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Article

Heartbeat Detection in Gyrocardiography Signals without Concurrent ECG Tracings

by
Salvatore Parlato
,
Jessica Centracchio
*,
Daniele Esposito
,
Paolo Bifulco
* and
Emilio Andreozzi
Department of Electrical Engineering and Information Technologies, University of Naples Federico II, Via Claudio 21, 80125 Naples, Italy
*
Authors to whom correspondence should be addressed.
Sensors 2023, 23(13), 6200; https://doi.org/10.3390/s23136200
Submission received: 14 June 2023 / Revised: 29 June 2023 / Accepted: 3 July 2023 / Published: 6 July 2023
(This article belongs to the Special Issue Sensors for Physiological Parameters Measurement)
Browse Figures
Versions Notes

Abstract

:
A heartbeat generates tiny mechanical vibrations, mainly due to the opening and closing of heart valves. These vibrations can be recorded by accelerometers and gyroscopes applied on a subject’s chest. In particular, the local 3D linear accelerations and 3D angular velocities of the chest wall are referred to as seismocardiograms (SCG) and gyrocardiograms (GCG), respectively. These signals usually exhibit a low signal-to-noise ratio, as well as non-negligible amplitude and morphological changes due to changes in posture and the sensors’ location, respiratory activity, as well as other sources of intra-subject and inter-subject variability. These factors make heartbeat detection a complex task; therefore, a reference electrocardiogram (ECG) lead is usually acquired in SCG and GCG studies to ensure correct localization of heartbeats. Recently, a template matching technique based on cross correlation has proven to be particularly effective in recognizing individual heartbeats in SCG signals. This study aims to verify the performance of this technique when applied on GCG signals. Tests were conducted on a public database consisting of SCG, GCG, and ECG signals recorded synchronously on 100 patients with valvular heart diseases. The results show that the template matching technique identified heartbeats in GCG signals with a sensitivity and positive predictive value (PPV) of 87% and 92%, respectively. Regression, correlation, and Bland–Altman analyses carried out on inter-beat intervals obtained from GCG and ECG (assumed as reference) reported a slope of 0.995, an intercept of 4.06 ms (R2 > 0.99), a Pearson’s correlation coefficient of 0.9993, and limits of agreement of about ±13 ms with a negligible bias. A comparison with the results of a previous study obtained on SCG signals from the same database revealed that GCG enabled effective cardiac monitoring in significantly more patients than SCG (95 vs. 77). This result suggests that GCG could ensure more robust and reliable cardiac monitoring in patients with heart diseases with respect to SCG.

