Original Research ARTICLE
Slowing of electrical activity in ventricular fibrillation is not associated with increased defibrillation energies in the isolated rabbit heart
- Institute of Cardiovascular and Medical Sciences, University of Glasgow, Glasgow, UK
Prolonged out-of-hospital ventricular fibrillation (VF) arrests are associated with reduced ECG dominant frequency (DF) and diminished defibrillation success. Partial reversal of ischemia increases ECG DF and improves defibrillation outcome. We have investigated the metabolic components of ischemia responsible for the decline in ECG DF and defibrillation success. Isolated Langendorff-perfused rabbit hearts were loaded with the voltage-sensitive dye RH237. Using a photodiode array, epicardial membrane potentials were recorded at 252 sites (15 mm × 15 mm) on the anterior surface of the left and right ventricles. Simultaneously, a global ECG was recorded. VF was induced by burst pacing, and after 60s, perfusion was either reduced to 6 ml/min or the perfusate composition changed to impose hypoxia (95% N2/5% CO2), pH 6.7 (80% O2/20% CO2), or hyperkalemia (8 mM). Using fast Fourier transform, power spectra were created from the optical signals and the global ECG. The optical power spectra were summated to give a global power spectrum (pseudoECG). At 600 s the minimum defibrillation voltage (MDV) was determined by step-up protocol. During VF, the ECG and pseudoECG DF were reduced by low-flow ischemia (9.0 ± 1.0 Hz, p < 0.01, n = 5) and raised [K+]o (12.2 ± 1.3 Hz, p < 0.05, n = 7) compared to control (19.2 ± 1.5 Hz, n = 20), but were unaffected by acidic pHo (16.7 ± 1.1 Hz, n = 11) and hypoxia (14.0 ± 1.2 Hz, n = 10). In contrast, the MDV was raised by acidic pH (156.1 ± 26.4 V, p < 0.001) and hypoxia (154.1 ± 22.1 V, p < 0.01) compared to control (65.6 ± 2.3 V), but comparable changes were not observed in low-flow ischemia (61.0 ± 0.5 V) or raised [K+]o (56 ± 3 V). In summary, different metabolites are responsible for the reduction in DF and the increase in defibrillation energy during ischemic VF.
Ventricular fibrillation (VF) is the major cause of sudden death, with an estimated Europe-wide annual mortality of 123,000 (Atwood et al., 2005). In VF, the dyssynchronous electrical activity within the ventricles results in loss of cardiac output and death, unless corrective measures, including electrical defibrillation, are undertaken (Rubart and Zipes, 2005). It is well established that prolonged out-of-hospital VF arrests are associated with slowing of the heart’s electrical activity, as reflected by lowering of the frequency of oscillation in the surface ECG (Stewart et al., 1992). This slower electrical activity is associated with diminished defibrillation success (Stewart et al., 1992). More recently, studies have shown that partial re-establishment of perfusion by CPR increased the ECG dominant frequency (DF; Eftestol et al., 2004) and improved defibrillation success (Wik et al., 2003). This suggests that the energy required to defibrillate successfully (defibrillation threshold, DFT) is increased by ischemia, and reduced by partial restoration of coronary perfusion.
In contrast, experimental assessments of DFT failed to show any increase in DFT during global ischemia (Behrens et al., 1997; Barton et al., 2000) but DFTs were increased during localized regional ischemia (Ouyang et al., 1981; Qin et al., 2002; Anastasiou-Nana et al., 2005). Similarly computer simulations predict a reduction of DFT in global ischemia (Rodriguez et al., 2004) and an increase in cardiac vulnerability to recurrent VF after defibrillation in regional ischemia (Rodriguez et al., 2006).
One possible explanation for this apparent paradox is that the principal metabolic components of ischemia, namely hypoxia, acidosis, and hyperkalemia, individually affect the DF and DFT in different ways. Altering the proportions of these individual components could therefore affect the apparent relationship between DF and DFT. The aim of this study was to determine the individual effects of hypoxia, acidosis, and hyperkalemia on the frequency of the electrical oscillations during VF and the required defibrillation energy.
