.33-0.82; P < 0.01). For paired comparison of defibrillation efficacy under different experimental conditions, the sample sizes required to detect differences of 2 J, 3 J, and 4 J (80% power, P < 0.05) were 52, 24, and 15 for DFT versus 15, 8, and 6 for ULV. We conclude that a simple, clinically applicable method for determination of ULV is more reproducible than the single point DFT. Measured correlations between the ULV and single point are limited by the reproducibility of the DFT measurement.

Shock-induced depolarization of refractory myocardium prevents wave-front propagation in defibrillation

The elimination of most, if not all, propagating wave fronts of electrical activation by a shock constitutes a minimum prerequisite for successful defibrillation. However, the factors responsible for the prevention of postshock propagating activity are unknown. We investigated the determinants of this effect of defibrillation shocks in 23 Langendorff-perfused rabbit hearts by optically mapping cardiac cellular electrical activity by means of laser scanning. The optical action potentials obtained by this method were continuously recorded from 100 ventricular epicardial sites before, during, and after shock delivery during fibrillation. Analysis of activation maps showed that postshock propagating activity arose from areas depolarized by the shock. In 273 shock episodes, 898 sites at the border of shock-depolarized areas (BSDAs) from which wave-front propagation could have arisen were identified. The incidence of postshock propagation from BSDA sites was inversely related to refractoriness, as indexed by coupling interval (CI) or the optical takeoff potential (Vm). Specifically, there was a near-zero probability of postshock propagation if the shock caused depolarization at CIs < 50% of the fibrillation cycle length or from myocardium still depolarized to > or = 60% of the amplitude of a paced action potential (APA). Furthermore, incidences of wave-front propagation following shocks were consistently lower than the propagation incidences of naturally occurring unshocked fibrillation wave fronts, at comparable CIs and Vms. We conclude that the incidence of postshock wave-front propagation decreases with increasing refractoriness at the BSDA and that shock-induced depolarization of effectively refractory myocardium (ie, depolarized to > or = 60% APA) is required to guarantee the cessation of continued wave-front propagation in defibrillation.

Setting of relatively low energy outputs may permit implantation of a nonthoracotomy automatic cardioverter defibrillator system when high energy outputs prove ineffective

At intraoperative testing of defibrillation thresholds during implantation of internal cardioverter defibrillators, standard step-down approaches of energy outputs are used. If relatively high energy outputs are not successful at defibrillating the heart, the electrodes are frequently reconfigured. When attempting implantation of a nonthoracotomy lead system, high defibrillation thresholds may warrant opening of the chest cavity to place one or more epicardial electrodes. A case is presented where a nonthoracotomy system was able to be implanted using relatively low energy outputs which were reproducibly successful at terminating ventricular fibrillation when higher energy outputs were unsuccessful. Mechanisms for this phenomenon and alternate recommendations for defibrillation testing are presented.

The electrophysiological mechanism of ventricular arrhythmias in the long QT syndrome. Tridimensional mapping of activation and recovery patterns

We have previously developed a canine in vivo model of the long QT syndrome (LQTS) using the neurotoxin anthopleurin A (AP-A), which acts by slowing sodium channel inactivation. The recent discovery of a genetic mutation in the cardiac sodium channel in some patients with the congenital LQTS, resulting in abnormal gating behavior similar to sodium channels exposed to AP-A, provides a strong endorsement of this animal model as a valid surrogate to the clinical syndrome of LQTS. In the present study, we conducted high-resolution tridimensional isochronal mapping of both activation and repolarization patterns in puppies exposed to AP-A that developed LQTS and polymorphic ventricular tachyarrhythmias (VTs). To map repolarization, we measured activation-recovery intervals (ARIs) using multiple unipolar extracellular electrograms. We demonstrated, for the first time in vivo, the existence of spatial dispersion of repolarization in the ventricular wall and differences in regional recovery in response to cycle-length changes that were markedly exaggerated after AP-A administration. Analysis of tridimensional activation patterns showed that the initial beat of polymorphic VT consistently arose as focal activity from a subendocardial site, whereas subsequent beats were due to successive subendocardial focal activity, reentrant excitation, or a combination of both mechanisms. Reentrant excitation was due to infringement of a focal activity on the spatial dispersion of repolarization, resulting in functional conduction block and circulating wave fronts. The polymorphic QRS configuration of VT in the LQTS was due to either changing the site of origin of focal activity, resulting in varying activation patterns, or varying orientations of circulating wave fronts.