1. Introduction

Heart rate monitoring plays a key role in the assessment of cardiovascular function. Continuous, long-term cardiac monitoring has long been recognized as a critical task to improve the diagnosis and treatment of cardiac diseases [1,2,3,4]. To date, electrocardiography (ECG) is widely recognized as the gold standard for heart rate measurement via recording the myocardial electrical activity. However, ECG examinations can only be performed by skilled clinical professionals using approved medical devices. In addition, various practical drawbacks, such as detachments/slipping of electrodes, drying of electrolytic gel, and susceptibility to electromagnetic interferences, make electrocardiography not appealing for continuous, long-term monitoring, particularly in non-clinical settings [5,6,7,8,9,10,11]. Heart rate monitors based on plethysmographic techniques are available as alternatives to ECG, as well as in the form of wearable devices (e.g., smartwatches and fitbands). However, their strong sensitivity to motion artifacts usually limits their application to continuous, long-term monitoring for clinical purposes [11,12,13,14,15,16,17,18]. Cardio-mechanical monitoring techniques represent a further alternative for non-invasive assessment of cardiac function. Many of these techniques record the mechanical activity of the heart from a subject’s chest, essentially replicating the ancient practice of palpation [11,19]. From the end of the 19th century, various techniques have been proposed to record the tiny vibrations induced on the human body by the mechanical activity of the cardiovascular system [20]. Indeed, specific events of the cardiac cycle could be monitored by analyzing the peaks and valleys of cardio-mechanical signals. However, the bulky instrumentation and complexity of signal interpretation, as well as the considerable inter-subject variability, led most of these techniques to fall into disuse in favor of the emerging ultrasound imaging, which offered the unprecedented opportunity to visually inspect the anatomy and physiology of the cardiovascular system. Indeed, ultrasound imaging and Doppler techniques are currently reference clinical examinations for assessing the mechanical properties of the myocardium, which cannot be evaluated from ECG. However, ultrasound techniques also require highly qualified specialists, and are not suitable for continuous, long-term cardiac monitoring.
In the last two decades, the manufacturing of small, lightweight, inexpensive sensors based on micro-electromechanical system (MEMS) technologies has rejuvenated the interest in Ballistocardiography (BCG), which records the mechanical vibrations of the whole body due to blood ejection towards the feet [21,22,23,24,25,26], as well as Seismocardiography (SCG), which measures the infrasonic three-dimensional accelerations of the precordium induced by heart contractions [26,27,28,29,30,31,32,33]. In addition, the availability of modern electronic stethoscopes fostered the use of phonocardiography (PCG) to record heart sounds [34,35,36,37,38,39].
Recently, novel, non-invasive, cardio-mechanical monitoring techniques have been introduced, namely Forcecardiography (FCG) [40,41,42,43,44,45,46] and Gyrocardiography (GCG) [47,48,49,50], and even the combination of SCG with BCG [51] and GCG [52,53] has been investigated. FCG captures precordial vibrations using broadband force sensors, which are able to monitor respiration, infrasonic cardiac vibrations, and heart sounds, all simultaneously from a single site on the chest. On the other hand, GCG makes use of tri-axial gyroscopes to measure the infrasonic angular velocities of the thorax induced by heart contraction. Indeed, up to 60% of cardiac vibrational energy has been reported to be contained in the GCG signal [49]. Furthermore, peaks and valleys of GCG signals also have a clear correlation with important cardiac cycle events, thus allowing for the estimation of cardiac time intervals of diagnostic relevance [49,50]. Generally, the angular velocities around the latero–lateral axis (GCGx) and cranio–caudal axis (GCGy) are analyzed. During the cardiac cycle, the twisting and untwisting motion of the heart, which results from the contraction and relaxation of the helically oriented myocardial fibers, causes the chest wall to move accordingly. The specific arrangement of myofibrils, which form two oppositely oriented eight-shaped configurations, is responsible for the torsional motion of the heart. Indeed, during systole, the apex of the heart rotates counterclockwise, while the base rotates clockwise; on the contrary, during diastole, the opposite occurs [54,55,56]. This movement is mainly captured by the y component of the GCG signal [49].
Beat-by-beat heart rate monitoring from GCG signals is feasible. Specifically, precise identification of the temporal locations of all heartbeats and accurate measurement of inter-beat intervals are demanded to accomplish this task. Generally, heartbeats are localized by taking advantage of the a priori knowledge of R-peaks on a simultaneous ECG recording [49,57,58,59]. However, GCG-based heartbeat detectors that remove the need for concurrent ECG signals have also been proposed. In this regard, various approaches are available, such as short-term autocorrelation [60,61]; envelope extraction through wavelet [62] or Hilbert [63,64,65] transform, even combined with adaptative thresholding [66], clustering [67] or autoregressive models [68]; calculation of the kinetic energy waveform followed by Sparse Fast Fourier Transform [69]; and the autocorrelated differential algorithm [51,70]. A great part of these methods is based on rather complex algorithms and has only been tested on GCG signals recorded from subjects without any history of cardiovascular diseases. On the contrary, the method presented in [67], which combines GCG envelope extraction and unsupervised k-means clustering, was also assessed on a limited cohort of 12 patients with coronary artery disease. Moreover, GCG signals from 40 patients with atrial fibrillation, 21 patients with coronary artery disease, and 21 patients with myocardial ischemia were considered in [61], but any information is reported on the performance of heartbeat detection and the accuracy of inter-beat interval measurements. Heartbeats have also been recognized by combining GCG and SCG recordings [51,65,71]. As an example, independent component analysis was first employed in [65] for data fusion; then, an envelope-based heartbeat detector was tested on 19 patients with coronary artery disease. Furthermore, in [69], heartbeats were located on the kinetic energy waveform, which was obtained as the ensemble averaging of SCG and GCG signals. Deep learning methods for biosignal analysis [72,73,74] have also been proposed for ECG-free heartbeat detection in SCG [75] and BCG [76] signals, but not in GCG signals.
This study aims to demonstrate the suitability of a template matching approach for ECG-free heartbeat detection in GCG signals. The algorithm proposed here is based on the well-established normalized cross-correlation (NCC) function [77,78,79] to assess the morphological similarity between a selected template and signal chunks. This allows for capturing the heartbeat pattern in the signal without any a priori assumptions about the signal waveform. The performance of the proposed approach was extensively evaluated on SCG signals of 100 patients with one or more valvular heart diseases (VHDs) [80], made available in a public database [81]. To the best of our knowledge, for the first time in the literature, a template matching algorithm has been shown to provide high precision in heartbeat detection, as well as high accuracy in inter-beat intervals estimation, on a large cohort of pathological subjects [80]. As the database considered also contained simultaneous GCG recordings, the feasibility of this method on GCG signals from the same 100 VHD patients was evaluated in this work. To this end, the temporal locations of heartbeats were identified from both GCG signals and reference ECG recordings, and inter-beat interval measurements were compared via statistical analyses. The results showed that even on GCG signals the template matching offers a simple, yet effective and robust way for continuous heart rate monitoring.

