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Bostock, Reza Razavi, Frits Prinzen and C. Aldo RinaldiManav Sohal, Anoop Shetty, Steven Niederer, Zhong Chen, Tom Jackson, Eva Sammut, Julian
Ventricular and Biventricular Endocardial Pacing: Insights from Electro-Anatomical MappingDelayed Trans-Septal Activation Results in Comparable Hemodynamic Effect of Left
Print ISSN: 1941-3149. Online ISSN: 1941-3084 Copyright © 2014 American Heart Association, Inc. All rights reserved.
Dallas, TX 75231is published by the American Heart Association, 7272 Greenville Avenue,Circulation: Arrhythmia and Electrophysiology
published online March 7, 2014;Circ Arrhythm Electrophysiol.
http://circep.ahajournals.org/content/early/2014/03/07/CIRCEP.113.001152World Wide Web at:
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by guest on March 8, 2014http://circep.ahajournals.org/Downloaded from by guest on March 8, 2014http://circep.ahajournals.org/Downloaded from
DOI: 10.1161/CIRCEP.113.001152
1
Delayed Trans-Septal Activation Results in Comparable Hemodynamic Effect
of Left Ventricular and Biventricular Endocardial Pacing:
Insights from Electro-Anatomical Mapping
Running title: Sohal et al.; Endocardial CRT and delayed trans-septal activation
Manav Sohal, MRCP1,2; Anoop Shetty, MD1,2; Steven Niederer, PhD1; Zhong Chen, MRCP1;
Tom Jackson, MRCP1; Eva Sammut, MRCP1; Julian Bostock, MSc2; Reza Razavi MD1;
Frits Prinzen, PhD3; C. Aldo Rinaldi, MD1,2
1Division of Imaging Sciences and Biomedical Engineering, King’s College; 2Cardiovascular Department, Guy’s and St. Thomas’ NHS Foundation Trust, London, United Kingdom; 3Maastricht
University Medical Center, Cardiovascular Research Institute (CARIM), Maastricht, the Netherlands
Correspondence:
Dr Manav Sohal
King’s College London
Division of Imaging Sciences and Biomedical Engineering
Rayne Institute, 4th Floor Lambeth Wing
St. Thomas’ Hospital
Westminster Bridge Road
London SE1 7EH
United Kingdom
Tel: 0044(0) 207 188 8382
Fax: 0044(0) 207 188 5442
Email: [email protected]
Journal Subject Codes: [11] Other heart failure, [110] Congestive, [120] Pacemaker, [106] Electrophysiology
;
2222
s rm rty Medical Center, Cardiovascular Research Institute (CARIM), Maastricht, the Netherl
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DOI: 10.1161/CIRCEP.113.001152
2
Abstract:
Background - We sought to compare left ventricular (LVepi) and biventricular epicardial pacing
(BIVepi) with left ventricular (LVendo) and biventricular endocardial pacing (BIVendo) in patients
with chronic heart failure with an emphasis on the underlying electrophysiological mechanisms
and hemodynamic effects.
Methods and Results - 10 patients with chronically implanted cardiac resynchronization devices
underwent temporary LVendo and BIVendo pacing with an LV endocardial roving catheter. A
pressure wire and non-contact mapping array were placed to the LV cavity to measure
LVdP/dtmax and perform electroanatomical mapping. At the optimal endocardial position the
acute hemodynamic response (AHR) was superior to epicardial stimulation, the AHR to BIVendo
pacing and LVendo pacing being comparable (21±15% vs 22±17%; P=NS). During intrinsic
conduction QRS duration (QRSd) was 185±30ms, endocardial LV total activation time
(LVTAT) 92±27ms and trans-septal activation time (TSAT) 60±21ms. With LVendo pacing
QRSd (187±29ms; P=NS) and endocardial LVTAT (91±23ms; P=NS) were comparable to
intrinsic conduction. There was no significant difference in endocardial LVTAT between LVendo
and BIVendo pacing (91±23 vs 85±15ms; P=NS). Assessment of isochronal maps identified slow
trans-septal conduction with both LVendo and BIVendo pacing resulting in activation of almost the
entire LV endocardium prior to septal breakout thereby limiting any possible fusion with either
pacing mode.
Conclusions - The equivalent AHR to LVendo and BIVendo pacing may be explained by prolonged
trans-septal conduction limiting electrical fusion. The optimal AHR was associated with
predominantly LV pre-excitation and depolarization. Our results suggest that LV pacing alone
may offer a viable endocardial stimulation strategy to achieve cardiac resynchronization.
Key words: pacing, heart failure, cardiac resynchronization therapy, left bundle branch block, electroanatomic mapping
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DOI: 10.1161/CIRCEP.113.001152
3
Background
The last two decades have seen cardiac resynchronization therapy (CRT) establish itself as a
powerful tool in selected heart failure patients with evidence of electrical dyssynchrony.
