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Threedimensional dominant frequency mapping using autoregressive spectral analysis of atrial electrograms of patients in persistent atrial fibrillation
BioMedical Engineering OnLine volume 15, Article number: 28 (2016)
Abstract
Background
Areas with high frequency activity within the atrium are thought to be ‘drivers’ of the rhythm in patients with atrial fibrillation (AF) and ablation of these areas seems to be an effective therapy in eliminating DF gradient and restoring sinus rhythm. Clinical groups have applied the traditional FFTbased approach to generate the threedimensional dominant frequency (3D DF) maps during electrophysiology (EP) procedures but literature is restricted on using alternative spectral estimation techniques that can have a better frequency resolution that FFTbased spectral estimation.
Methods
Autoregressive (AR) modelbased spectral estimation techniques, with emphasis on selection of appropriate sampling rate and AR model order, were implemented to generate highdensity 3D DF maps of atrial electrograms (AEGs) in persistent atrial fibrillation (persAF). For each patient, 2048 simultaneous AEGs were recorded for 20.478 slong segments in the left atrium (LA) and exported for analysis, together with their anatomical locations. After the DFs were identified using ARbased spectral estimation, they were colour coded to produce sequential 3D DF maps. These maps were systematically compared with maps found using the Fourierbased approach.
Results
3D DF maps can be obtained using ARbased spectral estimation after AEGs downsampling (DS) and the resulting maps are very similar to those obtained using FFTbased spectral estimation (mean 90.23 %). There were no significant differences between AR techniques (p = 0.62). The processing time for ARbased approach was considerably shorter (from 5.44 to 5.05 s) when lower sampling frequencies and model order values were used. Higher levels of DS presented higher rates of DF agreement (sampling frequency of 37.5 Hz).
Conclusion
We have demonstrated the feasibility of using AR spectral estimation methods for producing 3D DF maps and characterised their differences to the maps produced using the FFT technique, offering an alternative approach for 3D DF computation in human persAF studies.
Background
Atrial fibrillation (AF) is the commonest heart rhythm disturbance seen in clinical practice, affecting almost 1 % of the worldwide population. It is more prevalent in older patients, affecting over 10 % of those above 80 years old [1]. AF increases the risk of stroke fivefold and the risk of heart failure and mortality [2]. It is reason for frequent medical appointments and admissions, contributing to elevated costs of health care [2]. Despite extensive research into the pathophysiology of AF, the mechanisms of its triggering and maintenance are still controversial and effective treatment is still elusive [3]. The success of using catheter ablation in paroxysmal AF patients has illustrated the usefulness of the technique [4], however the treatment of persistent AF (persAF) via ablation is still a challenge. Different techniques have been employed to improve ablation outcome in persAF [5] and it has been suggested that dominant frequency (DF), defined as the frequency of the highest peak of the AF frequency spectrum, could help identify targets for ablation [6]. Investigators using spectral analysis observed that the activation rates of localized endocardium areas were well correlated with DF [7]. It has been suggested that regions with highest DF may be responsible for the AF maintenance and hence should be targets for ablation [8]. This highlights the need for their accurate localization and a system with highresolution simultaneous endocardial recordings [6, 9] enables accurate mapping and facilitates targeting of potential arrhythmic sites and circuits [9]. Spectral analysis of these electrograms may serve as a powerful tool for identifying AF candidates [6, 9].
The majority of the AF studies that studied the DF [10] were implemented using Fourierbased spectral analysis techniques. As the temporal behaviour of DF is not stable [11], it is desirable to track its trajectory over time using short segments of atrial electrograms for the spectral analysis. It is well known that Fourierbased spectral analysis suffers from low spectral resolution when the length of the time segment is short [12–14]. In these cases, ARbased spectral analysis might be an interesting alternative as it has superior spectral resolution [13].