2. Materials and Methods

2.1. Dataset

GCG and ECG signals of 100 VHD patients (59 males and 41 females, age 68 ± 14 years) from a public database [81] were considered in this study. The subjects suffered from one or more VHDs at a moderate or severe stage. In particular, 23 subjects were affected by mitral valve stenosis, 51 by mitral valve regurgitation, 39 by aortic valve stenosis, 28 by aortic valve regurgitation, 40 by tricuspid valve regurgitation, and 59 subjects suffered from more than one VHD (more detailed information on the patients is available in [81] and at the database repository). GCG and ECG signals were recorded on subjects’ chest by means of a tri-axial MEMS gyroscope and an ECG front-end, respectively, integrated in the Shimmer 3 ECG module (Shimmer Sensing, Dublin, Ireland). Signals were acquired simultaneously at a sampling rate of 256 Hz (patient IDs #CP-01 to #CP-70 and #UP-01 to #UP-21) or 512 Hz (patients IDs #UP-22 to #UP-30), from subjects lying supine and breathing at a natural pace. Only GCGy signals and ECG leads II were considered for the analysis. Recordings corresponding to patient ID #UP-28 were discarded due to the lack of a simultaneous ECG signal. In addition, four recordings (patient IDs #CP-24, #CP-31, #CP-55, and #UP-22) were excluded from the analysis because of poor GCG signal quality. Therefore, signals from a total of 95 subjects were analyzed in this study.

2.2. Signals Pre-Processing

Matlab® R2018b (The MathWorks, Inc., 1 Apple Hill Drive, Natick, MA 01760, USA) was used for all signal processing operations. First of all, a linear interpolation was carried out via the Matlab® function interp1 to oversample the signals up to 1 kHz, in order to improve their temporal resolution. Afterwards, the ECG signal was filtered in the 0.5–40 Hz frequency band using a fourth order zero-lag Butterworth band-pass filter; then, the 50 Hz powerline interference and its higher harmonics were filtered out by means of a comb notch filter; finally, the temporal locations of R-peaks were identified by the well-kwown Pan and Tompkins algorithm [82], implemented in the BioSigKit Matlab® toolbox [83]. On the other hand, the GCG signal was processed via a fourth order zero-lag Butterworth filter with 7–30 Hz pass band. Figure 1 shows an example of pre-processed ECG and GCG signals from patient #CP-63.

2.3. Template Matching

A template matching algorithm, previously proposed in a SCG [80] study, was implemented for heartbeat localization in GCG signals. As already reported in [80], the template matching first requires selecting a heartbeat template within the GCG signal, then calculating the NCC function between the selected template and GCG signal chunks, and finally identifying the temporal locations of the NCC peaks.