Effects of a class III antiarrhythmic drug and biphasic shocks on the postdefibrillation refractory period of relatively refractory myocardium

INTRODUCTION

This study was designed to test whether the refractory state of nondepolarized myocardium is a major determinant of electrical defibrillation.

METHODS AND RESULTS

Postshock recovery interval (PSRI) was estimated by measuring the residual refractory period after an appropriately timed field stimulus (1 to 16 V). The PSRI and transcardiac defibrillation threshold (DFT) were compared before and during the administration of E-4031, a new Class III antiarrhythmic drug (group 1, n = 10), or between monophasic and biphasic shocks (group 2, n = 14) in anesthetized open chest dogs. Group 1: E-4031 reduced the DFT from 2.6 +/- 0.6 J to 1.8 +/- 0.6 J (P < 0.01). The PSRI increased with the increase of the applied voltage and was almost always greater during E-4031 infusion than at baseline. There was an inverse correlation between the changes of DFT and PSRI measured with a 14-V stimulus (r = -0.80, P < 0.01) and a 16-V stimulus (r = -0.80, P < 0.01). Group 2: Mean DFTs were not statistically different between the two waveforms (3.3 +/- 1.0 J vs 2.9 +/- 1.4 J). However, there also was an inverse correlation between the differences in individual PSRIs and DFTs of the two waveforms (10-V stimulus: r = -0.62, P < 0.05; 16-V stimulus: r = -0.75, P < 0.01).

CONCLUSIONS

Modulation of defibrillation efficiency by E-4031 infusion or by changes of the shock waveform was related to the effect of these interventions on PSRI. These results suggest an independent role for the refractoriness of nondepolarized myocardium in the mechanism of defibrillation.

Reentrant wave fronts in Wiggers' stage II ventricular fibrillation. Characteristics and mechanisms of termination and spontaneous regeneration

The mechanisms of Wiggers' stage II ventricular fibrillation (VF) are poorly understood. Using computerized mapping techniques, we studied the patterns of activation during Wiggers' stage II VF in 13 open-chest dogs. In 7 of the 13 dogs, the right ventricular Purkinje fibers and adjacent subendocardial myocytes were ablated with Lugol solution. VF was induced electrically, and 3 to 5 seconds of data were obtained beginning approximately 2.5 seconds after the onset of VF. Dynamic displays of the activation patterns and isochronal maps revealed the presence of reentrant wave fronts in 17 of 33 runs of VF in ablated ventricles and in 12 of 45 runs of VF in intact ventricles. The incidence of reentry was not different between the subendocardium-ablated group versus the nonablated group (1.7 +/- 1.6 versus 1.2 +/- 1.6 rotations per episode of VF, P = .19). There were no differences in the core size (25 +/- 19 versus 29 +/- 18 mm2), life span (3.4 +/- 1.1 versus 3.2 +/- 1.2 rotations), or cycle length (111 +/- 12 versus 107 +/- 8 ms) in ablated ventricles versus intact ventricles, respectively. The core was unstable as it meandered within the mapped area displacing the entire reentrant wave front. In all episodes, the reentrant wave fronts were spontaneously initiated by an interaction between two propagating wave fronts roughly perpendicular to each other. The second wave front met the tail of the first wave front 69 +/- 11 ms (range, 40 to 90 ms) after its latest activation, indicating that the interaction occurred during a vulnerable period. The reentrant wave fronts terminated spontaneously (n = 7), as the result of interference by an invading wave front (n = 19 or meandered off the mapped region (n = 3). We conclude the following: (1) Reentrant activities with short life spans and meandering cores are present during Wiggers' stage II VF in dogs. (2) New reentrant wave fronts are generated when one wave front interacts with another wave front during its vulnerable period. (3) The reentrant wave fronts terminate spontaneously or as the result of interference. (4) Chemical subendocardial ablation does not affect the incidence, life span, cycle length, or core size of the reentrant wave fronts.