Materials and Methods
Adult male New Zealand White rabbits (weight 3–3.5 kg) were sacrificed by intravenous injection of 0.5 ml/kg Euthatal (sodium pentobarbitone 200 mg/kg, Rhône Mérieux) with 500 IU of heparin. Hearts were rapidly excised, and Langendorff-perfused with Tyrode’s solution at 37°C at constant rate of 40 ml/min [Tyrode’s composition (mM): Na 134.5, Mg 1.0, K 5.0, Ca 1.9, Cl 101.8, SO4 1.0, H2PO4 0.7, HCO3 20, acetate 20, glucose 50, and pH 7.4 (95% O2/5% O2)].
Hearts were placed in a custom-made Plexiglas chamber (Figure 1A) that allowed control of bathing solution composition and temperature via separate bath perfusion, recording of global ECG from fixed electrodes (Figure 1B) and defibrillation through two steel paddles that cradled the heart (n = 53). Optical mapping of the anterior epicardial surfaces of the left and right ventricles was performed as previously published (Kettlewell et al., 2004). Briefly, hearts were loaded with a bolus of 100 μl of 1 mg/ml RH237 (Molecular Probes), dissolved in DMSO. Light at 535 ± 25 nm (interference filter, Comar Instruments Ltd, UK) from four 75 W tungsten-halogen lamps illuminated the heart’s anterior surface. Fluorescent light was passed through a 695-nm long-pass filter, and focused onto a 16 × 16 photodiode array (C4675-102, Hamamatsu Photonics UK Ltd). Each diode detected light from 0.8 mm × 0.8 mm area of epicardium; the full array recorded from 15 mm × 15 mm area. Typical optical signals from a single diode are shown in Figure 1C. Digitalized data (1 kHz) were stored to disk, and analyzed using software written in Delphi (Borland Software Corp., CA, USA). During optical recordings hearts were immobilized by transient compression so that no excitation–contraction uncoupling agents were employed for the 4 s epoch of data recording.
Figure 1. (Ai) Langendorff-perfused rabbit heart in optical mapping chamber. The superimposed grid represents the area of the myocardium (16 × 16 pixels) visualized by the photodiode array. (Aii) Optically recorded action potentials (pacing cycle length 300 ms). ECG recording during (Bi) sinus rhythm and (Bii) ventricular fibrillation (VF). Optical pixel recordings in (Ci) sinus rhythm, (Cii) VF. (D) Superimposed power spectra of ECG (Bii) and the summary psECG of all 256 pixels in VF.
VF Protocol and Analysis
Ventricular fibrillation was induced by burst pacing (50 Hz stimulation for 8 s) via platinum hook electrodes placed in the RV. All hearts were perfused with normal Tyrode’s solution at 40 ml/min for the first 60 s of VF. A single protocol was carried out in each heart. ECG and optical recordings were taken every 60 s, each recording 4 s worth of VF. In control protocols, 40 ml/min perfusion with standard Tyrode’s solution was maintained. In experimental protocols, either the perfusion rate (low-flow ischemia = 6 ml/min), or solution composition was altered at 60 s. The heart chamber was filled in two ways: (i) indirectly from the coronary sinus effluent and (ii) directly from a second bath perfuser whose composition was changed inline with the Langendorff perfusate. VF continued in all protocols until 600 s. On completion of the recording at 600 s, ECG electrodes were isolated and hearts were defibrillated using a Ventak ECD 2815 (CPI, St Paul, MN, USA). This defibrillator contains a 140-μF capacitor with 80% fixed tilt, first phase 60% of total duration and automatic adjustment of waveform duration to resistance load (automatic impedance compensation). As heart resistance was constant at ∼48 Ω, the biphasic waveform duration was also constant at ∼14 ms. Shocks were delivered with fixed polarity orientation via custom-made stainless steel paddles (Figure 1A). Shocks of discrete strength settings were delivered by a step-up protocol. The time between shock applications was about 5 s, so the maximum delay between application of first shock and eventual defibrillation was 40 s. Minimum defibrillation voltage (MDV) was determined as the shock strength that successfully defibrillated VF into sinus rhythm (Barton et al., 2000). As shown in Table 1, there was slight variation in the actual shock delivered at each strength setting. The actual shock strength rather than the setting was recorded. The impedance compensation prohibited the use of additional resistors in series in attempts to apply lower strength shocks as the additional loading resulted in waveform prolongation. Increased waveform duration for same energy delivery has been linked to less efficient defibrillation (Natale et al., 1996; Ideker et al., 2006).