2.3.1. Template Selection

First, a template was identified in each GCG signal in order to capture the typical heartbeat waveform, which was regarded as a morphological reference. As illustrated in Figure 2, the template was selected according to the following criterion: “the template should start two or three waves before the highest local maximum in the systolic complex, where the amplitude of the waves is significantly lower than systolic peak magnitude, and should end after the last wave in the diastolic complex”. All GCG signals included in the dataset met this criterion. Hence, a template comprising both the systolic and diastolic complexes of the selected cardiac cycle was chosen for all of the GCG signals analyzed. Figure 3 shows an example of template selection for subject #CP-63.

2.3.2. Heartbeats Localization on Normalized Cross-Correlation Function

The NCC function was considered as a similarity measure between the template and signal chunks to find those that most resemble the template, as in [80]. Local maxima in the NCC function corresponded to signal chunks with highest local similarity to the selected template, so they marked the temporal locations of heartbeats. Therefore, once a template was selected, the NCC function was computed between the template and GCG signal chunks, after local mean removal. Then, the local maxima were identified in the NCC function obtained via the Matlab® function findpeaks, by setting a minimum peak prominence of 0.5 and a minimum peak distance of 500 ms for all of the GCG signals included in the dataset. Figure 4 shows some examples of heartbeat detection in the NCC function for patients #CP-63 and #CP-08.

2.3.3. Inter-Beat Intervals Estimation

Once NCC peak detection was completed, wrong and missed heartbeat detections among all NCC peaks were annotated with the support of reference ECG signals, as reported in [80]. Multiple NCC peaks within one cardiac cycle were considered as false positives (FPs); single NCC peaks within one cardiac cycle occurring at temporal locations that were unlikely to correspond to matched heartbeat templates were considered as detection errors (DEs); cardiac cycles with no NCC peaks were considered as false negatives (FNs). DEs essentially marked cardiac cycles where only one FP was found, and no true heartbeat was detected, so they contributed both to the number of FPs and FNs. Finally, inter-beat intervals were estimated from ECG and GCG signals as temporal differences between consecutive R-peaks and NCC-peaks, respectively, as depicted in Figure 5. Inter-beat intervals corrupted by FNs and DEs were obviously removed from the analysis.

2.4. Statistical Analyses

Sensitivity and positive predictive value (PPV) were considered as performance evaluation metrics of heartbeat detection. These metrics are defined by the following mathematical expressions:
S e n s i t i v i t y = T P T P + F N + D E · 100 ,
P P V = T P T P + F P + D E · 100 ,
where TP, FN, FP, and DE indicate the number of true positives, false negatives, false positives, and detection errors, respectively.
Furthermore, regression, correlation, and Bland–Altman [84,85] analyses were carried out via the Matlab® function bland–altman-and-correlation-plot [86], to compare the inter-beat interval measurements obtained from GCG signals with those provided by the reference ECG signals. In addition, the results obtained from the analysis of GCG signals were compared with those reported in the previous work on SCG signals [80], to assess the performance of the proposed template matching algorithm in the estimation of inter-beat intervals from the GCG and SCG signals acquired on the same VHD patients.

