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J Physiol 589.24 (2011) pp 6081–6092
Shaping a new Ca2+ conductance to suppress early
afterdepolarizations in cardiac myocytes
Roshni V. Madhvani1 , Yuanfang Xie2,3 , Antonios Pantazis1 , Alan Garfinkel2,5 , Zhilin Qu2,3 ,
James N. Weiss2,3,4 and Riccardo Olcese1,3
1
Division of Molecular Medicine – Department of Anesthesiology, 2 Department of Medicine (Cardiology), 3 Cardiovascular Research Laboratory,
Departments of Physiology, and 5 Departments of Integrative Biology & Physiology, David Geffen School of Medicine at University of California, Los
Angeles, CA 90095-7115, USA
The Journal of Physiology
4
Non-technical summary Diseases, genetic defects, or ionic imbalances can alter the normal
electrical activity of cardiac myocytes causing an anomalous heart rhythm, which can degenerate
to ventricular fibrillation (VF) and sudden cardiac death. Well-recognized triggers for VF are
aberrations of the cardiac action potential, known as early afterdepolarizations (EADs). In
this study, combining mathematical modelling and experimental electrophysiology in real-time
(dynamic clamp), we investigated the dependence of EADs on the biophysical properties of the
L-type Ca2+ current (I Ca,L ) and identified modifications of I Ca,L properties which effectively
suppress EAD. We found that minimal changes in the voltage dependence of activation or
inactivation of I Ca,L can dramatically reduce the occurrence of EADs in cardiac myocytes exposed
to different EAD-inducing conditions. This work assigns a critical role to the L-type Ca2+ channel
biophysical properties for EADs formation and identifies the L-type Ca2+ channel as a promising
therapeutic target to suppress EADs and their arrhythmogenic effects.
Abstract Sudden cardiac death (SCD) due to ventricular fibrillation (VF) is a major
world-wide health problem. A common trigger of VF involves abnormal repolarization of
the cardiac action potential causing early afterdepolarizations (EADs). Here we used a hybrid
biological–computational approach to investigate the dependence of EADs on the biophysical
properties of the L-type Ca2+ current (I Ca,L ) and to explore how modifications of these properties
could be designed to suppress EADs. EADs were induced in isolated rabbit ventricular myocytes
by exposure to 600 μmol l−1 H2 O2 (oxidative stress) or lowering the external [K+ ] from 5.4
to 2.0–2.7 mmol l−1 (hypokalaemia). The role of I Ca,L in EAD formation was directly assessed
using the dynamic clamp technique: the paced myocyte’s V m was input to a myocyte model with
tunable biophysical parameters, which computed a virtual I Ca,L , which was injected into the myocyte in real time. This virtual current replaced the endogenous I Ca,L , which was suppressed with
nifedipine. Injecting a current with the biophysical properties of the native I Ca,L restored EAD
occurrence in myocytes challenged by H2 O2 or hypokalaemia. A mere 5 mV depolarizing shift
in the voltage dependence of activation or a hyperpolarizing shift in the steady-state inactivation
curve completely abolished EADs in myocytes while maintaining a normal Cai transient. We
propose that modifying the biophysical properties of I Ca,L has potential as a powerful therapeutic
strategy for suppressing EADs and EAD-mediated arrhythmias.
(Received 26 August 2011; accepted after revision 21 October 2011; first published online 24 October 2011)
Corresponding author R. Olcese: Division of Molecular Medicine, BH 570 CHS, Department of Anesthesiology, D.
Geffen School of Medicine, University of California Los Angeles, CA, USA. Email: rolcese@ucla.edu
Abbreviations AP, action potential; APD, action potential duration; CaMKII, Ca2+ –calmodulin-dependent protein
kinase II; EAD, early afterdepolarization; I Ca,L , L-type Ca2+ current; RTXI, real-time experimental interface; SR,
sarcoplasmic reticulum; VF, ventricular fibrillation; VT, ventricular tachycardia.
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DOI: 10.1113/jphysiol.2011.219600
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R. V. Madhvani and others
Introduction
Early afterdepolarizations (EADs) are transient reversals of
normal repolarization (i.e. positive dV /dt), occurring in
late phase 2 or phase 3 of the cardiac action potential (AP).
These events, observable both at the cellular and tissue
level, are recognized as triggers of cardiac arrhythmias
(Sato et al. 2009; Weiss et al. 2010b). When EADs propagate
through cardiac tissue, they can generate premature
heart beats, ventricular tachycardia (VT) and ventricular
fibrillation (VF), common causes of sudden cardiac death
in a variety of clinical settings.
