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1Center for Arrhythmia Research. Internal Medicine, University of Michigan
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This report provides a detailed description of the methodology and results of simultaneous endocardial and epicardial optical mapping of electrical excitation in the intact left atrium of a Langendorff-perfused sheep heart during stretch-induced atrial fibrillation.
Filgueiras-Rama, D., Martins, R. P., Ennis, S. R., Mironov, S., Jiang, J., Yamazaki, M., et al. High-Resolution Endocardial and Epicardial Optical Mapping in a Sheep Model of Stretch-Induced Atrial Fibrillation. J. Vis. Exp. (53), e3103, doi:10.3791/3103 (2011).
Atrial fibrillation (AF) is a complex cardiac arrhythmia with high morbidity and mortality.1,2 It is the most common sustained cardiac rhythm disturbance seen in clinical practice and its prevalence is expected to increase in the coming years.3 Increased intra-atrial pressure and dilatation have been long recognized to lead to AF,1,4 which highlights the relevance of using animal models and stretch to study AF dynamics. Understanding the mechanisms underlying AF requires visualization of the cardiac electrical waves with high spatial and temporal resolution. While high-temporal resolution can be achieved by conventional electrical mapping traditionally used in human electrophysiological studies, the small number of intra-atrial electrodes that can be used simultaneously limits the spatial resolution and precludes any detailed tracking of the electrical waves during the arrhythmia. The introduction of optical mapping in the early 90's enabled wide-field characterization of fibrillatory activity together with sub-millimeter spatial resolution in animal models5,6 and led to the identification of rapidly spinning electrical wave patterns (rotors) as the sources of the fibrillatory activity that may occur in the ventricles or the atria.7-9 Using combined time- and frequency-domain analyses of optical mapping it is possible to demonstrate discrete sites of high frequency periodic activity during AF, along with frequency gradients between left and right atrium. The region with fastest rotors activates at the highest frequency and drives the overall arrhythmia.10,11 The waves emanating from such rotor interact with either functional or anatomic obstacles in their path, resulting in the phenomenon of fibrillatory conduction.12 Mapping the endocardial surface of the posterior left atrium (PLA) allows the tracking of AF wave dynamics in the region with the highest rotor frequency. Importantly, the PLA is the region where intracavitary catheter-based ablative procedures are most successful terminating AF in patients,13 which underscores the relevance of studying AF dynamics from the interior of the left atrium. Here we describe a sheep model of acute stretch-induced AF, which resembles some of the characteristics of human paroxysmal AF. Epicardial mapping on the left atrium is complemented with endocardial mapping of the PLA using a dual-channel rigid borescope c-mounted to a CCD camera, which represents the most direct approach to visualize the patterns of activation in the most relevant region for AF maintenance.
1. Heart removal and Langendorff perfusion
Sheep weighing 35-40 Kg are anesthetized using 4-6 mg/Kg propofol and 60-100 mg/Kg of sodium pentobarbital. Hearts are removed via thoracotomy and connected to a Langendorff-perfusion system with circulating oxygenated (95% O2, 5% CO2) Tyrode's solution at a constant flow rate of 240-270 ml/min, pH 7.4 and 35.5-37.5 °C. The Tyrode's composition (in mM) is: NaCl 130, KCl 4.0, MgCl2 1, CaCl2 1.8, NaHCO3 24, NaH2PO4 1.2, Glucose 5.6, and Albumin 0.04 g /L. Blebbistatin 10 μM (Enzo Life Science International, INC. Plymouth Meeting, PA, USA) is used to reduce the contractile force.