Therefore, the objectives of this paper were (1) to generate 3D DF maps using different autoregressive (AR) spectral estimation methods [with emphasis on selection of appropriate sampling rate and AR model order to estimate the DF for each of those 2048 simultaneous unipolar noncontact intracardiac atrium electrograms (AEGs)], (2) to compare the DF between those AR spectral estimation techniques and (3) to compare them with the maps produced using Fourierbased approach [15].
Methods
Overview of noncontact mapping
Noncontact mapping (NCM) is performed with a multielectrode array catheter (MEA) introduced into the cardiac chamber to record endocardial electrical activity without touching the heart walls. This technology uses an array catheter with 64 electrodes and an analysis system (EnSite 3000, St. Jude Medical) that generates anatomic mapping and electrogram reconstruction. The simultaneous potentials are obtained using inverse solution mathematics and up to 3600 AEGs sampled at 1200 Hz are projected onto 3D representation of the cardiac chamber in realtime [16].
The technique of using NCM with the MEA has previously been described and validated in the context of sinus rhythm as well as arrhythmia in humans [17, 18]. Estimation of DF via spectral analysis from NCM has been shown to be well correlated (agreement in approximately 95 % of cases) with DF estimation via spectral analysis from contact mapping for both paroxysmal AF and persAF [17, 18] and can be used in simultaneous high density 3D DF maps as a tool to identify sites with high frequency electrical activity during AF [18].
Data collection
An Ensite array balloon was introduced transseptally into the LA of eight patients with persAF with no previous history of heart diseases (patient characteristics are summarised in Table 1). Patients were in AF and 2048 AEGs for 20.478 slong segments were exported for analysis (3 × 6.826 s), together with their anatomical locations. The sampling frequency (Fs) was 1200 Hz. The length of the time window is such that it is long enough to allow the tracking of DF along time, as the time constant associated to the stability of DFs has been shown to be about 10 s [11]. The AEGs were highpass filtered at 1 Hz and, apart from the builtin antialiasing filter, no further filtering or preprocessing prior spectral analysis was applied to the signals to preserve signal integrity and low frequency components [7]. Approval was obtained from the Local Ethics Committee for patients undergoing AF ablation including blood sampling and collection of electrical data and all procedures were carried out after informed consent.
Spectral analysis
AR modelbased spectrum analysis of the AEGs was performed after the signals were downsampled in the time domain with nine different sampling frequency values, from 600 Hz down to 37.5 Hz prior to spectral analysis (Fig. 1). The downsampling AEG process was performed by the function ‘resample’ of the Matlab 64bit R2012a through the Signal Processing toolbox [version 6.17]. In this function an antialiasing (lowpass) linearphase FIR filter is implemented with a Kaiser window to minimize the weighted, integrated squared error between the ideal piecewise linear function and the filter magnitude response. The method follows up sampling the output signal to then insert zeros. The resulting signal is filtered by a FIR and downsampled from 1200 to 37.5 Hz and illustrated on Fig. 1. An AEG recorded from the LA sampled originally at 1200 Hz is presented on Fig. 2. The respective signal is also displayed after a downsampling factor of 32 times (resampling frequency = 37.5 Hz) illustrating how much of the signal information is preserved.
After the resampling strategy, 3D DF maps with 2048 AEGs were produced for the different frequency sampling strategies to assess the behaviour of DF maps. DF was defined as the fundamental frequency with the highest power between 4 and 12 Hz [10] after the ventricular far field cancellation using a previously described algorithm [19]. The results obtained through the AR modelbased methods were compared with DF maps recently described using the Fourierbased approach [15].
Autoregressive model analysis
In the AR model approach [20–22], the signal x[n] is modelled as the output of an allpole filter of model order p with coefficients a[k] for a white noise input driving sequence w[n] as follows.
The power spectral density (PSD) of an autoregressive process P _{ AR } [f] is the continuous function of f as given by Eq. (2) [20–22],
where σ ^{2} is the variance of the driving white noise w[n] and T is the sampling period.