EADs classically occur during bradycardia under
conditions of reduced repolarization reserve, due to either
abnormally decreased outward currents, or increased
inward currents, or both. The predominant inward
currents in ventricular myocytes which have been
implicated in EAD genesis are the persistent I Na (Maltsev
et al. 1998), I NCX (Volders et al. 1997; Szabo et al.
1994) and I Ca,L (January & Riddle, 1989). Previous work
has shown that reactivation of the L-type Ca2+ current
(I Ca,L ) during phase 2 and 3 of the action potential (AP)
plateau plays a major role in EAD formation (January
et al. 1988), although other factors are also important
(Weiss et al. 2010a). Most EADs are initiated between
−40 and 0 mV (Fig. 1), corresponding to the range of
membrane potentials where the steady-state activation
and inactivation curves of I Ca,L overlap, often referred to
as the ‘window current’ region (January & Riddle, 1989;
Antoons et al. 2007a). As the AP repolarizes into this
voltage ‘window’, a fraction of the L-type Ca2+ channels
not inactivated may be available for reactivation to
generate the upstroke of the EAD. In this study, we sought
to determine the relevance of I Ca,L in EAD formation, and
investigated whether EAD suppression can be achieved
solely by manipulating I Ca,L without altering other
ionic conductances or signalling pathways. We analysed
whether EAD formation can be suppressed by minimal
perturbation of the biophysical properties of L-type Ca2+
channels affecting the I Ca,L window voltage region. Since
it is difficult to control these properties experimentally
with any degree of precision, we adopted a hybrid
biological–computational approach using the dynamic
clamp technique (Dorval et al. 2001; Berecki et al. 2005,
2006, 2007; Wilders, 2006). This allowed us to replace
the native I Ca,L of the myocyte with a computed virtual
I Ca,L with programmable properties. Our findings show
that EAD formation is highly sensitive to I Ca,L properties
and properties of the window region (such as the slopes
of the activation and inactivation curves (Tran et al.
2009)), such that subtle shifts in the voltage dependence
of steady-state I Ca,L activation or inactivation can abolish
EADs. Moreover, these changes are predicted to have no
significant effects on the amplitude or kinetics of the intracellular Ca2+ transient, suggesting that pharmacological or
J Physiol 589.24
genetic manipulation of the voltage-dependent properties
of I Ca,L could have therapeutic potential for suppressing
EAD-mediated arrhythmias without adversely affecting
excitation–contraction coupling.
Methods
Ethical approval
All animal protocols were approved by the UCLA
Institutional Animal Care and Use Committee and
conformed to the Guide for the Care and Use of Laboratory
Animals published by the US National Institutes of Health.
Electrophysiology
Ventricular myocytes were isolated from New Zealand
White rabbits as previously described (Mahajan et al.
2008a). All animals were anaesthetized with 50 mg ml−1
intravenous pentobarbital, before excision of the hearts,
which were subsequently submerged in Ca2+ -free Tyrode
solution containing (in mmol l−1 ): 136 NaCl, 5.4 KCl,
1 MgCl2 , 0.33 NaH2 PO4 , 10 glucose, and 10 Hepes,
adjusted to pH 7.4. The hearts were cannulated
and perfused retrogradely on a Langendorff apparatus
with Ca2+ -free Tyrode buffer containing 1.65 mg ml−1
collagenase and 0.8 mg ml−1 bovine serum albumin for
30–40 min. After washing out the enzyme solution, the
hearts were swirled in a beaker to dissociate cells. The Ca2+
concentration was gradually increased to 1.8 mmol l−1 ,
and the cells were stored at room temperature. This
procedure typically yielded 50% rod-shaped Ca2+ -tolerant
myocytes. Only Ca2+ -tolerant, rod-shaped ventricular
myocytes with clear striations were randomly selected
for electrophysiological studies within 8 h of isolation.