3. Results

The number of ECG heartbeats (R-peaks) and GCG heartbeats (NCC-peaks) identified for each subject, together with the number of FPs, FNs, and DEs, are outlined in Table A1 in Appendix A. This table also reports the number of inter-beat intervals compared via the statistical analyses. An overall number of 40,527 and 38,565 heartbeats were identified in the ECG and GCG signals, respectively. In particular, 35,383 TPs, 526 FPs, 2486 FNs, and 2656 DEs were detected in the GCG signals. Hence, heartbeat detection in GCG signals achieved a sensitivity of 87% and a PPV of 92%. Furthermore, an overall number of 31,831 inter-beat intervals were compared via regression, correlation, and Bland–Altman analyses. The regression and correlation analysis reported a slope of 0.995, an intercept of 4.06 ms (R2 > 0.99), and a Pearson’s correlation coefficient r of 0.9993 (p < 0.001), as illustrated in Figure 6a. Moreover, limits of agreement (LoA) of [−12.85, 13.15] ms, with a 95% confidence interval (95% CI) of [−12.97, 13.27] ms, and a negligible bias of 0.15 ms (p < 0.001), with a 95% CI of [0.08, 0.22] ms, were obtained from the Bland–Altman analysis (see Figure 6b). The results of statistical analyses are also summarized in Table 1.
To compare the performance of heartbeat detection in GCG and SCG signals from the same database [81], Table A2 in Appendix A reports, for each of the 100 VHD patients, the number of heartbeats identified in the ECG signals; the number of TPs, FPs, and FNs detected in the GCG recordings analyzed in this study; and the number of TPs, FPs, and FNs recognized in the SCG recordings obtained in a previous study [80]. In particular, the table also highlights which patients were excluded from the analyses of GCG and/or SCG signals due to very poor signal quality (see dashes in the table). In addition, a comparison of the performances achieved in the inter-beat interval estimation from GCG and SCG recordings against the reference ECG was carried out. To this aim, 76 patients were considered, for which both GCG and SCG analysis was feasible, and then regression, correlation, and Bland–Altman analyses of inter-beat intervals were performed. In detail, a total of 41,320 heartbeats were detected in the ECG signals, while 35,383 TPs, 3182 FPs, and 5142 FNs were identified in GCG recordings, and 29,583 TPs, 2976 FPs, and 3678 FNs were detected in the SCG recordings. Hence, the GCG signals scored a sensitivity of 89% and a PPV of 93%, while SCG scored a sensitivity of 90% and a PPV of 91.5%. Moreover, a slope of 0.995, an intercept of 4.51 ms (R2 > 0.99), and a Pearson’s correlation coefficient r of 0.9993 (p < 0.001) were obtained for GCG signals, while a slope of 0.995, an intercept of 3.92 ms (R2 > 0.99), and a Pearson’s correlation coefficient r of 0.9993 (p < 0.001) were found for the SCG signals (see Figure 7a). As shown in Figure 7b, the Bland–Altman analyses reported a negligible bias of 0.16 ms (p < 0.001), with a 95% CI of [0.09, 0.23] ms, and LoA of [−11.84, 12.16] ms, with a 95% CI of [−11.97, 12.29] ms, for the GCG signals, as well as a non-significant bias (p = 0.09), with 95% CI of [0.01, 0.17] ms, and LoA of [−12.91, 13.09] ms, with 95% CI of [−13.05, 13.23] ms, for the SCG signals. The results of these statistical analyses are also outlined in Table 2 (see [80] for further details on the results obtained for SCG signals).