However, when applying internationally recognized selection criteria for CRT there is a non-
response rate of 30-40%.1, 2 CRT is conventionally delivered as biventricular pacing with
endocardial stimulation of the right ventricle and epicardial left ventricular (LV) stimulation via
the coronary sinus (BIVepi). Clinical studies have shown similar outcomes with LV and BIV
pacing suggesting that epicardial LV only pacing (LVepi) may be as beneficial as BIVepi.3 A
recent canine study suggested delayed trans-septal activation results in the majority of LV
depolarisation occurring prior to any contribution from right ventricular (RV) stimulation
thereby limiting fusion of electrical wave-fronts.4 LV pacing alone has potential advantages over
BiV pacing as it may preserve intrinsic conduction, avoid detrimental effects of RV pacing and
reduce the number of electrodes making implantation less technically challenging. Endocardial
LV pacing (BIVendo) pacing is not limited by CS anatomy and has been shown to improve acute
and medium-term CRT response5-8 due to a more physiological electrical and mechanical
propagation.9, 10 The relative effect of endocardial pacing (LVendo) alone compared to BIVendo
pacing is not well defined. We therefore sought to compare the hemodynamic effects of LVepi
and BIVepi with LVendo and BIVendo pacing in patients with chronic heart failure with an
emphasis on the underlying electrophysiological mechanisms that might explain the response to
these different pacing modalities.
Methods
The study was approved by the local ethics committee and informed consent was obtained from
each patient. The study population consisted of 10 patients with a chronically implanted CRT
beneficial as BIVepepppiiii..3
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4
system in-situ for at least three months (St Jude Medical, Sylmar, CA, USA). All patients
fulfilled standard criteria for CRT (NYHA class II-IV drug refractory he
pacing). Patients with a mechanical aortic valve or significant peripheral vascular disease were
excluded. Baseline assessment included NYHA functional class, ECG and 2D echocardiography
prior to the original CRT implant. Each patient’s heart failure etiology was confirmed on the
basis of clinical history, coronary angiography and/or cardiac magnetic resonance (CMR)
imaging. In all cases a temporary LV endocardial lead was used to perform LV endocardial
stimulation.
Invasive Hemodynamic and Electro-anatomical Study
The protocol used has previously been described.11 Patients were lightly sedated using diazepam
(5-10mg). A steerable 6Fr Livewire decapolar catheter (St Jude Medical, Sylmar, CA, USA)
was passed from the left femoral artery retrogradely to the LV cavity to stimulate multiple sites
within the LV. A non-contact mapping (NCM) array was passed retrogradely into the LV cavity
and an 0.014 inch diameter high fidelity Certus PressureWire and PhysioMon software (RADI
Medical Systems, Uppsala, Sweden) with a 500Hz frequency response and 50Hz filter
bandwidth were used to assess real-time mean peak LVdP/dtmax.7
Acute Hemodynamic Measurement
LVdP/dtmax was recorded for at least 20 s to ensure steady-state conditions during any pacing
modality. LVdP/dtmax during atrial pacing (AAI) or RV pacing (if the patient was in AF) at 5-10
beats above intrinsic rate was used as baseline. A waiting period of at least 20 s was respected
after any change in pacing settings or lead position to achieve hemodynamic stabilization. These
methods have previously been shown to reliably measure LVdP/dtmax.12-17 Results at each pacing
rform LV endocarrdidididiala
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5
site were expressed as a percentage change from baseline. To minimize baseline drift in AHR the
baseline was reassessed prior to and after every change in pacing modality and comparisons were
made to a mean of these two readings. Data from premature ventricular complexes were
discarded.
Pacing protocol
A pacing protocol was performed: (5-10bpm above intrinsic rate, paced and sensed AV delay
100ms, AAI pacing as baseline and repeated after each pacing mode):
i)DDD-RV only
ii)DDD-LV only from the chronic epicardial CS lead (LVepi)
iii)DDD-BIV from the chronically implanted epicardial LV lead plus RV pacing with 0ms V-V
delay (BIVepi)
iv) LV only pacing from the endocardial catheter at multiple endocardial sites (LVendo)
v) LV endocardial and RV endocardial pacing from multiple LV endocardial sites with 0ms V-
V delay (BIVendo)
BIVendo and LVendo stimulation was repeated with the LV roving catheter in a random order in up
to 4 different LV endocardial positions including anterior, lateral, and posterior sites. Capture
was verified for each pacing modality by looking for a change in QRS morphology at a paper
speed of 200mm/s. This was also validated with reference to LV pacing by analysis of the
activation wavefront on non-contact mapping. For the purposes of this study the endocardial
position producing the best AHR with BiVendo pacing was chosen as the position used for
analysis.