All recordings were measured with AxoPatch 200B
(Axon Instruments). Whole-cell patch-clamp recordings
(in current or voltage clamp mode) were performed
at 34–36◦ C using pipettes of 1–2 M. The intracellular solution contained (in mmol l−1 ): 110 potassium
aspartate, 30 KCl, 5 NaCl, 10 Hepes, 0.1 EGTA, 5 MgATP,
5 creatine phosphate, 0.05 cAMP adjusted to pH 7.2. For
I Ca,L recordings the solutions were as described above,
except that K+ was replaced with Cs+ to abolish K+
conductance and 10 μmol l−1 TTX was added to the
extracellular solution to block Na+ conductance. The
L-type-specific Ca2+ current was determined by subtracting the current after 20 μmol l−1 nifedipine from
the total current. Data were acquired and analysed using
custom-made software (G-Patch, Analysis). Currents
were filtered at 1/5 of the sampling frequency. The
steady-state activation curves were constructed by dividing
the peak I–V curve by the driving force to calculate
conductance (G) and dividing G by G max . The inactivation
curves were constructed by plotting the normalized peak
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J Physiol 589.24
ICa,L window current properties set EAD susceptibility
current during a test pulse at 10 mV following a 300 ms
inactivating pulse at various voltages. The slope and
half-activation/inactivation potential of these curves were
estimated by fitting to a Boltzmann distribution, and
these parameters were used to constrain the dynamic
clamp model for both control and H2 O2 conditions. These
two versions of the model were then implemented for
Dynamic Clamp in RTXI (www.rtxi.org) (Lin et al. 2010).
Sampling/computation frequency was 10 kHz.
Rudy, 1994), where P o is formulated as:
Po = d f q
where d is the voltage-dependent activation gate, f is
the voltage-dependent inactivation gate and q is the
Ca2+ -dependent inactivation gate. The steady states
of these gating variables as functions of voltage are
formulated in the following manner:
1.0
1.0 + exp(−(v − dhalf )/dslope )
(3)
1.0 − p dest
+ p dest
1.0 + exp((v − dhalf )/dslope )
(4)
1.0
C s γ
1.0 + cst
(5)
d∞ (1 − exp(−v − (dhalf + a1 ))
a2 (dslope + a2 )(v − (dhalf + a1 ))
(6)
d∞ =
Intracellular calcium measurements
Myocytes were loaded with 10 μmol l−1 Fluo4-AM
(Molecular probes) for 30 min at room temperature.
Cells were then washed twice in regular Tyrode solution
and placed in a heated chamber at 34–36◦ C for
fluorescence and electrophysiology measurements. Intracellular calcium (Cai ) transients were recorded using a
CMOS camera (Silicon Imaging SI-1300, Niskayuna, NY,
USA).
Dynamic clamp
f∞=
q∞ =
τd =
τf = b1 exp(−b2 (v − (f half + b3 ))2 ) + b4
The ionic conductances included in the model are
I Ca,L , the fast sodium current I Na , the Na+ –K+ pump
current I NaK , the Na+ –Ca2+ exchange current I NCX , and
the Ca2+ -dependent slow component of the delayed
rectifier potassium channel I Ks . The intracellular Ca2+
concentration was divided into four compartments, i.e.
submembrane Ca2+ (C s ), cytosolic Ca2+ (C i ) and network
SR Ca2+ and junctional SR Ca2+ . The average submembrane Ca2+ concentration, C s , is used to compute
Ca2+ -dependent inactivation in the I Ca,L formulation. The
Ca2+ flux into the cell due to I Ca,L is given by (Mahajan
et al. 2008b):
J Ca = g Ca P o i Ca ,
4P Ca VF 2 C s e 2a − 0.341[Ca2+ ]o
RT
e 2a − 1
(7)
where τd and τf are the time constants of d gate and f
gate respectively, d half is the voltage at half maximum of
activation/inactivation (f half ), d slope is the slope factor of
the activation curve, pdest is the non-inactivating pedestal
of the inactivation gate, C s is the submembrane Ca
concentration in units of mM, Cst is the affinity for Ca
of the inactivation gate, and a1, a2, b1, b2, b3, and b4
are additional factors used for fitting. All the parameters
listed in the equations are fitted to our experimental data
(the fitting parameters are shown in online supplemental
materials). The Ca2+ cycling is the same as that in the rabbit
ventricular myocyte model (Mahajan et al. 2008b).
(1)
where J Ca is the current flux into the cell via L-type
Ca2+ channels, g Ca is determined by fitting to the
nifedipine-sensitive current traces measured under voltage
clamp, P o is the probability of finding an L-type Ca2+
channel in the open state, and iCa is the driving force for
Ca2+ given by:
i Ca =
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(2)
where C s is the submembrane concentration in units
of mmol l−1 , P Ca (0.00054 cm/s) is the Ca channel
permeability and V is the membrane voltage, F is the
Faraday constant, and T is temperature. In order to
facilitate shifts of the activation and inactiation curves, we
replaced the Markovian calcium channel open probability
P o (Mahajan et al. 2008b) with the Hodgkin–Huxley
formulation from the Luo–Rudy dynamic model (Luo &
Results
Oxidative stress-induced and hypokalaemia-induced
EADs in isolated rabbit ventricular myocytes
To determine the relevance of I Ca,L biophysical properties
to EAD formation and/or suppression, we used two
methods to induce EAD in whole-cell patch-clamped isolated rabbit ventricular myoyctes: (i) oxidative stress, by
exposure to 600 μmol l−1 H2 O2 (Xie et al. 2009), or (ii)
hypokalaemia, by lowering extracellular [K+ ] (from 5.4
to 2.0–2.7 mmol l−1 ). Myocytes were superfused in the
recording chamber at 34–36◦ C, and stimulated at a pacing
cycle length (PCL) of 5 s (Fig. 1). Under current clamp,
both H2 O2 (n = 14) and hypokalaemia (n = 8) prolonged
the APD significantly and consistently produced EADs in
∼70% of paced APs (Fig. 1A and B) within 5–10 min.