Ventricular fibrillation induction using nonsynchronized low energy external shock during rapid ventricular pacing: method of induction when fibrillation mode of ICD fails

Third-generation implantable cardioverter defibrillators (ICD) are frequently implanted with nonthoracotomy systems and provide noninvasive methods for electrical stimulation and ventricular fibrillation induction. These modalities facilitate postoperative testing of the ICD. Rapid right ventricular burst pacing via the defibrillator is commonly used for initiation of ventricular tachyarrhythmias. However, with the available third-generation devices, ventricular fibrillation (VF) induction may be impossible in up to 19% of the patients. In these cases, transvenous placement of a right ventricular catheter has been required to generate VF and appropriately evaluate the device. We report a new technique of noninvasive induction of VF using a low energy external nonsynchronized shock delivered during ICD fibrillation induction pacing. In three patients, after all efforts to induce VF by the Ventritex Cadence V-100 had failed, a 20 J nonsynchronized shock was delivered during rapid RV pacing. This resulted in VF on the first attempt in all patients. This noninvasive technique of VF initiation may provide a useful clinical approach to ICD testing that eliminates the costs and risks of an invasive procedure.

Induced termination of fibrillation

A previous communication in the Creative Musings section of this Journal summarized additions to the wavelet hypothesis related to the initiation of cardiac fibrillation. That hypothesis is also relevant to the termination of fibrillation, and further additions related to that event are presented in this report. Findings in both reports were obtained with a computer model based on the wavelet hypothesis, and results concerning initiation and termination of fibrillation were closely related. Refractory period (RP) conditions that terminated fibrillation were the inverse of those that increased vulnerability to the initiation of fibrillation. Increased RP range or decreased RP duration increased vulnerability to the initiation of fibrillation and decreased RP range or increased RP duration were capable of terminating fibrillation. Slow propagation increased vulnerability to initiation of fibrillation and acted to sustain fibrillation when instituted during fibrillation. The combination of increased duration and decreased range of RPs was more effective in terminating fibrillation than either alone. The magnitude of increased RP duration or decreased RP range required to terminate fibrillation and the effects of slow propagation on the maintenance of fibrillation depended on RP duration and range present during fibrillation. The findings extend the wavelet hypothesis of the nature of fibrillation to the prediction of conditions required to terminate fibrillation.

Effects of flecainide, encainide, and clofilium on ventricular refractory period extension by transcardiac shocks

OBJECTIVE

The mechanisms by which pharmacological agents alter electrical defibrillation are not fully understood. It has been proposed that, in addition to directly stimulating tissue, defibrillation may involve refractory period extension (RPE) produced by the shock. Accordingly, pharmacological agents might modulate defibrillation by altering RPE. This study examined the effect of Class I and Class III antiarrhythmic agents on RPE by transcardiac shocks.

METHODS

In four groups of pentobarbital anesthetized dogs, RPE was measured during rapid ventricular pacing before and after administration of either the Class I agents flecainide (n = 7) or encainide (n = 7), the Class III agent clofilium (n = 7), or vehicle (n = 5). Measurements included QRS duration during sinus rhythm and a conduction time, QTC interval and refractory period, and RPE for 4- to 10-V/cm shocks delivered 20-80 ms before the end of the tissue absolute refractory period. For the 6-V/cm shocks, the interval after the shock during which tissue remained refractory (RIAS) was also computed.

RESULTS

Drugs affected QRS duration, conduction time, QTC, and refractory period ( without shocks) in accordance with their anticipated Class I and Class III actions. Without drugs, significant RPE was observed in all animals for all shocks delivered 40 ms or less before the end of the refractory period. Clofilium, encainide, and flecainide had a tendency to increase RPE but only clofilium produced a significant increase. For 6-V/cm shocks with different timings, the minimum RIAS was found to be approximately 43 ms, and occurred for shocks given 20-30 ms before the end of the refractory period.

CONCLUSIONS

At drug dosages that produced moderate Class III ( approximately equal to 15%) or strong Class I (approximately equal to 35%) effects, only the Class III agent significantly increased RPE and RIAS. Thus, in addition to altering tissue excitability, the effect of antiarrhythmic agents to increase RPE and the minimum RIAS may help explain their influence on defibrillation threshold.