Electro-anatomical mapping
Analysis of the non-contact mapping data was performed by 2 independent observers blinded to
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6
the hemodynamic results. Endocardial maps were obtained at baseline and in each pacing
configuration. The virtual unipolar electrograms recorded at 1200Hz (temporal resolution of
0.83ms) from the endocardial surface were used to measure the endocardial left ventricular total
activation time (LVTAT).18 The high pass filter was set at 8Hz. The onset of LV activation was
defined as the first peak negative dV/dt at any point in the LV and the end of LV activation was
defined as the time of the latest peak negative unipolar electrogram on the virtual endocardial
surface. The trans-septal activation time (TSAT) was defined as the time from the onset of the
earliest QRS complex to the time of the first detected LV endocardial breakthrough as described
previously by Auricchio et al.19
Statistical Analysis
Statistical analysis was performed on PASW Statistics 20 (SPSS Inc, Chicago, IL, USA). Data
were analyzed using generalized estimating equations using an exchangeable correlation
structure, to explore the extent of differences between pacing methods. Pacing methods were
compared to each other and to avoid type 1 errors, P values were corrected using the Bonferroni
adjustment. Descriptive results are expressed as mean± SD.
Results
Patient demographics (table 1)
Baseline characteristics are shown in table 1. All patients were male with a mean age of 62 ± 8
yrs. The mean LVEF was 26 ± 8% and there were equal numbers of ischemic and non-ischemics
(5/5). The mean QRS duration was 186±27 ms and morphology was LBBB in 9 and RV paced
rhythm in the remaining patient. The epicardial LV lead was in a lateral or postero-lateral
position in 8 (80%) patients and in an anterior position in 2 (20%) patients. Table 2 displays the
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epicardial LV lead positions for each patient along-side the optimal LV endocardial pacing
position in each case. There was concordance in four cases (table 2).
Acute hemodynamic response (figure 1 and table 3):
LV dP/dtmax whilst AAI pacing 5-10 beats above intrinsic rate was taken as the baseline to which
all pacing measurements were compared in each patient. Table 3 shows the mean (SD)
percentage increase in LV dP/dtmax for each pacing mode over baseline. Compared to baseline,
LVepi pacing from the chronically implanted epicardial lead gave a 10±14% increase in LV
dP/dtmax. BIVepi pacing increased LV dP/dtmax over baseline by 15±15% whilst LVendo and
BIVendo pacing increased LV dP/dtmax over baseline by 22±17% and 21±15% respectively. The P
value for the overall test for variability across all pacing modalities was significant at 0.001
(figure 1). BIVepi increased LV dP/dtmax by a mean of 4.1% (95% CI 1.2 to 7.0). However the
AHR to BIVendo pacing and LVendo pacing were comparable with a mean difference of 1.1%
(95% CI -5.5 to 7.8). At the optimal endocardial position, hemodynamics were superior to
epicardial stimulation with a mean difference of 6.2% (95% CI 0.5 to 11.8 for BIVendo vs BIVepi
pacing).
QRS duration, LVTAT and Transeptal Activation Times (TSAT) (figure 1 and table 3):
Intrinsic QRSd was 185±30ms and the intrinsic endocardial LVTAT was 92±27ms. Four
patients exhibited a type I pattern of endocardial activation (homogenous spread from the septum
to lateral wall) whilst 6 patients exhibited a type II pattern of activation (characterized by a line
of functional block between the septum and lateral wall).19 TSAT in intrinsic rhythm was
60±21ms and lengthened with RV pacing to 71±13ms (mean difference 10.4, 95% CI 0.6 to
20.2). Figure 2 demonstrates the delay in endocardial breakout on the left side of the
interventricular septum following RV pacing. LVepi pacing resulted in a similar QRSd to
5% whilst LVendo anananand ddd
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5.5 to 77.7 8)8)8). AtAtAt ttthehhh optptptimii alll enddddocardidididial ppposiiti ioiii n, hehhh modydydyynamimimiics were supepeeperiririr orooo to
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DOI: 10.1161/CIRCEP.113.001152
8
intrinsic (187±25ms vs 185±30ms) and a similar endocardial LVTAT (93±17). BIVepi however,
significantly reduced QRSd to 142±12ms (mean difference -42.3; 95% CI -61.0 to -23.6) and
shortened endocardial LVTAT to 72±15ms (mean difference -20.1; 95% CI -41.4 to 1.2)
suggesting a degree of fusion of RV and LV wavefronts. The mean QRSd and endocardial
LVTAT with LVendo pacing were comparable to intrinsic rhythm (187±29ms and 91±23ms
respectively). BIVendo pacing from the same position as LVendo reduced QRSd over intrinsic
rhythm to 155±28ms however there was no significant difference between the endocardial
LVTAT between LVendo and BIVendo pacing (91±23 vs 85±15ms; mean difference -5.9; 95% CI -
14.6 to 2.8).