Table 1. Energy settings of the Ventak ECD 2815 with the corresponding voltage, energy, and waveform delivered.
Fast Fourier transform (FFT) of the ECG and optical signals during VF was performed on 4 s data recordings. As with previous clinical studies (Strohmenger et al., 1997), the DF of these signals was taken as the frequency with the greatest power between 3 and 50 Hz. The peak (dominant) frequency (DF) was identified from power spectra of ECG (Carlisle et al., 1990; Strohmenger et al., 1997) and optical signals (Chen et al., 2000; Samie et al., 2001; Choi et al., 2006). Summing the power spectra from all 256 pixels gave a global or pseudoECG (psECG) power spectrum (Figure 1D). The progressive changes in psECG DF were similar to ECG DF, therefore only the psECG DF data are presented (Figure 2).
Figure 2. Minimum defibrillation voltage and psECG DF. (A) Plot of mean psECG DF at point of defibrillation. The psECG DF was significantly lower than control during low-flow ischemia** and 8 mM [K+]o*. (B) Plot of mean MDV ± SE. The MDV was significantly raised by pH 6.7** and 0% PO2** when compared to control. (C) Scattergram of MDV against psECG DF at defibrillation. Although there was a tendency for MDV to increase with DF in 0% PO2 and pH 6.7, there were no such associations in low-flow ischemia, 8 mM [K+]o or control. (*p < 0.05, **p < 0.01). Considering all MDV vs DF, there was no significant correlation between the two parameters (r = 0.13).
Heterogeneity of repolarization and refractoriness is thought to play a role in defibrillation outcome (Ujhelyi et al., 1999). During VF, it is assumed that a heart cell is activated as soon as it is able and the interval between activations (i.e., the VF interval, VFI) reflects the refractory period of the underlying tissue (Opthof et al., 1991, 1993). Epicardial refractoriness during VF can be assessed by measurement of the VFI over the surface sites. Therefore the dispersion of refractoriness can be measured by quantifying the coefficient of variance (CoV) of VFIs. In this study, the CoV was measured as the standard deviation of the mean DF across the epicardial surface relative to the mean DF (SD × 100/mean) and was used to represent the dispersion of refractoriness (Opthof et al., 1991, 1993; Burton and Cobbe, 1998; Burton et al., 2000). As well as measuring the CoV, the fractional change in the CoV at defibrillation was compared to that immediately on VF induction to quantify the relative change in CoV for each condition.
Components of Ischemia
To study the contribution of individual ischemic components to the changes in DF, CoV, and MDV, standard Tyrode’s solution was altered to impose each component according to previous studies (Kleber, 1983; Jennings et al., 1990; Bethell et al., 1998). Acidic pHo = 6.7 was produced by bubbling with 20% CO2/80% O2 (Bethell et al., 1998); hypoxia was produced by bubbling with 5% CO2/95 %N2 mixture (Jennings et al., 1990); hyperkalemia was produced using 8 mM or 10 mM [K+]o (Kleber, 1983). Perfusion with experimental solutions cause no visible change in isolated heart dimensions suggesting no major shifts in intracellular fluids during the various interventions.