Effects of pacing on stationary reentrant activity. Theoretical and experimental study

It is well known that electrical pacing may either terminate or change the rate and/or ECG appearance of reentrant ventricular tachycardia. However, the dynamics of interaction of reentrant waves with waves initiated by external pacing are poorly understood. Prevailing concepts are based on simplistic models in which propagation occurs in one-dimensional rings of cardiac tissue. Since reentrant activation in the ventricles occurs in two or three dimensions, such concepts might be insufficient to explain the mechanisms of pacing-induced effects. We used numerical and biological models of cardiac excitation to explore the phenomena, which may take place as a result of electrical pacing during functionally determined reentry. Computer simulations of a two-dimensional array of electrically coupled FitzHugh-Nagumo cells were used to predict the response patterns expected from thin slices of sheep ventricular epicardial muscle, in which self-sustaining reentrant activity in the form of spiral waves was consistently initiated by premature stimulation and monitored by means of video mapping techniques. The results show that depending on their timing and shape, externally induced waves may collide with the self-sustaining spiral and result in one of three possible outcomes: (1) direct annihilation of the spiral, (2) multiplication of the spiral, or (3) shift of the spiral center (ie, core). Multiplication and shift of the spiral core were attended by changes in rate and morphology of the arrhythmia as seen by "pseudo-ECGs." Furthermore, delayed termination (ie, termination of the activity one to three cycles after the stimulus) occurred after both multiplication and shift of the spiral center. Both numerical predictions and experimental results support the hypothesis that whether a pacing stimulus will terminate a reentrant arrhythmia or modify its ECG appearance depends on whether the interactions between the externally induced wave and the spiral wave result in the de novo formation of one or more "wavebreaks." The final outcome depends on the stimulus parameters (ie, position and size of the electrodes and timing of the stimulus) as well as on the position of the newly formed wavebreak(s) in relation to that of the original wave.

Effects of bipolar point and line stimulation in anisotropic rabbit epicardium: assessment of the critical radius of curvature for longitudinal block

Excitation front shape and velocity were studied in anisotropic perfused rabbit epicardium stained with potentiometric fluorescent dye. In the combined results from all experiments, convex excitation fronts produced by stimulation with a single electrode propagated longitudinally 13.3% slower than flat excitation fronts produced by stimulation with a line of electrodes. For transverse propagation, the two stimulation methods produced similar flat excitation fronts and velocities. The critical excitation front radius of curvature for longitudinal block (Rcr), calculated from excitable media theory, was 92 microns in control hearts. In hearts exposed to diacetyl monoxime (20 mmol/L), which decreases inward sodium current, Rcr was 175 microns. The slower longitudinal propagation velocity of convex fronts versus flat fronts and the theoretically predicted critical radius of curvature may be important for propagation and block of ectopic depolarizations in the heart.

Analysis of the body surface ECG measured in independent leads during ventricular fibrillation in humans

The degree of myocardial electrical organization during ventricular fibrillation remains unknown. The aim of this study was to compare the characteristics of the surface ECG on three independent and approximately orthogonal leads. Ten recordings of ventricular fibrillation, each induced at electrophysiology study and successfully terminated by direct current shock, were analyzed. Each recording was divided into 1-second epochs for analysis. Frequency analysis using the Fast Fourier Transform showed that the frequency of the dominant spectral peak increased significantly from a mean of 4.1 +/- 0.8 Hz to 5.2 +/- 0.7 Hz during the first 5 seconds of ventricular fibrillation. In 95% of the epochs analyzed, a similar dominant frequency was observed on either two or three ECG leads. Frequency agreement tended to increase as ventricular fibrillation evolved. This study shows that the rate of ventricular fibrillation increases rapidly during the first 5 seconds but only gradually thereafter, and that similar signal characteristics are observed on independent ECG leads. These findings are not compatible with the traditional view of incoherent myocardial activity during ventricular fibrillation.

Circadian variation in human ventricular refractoriness

BACKGROUND

The incidence of sudden cardiac death is highest in the morning hours. Although a circadian variation in myocardial ischemia may be responsible in part for this observation, other factors also may be contributory. It is not known whether a circadian variation in ventricular refractoriness exists that may be related to the increased morning incidence of sudden cardiac death.