4. Discussion

The proposed method was able to recognize heartbeats in GCG signals of 95 out of 99 patients (96%) with a sensitivity and PPV of 87% and 92%, respectively, also providing accurate measurements of inter-beat intervals compared with ECG (LoA of about ± 13 ms). It is worth noting that, when applied on SCG, the templatematching method ensured accurate heartbeat detection in 77 out of 99 patients (78%) with similar values of sensitivity and PPV, as well as of LoA for inter-beat interval estimation. In both SCG and GCG, the inability to ensure an acceptable performance in heartbeat detection was due to an extremely poor signal quality.
The measurement errors in inter-beat intervals obtained by SCG and GCG compared with ECG have various contributions. First of all, assuming the ideal capability of locating the timing of the aortic valve opening with maximum accuracy in SCG and GCG signals (AO peaks), it must be considered that the time delay between ECG R peaks and AO peaks, which is a component of the pre-ejection period, changes over time. Therefore, if the R–AO time delays of two consecutive heartbeats are different, then the related AO–AO interval will differ from the R–R interval, thus leading to a measurement error. Moving forward to less ideal conditions, it is important to consider that motion artifacts and noise may corrupt the heartbeat morphology in SCG and GCG signals, thus potentially leading to imprecise localization of the AO peaks, and eventually to errors in inter-beat intervals measurements. Finally, it must be considered that in the proposed approach the heartbeat markers are the peaks of NCC between the selected template and the signals, and not the actual AO peaks. This is important as the time delay between the NCC peaks and the actual AO peaks may change over time, because the heartbeat morphology is not always exactly the same of the template, so the local maximum of NCC may not always occur at a fixed time distance from the related actual AO peak. Again, different AO–NCC-peaks time delays in two consecutive heartbeats would lead to differences between NCC peak–NCC peak intervals and AO–AO intervals, and eventually in additional measurement errors with respect to R–R intervals. Anyway, the impact of these errors on the parameters of clinical relevance, such as the mean heart rate and HRV indices, has yet to be evaluated, and will be the subject of a future study.
This is the first study that assessed the performance of an algorithm for ECG-free heartbeat detection in GCG signals on such a large cohort of subjects. In addition, it is also the first time that the heart monitoring performances of SCG and GCG have been thoroughly compared for such a large cohort of pathological subjects. Indeed, the results suggest that, for patients affected by valvular heart diseases, the heartbeat morphology is more stable in GCG than in SCG signals. This result has important implications in the development of devices and methods for continuous, long-term patient surveillance based on cardio-mechanical monitoring techniques. In fact, the superior performances achieved by GCG suggest that its use could ensure a more reliable and robust monitoring of actual patients. However, considering that electronic microchips of inertial measurement units incorporating both accelerometers and gyroscopes are widely available nowadays, it might be advantageous to apply sensor fusion approaches to design heartbeat detectors that jointly use SCG and GCG signals, in order to leverage their strengths and compensate for their weaknesses. Undoubtedly, the availability of a quantitative index of signal quality could help to dynamically identify the most reliable signal, thus possibly improving the performance of heartbeat detection.
Overall, the proposed templatematching method achieves very high performance on both SCG and GCG signals, which makes it effective for ECG-free cardiac monitoring. The modest computational burden of the proposed method also makes it very efficient and suitable for implementation on resource-constrained computing platforms, possibly also in real time. To date, not many ECG-free methods have been proposed in the literature. The few proposed methods are based on rather complex procedures, or on computationally intensive transformations, or even on machine learning and deep learning techniques, which require very high-performing processors. However, such artificial intelligence methodologies can potentially provide valuable support for the classification and interpretation of signals to offer not only information on heart rhythm, but also on other cardiovascular functions and pathologies.
The results obtained in this study cannot be directly compared with those of previous studies for different reasons. First, the performance of different algorithms must be compared on the same data for consistency, but none of the methods proposed in the literature has been assessed on the same database. Furthermore, other methods have been evaluated on much smaller cohorts of subjects. Data from these cohorts were likely to be characterized by a lower inter-subject variability, which has long been recognized as a factor affecting the accuracy of biosignal analysis. In addition, these cohorts mainly consisted of healthy subjects, sometimes with the presence of a small number of pathological subjects. It is well known that cardio-mechanical signals from pathological subjects exhibit atypical waveforms, with higher morphological variability and difficulty in annotation and interpretation compared with healthy subjects [87], thus making the heartbeat detection task far more complex. Therefore, the methods proposed in the literature have been tested on signals with undoubtedly higher quality and with lower inter-subject variability than those considered in this study, so it is more likely that the results of other methods have been overestimated.
Obviously, the need for manual selection of the heartbeat template is the main limitation for the use of the template-matching method by unskilled users who are unable to follow the suggested guidelines. Therefore, an automated template selection algorithm could be beneficial to improve the reproducibility of the proposed technique.

5. Conclusions

This study presents an extensive performance analysis of an ECG-free heartbeat detection method in Gyrocardiography signals. The method is based on a template matching approach and was tested on GCG signals from a public database of 100 patients with valvular heart diseases. The algorithm has previously been tested on Seismocardiography signals from the same database.
This study provides, for the first time, an extensive comparison of heart rate monitoring performances of SCG and GCG on a large cohort of pathological subjects. The morphology of heartbeats turned out to be more stable in GCG than in SCG signals, thus providing a superior performance in heartbeat detection. According to these results, GCG could ensure a more reliable and robust monitoring of actual patients. However, these findings should be confirmed also on patients affected by other cardiac diseases.
Overall, the proposed method achieves very high performance for both SCG and GCG signals, and presents a modest computational burden compared with other methods proposed in the literature. These aspects make the template matching algorithm effective and efficient for ECG-free cardiac monitoring. It is also suitable for real-time implementation on resource-constrained computing platforms, which is appealing to enable the continuous, long-term monitoring of heart rate.