Data are expressed as mean ± SEM. Significance testing with repeated paired ANOVA was performed using Instat3 (GraphPad Software Inc., USA) after all parameters were tested for normality. Comparisons at defibrillation were made between psECG DFs, the MDVs, and the fractional change of the CoV compared to baseline. All graphs including scattergrams were plotted using Origin (OriginLab Corp., MA, USA). The linear-fit algorithms within this software package used to assess the correlation coefficient.
Variation of psECG DF
Figure 2A shows that at defibrillation, the psECG DF in low-flow ischemia of 9.0 ± 1.0 Hz (n = 5) was significantly lower than psECG DF in control of 19.2 ± 1.5 Hz (**p < 0.01, Figure 2A). Similarly, psECG DF in 8 mM [K+]o of 12.2 ± 1.3 Hz (n = 7) was significantly lower than control (n = 20; *p < 0.05, Figure 2A). During perfusion with 10 mM [K+]o, VF converted spontaneously to a regular ventricular escape rhythm (∼3 Hz).
In contrast, psECG DF of 16.7 ± 1.1 Hz in pH 6.7 (n = 11), and 14.0 ± 1.2 Hz in hypoxia (n = 10) were not significantly different from control (Figure 2A).
Minimum Defibrillation Voltage
As shown in Figure 2B, the mean MDV required to defibrillate VF in low-flow ischemia of 61.0 ± 0.5 V was not significantly different from the 65.6 ± 2.3 V in control. Although there was a tendency for MDV to be reduced to 59.0 ± 0.3 V in 8 mM [K+]o, this was not significantly different from control. 10 mM [K+]o solution spontaneously converted VF to a regular ventricular escape rhythm before 600 s. All defibrillations in this group were achieved using the minimum setting on the defibrillator. The variation in recorded voltages reflects the variation in the resistance of the isolated heart preparations.
Figure 2B also shows that significantly stronger shocks were required to defibrillate VF during pH 6.7 and hypoxia compared to control. In pH 6.7 the MDV was 156.1 ± 26.4 V (**p < 0.01), and in hypoxia the MDV was 154.1 ± 22.1 V (**p < 0.01).
DF and MDV
The mean MDV and psECG DF data did not display any correlation. Therefore individual MDVs were plotted against the respective psECG DF as a scattergram (Figure 2C). In acidic pHo and hypoxia there was no correlation between MDV to increase as DF increased. Nor was there any correlation in the control, low-flow ischemia or raised [K+]o.
Coefficient of Variance
Immediately post VF induction, the CoV was not different between protocols (data not shown). As VF progressed, the CoV tended to increase with time in all protocols apart from the pH 6.7 group, where it remained relatively constant (Figure 3A). However, at defibrillation there were no significant differences in CoV as assessed by absolute values and fractional changes (Figure 3B).
Figure 3. Coefficient of variance of optical DF. (A) Time course of coefficient of variance during VF in low-flow ischemia, pH 6.7 and control conditions. There was a tendency for the coefficient to increase with time in low-flow ischemia and control. In comparison, the coefficient tended to remain stable in pH 6.7. (B) Fractional change in the coefficient of variance at time of defibrillation compared to baseline values at VF onset. The fractional change was not significantly different between the experimental groups.
This study demonstrated that in the isolated Langendorff-perfused rabbit heart, conditions that slow the electrical activity in VF do not increase the required defibrillation energy. The electrical activity in VF was significantly slowed by low-flow ischemia and raised [K+]o, whilst MDV was not increased above the minimum values that could be delivered by the defibrillator. In contrast, MDV was significantly increased by perfusion with acidic solutions (pH 6.7) and hypoxia. Neither of these condition had significant effects on the VF frequency. These results establish for the first time that DF and DFT may not be mechanistically linked. The limited area of epicardium imaged in these experiments was considered to sample the major axis of heterogeneity in VF frequency in the rabbit ventricle. In support of this, previous studies (Wu et al., 2006) found that the greatest differential in the DF of VF was during low-flow ischemia, with a lower DF value in LV epicardial relative to RV. No significant differences between LV and RV endocardium and RV epicardium were observed.