METHODS AND RESULTS

Nine subjects with primary conduction system disease, no evidence of structural heart disease, and permanent pacemakers were studied. Autonomic nervous system function as assessed by tilt table and baroreflex sensitivity testing was normal in all subjects. Using noninvasive programmed stimulation, ventricular effective refractory periods were measured hourly for 24 hours. Potassium, epinephrine, and norepinephrine levels also were measured hourly. In a subset of five subjects, ventricular refractory periods were again measured hourly over 24 hours during beta-blockade. A significant circadian variation in ventricular refractoriness was noted, with a mean difference between the shortest and longest refractory periods in individual subjects of 23 ms and 21 ms at drive cycle lengths of 600 ms and 400 ms, respectively. In eight subjects, the shortest refractory periods observed over 24 hours occurred within 2 hours of waking (random probability < 10(-8)). Adjustment of refractory period data according to the hour of waking resulted in a better correlation between ventricular refractory periods and time. Although a significant circadian variation was observed in potassium and catecholamine levels, neither was an independent predictor of refractory periods after adjustment for the hour of waking. The adjusted time of day was the only significant (P < .0001) independent predictor of refractory periods. beta-Blockade abolished the circadian variation in ventricular refractory periods.

CONCLUSIONS

A significant circadian variation in ventricular refractory periods exists. Maximal shortening between hourly refractory periods as well as the shortest refractory periods occur in the early morning hours when the incidence of sudden cardiac death is greatest. Fluctuations in beta-adrenergic tone appear to be largely responsible for this phenomenon.

Effect of rapid pacing and T-wave scanning on the relation between the defibrillation and upper-limit-of-vulnerability dose-response curves

BACKGROUND

The critical-point and upper-limit-of-vulnerability (ULV) hypotheses predict that the ULV dose-response curve should be steeper and to the right of the defibrillation (DF) curve. Yet, some recent experimental data contradict this prediction. Two studies are presented that test two explanations for the contradiction: (1) Testing at a single point in the T wave underestimates the ULV dose-response curve and (2) ULV testing at normal heart rates does not mimic the mechanical or electrical state of the heart in ventricular fibrillation (VF).

METHODS AND RESULTS

A nonthoracotomy lead system with a biphasic waveform was used throughout. In eight dogs, the dose-response curve widths (a measure of steepness) were compared between DF data and ULV data gathered at the peak (ULVPK), middownslope (ULVDWN), midupslope (ULVUP), and all times (scanning or ULVSCN) in the T wave. In another eight dogs, ULV data (ULVRAP) were gathered by scanning the T wave after 15 rapidly paced beats (166- to 198-ms pacing interval). The rapid pacing interval was chosen to more closely mimic the hemodynamics and activation rate of early VF. ULV data (ULVSTD) at normal heart rates were gathered for all animals. In the first study, scanning significantly reduced the ULV curve width (ULVSCN, 63.5 +/- 29.7 V; ULVPK, 81.9 +/- 45.2 V; ULVDWN, 116 +/- 36.5 V; DF, 105 +/- 22.0 V; P < .03) and significantly shifted the ULV curve to the right (ULV80 SCN, 410 +/- 62.6 V; ULV80 PK, 266 +/- 35.3 V; ULV80 DWN, 355 +/- 80.4 V; DF80, 427 +/- 60.9 V; P < .001). The subscript 80 signifies that the subject was left in normal sinus rhythm 80% of the time after that stimulus strength was delivered. In the second study, the ULVRAP curve was shifted dramatically to the right, the average ULV50 RAP being greater than the average DF90. Furthermore, 92% of the ULVRAP VF inductions occurred between 10 ms before and 50 ms after the peak of the T wave, suggesting that scanning of the entire T wave may not be necessary.

CONCLUSIONS

With a single rapidly paced ULV sequence with limited T-wave scanning, it may be possible to estimate highly effective defibrillation doses with few VF episodes and high-voltage stimuli.

Alteration of ventricular fibrillation by propranolol and isoproterenol detected by epicardial mapping with 506 electrodes

INTRODUCTION

We hypothesized that drugs which alter ventricular refractoriness or excitability produce quantifiable changes in ventricular fibrillation.