Author Contributions

Conceptualization, J.C. and E.A.; methodology, S.P., J.C. and E.A.; software, S.P.; formal analysis, S.P. and E.A.; investigation, S.P., J.C., D.E., P.B. and E.A.; data curation, S.P.; writing—original draft preparation, S.P., J.C. and E.A.; writing—review and editing, S.P., J.C., D.E., P.B. and E.A.; visualization, S.P.; supervision, P.B. and E.A. All authors have read and agreed to the published version of the manuscript.

Funding

This research received no external funding.

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

All of the relevant research data will be made available upon request after the publication of the paper.

Conflicts of Interest

The authors declare no conflict of interest.

Appendix A

Table
Table A1. Number of heartbeats detected in the ECG and GCG signals, along with the number of FP, FN, and DE identified in GCG signals and the number of compared inter-beat intervals.
Table A1. Number of heartbeats detected in the ECG and GCG signals, along with the number of FP, FN, and DE identified in GCG signals and the number of compared inter-beat intervals.
Patient
ID #		ECG
Heartbeats
(R-Peaks)		GCG
Heartbeats
(NCC-Peaks)		FPFNDECompared Inter-Beat Intervals
CP-01448448002443
CP-026516333213609
CP-03481474299451
CP-0466162923416562
CP-05509502296484
CP-062942862107264
CP-07451450345435
CP-08544544004536
CP-0936432024657190
CP-10506485194041347
CP-1165662733257500
CP-12423425973404
CP-13837829081819
CP-1447242964827319
CP-1563061801216590
CP-16355354124342
CP-1736236613942272
CP-18601599131593
CP-1948447381932404
CP-20391393310388
CP-21247247002242
CP-2261053458171368
CP-23235235000234
CP-2560249410118147166
CP-263893792126352
CP-27130130110127
CP-28238239102233
CP-292901920982091
CP-305235120113500
CP-32527493154991298
CP-3344948740210424
CP-34462455295436
CP-354844831314125269
CP-3638640926319773
CP-37342343323331
CP-38406339239053161
CP-395185150339448
CP-4050941309619328
CP-41349349001346
CP-423463436918296
CP-434604081567138159
CP-44321321004312
CP-45357359181658232
CP-4649948931321441
CP-47537457119138319
CP-486375883382121313
CP-49451425133927325
CP-50781679010230547
CP-516216210052543
CP-52728494023454212
CP-5356249706549377
CP-5439736613236275
CP-5674262901136511
CP-57507507113499
CP-58525525111521
CP-59405405111400
CP-605125030910484
CP-61397397002393
CP-625725001735424
CP-63610609010607
CP-643823961404373
CP-65369369005361
CP-66468468110465
CP-67539514103525429
CP-683273482321320
CP-69587585022578
CP-70422429191244324
UP-01239232222958111
UP-0228626852366134
UP-0326421814734135
UP-0425824771823183
UP-05462412252122178
UP-0645839806016325
UP-07376372153359
UP-08257257002252
UP-09286285237267
UP-101651611512131
UP-11417386255610297
UP-123393362525283
UP-1310610402789
UP-14340341109321
UP-15214215100213
UP-162212204436150
UP-1761354417062421
UP-18350351103343
UP-1911611611114526
UP-20617494312655329
UP-21305308302300
UP-23565570503558
UP-2434933501411308
UP-25244222123444131
UP-26160158021154
UP-27269276221574131
UP-29146146115133
UP-302282302039150
Total40,52738,5655262486265631,831
Table
Table A2. Comparison of SCG and GCG results on the whole database. The table reports the number of heartbeats detected in the ECG signals, together with the number of TP, FP, and FN detected in both SCG and GCG recordings (the number of DE was added to those of FP and FN). Black dashes indicate the SCG and/or GCG recordings discarded from the analysis due to very poor signal quality. Recordings of patient #UP-28 were not analyzed because ECG was unavailable (NA: not available).