Assessment of the isochronal activation maps of the LV during the various pacing modes
demonstrated fusion of electrical wave-fronts with BIVepi pacing (figure 3). LVepi pacing
resulted in minimal fusion of RV and LV activation wave fronts. No significant fusion was seen
with BIVendo pacing and the activation maps were strikingly similar to LVendo pacing (figure 3).
The non-contact maps identified slow trans-septal conduction during both LVendo and BIVendo
pacing. This resulted in activation of almost the entire LV endocardium prior to septal breakout,
thereby limiting any possible fusion with either pacing mode. With BIVepi pacing, endocardial
breakthrough from the epicardial LV lead was sufficiently delayed to allow fusion of electrical
wave fronts.
Discussion
The present study provides new insights into the electrical mechanisms of epicardial and
endocardial CRT. The principal findings of our study are as follows: 1) trans-septal LV
activation was prolonged during both intrinsic rhythm and RV pacing (equivalent to
approximately 33% of the QRSd); 2) there was no significant difference between the AHR
n difference -5.9;; 95959595%
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ontact maps identified slo trans septal cond ction d ring both LV and BIV
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teeede fusion of eeleectrrriccal wawawave-frfrfrf onnntts wwittth BIBIVepi papapapacinggg (((figurure 3333)))). LVVVVeppppi papacingngng
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ndo papp ciiinggg andndnd thththt e actiiivatiiion mappps were strikikikiiini glglglly yy siiimiiilalaaar to LLLLVVVVendo papp ciiiingnggng ((((fifififigugg r
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derived from LVendo and BIVendo at the optimal site whereas BIVepi appeared superior to LVepi
pacing; 3) Endocardial LVTAT and LV endocardial activation patterns were comparable
between BIVendo and LVendo pacing suggesting minimal fusion of LV and RV wave-fronts. 4)
LVendo pacing may be equivalent to BiVendo pacing.
Endocardial pacing hemodynamics and electrical changes
BIVendo stimulation at the optimal site gave a superior AHR to epicardial pacing which was site
specific. LVendo stimulation at a short AV delay produced a similar AHR to BIVendo pacing
(22±17% vs 21±15%, P=NS) suggesting no incremental benefit in BIVendo over LVendo pacing
(when pacing at a short AV delay) in comparison to epicardial stimulation. Our findings may be
explained on the basis of the long trans-septal activation times seen in our patients with LBBB so
that by the time the RV pacing impulse had broken through the septum into the LV cavity
(approximately 70msecs) the majority of LV endocardial activation had already occurred. This is
supported by examination of the isochronal activation maps of BIVendo and LVendo pacing which
were almost identical, suggesting an absence of fusion (figure 3). The short AV interval of
100ms used in our study may explain the apparent lack of fusion seen with LVendo/epi pacing and
the PR interval in our group was 182±19ms therefore at an AV delay of 100ms one would not
expect any fusion from intrinsic activation via the right bundle branch. A reduction in QRSd
was noted with BIVendo pacing but endocardial LVTAT remained similar between LV and
BIVendo pacing. The surface QRSd represents a summation of LV and RV activation times and
therefore the QRS reduction seen with BIV pacing may reflect a reduction in RV (and not LV)
activation time. We measured only LV endocardial activation time (and not epicardial) and the
reduction may be related to changes occurring in the epicardium as has been shown in the canine
model.4 We saw divergent findings for LVepi and BIVepi pacing with an improvement in AHR
Vendo over LVendo papapapacic
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with BIVepi pacing over LVepi accompanied by a reduction in both QRSd and endocardial
LVTAT. The electrical findings may be accounted for by the fact that pacing from the
epicardium resulted in a sufficient delay to compensate for prolonged trans-septal conduction
thereby allowing fusion of electrical wave-fronts from RV and LV stimulation. A reduction in
RV activation time (which was not measured) may have also contributed to the reduction in
QRSd with BIVepi pacing (the reduction in QRSd between LVepi and BIVepi was greater than
the reduction between LVendo and BIVendo). Our results would suggest a mismatch between
hemodynamic response and electrical paramaters with the best hemodynamic response being
relatively equal between LVendo and BIVendo pacing, however with epicardial pacing this differed.
This may suggest that optimal pacing LV endocardially may only require a single lead. The long
TSAT seen in our group would suggest that most LV depolarization occurs via the LV pacing
impulse in both LVendo and BIVendo modes.