2. Stretch-induced atrial fibrillation in the Langendorff-perfused sheep heart
The isolated, coronary perfused heart undergoes an atrial trans-septal puncture to enable equalized intracavitary pressure in both atria. All vein orifices are then sealed, except the inferior vena cava, which is cannulated and connected to a digital sensor (Biopac Systems transducer-TSD104A; Biopac Systems, Inc., Goleta, CA, USA) and to an outflow cannula whose open-ended height above the atria controls the intra-atrial pressure. The pressure is then increased to 12 cm H2O, which leads to a ~30% increase in atrial volume relative to the volume at 6 cm H2O. The pressure is maintained stable throughout the experiment. Prior to sealing the veins tetrapolar electrode catheters (Torq, Medtronic Inc./Minneapolis/MN/USA) are placed in each of the pulmonary veins to record bipolar signals from the two distal electrodes (sampling rate, 1.0 kHz) using a Biopac Systems amplifier (DA100C; Biopac Systems, Inc., Goleta, CA, USA). Two additional custum-made bipolar electrodes are placed on the roof of left atrial appendage (LAA) and the top of right atrial appendage.
3. Optical mapping set up
4. Atrial fibrillation protocol
Under continuous atrial stretch AF is induced via burst pacing (12 Hz, 5 ms pulses, 2x diastolic threshold) by a pacing electrode located on top of the LAA. AF is allowed to continue for 50 minutes and 5-sec optical movies are acquired at two min intervals. Bipolar recordings are collected continuously. Acquisition of the optical movies triggers simultaneous acquisition of 5-sec segments of the bipolar recordings.
5. Frequency analysis
Frequency analysis allows identification of regions with high activation rate during AF, along with frequency gradients between left and right atrium. Dominant frequency (DF) maps are obtained from each optical movie after applying a fast Fourier transform algorithm (FFT) to the time-series fluorescence signal recorded at each pixel.7 FFT is also applied to the 5 second bipolar signals (High-pass filtered at 3 Hz and low-pass filtered at 35 Hz) synchronized with the optical movies.
6. Atrial fibrillation dynamics
Further quantification allows spatial correlation of highest frequency domains with the most common pattern of activation obtained from that particular region. The latter highlights the crucial role of mapping the endocardial surface of the PLA, since it commonly represents the region where the highest frequency domains are located during acute AF.
7. Representative Results:
Dominant frequency (DF) gradients from PLA to LAA and RAA are present during acute stretch-induced AF. The highest DF region is localized either at or near one of the pulmonary veins or somewhere in the PLA.11 A representative AF episode is shown in Figure 3, in which the highest DF is localized on the PLA (Right inferior pulmonary vein). The results support the presence of high frequency sources in the PLA driving AF consistent with the left to right DF gradients observed during ablative procedures in paroxysmal human AF.16
Quantification of patterns of activation using phase map movies shows that the highest number of rotors is found at the PLA and the junction between the PLA and the LAA.8 Occasionally it is possible to identify long-lasting rotors whose center of rotation (Singularity point) localizes with the highest frequency domain.10 Since atrial tissue represents a three-dimensional structure, identifying rotors on the mapped endocardial surface of the PLA suggests that the center of rotation of those rotors (filament) is eventually perpendicular to the surface of the mapping area. Figure 4 shows such a rotor recorded from the endocardium of the PLA with simultaneous fibrillatory conduction toward the LAA, which also correlates with a frequency gradient between the PLA and the LAA (9 and 6.4 Hz respectively). The number of rotors is consistently higher at the PLA than the LAA, which suggests an essential role of reentry on the PLA to maintain the arrhythmia in this model.
Overall, the results support the theory that stable and fast rotors in the left atrium may drive acute stretch-induced AF and emanating waves undergo complex, spatially distributed conduction block patterns as they head toward the right atrium, manifesting as fibrillatory conduction and progressively decreasing dominant frequency.
Figure 1. Diagrammatic representation of the experimental set up. A: A rigid borescope is introduced through the anterior wall of the left ventricle and the mitral valve orifice and focused on the endocardial surface of the posterior left atrium (PLA). A CCD camera is coupled to the borescope and laser illumination is provided through a laser liquid guide connected to the inferior part of the borescope. Epicardial mapping is performed on the LAA. Bipolar electrodes are placed on right atrium and roof of the left atrium. Additional bipolar signals are obtained from the pulmonary veins. B: Lateral view of the left atrium following opening the lateral wall for illustration purposes. The tip of the borescope illuminates the endocardial surface of the PLA. A bipolar electrode is located on the roof of the left atrium. LAA: left atrial appendage. LV: left ventricle. RA: right atrium. RV: right ventricle.