METHODS AND RESULTS

We used a 528-channel mapping system to quantify the effects of the beta-antagonist, propranolol, and the beta-agonist, isoproterenol, on activation patterns in ventricular fibrillation. A plaque of 506 (22 x 23) electrodes spaced 1.12 mm apart and covering about 5% of the ventricular epicardium was sewn to the anterior right ventricle in 18 pigs (30 kg). Propranolol (0.25 to 0.4 mg/kg) increased the refractory period at a right ventricular epicardial site while isoproterenol (3 to 5 micrograms/min) shortened it. Ventricular fibrillation was induced by programmed stimulation, and unipolar electrograms were recorded from the 506 plaque electrodes for 2 seconds beginning 1, 15, and 30 seconds after the onset of fibrillation. Active epicardial recording sites were identified from the first derivative of the unipolar potentials (dV/dt) detected at each electrode. Then, neighboring active sites were grouped into activation fronts by computer analysis. In six pigs the effect of repeated inductions of ventricular fibrillation was assessed by comparing ventricular fibrillation after saline with a preceding control episode of fibrillation. Each activation front excited 40% +/- 46% of the mapped region before blocking. No changes were observed with saline and multiple inductions of fibrillation. In another six pigs, ventricular fibrillation after propranolol was compared with a preceding control episode of fibrillation. Ventricular fibrillation after propranolol exhibited a decreased activation rate per epicardial recording site and fewer activation fronts per second. There was no change in the amount of tissue excited by each activation front or the number of reentry cycles per activation front compared with control. In addition, there was no change in the maximum negative dV/dt detected per activation at an epicardial site. In six pigs ventricular fibrillation during isoproterenol was compared with control episodes of ventricular fibrillation before and 45 minutes after washout of the drug. The control episodes of fibrillation were not different from each other. Compared with control, ventricular fibrillation during isoproterenol exhibited an increased activation rate per epicardial site, an increased amount of tissue excited by each activation front, and an increased maximum negative dV/dt for each activation. There was no change in the number of activation fronts per second or the number of reentry cycles per activation front compared with control.

CONCLUSION

Quantitative analysis revealed that propranolol and isoproterenol do not have symmetrically opposite effects on ventricular fibrillation. Propranolol decreased the number of activation fronts while isoproterenol increased the amount of tissue excited by each activation front. Thus, drugs that alter ventricular refractoriness or excitability alter ventricular fibrillation.

Nonstationary vortexlike reentrant activity as a mechanism of polymorphic ventricular tachycardia in the isolated rabbit heart

BACKGROUND

Ventricular tachycardia may result from vortexlike reentrant excitation of the myocardium. Our general hypothesis is that in the structurally normal heart, these arrhythmias are the result of one or two nonstationary three-dimensional electrical scroll waves activating the heart muscle at very high frequencies.

METHODS AND RESULTS

We used a combination of high-resolution video imaging, electrocardiography, and image processing in the isolated rabbit heart, together with mathematical modeling. We characterized the dynamics of changes in transmembrane potential patterns on the epicardial surface of the ventricles using optical mapping. Image processing techniques were used to identify the surface manifestation of the reentrant organizing centers, and the location of these centers was used to determine the movement of the reentrant pathway. We also used numerical simulations incorporating Fitzhugh-Nagumo kinetics and realistic heart geometry to study how stationary and nonstationary scroll waves are manifest on the epicardial surface and in the simulated ECG. We present epicardial surface manifestations (reentrant spiral waves) and ECG patterns of nonstationary reentrant activity that are consistent with those generated by scroll waves established at the right and left ventricles. We identified the organizing centers of the reentrant circuits on the epicardial surface during polymorphic tachycardia, and these centers moved during the episodes. In addition, the arrhythmias that showed the greatest movement of the reentrant centers displayed the largest changes in QRS morphology. The numerical simulations showed that stationary scroll waves give rise to monomorphic ECG signals, but nonstationary meandering scroll waves give rise to undulating ECGs characteristic of torsade de pointes.

CONCLUSIONS

Polymorphic ventricular tachycardia in the healthy, isolated rabbit heart is the result of either a single or paired ("figure-of-eight") nonstationary scroll waves. The extent of the scroll wave movement corresponds to the degree of polymorphism in the ECG. These results are consistent with our numerical simulations that showed monomorphic ECG patterns of activity for stationary scroll waves but polymorphic patterns for scroll waves that were nonstationary.