Comparison with previous studies
Our findings of improved hemodynamic response with endocardial CRT are in keeping with
other groups. Strik et al demonstrated in a chronic canine heart failure model improved
hemodynamics as a result of LV endocardial pacing compared to conventional epicardial CRT
which could be explained by the shorter path length and more rapid conduction resulting from
endocardial LV pacing.20 Derval et al found better hemodynamic effects with LVendo versus
LVepi and in keeping with our study showed that there is not one pacing site (or combination of
pacing sites) that is best for all patients.6 The benefits of LV endocardial pacing seen in our
patients are likely to be due to a reduction in total LV activation time (endocardial and epicardial
activation) with the reduction predominantly in epicardial LV activation time (which we did not
specifically measure in this study. Our findings of slow trans-septal conduction are strikingly
yny amic respop nse bebebebeini
cardidiiialalll ppacacininii g g ttththisisisis ddddifif
uggest that optimal pacing LV endocardially may only require a single lead. The
n i
o
gs of impro ed hemod namic response ith endocardial CRT are in keeping it
ugggggegegegestststs tthahahahattt opppptitititimal pacing LV endocarddddiaiaialll y may onlyyy reqqquiuiuire a single lead. The
n innn n our group wwouuulddd sugggggggest ttt tththt aaat moosttt LVV depppolololaaara iizaaation ococcuuurrss via thhhe LLV pppaaaci
boththhh LVLVLVLVendo a ddndd BIBIBIB VVVVendo mmmmoddododes.
on wiii hthth prpp evvvioioioous stut dididies
ff iim ded hh dod iic iithth dnd didi lal CRCRTT iin kk ipi itit
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similar to those recently found in canines.4 Strik et al found a TSAT of 67±9ms in a canine
model of LBBB and pacing induced dysynchrony compared to 60±21ms in our patients with
LBBB and heart failure. In the same study there was no incremental benefit in BIV compared to
LV only pacing and this was due to predominant LV stimulation in both modes due to long
trans-septal activation times. This is in keeping with our findings with endocardial stimulation
where we saw no incremental benefit with RV and LV pacing due to apparent lack of fusion with
both modalities. Our results do however differ in that we found an incremental hemodynamic
benefit with BIVepi compared to LVepi associated with a reduction in the LVTAT and a degree of
fusion of wave fronts, which may be explained by much longer endocardial LVTAT than in the
dogs. Additionally, we saw that there was a delay between epicardial stimulation and endocardial
breakthrough (as seen in figure 3) thereby allowing for a delay in trans-septal conduction and
resulting in fusion of RV and LV wave fronts. We saw minimal fusion with LVepi pacing and
this may have been as a result of the short AV delay used in the study (100ms) versus the longer
mean PR interval (182ms) in intrinsic rhythm. The short AV delay when the RV was paced with
BIVepi pacing may have provided a sufficient head start and therefore earlier breakthrough into
the LV endocardium. The difference may also be explained by the differences between the
animal model in our patients with chronic heart failure, significantly dilated ventricles and the
presence of scar (50% of our patients were ischemic). Also the PR interval in our patients of over
180ms is longer in comparison to the canine model and likely explains the difference on the basis
of fusion with BIVepi pacing.
Human studies comparing LVepi pacing with BIVepi pacing would also seem to suggest
that there is little difference in terms of acute hemodynamics or medium-term clinical response
between the two.3, 21-23 We found a small (but statistically significant) benefit in AHR with
he LVTAT and a ddddegegee
ardiaal lll LVLVLVLVTATATATATTTT ththhthanananan iin
tionally, we saw that there was a delay between epicardial stimulation and endoc
g as seen in f ure there allowing for a delay in trans-septal conduction an
n fusion of RV and LV wave fronts. We saw minimal fusion with LVepi pacing
ave been as a result of the short AV delay used in the study (100ms) versus the lo
nter al (182ms) in intrinsic rh thm The short AV dela hen the RV as paced
tiononononalalalllylylyy, weweww ssawawawaw that there was a delay bebebebetwween epicardidd al sssstitt mulation and endoc
ggghg (as seen in ffiiguuuree 3) tttthhehh rebbbyb aaalllowwinng fofor a aa dededelllal yy innn tranns--sepepeptat l coooondndn ucuctiononon an
n fusioioioionnn ofofofo RRV VVV and ddd LVLVLVLV wavavavaveee frontstststs. WWWWe saw mimimimi iiniimammm l fufufufu iisiion witthhh h LVLVLVLVepiii paciiing
ave bbeb en as a rerrr sulllt of ff thhhe hshhort t AVAVAV ddddelayyy usedd d iiini thheh stutuuudydydy (((1010101000m00 s)s)s)) versuuuusss s ththththe lo
ntte lal ((181822m )s) ii iinttriin isi hh thth ThTh hsh tt AVAV dd lel hhe thth RVRV ded
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BIVepi pacing over LVepi pacing. The reason behind this may lie behind the fact that we
utilized a short AV delay of 100ms compared to a long mean intrinsic PR interval of 182ms.