In our analysis, we individually inspected each action
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potential for EAD occurrence, defined as well-resolved
deflections of the voltage with a positive dV /dt during
late phase 2 or phase 3 of the AP. EAD morphology
varied among experiments and also within the same action
potential as in Fig. 1B (under hypokalaemia). Typically,
EADs exhibited a positive voltage deflection of ≥5 mV
with durations (from inflection point to peak) between 30
and 150 ms).
Among other effects, oxidative stress with
H2 O2 is known to promote EADs by activating
Ca2+ –calmodulin-dependent protein kinase II (CaMKII)
(Xie et al. 2009), which alters I Ca,L (Dzhura et al. 2000)
and induces late I Na (Wagner et al. 2006; Wagner et al.
2011). To characterize how H2 O2 altered I Ca,L properties
under our experimental conditions, we recorded the
nifedipine-sensitive Ca2+ current in voltage-clamped isolated myocytes before and after exposure to 600 μmol l−1
H2 O2 (n = 5) (Fig. 2): in addition to an overall slowing
J Physiol 589.24
of inactivation (Fig. 2A and B), H2 O2 shifted the peak
of the current–voltage (I–V ) relationship by −5 mV as
shown in Fig. 2C. By constructing steady-state activation
and inactivation curves, we found that H2 O2 produced an
∼−5 mV shift of the steady state half-activation potential
(V 1/2,act ), accompanied by an ∼+5 mV shift in the steady
state half-inactivation potential (V 1/2,inact ) (Fig. 2D).
Effectively, H2 O2 increased the height of the I Ca,L window
current region, changes which are expected to promote
EAD formation (Antoons et al. 2007b; Qi et al. 2009; Tran
et al. 2009).
Role of oxidative stress-mediated I Ca,L alterations in
EAD generation
To understand how the H2 O2 -induced changes in I Ca,L
described above contributed to EAD formation, we next
used the dynamic clamp technique (Tan & Joyner, 1990) to
Figure 1. Oxidative stress and hypokalaemia generate EADs in dissociated rabbit cardiomyocytes
A, representative AP recordings in current-clamped ventricular myocytes stimulated at a pacing cycle length of
5 s. EADs, absent in control conditions, were consistently induced by addition of 600 µmol l−1 H2 O2 to the bath
solution or by reducing extracellular [K+ ] from 5.4 mmol l−1 to 2.7 mmol l−1 (hypokalaemia). The histogram to
the left of each trace shows the distribution of action potential duration measured at 90% repolarization (APD90 )
for each condition. B, action potentials in the dotted box in A are shown on an expanded scale (arrows point to
EADs). C, percent of action potentials displaying EADs in Control, H2 O2 and hypokalaemia conditions.
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J Physiol 589.24
ICa,L window current properties set EAD susceptibility
replace the myocyte’s native I Ca,L with a virtual I Ca,L with
programmable properties. The principle of the dynamic
clamp operation is illustrated in Fig. 3A. The recorded
membrane potential of a current-clamped myocyte (V m )
is fed into a Linux-based computer with the Real-time
Experimental Interface (RTXI) software (Dorval et al.
2001) running the UCLA ventricular myocyte AP model
(Mahajan et al. 2008b). The model computes, in real time,
the macroscopic L-type Ca2+ channel current, which is
injected continuously into the myocyte, in turn changing
its membrane potential. This cycle (V m sampling → I Ca,L
computation → I Ca,L injection → V m sampling . . .)
is iterated at 10 kHz, creating a dynamic, bidirectional
relationship between the model and the cell.
