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Introducing simulated IK1 into human iPSC-cardiomyocytes using
dynamic clamp on an automated patch clamp setup
Introduction Combining dynamic clamp with APC Applying seal compensation to
hiPSC-cardiomyocytes
Effect of applying seal compensation and simulated IK1 to hiPSC-cardiomyocytes on AP shape and pharmacology Conclusions
Gang Lu1, András Horváth2, Nadine Becker2, Sonja Stoelzle-Feix2, Alan Fabbri3, Christian Grad2, Michael George2, Niels Fertig2,
Teun P. de Boer3
1Nanion Technologies Inc, Livingston, NJ, USA, 2Nanion Technologies, Munich, Germany, 3Department of Medical Physiology, Division of Heart & Lungs, University Medical Center
Utrecht, Utrecht, Netherlands.
Dynamic clamp is a powerful tool to inject real-time simulated
currents into patch clamped cells1. This has been shown using
conventional patch clamp whereby the inward rectifier current IK1
was introduced into human induced pluripotent stem cell-derived
cardiomyocytes (hiPSC-CMs)2,3. IK1 is expressed at low levels in
these cells4, hence their membrane potential is more depolarized
than that of primary cardiomyocytes4,5, limiting their use in safety
pharmacology. Introducing simulated IK1 into hiPSC-CMs may
render them a viable alternative to scarcely available adult
human cardiomyocytes.
In this study, we combined dynamic clamp with an automated
patch clamp (APC) system to demonstrate that IK1 conductance
can be added to hiPSC-CMs on this platform, while at the same
time, applying automatic Rseal compensation (SC). Our results show
that virtual IK1 can be successfully injected into hiPSC-CMs in up to
8 cells simultaneously and that Rseal is correctly compensated
avoiding overcompensation. Our approach results in more stable
resting membrane potentials and improved action potential (AP)
shape. „L”-Type calcium channel opener BayK and channel
blocker nifedipine were also tested. Figure 1 Block diagram showing connections between Patchliner, patch
clamp amplifier and dynamic clamp system.
Figure 2 hiPSC Cellartis Cardiomyocytes recorded on the Patchliner.
A Na+ currents and average IV plot (B, n = 7). C Ca2+ currents and
average IV plot (D, n = 18). E Raw traces of Ca2+ current (black:
control, blue: nifedipine). F Nifedipine concentration response curve.
Data from Ref. 6.
Figure 3 Impact of seal compensation on the shape of the cardiac
AP recorded from hiPSC cardiomyocytes. Introducing 100% seal
compensation allowed to remove the majority of the holding
current. Combining seal compensation with various amounts of
virtual IK1 enhanced the 4th phase of the repolarization of the
cardiac AP.
Figure 4 Screenshot taken from the PatchMaster software
with 6 APs recorded in parallel from hiPSC-cardiomyocytes
on the Patchliner Octo. Seal compensation combined with
simulated IK1 using dynamic clamp resulted in longer APs.
Figure 5 A: APs recorded from Cor.4U hiPSC-CMs applying seal compensation and simulated IK1. B: Effect of seal compensation combined with simulated IK1 on APD90
compared to the use of holding current (*P<0.05, unpaired Student’s T-test) in Cor.4U hiPSC-CMs. C: Effect of 10 µM Nifedipine on APD90 in Cor.4U hiPSC-CMs (*P<0.05,
paired Student’s T-test). D: APs recorded from CDI2 hiPSC-CMs under control conditions and after addition of 10 µM BayK 8644 and 10 µM Nifedipine. E: Effect of BayK
8644 and Nifedipine on the APD90 of CDI2 hiPSC-CMs (*P<0.05, paired Student’s T-test). F: Dose-response curve of BayK 8644 on APD90 in CDI2 hiPSC-CMs.
• Dynamic clamp is a powerful tool to inject real-time simulated currents
into cells and here we combine the technique with an automated
patch clamp device, the Patchliner Octo.
• IK1 and seal compensation were successfully applied to hiPSC-CMs in
multiple cells simultaneously and effects on RMP and AP duration were
comparable to those obtained using manual patch clamp2,3.
• Ca2+ channel activator, BayK 8644, and blocker, nifedipine, prolonged
and shortened AP duration, respectively, as expected.
• Future goals:
• Test effects of the set of drugs defined by CiPA on action
potentials under dynamic clamp.
• Upgrade technique to higher throughput devices, e.g.
SyncroPatch 384/768PE.
References
1. Wilders R. J. Physiol. 2006;576:349–359
2. Bett GC, et al. Heart Rhythm. 2013;10:1903–1910.
3. Meijer van Putten RM, et al. Front. Physiol. 2015;6:7. doi: 10.3389/fphys.2015.00007
4. Jonsson MKB, et al. J. Mol. Cell Cardiol. 2012;52:998–1008
5. Rajamohan D, et al. Stem Cells Dev. 2016;25:439–452
6. Goversen B., et al. 2018. Front. Physiol. 6:1094
n = 7
Vhalf = -45 mV
n = 18
Vhalf = -5.8 mV
Control10 µM Nifedipine
Washout0
–50 mV
100 ms Only Ihold 70 % SC + 400 pS/pF IK1
0
50
100
150
200
*
n=23 n=20
AP
D9
0(m
s)
Control 10 µM Nifedipine0
50
100
150
200 *
AP
D9
0(m
s)
n=13A B C
Control10 µM BayK
10 µM Nifedipine0
–50 mV
100 msControl 10 µM BayK 10 µM Nifedipine
0
50
100
150
200
*
*
AP
D9
0(m
s)
n=11D E
0.0
0.5
1.0
-9 -8 -7 -6CTL
n=13EC50=233 nM
log [BayK] (M)
Ac
tiv
ati
on
%
Voltage clamp characteristics of
hiPSC-cardiomyocytes
F