Biphasic restitution of action potential duration and complex dynamics in ventricular myocardium

The purpose of this study was to determine whether biphasic restitution of action potential duration (APD) in ventricular muscle permits the development of complex dynamic behavior. Such behavior is expected because of the steep ascending slope of restitution and the presence of a maximum. Action potentials recorded from strips of epicardial muscle in which biphasic APD restitution occurred demonstrated a characteristic pattern of phase locking during progressive shortening of the pacing cycle length. 1:1 locking was replaced by irregular dynamics, which in turn was replaced by higher order periodic behavior (eg, 8:8 locking), then by 2:2 locking, and finally by 2:1 locking. Similar patterns of dynamic behavior were produced in a computer model by using a piecewise linear approximation of biphasic APD restitution. Features of APD restitution that were critical determinants of irregular dynamics included the slopes of the ascending and the nonmonotonic regions. These results suggest that rate-related alterations of APD and refractoriness may be affected significantly by small nonmonotonicities in APD restitution.

The effect of cardiac compression on defibrillation efficacy and the upper limit of vulnerability

INTRODUCTION

We determined the effects of decreasing the ventricular blood volume and altering cardiac geometry on defibrillation, the upper limit of vulnerability (ULV), and the relationship between them.

METHODS AND RESULTS

In six pigs, fibrillation/defibrillation trials were performed with a left ventricular apex patch to a superior vena cava catheter electrode configuration and a biphasic waveform. Thirty trials each were performed on a compressed versus noncompressed (normal) heart. Compression was achieved using direct mechanical ventricular actuation. Dose-response curves were constructed, and the 50% probability points (ED50) were compared for leading edge voltage (LEV), leading edge current (LEI), and total energy (TE). In another 12 pigs, triplicate defibrillation thresholds (DFTs) and ULVs were determined for each heart state. The T wave was scanned with shocks in 10-msec steps for determining the ULV. Compression resulted in decreased ED50s for LEV (delta = 138 +/- 77 V, P < 0.05, mean +/- SD), LEI (delta = 1.57 +/- 0.7 A, P < 0.05), and TE (delta = 4.9 +/- 3.6 J, P < 0.05) compared to normal. In the second study, compression significantly reduced DFT (P < 0.02) and ULV (P < 0.02) for LEV, LEI, and TE compared to normal. The ULV tended to be lower than the DFT for the normal heart state (delta = 23 +/- 46 V LEV: P = NS). However, the ULV was significantly greater than the DFT for the compressed heart state (delta = 19 +/- 25 V LEV; P < 0.03).

CONCLUSIONS

Shock delivery during cardiac compression improves defibrillation efficacy. Additionally, cardiac compression decreases both DFT and ULV, which supports the ULV hypothesis of defibrillation. Finally, maintaining the heart's geometric and volumetric state during ULV testing in paced rhythm and DFT testing in ventricular fibrillation moves the ULV higher than the DFT-the position predicted by the ULV hypothesis for defibrillation.

Reentry: insights from theoretical simulations in a fixed pathway

This review article summarizes theoretical insights into the principles and mechanisms associated with reentrant activity in cardiac tissue. A mathematical ring model is used in computer simulations to investigate, at the cellular level, mechanistic aspects of initiation, perpetuation, and termination of reentry. Taking advantage of the ability to compute membrane processes in this model, we relate dynamic properties of the reentrant action potential (e.g., beat-to-beat alternans) to the underlying kinetics of membrane ionic channels. Effects on reentry of inhomogeneities in refractoriness, excitability, cellular coupling at gap junctions, and fiber cross-section are also studied.