The virtual I Ca,L computed in the AP model was
tuned to fit experimental recordings of native I Ca,L
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recorded from rabbit ventricular myocytes (Fig. 3B). In
addition to computing I Ca,L , the model also computes
all other elements of Cai cycling in the UCLA rabbit
ventricular myocyte model (Mahajan et al. 2008b), which
is critical for simulating the effects of intracellular Ca2+
on Ca2+ -dependent inactivation of the virtual I Ca,L being
injected into the myocyte. Thus, this model also generates
a virtual intracellular Ca2+ transient, which showed good
agreement with the intracellular Ca2+ transient recorded
directly from a myocyte under control conditions (Fig. S1).
The model computes Ca2+ concentrations in four discrete
subcellular compartments (Fig. 3A), with the average
submembrane Ca2+ concentration (C s ) used for the
calculation of Ca2+ -dependent inactivation of I Ca,L , as
described previously (Mahajan et al. 2008b). Although we
initially used a seven-state Markovian description of I Ca,L ,
Figure 2. H2 O2 alters both the time-dependent and steady-state properties of ICa,L in rabbit ventricular
myocytes
A, voltage clamp recordings of nifedipine (20 µmol l−1 ) sensitive ICa,L in response to depolarizing pulses from
−40 mV (HP = −80 mV), under control conditions (black) or after 2 min of exposure to 600 µmol l−1 H2 O2
(red). B, voltage clamp recordings of nifedipine-sensitive ICa,L in response to a two-pulse protocol from a holding
potential of −90mV, under control conditions (black) or after 2 min of exposure to 600 µmol l−1 H2 O2 (red). The
inactivating pulse was 300 ms to approximate the duration of a normal action potential. C, the I–V relationship
for ICa,L (normalized to the peak current) under control conditions (black circles, n = 4) and H2 O2 (red circles,
n = 5). Note the negative shift of the I–V curve in H2 O2 . D, mean steady-state activation and inactivation curves
for ICa,L in control (black circles, n = 4) and H2 O2 conditions (red diamonds, n = 5). Note that the H2 O2 -induced
shift of steady-state curves results in a higher ICa,L window area. External solution (mmol l−1 ): 136 NaCl, 5.4 CsCl,
1 MgCl2 , 0.33 NaH2 PO4 , 1.8 CaCl2 , 10 glucose, 10 Hepes, and 10 µmol l−1 TTX, pH 7.4. Pipette solution (in
mmol l−1 ): 100 caesium aspartate, 30 CsCl, 5 NaCl, 10 Hepes, 0.1 EGTA, 5 MgATP, 5 creatine phosphate, 0.05
cAMP, pH 7.2. Temperature = 35–37◦ C.
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we achieved equivalent accuracy of fitting the experimental
I Ca,L data with a Hodgkin–Huxley type I Ca,L formulation,
with the advantage that the biophysical parameters
relevant to this work could be directly modified, such as
V 1/2,act and V 1/2,inact , which determine the steady-state
activation and inactivation properties of the injected
virtual I Ca,L .
In our experimental protocol utilizing the dynamic
clamp technique, we first paced a rabbit ventricular myocyte to record the AP in the current clamp mode (Fig. 4A,
trace 1). The recorded AP waveform was used to compute a
virtual Cai transient, displayed below the AP trace (Fig. 4B,
trace 1). The myocyte was then exposed to 600 μmol l−1
H2 O2 until EADs appeared consistently (Fig. 4A, trace
2). Nifedipine (20 μmol l−1 ) was then added to block
the native I Ca,L , which markedly shortened APD and
abolished EADs (Fig. 4, trace 3). Current injection by the
dynamic clamp was then turned on, adding the virtual
I Ca,L computed from the UCLA rabbit ventricular AP cell
model (Mahajan et al. 2008b), whose properties had been
adjusted to simulate the previously analysed effects of
H2 O2 on I Ca,L gating properties shown in Fig. 2. Injection
J Physiol 589.24
of this ‘H2 O2 -modified’ virtual I Ca,L effectively restored the
electrical properties of the myocyte membrane, resulting
in AP prolongation and the reappearance of EADs (Fig. 4,
trace 4). The associated computed virtual Cai transients
are shown in Fig. 4B.
To investigate the sensitivity of EAD formation to the
properties of the virtual I Ca,L , we then shifted the voltage
dependence of I Ca,L activation (V 1/2,act ) by +5 mV, to
resemble the normal steady activation curve prior to H2 O2
exposure. This small shift, which effectively suppressed the
I Ca,L ‘window’ current by reducing the overlap between the
steady state activation and inactivation curves to (Fig. 4C),
abolished EADs and restored the AP duration towards
the control value (Fig. 4, trace 5). Moreover, the virtual
Cai transient (Fig. 4B, trace 5) had similar amplitude
and kinetics to that computed for the normal control
AP (Fig. 4B, trace 1). Similar results were also achieved
by shifting the voltage dependence of I Ca,L inactivation
(V 1/2,inact ) in the negative direction to reduce the window
current region (not shown).