To estimate the AR coefficients \( \left\{ {a_{1} , \, a_{2} , \, a_{3} , \ldots , \, a_{p} , \, \sigma^{2} } \right\} \) a relationship between the AR parameters and the autocorrelation function that minimizes the residual error (the difference between x[n] and the output of the allpole filter as given later by Eq. 5) has been derived and is known as the YuleWalker equations (Eqs. 3 and 4 below). The derivation is shown by Kay and Marple in [20].
The verification that an autoregressive model can describe the AEG signals was performed by fitting an AR model to the AEG data and testing the residuals. The difference between the predicted and the true signal sequence values resulted in random residuals (uncorrelated in time) normally distributed. The autocorrelation function of the residuals fell inside the confidence interval of 95 % and was close to zero for all nonzero lags.
Different AR spectral estimation methods represent a tradeoff between spectral estimation and computational efficiency [14, 20, 22]. Levinson Durbin YuleWalker, Covariance, Modified Covariance and Burg).
LevinsonDurbin YuleWalker method
The parameters of an AR process with zero mean and model order p using the YuleWalker method with the LevinsonDurbin recursive algorithm are the solution of a set of linear equations which are obtained by the minimization of the estimate of the prediction error power (Eq. 5), with the extrapolation of the known estimated values (k) of the autocorrelation function (ACF) R_{xx} (Eq. 6). The algorithm has the advantage of being computationally efficient, requiring a number proportional to p^{2} mathematical operations and guarantees that the estimated poles lie within the unit circle.
Equation 6 is defined as the biased estimator of the ACF and is usually preferred since it tends to have smaller mean square error (variance) and decays faster in finite datasets when compared with the unbiased estimate (with scaling term 1/(Nk) rather than 1/N), where N is the number of samples [14, 20, 22]. To estimate the coefficients and variance, the method first requires the estimation of the first model order AR process parameters (Eq. 7). This is then followed by a recursive implementation for obtaining successively higher model orders from k = 2 to the desired model order (Eqs. 8–10). In Eqs. 7–10 two subscript indices are used to easily identify the coefficients as a _{ Order, Coef. Number } [20].
The YuleWalker approach is computationally very efficient when the LevinsonDurbin algorithm is employed [14].
Covariance method
In the Covariance method, the data are windowed and the points within the interval are used to compute the variance of the white noise. The estimated autocorrelation function \( c_{xx} \left[ {j,k} \right] = r_{xx} \left[ {j  k} \right] \) (summation of Np lag products) for each window location k and the variance are calculated using the following equations [20–22]:
Modified covariance method
In this method the AR parameters are estimated by minimizing the average (Eq. 13) of the estimated forward (Eq. 14) and backward (Eq. 15) prediction errors [21, 22].
The autocorrelation is estimated as
Burg method
The Burg method computes the reflection coefficients directly (Eq. 17) and from these the remaining AR parameters are obtained using the LevinsonDurbin algorithm. The reflection coefficients are obtained by minimizing the average of the backwards and forwards prediction errors in a constrained manner when compared with modified covariance method. Burg’s method assumes that a _{ kk } coefficient is estimated after the a _{ kk1} model order prediction error filter coefficients had been estimated by minimizing the a _{ kk1} model order prediction error power. First it is necessary to estimate the autocorrelation at lag zero with the forward and backward prediction errors (Eqs. 18 and 19). This is followed by the estimation of the reflection coefficients (Eq. 17) which are dependent of forward and backward prediction errors (Eqs. 11 and 12) [20–22]. \( k = 1,{ 2},\, \ldots ,\,p .\)
The recursive estimation of the variance and coefficients for the higher model orders are calculated using Eqs. 8 and 9 (LevinsonDurbin algorithm).
Model order selection criteria
Since the AR model order is not known a priori, it is necessary to apply a model order estimation technique for finding the best model order for the AR model. In this study we used Criterion AR Transfer Function (CAT), a method suggested by Parzen [23], for identifying the AR model order. Equation 20 presents the CAT method where p is the optimum model order, \( \sigma^{2}_{p} \) is the white noise variance and N is the number of samples of the data used.