MDV in Low-Flow Ischemia
Successful defibrillation requires a shock to depolarize sufficient myocardium homogeneously to stop fibrillation wavefronts without launching new activation waves. Defibrillation fails when the shock that terminates fibrillation also reinitiates fibrillation. Several mechanisms of VF reinitiation have been proposed; from critical point re-entry (Wharton et al., 1992), through virtual electrodes (Efimov et al., 1998) to delayed after depolarizations (DADs; Chattipakorn and Ideker, 2003). Equally controversial is the effect of ischemia on DFT; the small number of studies examining the effect of global ischemia on DFT have shown conflicting results (Behrens et al., 1997; Barton et al., 2000). In the present study MDV was unaffected by low-flow ischemia (flow rate = 15% control), but small changes in DFT may have occurred below the minimum energy the current device could deliver. Despite this technical limitation, this result compares well to previous research in isolated rabbit hearts during global low-flow ischemia at 20% control flow rate (Behrens et al., 1997). Here Behrens et al. found no difference in the DFT during low-flow ischemia and control. In contrast, in isolated pig hearts, Barton et al. (2000) observed that the MDV was lowered in low-flow ischemia (10% standard rate) compared to control. Barton et al. (2000) hypothesized that the slower ECG DF in low-flow ischemia represented more organized myocardial electrical activity, which could be defibrillated more easily. Similarly, computer simulations have predicted the need for greater energies to convert increasingly complex electrical activity (Hillebrenner et al., 2004; Plank et al., 2005). Hillebrenner et al. (2004) showed in a bidomain defibrillation model that multiple scroll waves had a reduced probability of successful defibrillation compared to a single scroll wave in the same tissue. In a similar bidomain model Plank et al. (2005) produced increasingly complex electrical activity by adjusting the spatial modulations of IKAch. This transformed a single scroll wave into complex fibrillating activity. They showed that with increasing complexity of fibrillation higher shock strengths were required to successfully terminate the arrhythmia.
MDV in Raised [K+]o
Although no significant change in MDV was demonstrated in 8 mM [K+] solution, higher [K+] solutions resulted in spontaneous defibrillation. This suggests that the MDV may have been reduced in 8 mM [K+]o, but this change could not be resolved by the current experimental arrangement. As shown in Table 1, the Ventak ECD 2815 can only deliver biphasic shocks >60 V, and so MDV less than ∼60 V cannot be detected. As MDV of VF during control was 65.6 ± 2.3 V, a significant reduction of MDV was impossible to detect. Previous research supports this suggestion as DFT has been shown to be lowered by raised [K+]o (Babbs et al., 1980). Here, cardiac perfusion was maintained by cardiopulmonary bypass, and arterial [K+]o raised by potassium chloride infusion. Babbs et al. (1980) demonstrated that the percentage reduction of DFT was linearly related to log[K+]o, and to the potassium equilibrium potential (EK). This linear relationship suggests that [K+]o reduces DFT by bringing the diastolic membrane potential closer to the cellular firing threshold of −55 ± 5 mV. Indeed, when the diastolic membrane potential was raised to −46 mV by 16 mM [K+]o, spontaneous defibrillation occurred (Babbs et al., 1980).
The direct relationship between [K+]o and DFT only applies to global increases in [K+]o. Regional increases in [K+]o increase the DFT (Sims et al., 2000). This was hypothesized to arise from the increased heterogeneity of various electrophysiology parameters such as repolarization, refractoriness, and conduction velocity.