The overall results, summarized in Fig. 5, demonstrate
that the small shifts in the V 1/2 of steady-state activation
Figure 3. The dynamic patch clamp implements a
virtual Ca2+ current computed with detailed Ca2+
cycling dynamics
A, diagram of the dynamic clamp system. A ventricular
myocyte is whole-cell patch-clamped with an amplifier
in current-clamp mode. The myocyte’s V m signal (red
arrow) is digitized and input to a computer running a
cardiac action potential model (Mahajan et al. 2008)
containing macroscopic Hodgin–Huxley (HH)-type
formulations for five conductances (ICa,L ; the fast Na+
channel INa ; the Na+ /K+ pump INaK ; the Na+ /Ca2+
exchanger INCX ; and the Ca2+ -dependent K+ rectifier
IKs ) and [Ca2+ ] in four discrete cellular compartments
(C s , C i , C jp and C j ). Ionic conductances and
concentrations can be fine-tuned by altering model
parameters online. The calculated ionic conductances
can be output in any combination to produce ICommand .
In this case, ICommand = ICa,L (blue arrow). ICommand is
combined with a pacing AP stimulus and converted to
analog before being input to the amplifier to be injected
into the clamped myocyte. This alters the myocyte V m ,
which is in turn sampled for the next computation.
Thus, there is a dynamic, bidirectional relationship
between V m and model conductance output, at a
sampling/computation frequency of 10 kHz. B, the
predicted ICa,L conductance from the model in panel A
(red) accurately predicts a current similar in amplitude
and kinetics to experimentally recorded ICa,L from rabbit
cardiomyocytes (black) in response to depolarizing
pulses from a holding potential of −40 mV.
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J Physiol 589.24
ICa,L window current properties set EAD susceptibility
and inactivation of I Ca,L strongly suppress EAD formation.
A +4 mV shift of the V 1/2,act from −5 mV to −1 mV
(Fig. 5A) shortened APD90 from 1197 ± 112 (n = 7) to
373 ± 15 ms (n = 4) (Fig. 5B) and suppressed EAD
occurrence from 91 ± 4% to 24 ± 20% of paced APs
(Fig. 5C). An additional +1 mV shift to 0 mV (Fig. 5A)
shortened APD90 to 331 ± 15 ms (n = 6) (Fig. 5B) and
further suppressed EAD occurrence to ∼2% (Fig. 5C).
Similar results were achieved with small hyperpolarizing
shifts in the V 1/2,inact . A −3 mV shift from −17 mV to
−20 mV (Fig. 5D) reduced APD90 to 696 ± 42 ms (n = 3)
(Fig. 5E) and EAD occurrence to 52% (Fig. 5F). Further
shifting V 1/2,inact by an additional −2 mV to −22 mV
(Fig. 5D) reduced APD90 to 488 ± 21 ms (n = 4) (Fig. 5E)
and EAD occurrence to 10%.
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Reducing I Ca,L window current also suppresses
hypokalaemia-induced EADs
To demonstrate that the results described above are not
unique to H2 O2 -induced EADs, we also assessed the
effectiveness of shifting V 1/2,act or V 1/2,inact at suppressing
hypokalaemia-induced EADs. Lowering extracellular K+
from 5.4 to 2.0 mmol l−1 hyperpolarized the resting
membrane potential to nearly −100 mV and induced
EADs within 5 min (Fig. 1 and 6). As with H2 O2 -induced
EADs, blocking I Ca,L with 20 μmol l−1 nifedipine
abolished EADs and shortened the action potential (not
shown). Adding a virtual I Ca,L with dynamic clamp
prolonged APD90 to 2170 ± 190 ms (n = 6) (Fig. 6C and
E, hatched bars) and reconstituted EADs in 83% of APs
Figure 4. Reconstitution of EADs by a virtual I Ca,L and their suppression by shifting I Ca,L V 1/2 activation
A, APs from rabbit ventricular myocytes recorded at a pacing cycle length of 5 s at 36–37◦ C in control conditions (1).