For each patient, the model order value for each of the 2048 AEGs, with segment length of 20.478 s and resampling frequency were estimated using CAT method. The model order value can be different for each AEG. Hence, a model order value that would mathematically attend the majority of the AEGs’ population is needed for generation of the 3D AR DF maps. The authors have defined this order, as the optimum order, identifying on the cumulative histogram the order that satisfies mathematically at least 95 % of the AEGs of the entire segment (illustrative example at Fig. 3a for one of the patients). Odd orders were avoided as one of their poles lies on the real axis so it does not affect much the DF; the order selected in this case is the next even value. As a next step, the model order value was extended for the remaining patients and different sampling frequencies strategies (please see Fig. 3b for illustration). The optimum model order values presented at Fig. 3b were obtained as above described by attending mathematically at least 95 % of 2048 AEGs with the segment length of 20.478 s for all patients.
Statistical analysis
We fitted a linear mixed effects model to the data, which included as random effects: (1) patient, (2) the interaction patient and down sampling (DS) in the time domain of the AEGs with different sampling frequencies (down sampled signal) and (3) the interaction between patient, down sampled signal, and DF estimation using each of the AR spectral techniques (YuleWalker, Covariance, Modified Covariance and Burg methods). As fixed effects we included: (1) DF estimation using each of the AR spectral techniques, (2) DS of the AEGs, and (3) the interaction between AR spectral estimation techniques and DS of the AEGs. These analyses tested whether any differences between the DF using the AR spectral estimation techniques varied by sampling frequency, while properly allowing for the nested structure of the data (i.e. where the DF calculated by each AR spectral technique was measured at each sampling frequency in each patient). The results were compared with those obtained using the FFTbased approach by the percentage of DF agreement. The analysis was performed using the nlme [24] package in R [25]. Mixed model ANOVA was used to study the effect of downsampling factor and DF estimation for the AR spectral techniques. Pvalues less than 0.05 were considered statically significant.
Results
Eight male patients with symptomatic drugrefractory persAF were included in this study (mean age of 47 ± 4 years). Patients presented a history of persAF episodes of 34 ± 9 months with a moderated dilated LA (48 ± 2 mm) and left ventricle ejection fraction above 55 % (5 out of 8). Patient characteristics are summarized in Table 1 and represent largely what we might expect for a persAF population undergoing catheter ablation.
Figure 2 shows an AEG originally sampled at 1200 Hz with a total of 8192 samples (upper trace). A resampled signal with downsampling of 32 times (new Fs = 37.5 Hz) is shown on the second trace. Spectral analysis performed using FFT (for the original signal) and AR YuleWalker (for the downsampled signal) illustrates that the DF of the signal can still be estimated after downsampling using the AR approach. Zero padding of 4 times resulted in a total of 32,768 samples produced a frequency step of 0.0366 Hz for the FFT approach. The PSD using AR YuleWalker model was applied for two different AR model orders (50 and 18) and since the AR spectrum is continuous, the number of spectral samples was chosen so that frequency intervals were the same as applied by using the FFT approach using the original sampling frequency (Fs = 1200 Hz).
Selection of model order
Model orders were estimated for different Fs and the results are illustrated in Fig. 3. Figure 3a shows the cumulative histogram of the AEGs (in %) against model order for one patient whose original signals were downsampled to 75 Hz. The model order value chosen was 24. Figure 3b shows the average behaviour of the estimated best AR model order for all patients for different downsampling strategies. The model order values for each Fs are 126, 104, 60, 42, 30, 24; 20; 18. The curve shows that the order decreases with Fs, as expected. Lower model order values result in shorter processing time.
Spectral analysis and 3D DF mapping
Three sequential 3D DF maps were generated with different Fs values and the results were concentrated on the impact of downsampling on the DF maps.