Figure 2.Different patterns of activation identified after the generation of phase movies. A: Sequential snap shots of the left atrial appendage (LAA) show the pivoting of a rotor around its center of rotation (Singularity point). From left to right, one full rotation is completed. B: A sample breakthrough activation pattern on the LAA. The wave appears on the upper right corner of the field of view and propagates outward. C: Four spatiotemporally organized periodic waves (At 0, 182, 352 and 512 ms, respectively) coming from the PLA region toward the LAA. Isochrones are plotted at 10 ms intervals. Bottom, key for the different phases of the action potential is color-coded.
Figure 3. Identification of the regions with the highest frequency activity during acute stretch-induced AF in a Langendorff-perfused isolated sheep heart. A: Anatomical view of the left atrial appendage (LAA), right atrial appendage (RAA) and posterior left atrium (PLA). PLA image is an endoscopic view of the mapped region with the four pulmonary veins (PVs). B: DF maps obtained by optical mapping on the LAA and PLA. Frequency value in the RAA was obtained from bipolar electrograms. The highest frequency region is located in the PLA. C: Representative power spectra, in which the maximum DF corresponds to 12.4 Hz at the PLA region of the right PVs. LSPV: left superior pulmonary vein. LIPV: left inferior pulmonary vein. RSPV: right superior pulmonary vein. RIPV: right inferior pulmonary vein. Reproduced from reference 11 (David Filgueiras Rama & José Jalife. Mechanisms Underlying Atrial Fibrillation. in Basic Science for Clinical Electrophysiologist, Vol. 3 (ed. Charles Antzelevitch) 141-156 (SAUNDERS, 2011).
Figure 4. Simultaneousphase maps (A, B) and dominant frequency maps (C) from posterior left atrium (PLA) and left atrial appendage (LAA). A: Sequential snap shots from the PLA showing a rotor and the drifting of its singularity point. B: Simultaneous phase snap shots from the LAA. Patterns of activation show propagation waves compatible with fibrillatory conduction. Singularity points are also present in correlation with wavebreaks in the fibrillatory conduction region. (See also video 4) C: Simultaneous dominant frequency maps from the PLA and the LAA. The fastest region is located at the PLA (9 Hz), which correlates with the presence of a rotor in the phase map analysis. The highest frequency at the LAA is 6 Hz, which correlates with fibrillatory conduction. On the right side of panel C, single pixel optical activations from PLA and LAA are shown.
The characteristics of acute stretch-induced AF in the isolated sheep heart resemble some of the properties of human paroxysmal AF. An acute increase in intra-atrial pressure in the sheep heart allows the maintenance of AF for long periods of time, similar to a higher risk of AF observed in patients with atrial dilatation.1 The presence of left-to-right DF gradients in the sheep atria is also similar to those registered in human electrophysiological studies.16 Therefore, understanding the mechanism sustaining AF in this acute model may improve the therapeutic strategies currently used in human paroxysmal AF. Some of the limitations of the current approach are: first, the difficulty of reproducing the effect of the autonomic nervous system on the fibrillation in isolated hearts, which precludes extrapolation of the results to in vivo situations. And second, the model focuses on acute stretch-induced AF, and therefore conclusions should not be extended to structurally remodeled hearts, in which fibrosis and alterations in electrical properties might affect patterns of activation on the PLA and LAA. Lastly, it should be noted that due to optical constraints as well as toxicity of voltage-sensitive dyes and motion-uncoupling compounds, optical mapping techniques are currently not feasible in living subjects.
Notwithstanding, the use of optical mapping and specifically the endocardial mapping of the PLA as demonstrated in this protocol advances our mechanistic understanding of AF by identifying the highest number of rotors in the fastest frequency domains. The latter suggest that reentry may be essential to sustain the arrhythmia. Thus, different pharmacological strategies focus on terminating reentry can be studied using this model, which makes it suitable for relevant translational studies.