Addition of 600 µmol l−1 H2 O2 to the bath solution induced EADs within 5–10 min (2). Addition of 20 µmol l−1
nifedipine blocked the native ICa,L , shortened APD and abolished EADs (3). The dynamic clamp was then turned on
to inject a virtual ‘ICa,L ’ computed in real time (red trace), which restored EADs (4). Varying a single ICa,L parameter
(V 1/2 activation) by +5 mV to effectively reduce the ‘ICa,L window region’ abolished EADs, despite the presence
of H2 O2 (5). B, representative action potentials from each condition (numbered) in A and their corresponding
virtual Cai transients. Note that both action potential duration and the shape and amplitude of the computed
Cai transient in conditions (1) and (5) are similar. C, graphical representation of the change in the overlap of the
activation and steady-state inactivation curves upon a +5 mV shift in the V 1/2 of activation.
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(Fig. 6D and F, hatched bars). A +5 mV depolarizing shift
in the steady state activation curve from −1 to +4 mV
shortened APD90 to 476 ± 39 ms (n = 3) (Fig. 6C, open
bar) and reduced EAD occurrence to 0% (Fig. 6D, open
bar). Similarly, a hyperpolarizing shift in the steady state
inactivation curve from −18 to −23 mV shortened APD90
to 869 ± 167 ms (n = 3) and reduced EAD occurrence to
10% of APs.
Discussion
It is widely accepted that EADs are important cellular
triggers for VT and VF when repolarization reserve
is reduced, as can occur clinically in acquired and
congenital long QT syndromes and heart failure (Huffaker
et al. 2004; Maruyama et al. 2011). In the present
study, we used two different conditions, oxidative stress
J Physiol 589.24
(H2 O2 ) and hypokalaemia (Fig. 1), which reliably induce
bradycardia-dependent EADs (positive dV /dt during
phase 2 or 3) by different mechanisms in >90% of
rabbit ventricular myocytes within 5–10 min of exposure.
After blocking the native I Ca,L with nifedipine, we used
the dynamic clamp technique to inject a virtual I Ca,L ,
which successfully reconstituted EADs. Moreover, the
biophysical properties of the virtual I Ca,L could be
reprogrammed to explore its role in EAD formation. Our
major findings are: (i) EAD formation is very sensitive
to small shifts in the voltage sensitivity of steady state
activation and inactivation of I Ca,L , such that a +5 mV
depolarizing shift in V 1/2,act , or a −5 mV hyperpolarizing
shift in V 1/2,inact powerfully suppressed EAD formation
(Figs 4–6); (ii) these small shifts were predicted to have
minimal effects on peak I Ca,L during the AP, such that
the Cai transient, hence excitation–contraction coupling
Figure 5. EADs induced by oxidative stress are steeply dependent on V 1/2 of activation and inactivation
A, steady-state activation and inactivation of the virtual ICaL under control conditions (black) and with the V 1/2
activation shifted by −1 (blue) or −5 mV (red) to partially simulate the effects of oxidative stress increasing the ICaL
window region (cross-hatched). B and C, APD90 (B) and the percentage of AP’s exhibiting EADs (C) corresponding
to the virtual ICa,L activation/inactivation properties in A, when the respective currents were injected by the
dynamic clamp into ventricular myocytes in the presence of 0.6 mmol l−1 H2 O2 and 20 µmol l−1 nifedipine. The
virtual ICa,L simulating oxidative stress caused marked AP prolongation and EADs, which were suppressed by
returning the V 1/2 activation towards normal (blue and black). D, steady-state activation and inactivation of the
virtual ICa,L under control conditions (black) and with the V 1/2 inactivation shifted by +3 (blue) or +5 mV (red)
to partially simulate the effects of oxidative stress increasing the ICa,L window region (cross-hatched). E and F,
APD90 (E) and the percentage of APs exhibiting EADs (F) corresponding to the virtual ICa,L activation/inactivation
properties in A, when the respective currents were injected by the dynamic clamp into ventricular myocytes in
the presence of 0.6 mmol l−1 H2 O2 and 20 µmol l−1 nifedipine. The virtual ICa,L corresponding to the red curve
simulating oxidative stress caused marked AP prolongation and EADs, which were suppressed by returning the
V 1/2 inactivation towards normal (blue and black).
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J Physiol 589.24
ICa,L window current properties set EAD susceptibility
and contractility, remain normal (Fig. 4B); (iii) the same
strategy was effective at suppressing EADs generated by
two different mechanisms (Figs 4 and 6): oxidative stress
in which CaMKII activation potentiating inward Na+ and
Ca2+ currents plays a critical role (Dzhura et al. 2000;
Anderson, 2004; Wagner et al. 2006; Xie et al. 2009; Koval
et al. 2010; Wagner et al. 2011), and hypokalaemia, in
which decreased outward K+ currents play the major role
(Sato et al. 2010). Moreover, the degree of hypokalaemia
used in this study is clinically relevant to values associated
with EAD-mediated arrhythmias in patients (Osadchii,
2010).