For the AR spectral analysis, the mixed model ANOVA of the entire AF segment revealed that the interaction between downsampling factor and DF estimation with AR spectral techniques had a nonsignificant statistical effect (p = 1). In other words, our result showed that any differences between AR techniques did not depend on the resampling factor on the AEG. The main effect of the AR spectral estimation techniques (i.e. the effect of technique averaged over sampling frequency) was also not statistically significant (p = 0.62) as detailed in Fig. 4. This suggests no significant differences between AR techniques overall. Although there was no evidence of statistical differences between AR techniques, statistically significant differences between Fs values were found (p = 0.03). As Fig. 4 shows, Fs = 37.5 Hz had the greatest level of agreement, while the Fs = 100 Hz had the lowest level of agreement (albeit only around 2 % lower than at 37.5 Hz). DF values of all 2048 AEGs were compared between the 3D DF maps obtained by AR and FFT spectral analysis techniques. The total proportion of ‘similar’ DF points between techniques (percentage of DF agreement) is presented in Fig. 4.
Figure 5 shows a typical case of a 3D DF map using the FFTbased approach and the four AR techniques with the model order selection presented in Fig. 3b. Both methods result in similar 3D DF maps with a good agreement and the percentage of equal points between FFT vs. AR YuleWalker was 93.8 %, FFT vs. AR Burg was 93.6 %, FFT vs. AR Covariance was 93.8 % and FFT vs. AR Modified Covariance was 93.2 %.
DF estimation using AR YuleWalker method has the advantage of being computationally efficient. Aiming to observe the impact of the sampling frequencies to generate the 3D DF maps, the processing times of FFT and AR YuleWalker were measured for estimation of 3D DF maps. The processing time for the FFT at Fs = 1200 Hz was 7.65 s and the processing time for the AR YuleWalker, as expected, decreased with sampling frequency to: 5.44 s (Fs = 100 Hz), 5.35 s (Fs = 75 Hz), 5.32 s (Fs = 60 Hz), 5.27 s (Fs = 50 Hz), 5.15 s (Fs = 40 Hz) and 5.05 s (Fs = 37.5 Hz).
Discussion
Spectral analysis has been used as a tool to provide information about the behaviour of the electrical activity of the heart. Areas with high frequency activity are thought to be ‘driving’ the rhythm in patients with AF and hence are possible targets for catheter ablation. 3D DF mapping using FFTbased approach has been shown to enable the location of highfrequency areas [26–28] and ablation of these areas seems to be an effective therapy in eliminating DF gradient and restoring sinus rhythm [26, 27]. The majority of the studies that identify DF of endocardial electrograms during EP procedures used FFTbased approaches. For time varying spectra usually short segments of the signal are used for spectral analysis and it is well known that the spectral resolution of Fourierbased spectral analysis is poor for shorter segments [12, 13]. Therefore, investigation of alternative spectral analysis methods to track DF using shorter time segments while maintaining good timespectral resolution has its importance in the literature [13, 29–31]. In this study, we demonstrated that autoregressive spectral analysis can be used to generate dominant frequency maps of atrial electrograms of patients in persistent atrial fibrillation. The use of this technique in AF studies might be potentially avoided by reasons such as its time processing, the choice of the suitable AR technique and ‘model order’. The manuscript has covered all points by demonstrating that through a suitable downsampling strategy, AR could be performed faster than the FTT and with adequate model order selection. Moreover, apart from the technical ‘sophistication’ between the AR techniques to estimate the spectrum, the results were similar them and also similar with the FFT where all techniques were applied to electrograms with segment sizes commonly seen in AF studies.