Correlation among fibrillation, defibrillation, and cardiac pacing

An electrical stimulus must create an electric field of approximately 1 V/cm in the extracellular space to stimulate myocardium during diastole. To initiate fibrillation by premature stimulation during the vulnerable period or to defibrillate, an extracellular electric field of approximately 6 V/cm is required, a value approximately six times greater than that necessary for diastolic pacing. Yet, the current strength of the pulse given to the stimulating electrode to initiate fibrillation or to defibrillate is much greater than six times the diastolic pacing threshold. The ventricular fibrillation threshold is typically 40 times greater than the diastolic pacing threshold expressed in terms of current. The defibrillation threshold in terms of current is typically thousands of times greater than the diastolic pacing threshold. The reason that these thresholds vary so much more in terms of stimulus current than in terms of extracellular potential gradient is that each of the three thresholds requires creation of the required potential gradient at different distances from the stimulating electrode. Pacing requires a potential gradient of approximately 1 V/cm only in a small liminal volume of tissue immediately adjacent to the electrode. Initiation of ventricular fibrillation by premature stimulation during the vulnerable period requires a potential gradient of approximately 6 V/cm about 1 cm away from the stimulating electrode to allow sufficient space for the central common pathway of a figure-eight reentrant circuit to form. Since the potential gradient falls off rapidly with distance from the stimulating electrode, a stimulating current about 40 times greater than the diastolic pacing threshold is required to generate an electric field of 6 V/cm approximately 1 cm away from the stimulating electrode. Defibrillation requires an electric field of approximately 6 V/cm throughout all or almost all of the ventricular myocardium. Since some portions of the ventricles can be more than 10 cm away from the defibrillation electrodes, a shock of several amps is required to create this field, a current thousands of times greater than the pacing threshold.

Comparison of upper limit of vulnerability and defibrillation probability of success curves using a nonthoracotomy lead system

BACKGROUND

An upper limit to the strength of shocks that induce fibrillation during the vulnerable period, the upper limit of vulnerability (ULV), has been shown to exist in both humans and animals. The purpose of this study was to compare ULV and defibrillation (DF) probability of success curves for a clinically useful nonthoracotomy lead system.

METHODS AND RESULTS

Sixteen pentobarbital-anesthetized pigs were studied. Single-capacitor biphasic waveforms with both phases 5.5 ms in duration were used for ULV and DF testing. A right ventricular catheter electrode served as first-phase cathode and a superior vena cava catheter electrode coupled with a cutaneous R2 patch electrode served as common first-phase anodes. A pacing catheter was placed in the right ventricle to deliver a train of 15 S1 stimuli at a pacing interval of 250 to 300 ms. A ULV shock was delivered on the peak of the T wave as measured from the surface ECG; if ventricular fibrillation was induced, a DF shock was delivered after 10 seconds of fibrillation. Shock voltages were determined by an up-down protocol. Ventricular fibrillation was induced an average of 53 times in each animal. The composite data indicate that below V97, that is, the voltage that leaves the animal in normal sinus rhythm 97% of the time when delivered on the peak of the T wave or the voltage that defibrillates 97% of the time, ULV is lower than DF. ULV and DF became significantly correlated at V80 and maximally correlated at V97. Even at V97, however, ULV and DF differed by more than 100 V in 2 of the 16 animals.

CONCLUSIONS

ULV approximately equaled DF at V97. This is fortunate because it is clinically important to set the device voltage at the uppermost portion of the probability of success curve. Estimating DF V97 from ULV V97 would reduce the number of fibrillation inductions needed to establish defibrillation shock strength requirements. However, the large difference between ULV V97 and DF in a few animals indicates that further improvement and testing of algorithms for determining ULV V97 must be developed before the technique is used clinically.

Mechanisms of defibrillation. Critical points and the upper limit of vulnerability

The upper limit of vulnerability hypothesis for defibrillation states that a successful defibrillation shock must both stop the fibrillation wave fronts on the heart at the time that the shock is delivered and not start new wave fronts that will lead to reentrant circuits being formed, causing the heart to refibrillate. Mapping studies have demonstrated that defibrillation shocks can halt all wave fronts on the heart but fibrillation will begin again with an initial activation pattern that is different from the activation pattern on the heart just before the shock is delivered. In a fashion similar to the reinitiation of fibrillation following a failed defibrillation shock, properly sized and timed shocks can be delivered to the heart during paced rhythm to induce functional reentry that will initiate fibrillation. If the shocks are made incrementally larger, a shock level will be reached that is high enough not to start fibrillation in regular rhythm regardless of when it is delivered during the cardiac cycle. This shock level is called the upper limit of vulnerability. In this study, the formation of reentrant circuits with defibrillation-sized shocks and how this formation of reentrant circuits may be related to mechanism of defibrillation, via the upper limit of vulnerability hypothesis are discussed.