MDV In Acidic pHo
In this study acidic pHo significantly increased the MDV compared to control. Once again previous research into the effects of acidic pHo on defibrillation is limited and conflicting. Kerber et al. (1983) showed no change in DFT with respiratory or metabolic acidosis, but the arterial pH was only reduced to 7.25. In contrast, another group demonstrated the need for more countershocks, with greater total defibrillation energy in hypercarbic acidosis with arterial pH 6.7 (Maldonado et al., 1993).
Acidic pH is well recognized for its arrhythmogenicity, being able to precipitate arrhythmias through four possible mechanisms: (i) triggered activity of EADs (Coraboeuf et al., 1980) and DADs (Coetzee and Opie, 1987), (ii) producing a re-entrant substrate such as calcium alternans (Orchard et al., 1991), (iii) conduction slowing (Kagiyama et al., 1982), and (iv) increased gap junction resistance (Eloff et al., 2003). All of these mechanisms have been associated with defibrillation failure (Chattipakorn and Ideker, 2003; Chattipakorn et al., 2004).
MDV in Hypoxia
In VF during hypoxia, the MDV was significantly increased. To date, only a few studies have investigated the effect of hypoxia on DFT. Of these studies, one canine study demonstrated that hypoxia lowered DFT (Kerber et al., 1983), whereas another showed the DFT to be unchanged (Yakaitis et al., 1975). Both studies used in situ hearts with CPR during VF. In such preparations the hypoxia-induced K+ efflux may be significant, thereby depolarizing the diastolic membrane potential, and thus lower the DFT (Babbs et al., 1980). In Langendorff-perfused rabbit hearts, the hypoxia-induced K+ efflux cannot accumulate. In contrast hypoxia results in severe metabolic acidosis secondary to the accumulation of lactic acid (Bright and Ellis, 1992). Thus the electrophysiological adaptations that could contribute to MDV elevation in acidic pHo could also explain the increase MDV in hypoxia.
Lack of Relationship between DF and MDV
As discussed above, previous isolated heart studies have suggested a correlation between the complexity of the electrical activity and the required defibrillation energy (Barton et al., 2000; Hillebrenner et al., 2004; Rodriguez et al., 2004). In contrast, the slower electrical activity in clinical and in situ heart animal studies are associated with less successful defibrillation (Brown et al., 1989; Stewart et al., 1992), and partial restoration of perfusion increases the ECG DF (Berg et al., 2004; Eftestol et al., 2004), and improves defibrillation success (Niemann et al., 2000; Wik et al., 2003).
In this study, there was no correlation between the VF electrical activity as measured by the psECG DF immediately prior to defibrillation and the MDV. This lack of correlation is not surprising as the outcome of defibrillation is influenced by more than the electrical co-ordination at the point of defibrillation. Factors such as heterogeneity of refractoriness, conductivity (Kagiyama et al., 1982), and DAD (Chattipakorn and Ideker, 2003) all have roles to play in defibrillation failure.
Mechanistic Insights into Increased MDV
To date several theories exist as to why VF is reinitiated after defibrillation. This study highlights how no single electrophysiological mechanism is responsible in all cases of failed defibrillation.
Dispersion of repolarization and refractoriness
A key concept in defibrillation is heterogeneity of repolarization and refractoriness at defibrillation. Computer simulations predict that such increased electrical complexity will increase DFT by increased complexity of virtual electrode polarizations and therefore increasing the likelihood of formation of point singularities to re-establish VF (Plank et al., 2005). Previous studies have used the CoV of the VFI to assess the dispersion of refractoriness (Opthof et al., 1991, 1993; Burton and Cobbe, 1998; Burton et al., 2000). In this study, the CoV of DF was calculated. This failed to show any significant change in electrical heterogeneity either between, or within protocols. This suggests that increased dispersion of heterogeneity of refractoriness is not a pre-requisite to increased defibrillation energy.