For tracking the DF, two different definitions for DF are commonly presented in the literature [7, 32]. We have chosen the approach that has been used and validated previously with the St Jude´s system for noncontact AEGs [7]. In this approach, a highpass filter is implemented and no further action is needed to identify the DF through spectral analysis after QRST removal [7, 19]. The AR spectral estimation techniques were implemented after a selection of appropriate sampling rate and AR model order to generate highdensity 3D DF maps. As previously stated, our results demonstrated that the ARbased 3D DF maps produce good agreement when compared with the maps recently validated using FFTbased approach [15]. The agreement between AR and FFT techniques increased with higher levels of downsampling on the AEGs (Fig. 4). These results suggest that if downsampling of 32 times is implemented on AEG of persAF patients, the 3D DF maps of FFT and AR model will have good similarity (Fig. 5) with an average of the DF agreement at 93.6 ± 029 %. Although this result (better agreement with higher downsampling) might seem surprising, it is wellknown that for ARbased spectral analysis the sampling rate should not be exaggerated compared to the Nyquist frequency [12].
It has been argued that LevinsonDurbin YuleWalker produces poorer spectral resolution than other ARbased methods [14], however no statistically significant difference between LevinsonDurbin YuleWalker and the other three techniques was observed. The advantage of the LevinsonDurbin YuleWalker method is that it is faster than the other three techniques [14]. Although it is described in the literature differences of spectral estimation between the methods for test signals (with the LevinsonDurbin YuleWalker method faring slightly worse than the other three approaches [22]), our results showed no statistical differences between the AR methods. Moreover, a slight advantage to LevinsonDurbin YuleWalker in terms of DF similarity and processing time could be seen. This approach can substitute the frequency mapping systems currently used to help identify endocardium areas responsible for the AF maintenance and hence targets for ablation [7, 11, 15, 26, 27, 33].
We have tested several methods (not presented here) for estimation of AR model order and observed good agreement between them [34]. The CAT method was presented in this study. The model order values shown on Fig. 3 were implemented to generate the 3D AR DF maps. The effects of under/over estimating the order were explored by Schlindwein and Evans [34]. They showed that the effect on the spectral estimates of using too high a model order (twice the correct order for a known AR series) is usually not significant, while using too low an order (half the correct order for a known AR series) can change the estimate much more dramatically, that is, overestimating the AR model order is better than underestimating it. The comparisons of the spectral estimations obtained using the AR approach with the orders suggested with the FFTbased spectra show that no statistically significance overfitting was employed.
We have studied the three main issues that have made ARbased spectral analysis difficult for this application, namely the sampling frequency to be used, the AR model order to be chosen and the technique to find the AR coefficients. Our recommendations are that, for this application, the sampling frequency should be around 37.5 Hz, the order of the model should be 24 or slightly higher, and that the YuleWalker LevinsonDurbin approach should be chosen to find the AR coefficients. We have shown that the ARbased DF maps of AEGs from persAF patients are very similar (more than 90 % of similarity) to those obtained using FFTbased maps. No statistically significant differences between the four AR techniques we tested were found, but AR LevinsonDurbin YuleWalker has greater computational efficiency compared to the other three AR methods. Using the values and approach recommended above, the processing time (another issue that normally makes AR spectral estimation less attractive than the FFTbased approach) compares well with that of FFT, allowing for realtime implementation (ARbased spectral estimation takes 5.05 s for segments that are 6.826 s long).
Finally, concerning the limitations of the technology, AEGs acquired from remote areas (>4.0 cm) from the centre of the MEA have been shown to be significantly attenuated making the technology not suitable for large cardiac chambers. Movements of the balloon will produce distorted AEGs and as consequence, a new 3D geometry needs to be redone if the balloon moves. The use of NCM to determine electrical activation in tubular structures (i.e. pulmonary vein, superior or inferior vena cava) is a challenge due to the “lineofsight issue”.
Conclusions
This study showed the feasibility of AR spectral estimation techniques for producing 3D DF maps with appropriate sampling rate and AR model order, offering an alternative approach for 3D DF computation in human persAF studies that might contribute as an auxiliary tool for the study of AF ablation.
Abbreviations
 AR:

autoregressive
 3D:

three dimensional
 DF:

dominant frequency
 AEGs:

atrial electrograms
 persAF:

persistent atrial fibrillation
 DS:

downsampling
 AF:

atrial fibrillation
 CFAE:

complex fractionated atrial electrograms
 FFT:

fast fourier transform
 PSD:

power spectral density
 LA:

left atrium
 NCM:

noncontact mapping
 MEA:

multielectrode array catheter
 EP:

electrophysiological
 Fs:

sampling frequency
 CAT:

criterion AR transfer function
References
Alcaraz R, Hornero F, Rieta JJ. Dynamic time warping to estimate AF temporal organization from surface electrocardiogram. Med Eng Phys. 2013;35(9):1341–8.
Seeck A, Rademacher W, Fisher C, Hauesein J, Surber R, Voss A. Prediction of AF recurrence after cardioversioninteraction analysis of cardiac autonomic regulation. Med Eng Phys. 2013;35(3):376–82.
Alcaraz R, Hornero F, Rieta JJ. Surface ECG organization time course analysis along onward episodes of paroxysmal AF. Med Eng Phys. 2011;33(5):597–603.
Terasawa T, Balk EM, Chung M, Garlitski AC, AlsheikhAli AA, Lau J, et al. Systematic review: comparative effectiveness of radiofrequency catheter ablation for AF. Ann Intern Med. 2009;151(3):191–202.
Aliot E, Ruskin JN. Controversies in ablation of AF. Eur Heart J. 2008;Suppl 10(Supplement H):H32–H54.
Lin YJ, Tsao HM, Chang SL, Lo LW, Hu YF, Chang CJ, et al. Role of high dominant frequency sites in nonparoxysmal AF patients: insights from highdensity frequency and fractionation mapping. Heart Rhythm. 2010;7(9):1255–62.
Gojraty S, Lavi N, Valles E, Kim SJ, Michele J, Gerstenfeld EP. Dominant frequency mapping of AF: comparison of contact and noncontact approaches. J Cardiovasc Electr. 2009;20:997–1004.
Skanes AC, Mandapati R, Berenfeld O, Davidenko JM, Jalife J. Spatiotemporal periodicity during AF in the isolated sheep heart. Circulation. 1998;12:1236–48.
Berenfeld O, Mandapati R, Dixit S, Skanes AC, Chen J, Mansour M, et al. Spatially distributed dominant excitation frequencies reveal hidden organization in AF in the Langendorffperfused sheep heart. J Cardiovasc Electr. 2000;11(8):869–79.
Panfilov AV. Computational biology of the heart. ed. Wiley; 1997.
Salinet JL, Tuan JH, Sandilands AJ, Stafford PJ, Schlindwein FS, Ng GA. Distinctive patterns of dominant frequency trajectory behavior in drugrefractory persistent AF: preliminary characterization of spatiotemporal instability. J Cardiovasc Electr. 2014;25:371–9.
Kitney RI, Giddens DP. Linear estimation of blood flow waveforms measured by Doppler ultrasound. In: MEDINFO 86, Salamon R, Blum B, Jorgensen M, editors. North Holland: Elsevier Science Publishers BV. p. 672–77.
Marple L. Resolution of conventional Fourier, autoregressive and ARMA methods of spectrum analysis, Proceedings. Hartford: IEEE Int Conference on ASSP; 1977. p. 74–7.
Kay SM. Modern spectral estimation. PrenticeHall; 1987. p. 153–239.
Salinet JL Jr, Oliveira GN, Vanheusden FJ, Comba JLD, Ng GA, Schlindwein FS. Visualizing intracardiac AF electrograms using spectral analysis. Comp Sci Eng. 2013;15(2):79–87.
Tai C, Chen S. Noncontact mapping of the heart: how and when to use. J Cardiovasc Electrophysiol. 2009;20:123–6.
Schilling RJ, Peters NS, Davies W. Simultaneous endocardial mapping in the human left ventricle using a noncontact catheter—comparison of contact and reconstructed electrograms during sinus rhythm. Circulation. 1998;9:887–98.
Schilling RJ, Peters NS, Davies DW. Feasibility of a noncontact catheter for endocardial mapping of human ventricular tachycardia. Circulation. 1999;19:2543–52.
Salinet JL Jr, Madeiro JPV, Cortez PC, Stafford PC, Ng GA, Schlindwein FS. Analysis of QRST subtraction in unipolar AF electrograms. Med Biol Eng Comput. 2013;51:1381–91.
Kay SM, Marple SL Jr. Spectrum analysis—a modern perspective. P IEEE. 1981;69(11):1380–419.
Marple Jr SL. Digital spectral analysis. PrenticeHall; 1987. p. 189–260.
Diniz PSR, da Silva EAB, Netto SL. Digital signal processing: system analysis and design. Cambridge University Press; 2010. p. 409–51.