Technological improvements in the optical mapping approach are continually being sought after. Although the wide-field view and high spatial and temporal resolution obtained with optical mapping allows the identification of long lasting rotors on the 2D mapped surface, very often those rotors drift away from the field of view. Thus, a more panoramic optical mapping approach would enable better tracking of drifting rotors and the arrhythmia in general. New dyes that provide deeper-penetrating signals and new mathematical analyses might also allow tracking rotors and their filaments inside the 3D structure of the PLA wall. The latter would also allow a better understanding of patterns of activations previously described as surface breakthroughs, which might represent intramural reentrant activity. Additional improvements being pursued include: reduced toxicity of the voltage-sensitive dyes; optical probes for further physiological parameters, such as intracellular calcium concentration; improved compounds and techniques for motion reduction.
No conflicts of interest declared.
Supported in part by NHLBI Grants P01-HL039707 and P01-HL087226 and the Leducq Foundation (J.J. and O.B.), by a Spanish Society of Cardiology Fellowship, Fundación Pedro Barrié de la Maza and Fundación Alfonso Martín Escudero (D.F.R.), by Fédération Française de Cardiologie (R.P.M.), by a Heart Rhythm Society fellowship Award, The Fellowship of Japan Heart Foundation/The Japanese Society of Electrocardiology (M.Y.).
|Pentobarbital||Lundbeck Inc||NDC 67386-501-55|
|Introducer 18 Gauge||Terumo Medical Corp.||SS*FF1832|
|Cuffed endotracheal tube (9 mm)||DRE Veterinary||#9440|
|Fiber Optic Laryngoscope Case||DRE Veterinary||#991|
|Fiber Optic Blade||DRE Veterinary||#984|
|Operating Scissors||DRE Veterinary||#9702#1944|
|Scalpel Handle #3 Solid 4"||Roboz Surgical Instruments Co.||RS-9843|
|Sterile Scalpel Blades||Roboz Surgical Instruments Co.||RS-9801-10|
|Sims Scissors Curved Sharp/Blunt||Roboz Surgical Instruments Co.||RS-7035|
|Tissue Forceps (×2)||DRE Veterinary||#1895|
|KANTROWITZ Thoracic Forceps, 11"||Biomedical Research Instruments||34-1980|
|Finochietto Large Chest Spreader||Kapp Surgical Instrument Inc.||KS-7301|
|Thoracotomy shears||Rostfrei Solingen|
|Plastic tray||Nalge Nunc international||Fischer|
|Bonn Scissors (×2)||Roboz Surgical Instruments Co.||RS-5840SC|
|Surgical silk||Fisher Scientific||50-900-04214|
|Micro Dissecting Forceps||Roboz Surgical Instruments Co.||RS-5130|
|Tetrapolar electrode catheters (Torq) (×4)||Medtronic Inc.||05580SP|
|Digital sensor. Biopac Systems transducer||Biopac Systems, Inc.||RX104A|
|Biopac Systems amplifier||Biopac Systems, Inc.||DA-100C|
|Blebbistatin||Enzo Life Sciences||BML-E1315-0025|
|LittleJ– CCD video camera(×2)||SciMeasure Analytical Systems, Inc.|
|Dual-channel rigid borescope||Everest VIT, Inc.||R10-25-0-90|
|Perfusion pumps (×2)||Cole-Parmer||GK-77920-30|
|pH meter||Fisher Scientific||01-913-806|
|Digital temperature gauge||Cole-Parmer||GK89000-10|
|Silicon perfusion tubes (L/S 15)||Masterflex (Cole Palmer)||96410-15|
|Laser light guides (×6)||Oriel Corp.||77536|
|Liquid light-guide (0.2 in core)||Newport Corp.||77556|
|Laser generator (1 watt) (×1)||Shanghai Dream Lsaer Tecchnology||SDL-532-1000T|
|Laser generator (5 watt) (×1)||Newport Corp.||MILL 5sJ|
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