Coefficient of variance of DF does not examine the influence of alteration of repolarization. However this is also unlikely to be a pre-requisite for defibrillation failure as in this study both hypoxia and acidic pHo were responsible for increasing MDE. Previous studies show that hypoxia results in early shortening of repolarization (Kodama et al., 1984; Tissier et al., 2002), whereas acidic pHo is more likely to cause APD prolongation (Spitzer and Hogan, 1979; Kagiyama et al., 1982). However, action potential duration does not necessarily correlate with DF because changes in post-repolarization refractoriness do not always follow action potential duration. Previous studies by Caldwell et al. (2007) show a shortening of action potential duration during perfusion with raise extracellular potassium, but no change in effective refractory period.
Alteration in conduction velocity
Alterations in conductivity have also been implicated in defibrillation failure by increasing the likelihood of point singularity formation (Plank et al., 2005). Although not examined in this study alterations in conductivity are again unlikely to be the unifying mechanism of increased MDE. Whilst hypoxia has minimal effect on conductivity (Veenstra et al., 1987), acidic pH has a profound slowing effect (Kagiyama et al., 1982; Veenstra et al., 1987).
A final mechanism of defibrillation failure suggested by Chattipakorn and Ideker (2003) is the reinitiation of VF by DADs. This hypothesis was suggested after the DAD inhibitor, flunarizine, was shown to significantly improve defibrillation efficacy. This is unlikely to be a unifying mechanism to the varied MDEs observed in this study. Whilst acidic pHo has been shown to increase the likelihood of DADs, hypoxia has been documented to decrease their incidence (Coetzee and Opie, 1987).
In summary, conditions that reduced the overall frequency of VF (i.e., low-flow ischemia or raised extracellular [K+]o) did not increase the defibrillation energy to the same extent as that induced by acidic and hypoxic conditions. Neither of these latter conditions significantly affected the frequency of VF. This is the first study to report two ischemic conditions (acidic pH and hypoxia) that substantially increase MDV without changing the DF of VF. The study also shows a lack of association between dispersion of refractoriness and defibrillation energies, suggesting that increased heterogeneity of refractoriness is not a pre-requisite for reduced defibrillation success.
This study demonstrated that during prolonged VF the MDV was increased by hypoxia and acidic pHo. The reversal of acidosis with buffering agent has previously been attempted with varying success (Kette et al., 1990; Bar-Joseph et al., 1998). This probably relates to the fact that in ischemia the acidosis is primarily an intracellular lactic acidosis, which buffers are less able to reverse (Kette et al., 1990). Establishing perfusion and maximizing oxygenation are more likely to reverse this acidosis (Idris et al., 1994).
Conflict of Interest Statement
The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.
Dr. Jane C. Caldwell was supported during this work through the British Heart Foundation Clinical PhD Fellowship scheme.
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Keywords: optical mapping, ischemia, ventricular fibrillation, defibrillation
Citation: Caldwell JC, Burton FL, Cobbe SM and Smith GL (2011) Slowing of electrical activity in ventricular fibrillation is not associated with increased defibrillation energies in the isolated rabbit heart. Front. Physio. 2:11. doi: 10.3389/fphys.2011.00011
Received: 16 September 2010;
Accepted: 09 March 2011;
Published online: 06 April 2011.
Edited by:Tobias Opthof, Academic Medical Center, Netherlands
Reviewed by:Haruo Honjo, Research Institute of Environmental Medicine, Nagoya University, Japan
Antoni Cg Van Ginneken, Academic Medical Centre, Netherlands
Copyright: © 2011 Caldwell, Burton, Cobbe and Smith. This is an open-access article subject to a non-exclusive license between the authors and Frontiers Media SA, which permits use, distribution and reproduction in other forums, provided the original authors and source are credited and other Frontiers conditions are complied with.
*Correspondence: Godfrey L. Smith, University of Glasgow, West Medical Building, Glasgow G128QQ, UK. e-mail: firstname.lastname@example.org