This meant that we saw minimal fusion with LVepi pacing (see figure 3) and this in turn may
have attenuated the AHR. Auricchio et al also studied the differences in LVdP/dtmax between
LVepi and BIVepi pacing and found LVepi to be associated with a slightly greater AHR.24
Crucially, pacing was performed in VDD mode (atrial sensing) and so did not control for heart
rate which is one of the key determinants that affects absolute values of LVdP/dtmax.
Additionally, most LV leads were positioned apically and this has been shown to attenuate the
response to BIV stimulation.25 These differences may also explain why our results vary in this
respect.
Study Limitations
This study is limited by its small sample size, however given the highly invasive and time-
consuming nature of the study the size was limited to the smallest size needed to provide
significant results in this proof of principle study. Ideally a range of AV delays and VV delays
would have been assessed but this was not possible because of time constraints and will need to
be assessed in future studies. Our study used a short AV delay of 100ms and this may in some
part explain the results. With such a short AV delay there was likely to be little intrinsic fusion
in the LV only modes (intrinsic PR interval was over180ms). At a short AV delay, LV and BIV
endocardial pacing appear equivalent, although we cannot rule out the possibility that at different
AV delays this may have differed due to ‘LV fusion’ pacing. Our measures of LV activation
were endocardial and we did not study epicardial activation specifically. We do, however, have
data on QRS duration which is a measure of total electrical activation of the heart. We did not
specifically look at areas of myocardial scar in relation to lead positioning in our patients may
n shown to attenuuuatatatatee
hy ourur rresesulullltststt vvara y y yy inininin
m
g
res lts in this proof of principle st d Ideall a range of AV dela s and VV del
miiiitaaaations
is limimimmitiititedededed by ititits sm lllall ll sampmpmpmplllle sizeee,e hhhhowoo ever gigiigiveveveven nn ththththe hihihihi hghghllly iinvasasasasivivivive anddd tititime-
g gg nature off f thhheee sssts udddy yy hhthe siiize was lllimii iiti edddd to ththhhe smallestt sizii e nennn dedd ddedd to prpp ovovovovidididde
ltlt iin tthihi ff fof iri iiplle tt dd IdId llll fof AAVV ddella dnd VVVV ddell
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which may be important in determining both the optimal epicardial and endocardial stimulation
sites. There was concordance between epicardial and endocardial lead position in only four cases
meaning that comparisons between endocardial and epicardial CRT should be made with caution
and the benefits of LV endocardial pacing seen in this study may be related to the lack of being
constrained by coronary venous anatomy and so being able to pace from a more optimal position.
Our assessment of CRT response using AHR may not necessarily translate into chronic response,
however, previous work from our institution has suggested a good correlation with chronic
response albeit predominantly in non ischemic patients.17
Clinical implications
Our findings may have important implications for the practice of endocardial CRT. This type of
CRT may become more prevalent in an attempt to improve CRT response. Our results would
suggest that in such patients LVendo pacing may be a viable treatment strategy and that in
patients not requiring an RV lead (for potential defibrillation) it may be reasonable to implant an
LV lead alone.
Conclusion
Endocardial LV pacing from the optimal site is hemodynamically superior to conventional
epicardial CRT, but biventricular endocardial pacing did not produce an incremental
hemodynamic benefit over endocardial LV pacing alone. This may be due to long trans-septal
activation times resulting in lack of fusion of LV and RV wavefronts. Indeed the optimal
hemodynamic response would appear to be associated with predominantly LV pre-excitation and
depolarization. Our results suggesting that LV pacing alone may offer a viable endocardial
stimulation strategy to achieve CRT.
g p
b u
a
a
one
gs mmmmayayaya hhhhavavava ee immmportant implications for tttheheheh practice of eeendocococo ardial CRT. This typ
beecccoc me more prprevalalalent inininn an aatteemmptt ttto immmpprovoove e e e CRCCRC TTT rrresponnseee. Our r reeesuullts wowowou
at in susussuchchchch ppattttieiii ttnts LVLVLVLVendodododo pppacingg mamamamay bebbb a viaiaiiablblblb e trtrtrtreatmtmtmmenttt ttstratetetetegygygygy anddd ttthahhh ttt iiin
t reqqquiiiriiinggg annn RVRVRVRV lell ddad (((foff r popp tet ntiiialll l dded fififif bbbrilllllllatiitiion))) itt mmmmayayy bbbe eee reasonabbblelll tttto ooo imimimmplpp ayyy
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Conflict of Interest Disclosures: Drs. Sohal and Shetty are supported by an educational grant from St. Jude Medical. Dr. Niederer receives research support from Boston Scientific Corp.Professor Razavi receives research support from Philips Healthcare. Professor Prinzen has received research grants from Medtronic Inc., Boston Scientific Corp., MSD, Biological Delivery System (Cordis) and EBR Systems. Dr. Rinaldi receives research support form St. Jude Medical and Medtronic Inc. All other authors state that they have no conflicting interests to declare.