Parzen E. Multiple time series: determining the order of approximating autoregressive schemes. Technical report 1975 no. 23. Buffalo: Statistical Sciences Division, State University of New York; 1975.
Pinheiro J, Bates D, DebRoy S, Sarkar D, R Development Core Team. Nlme: linear and nonlinear mixed effects models. 2012. R package version 3.1103.
R Development Core Team. R: a language and environment for statistical computing. Vienna: R Foundation for Statistical Computing; 2012. ISBN 3900051070, url http://www.Rproject.org/.
Atienza F, Almendral J, Jalife J, Zlochiver S, PloutzSnyder R, Torrecilla EG, et al. Realtime DF mapping and ablation of DF sites in AF with lefttoright frequency gradients predicts longterm maintenance of sinus rhythm. Heart Rhythm. 2009;6:33–40.
Sanders P, Berenfeld O, Hocini M, Jaïs P, Vaidyanathan R, Hsu LF, et al. Spectral analysis identifies sites of highfrequency activity maintaining AF in humans. Circulation. 2005;112:789–97.
Guillem MS, Climent AM, Millet J, Arenal A, FernándezAvilés F, Jalife J, et al. Noninvasive localization of maximal frequency sites of AF by body surface potential mapping/clinical perspective. Circ Arrhythm Electrophysiol. 2013;6(2):294–301.
Ciaccio EJ, Biviano AB, Garan H. Software algorithm and hardware design for realtime implementation of new spectral estimator. BioMed Eng Online. 2014;13:61.
Ciaccio EJ, Biviano AB, Garan H. Computational method for high resolution spectral analysis of fractionated atrial electrograms. Comput Biol Med. 2013;43(10):1573–82.
Ciaccio EJ, Biviano AB, Garan H. Improved frequency resolution for characterization of complex fractionated atrial electrograms. BioMed Eng Online. 2012;11:17.
Botteron G, Smith J. Quantitative assessment of the spatial organization of AF in the intact Human heart. Circulation. 1996;93:513–8.
Li X, Salinet JL Jr, Almeida TP, Vanheusden FJ, Chu G, Ng GA, Schlindwein FS. A platform to guide catheter ablation of persistent atrial fibrillation using dominant frequency mapping. Proc Comput Cardiol (Comput Cardiol). 2014;41:649–52.
Schlindwein FS, Evans DH. Selection of the order of autoregressive models for spectral analysis of Doppler ultrasound signals. Ultrasound Med Biol. 1990;16(1):81–91.
Authors’ contributions
JLS: concept/design study, data analysis/interpretation of results, drafting manuscript, critical revision of manuscript and ‘offline’ data collection. NM: interpretation of results and statistics. PJS: EP studies and ablation procedures, interpretation of results, critical revision of manuscript. GAN: EP studies and ablation procedures, interpretation of results, critical revision of manuscript. FSS: design study, data analysis/interpretation of results, and critical revision of manuscript. All authors read and approved the final manuscript.
Acknowledgements
This study is part of the research portfolio supported by the Leicester NIHR Biomedical Research Unit in Cardiovascular Disease. Dr. Salinet has received research grant from Conselho Nacional de Desenvolvimento Científico e Tecnológico (CNPq, Brazil, Grant N. 200598/20090). The authors wish to thank Mr. TP Almeida, and the reviewers for their suggestions to improve the paper.
Competing interests
Dr. Stafford has received speaker fees from St. Jude Medical and Biosense Webster. Prof. Ng has received research fellowship from St. Jude Medical and speaker fees and honoraria from Biosense Webster. All other authors have declared that they have no competing interests.
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Salinet, J.L., Masca, N., Stafford, P.J. et al. Threedimensional dominant frequency mapping using autoregressive spectral analysis of atrial electrograms of patients in persistent atrial fibrillation. BioMed Eng OnLine 15, 28 (2016). https://doi.org/10.1186/s1293801601438
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DOI: https://doi.org/10.1186/s1293801601438
Keywords
 Autoregressive model
 Atrial fibrillation
 Unipolar electrograms
 Noncontact mapping
 Dominant frequency mapping