These findings have therapeutic implications, namely
that novel agents which alter the voltage dependence
and/or kinetics of I Ca,L could be developed to suppress
EAD-mediated arrhythmias without adversely depressing
excitation–contraction coupling.
Sensitivity of EADs to I Ca,L properties
In the present study, we analysed the effects of small
shifts in the V 1/2,act and V 1/2,inact on EAD formation,
6089
as a convenient way to suppress I Ca,L reactivation in
the window voltage region. However, I Ca,L reactivation
causing EADs during AP repolarization is not solely
dependent on V 1/2,act and V 1/2,inact , but instead is a
complex function of many I Ca,L parameters juxtaposed
with other factors, such as K+ currents influencing
the speed of repolarization (Tran et al. 2009). With
respect to I Ca,L , other parameters in addition to
V 1/2,act and V 1/2,inact influence I Ca,L reactivation during
repolarization, including the maximal L-type Ca2+
current conductance; the steepness (slope factor) of
voltage-dependent activation and inactivation; the time
constants of activation, inactivation (both Ca2+ dependent
and voltage dependent), and recovery from inactivation;
and the amplitude of the non-inactivating pedestal
current. These factors can be combined into a single
mathematical expression giving a necessary condition
for EADs (Tran et al. 2009). In the present study, our
modifications to the virtual I Ca,L assumed that all of these
other factors remained constant, allowing us to examine
the isolated effects of V 1/2,act and V 1/2,inact . Thus, a major
advantage of the dynamic clamp approach is that the
Figure 6. EADs induced by hypokalemia are steeply dependent on V1/2 of activation and inactivation.
A, Under hypokalemic conditions (2.0 mM external K+ ), EADs (blue) were reconstituted in the presence of
20 mM nifedipine by injecting via the dynamic clamp a virtual ICa,L , with normal activation (blue) and inactivation
(black) properties. Shifting the V1/2 of activation by +5 mV (black) to reduce the ICa,L window region reversed AP
prolongation and abolished EADs. B, Similar effects were observed when V1/2 of inactivation was shifted by −5 mV
to reduce the ICa,L window region. C, The +5 mV shift in the activation curve shortened and D, abolished EADs.
E, The −5 mV shift in the inactivation curve also shortened APD90 and F, dramatically reduced EAD occurrence.
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R. V. Madhvani and others
virtual I Ca,L can be programmed to simulate all of the
effects that a candidate agent has on these I Ca,L properties,
once they have been characterized experimentally. The
appropriately reshaped virtual I Ca,L can then be evaluated
to determine whether or not it suppresses EADs in
real myocytes when introduced by the dynamic clamp
technique.
Limitations
J Physiol 589.24
2009) such as α2 δ or β subunits. These accessory subunits are highly specific for the channel and are known
to modulate its biophysical properties (Birnbaumer et al.
1998; Olcese et al. 1994; Platano et al. 2000). Thus, genetic
interventions to tune the biophysical properties of I Ca,L
by altering its subunit composition could be a promising
approach to suppress EAD formation in a highly specific
manner.
References
Although the dynamic clamp provides a technique to
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that a virtual I Ca,L does not trigger SR Ca2+ release, so
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virtual I Ca,L on the Cai transient or cell shortening. This
limitation was partially offset by using an AP model
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Author contributions
R.V.M. performed research. Y.X. and A.P. provided analytical
tools. R.V.M. and R.O. analyzed data. R.V.M, A.G., Z.Q., J.N.W,
and R.O. designed research. R.V.M, A.P., A.G., Z.Q., J.N.W and
R.O. wrote the paper. All authors have approved the final version
of the paper for publication. The authors have no disclosures.
Acknowledgements
We are grateful to David Cristini and Jonathan Bettencourt for
providing expert support with RTXI installation and Maurizio
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6092
R. V. Madhvani and others
Carnesecchi for contributing analytical software. We thank the
members of the Olcese, Weiss, Qu, Garfinkel, Karaguezian
and Chen laboratories for constructive discussions during the
development of the project. This work was supported by research
grants NIH/NHLBI P01HL078931 and R01 HL103662 (to
J Physiol 589.24
J.W.), NIH/NIGMS R01GM082289 (to R.O.), American Heart
Association Predoctoral Fellowship (W.S.A.) 10PRE3290025 to
R.M. and American Heart Association Postdoctoral Fellowship
(W.S.A.) 11POST7140046 to A.P., and the Laubisch and Kawata
endowments (to J.W.).
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