References:
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t B,B,B,B, DDDDuchaaarmrmrr e AA,AA Harel F, White M, O'MMMeaara E, Guerrrrtititiin MCMCMCMC, Lavoie J, Frasure-MMMM, GGuerra P, MaMM clcllcle L,LL,L RRRRivivivivarrrrd d d d LL,LL RRoyy DDD, TaTalaaajijijij c MM,MM KKKKhahhahaiririry yy PP. LLLLefefefeft veveveentntntrririicucucuulalalaar r veuuusu bbbbiventricullarr pacaacing innnn patiennntss withhh heaeart fffaiaiaiailululurre aaannnd a QQRSSS comppppllel xx 122000ds. CiCCiCircrcrccululululatatata ioiooonnn. 202020011111;1; 24242424:2:2:2:287878787444-2828282881818181
van nnn DeDeDeD ururursesesennn CJCJCJCJ,,,, vavavannn MiMiMiddddddddenenendododod rprprp LLLLBB,B vvvananan HHHHunununnninininik kk A,A,A,A KKKKuiuiuipepepeerrr r M,MM,M, AAAAurururiciciccchchchioioio AAAA, WW. TrTranananssssssepepeptatatall cococondnducucuctitiononon aaasss ananan iimpmpmpororortatatantntnt ddetetetererermiminananantntnt ffororor cccararardidiacacac rrresesesynynynchchrororoninizazaza
reeveveala eddded bbbby y exe tetet nssivivvi e e elelllecectrtrt iciciicallal mappappipiingg iiin thhthhe e dydydydyssssyny chchhhroonoousus ccana ininii e e heeara t.t. CC
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tricular electric accctitititivavvvnanananatotototomimimimicccc mamamamappppppppinininingg.g.g CCCiCirrrr
lder BM, Meijer A, Bracke FA. Stimulation rate and the optimal interventricularr .n
dm cu
lder BM Bracke FA Meijer A Laker eld LJ Pijls NH Effect of optimi ing the
lderererer BBBBMM,M MMMeiiijejejer A, Bracke FA. Stimulatatatioioioi n rate and theh optptptptimii al interventricularrininini gggg cardiaaaacccc rereresysss nccnchrhrhrononononizzatatata ioioioon n thththeree apapapy yy in ppatieeentntntntssss wiwithththth ccchrhhrononono ic aatrtrtrtriaiaiaalll fibrbrbrililili lalalatitititiono .nnn n EElE ectrophysiool. 20202008;33;31:56666999-9 575574.
d MAAAA, vaavavann Geldldlder BBBMMMM, Brararaackkckcke FAAAA, vavavan ZuZZZ ddndderrrtttt AAAAAAAA, vaaannn n StStStS ratttet n AHAHAHAH. AcAAA ttute mic efefefeffefefef ctctctsss ofofofof ccccararardidididiacacacc rrrresesesynynynynchc rorororoninininizazazazatittit onnn ttthhhererererapapapapy yyy ininini ppppatatatatieieeientntntsss wiwiwiw thththth pppoooooooorr r leleleleftfttft vvvenenenntricuring gg ca drddiac sususuurgggery.yy JJJ CaCC rd SSSSurggg. 2020202 09999 22;244:4 585858555-5 5959595 0.00
ldld BBMM BB kck FAFA MMeijij AA LLakke leldd LJLJ PiPijljl NHNH EEffff tt fof tptiimii iin thth
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20. Strik M, Rademakers LM, van Deursen CJ, van Hunnik A, Kuiper M, Klersy C, Auricchio A, Prinzen FW. Endocardial left ventricular pacing improves cardiac resynchronization therapy in chronic asynchronous infarction and heart failure models. Circ Arrhythm and Electrophysiol.2012;5:191-200.
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heart failure: Resusuuultltltlts
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Table 1: Patient characteristics
Characteristic
Age (years) 62 ± 8 Gender n(%) Male 10 (100)
Female 0 (0)Etiology n(%) Ischemic 5 (50)
Non-ischemic 5 (50)NYHA class n(%) Class II 4 (40)
Class III 6 (60)LV ejection fraction* (%) 26 ± 8 Intrinsic PR interval (ms) 182 ± 19 QRS duration (ms) 185 ± 30QRS morphology n(%) LBBB 9 (90)
RV paced 1 (10) Epicardial LV lead position n(%) Lateral 4 (40)
Posterolateral 4 (40) Anterior 2 (20)
derived from 2D echocardiography using the modified Simpson’s biplane method Continuous variables are expressed as mean ± standard deviation
Table 2: Comparison between the position of the chronically implanted epicardial LV lead and the optimal position for LV endocardial pacing
Patient Epicardial lead position Optimal endocardial lead position
1 Posterolateral Posterolateral2 Posterolateral Inferoseptal3 Lateral Lateral4 Posterolateral Lateral5 Anterior Lateral6 Lateral Posterior7 Lateral Septal8 Lateral Septal9 Posterolateral Posterolateral10 Anterior Anterior
RV paced 1 (10)
fro
RV pacededed 1 (10)LLLLV V V V lead posooo itioioioi n n(n(n(n %)%)%) Laaateteterar l 4 (40)0)0))
Possteerollaaterrrralalal 444 (4404 ))) Annteeerior 2 ((((20202020)
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Table 3: Hemodynamic and electrical parameters compared across pacing modalities
Modality % change in
dP/dtmax
over baseline
QRSd
(ms)
Mean change
in QRSd
over baseline
TSAT
(ms)
Mean change
in TSAT
over baseline
LVTAT
(ms)
Mean change
in LVAT
over baseline
Baseline n/a 185±30 n/a 60±21 92±27
RV 1±3 195±30 10.0
(0.9 to 19.1; P=0.035)
71±13 10.4
(0.6 to 20.2; P=0.040)
93±26 1.6
(-8.6 to 11.8; P=0.730)
LVepi 10±14 187±25 2.3
(-11.9 to 16.5; P=0.723)
93±17 1.8
(-19.6 to 23.2; P=0.853)
BiVepi 15±15 142±12 -42.3
(-61.0 to -23.6; P=0.001)
72±15 -20.1
(-41.4 to 1.2; P=0.062)
LVendo 22±17 187±29 2.8
(-10.2 to 15.8; P=0.639)
91±23 -0.4
(-21.5 to 20.7; P=0.967)
BiVendo 21±15 155±28 -30.1
(-47.0 to -13.2; P=0.003)
85±15 -6.3
(-21.4 to 8.8; P=0.369)
Abbreviations: LVepi – AV synchronous LV pacing from the epicardial LV lead; BiVepi – AV synchronous biventricular pacing using the chronically implanted CRT system; LVendo – AV synchronous LV pacing from the temporary endocardial LV pacing catheter; BiVendo – AV synchronous biventricular stimulation using the temporary endocardial LV pacing catheter for LV stimulation; QRSd – QRS duration; TSAT –transseptal activation time; LVAT – endocardial LV activation time
2020020 222.2; ; ; ; P=P=P=P=0.0.0.0.040404040)0)0)0)
22.22 3
(---11.9 to 161116.555;;; P=P=P=P=0.0.0.0.77727 3)3)3)3)
-4442.2.2.2 3333
(-(-6161 0.0 ttoo -22-2233.6;6; PP=0=0 0.00101))
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DOI: 10.1161/CIRCEP.113.001152
19
Figure Legends:
Figure 1: Mean change from baseline in dP/dtmax, QRS duration and LV activation time for each
pacing modality. This is displayed as the percentage mean change each variable resulting from
pacing in each pacing configuration, compared with baseline (AAI pacing). Abbreviations as for
table 2.
Figure 2: Isochronal map derived from non-contact mapping in a patient with RV pacing
(referenced to RV stimulation artifact). The left hand panel is in a right anterior oblique (RAO)
orientation and the right panel is in a left anterior oblique (LAO) orientation. Septal breakout is
identified as the site of earliest onset in the LV (white colour scale on the map). Inspection of
the scale bar on the left shows that it takes approximately 65ms from the onset of RV stimulation
before septal breakout occurs and begins spreading across the LV.
Figure 3: Isochronal maps from the same patient as figure 2, with LVepi pacing (top panels) and
BIVepi pacing (bottom panels). There is a change in endocardial electrical activation between
LVepi and BIVepi modalities. Inspection of the colour scale bar on the left shows that there is a
delay between epicardial stimulation and endocardial breakthrough and this is sufficient to allow
some fusion of endocardial activation of the LV from RV and LV epicardial stimulation.
Figure 4: Isochronal maps from the same patient as figure 2, with LVendo pacing (top panels)
and BIVendo pacing (bottom panels). Endocardial stimulation results in a broad region of early
activation with both pacing modalities and endocardial activation that is broadly similar for both
(implying minimal fusion of RV and LV stimulation wavefronts).
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-20
-10
0
10
20
30
40
50
60
LVepi BiVepi LVendo BiVendo
Pacing Configuration
Chan
ge in
LV d
P/dt
max
from
bas
elin
e (%
) Overall test of variability across all pacing modes: P=0.012
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-40
-30
-20
-10
0
10
20
30
LVepi BiVepi LVendo BiVendo
Pacing Configuration
Chan
ge in
QRS
dur
atio
n fr
om b
asel
ine
(%)
Overall test of variability across all pacing modes: P<0.001
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-60
-40
-20
0
20
40
60
80
LVepi BiVepi LVendo BiVendo
Pacing Configuration
Chan
ge in
end
ocar
dial
LVAT
from
bas
elin
e (%
) Overall test of variability across all pacing modes: P<0.001
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