Table A2. Comparison of SCG and GCG results on the whole database. The table reports the number of heartbeats detected in the ECG signals, together with the number of TP, FP, and FN detected in both SCG and GCG recordings (the number of DE was added to those of FP and FN). Black dashes indicate the SCG and/or GCG recordings discarded from the analysis due to very poor signal quality. Recordings of patient #UP-28 were not analyzed because ECG was unavailable (NA: not available).
Patient
ID #		ECG
Heartbeats
(R-Peaks)		SCGGCG
TPFPFNTPFPFN
CP-014484480044622
CP-026516063745627624
CP-03481―――4631118
CP-0466160747546111850
CP-055094961113494815
CP-06294―――277917
CP-074514458644289
CP-08544520182454044
CP-0936422212014226159103
CP-105063291761774256081
CP-1165658082765676089
CP-1242340627174131210
CP-1383782451282819
CP-144722781991943963375
CP-156306203106021628
CP-16355332282334956
CP-17362―――3115551
CP-18601―――59724
CP-1948444548394334051
CP-203913901139031
CP-212472443324522
CP-22610528678245876152
CP-23235197283823500
CP-24(1036)――――――
CP-25602―――337157265
CP-263893711018371818
CP-271301300012911
CP-282382325623632
CP-29290―――17220118
CP-30523508215509314
CP-31(948)――――――
CP-32527353133174387106140
CP-3344943224174375012
CP-34462452810448714
CP-35484―――345138139
CP-36386268109118186223200
CP-3734219014515233765
CP-38406356645026376143
CP-39518510884763942
CP-4050924625926339419115
CP-413493413834811
CP-4234627268743192427
CP-43460346132114255153205
CP-443213182331744
CP-4535732617312837674
CP-46499―――4652434
CP-47537505173240849129
CP-486375606677434154203
CP-4945139958523854066
CP-50781―――64930132
CP-51621―――5695252
CP-527284943823444054288
CP-535625610144849114
CP-54397―――3293768
CP-55793339263454―――
CP-567425331602066236119
CP-575075015650344
CP-585255231252322
CP-594054051040322
CP-605125021104931019
CP-613973967139522
CP-62572―――494678
CP-636106080260901
CP-64382381101378184
CP-653693651436455
CP-664684671146711
CP-67539―――4793560
CP-683272755552324243
CP-695875850258324
CP-7042237636463666356
UP-0123919051491528087
UP-02286―――1977189
UP-03264―――1833581
UP-042582447142173041
UP-05462―――288124174
UP-0645837129873821676
UP-073763703636848
UP-082572551225522
UP-0928627808276910
UP-101651516141481317
UP-1141734371743513566
UP-1233926087793092730
UP-13106921149779
UP-1434033357331109
UP-1521418902521410
UP-1622119519261804040
UP-1761359671748163132
UP-183503481234743
UP-19116―――605656
UP-206176132443658181
UP-213053032230352
UP-22(700)――――――
UP-235655652056283
UP-2434932911203241125
UP-25244―――1665678
UP-26160―――15713
UP-2726924637231809689
UP-28NANANANANANANA
UP-291461411514066
UP-302282281601894139
Total41,32029,5832976367835,38331825142

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Figure 1. An example of pre-processed ECG (blue line) and GCG (green line) signals from patient #CP-63. Red points mark R peak locations.
Figure 1. An example of pre-processed ECG (blue line) and GCG (green line) signals from patient #CP-63. Red points mark R peak locations.
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Figure 2. An example of the recommended template waveform extracted from subject #CP-63.
Figure 2. An example of the recommended template waveform extracted from subject #CP-63.
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Figure 3. An example of an ECG signal (blue line), GCG signal (green line), and selected template (red line) from subject #CP-63. The template corresponds to that highlighted in Figure 2. Red points mark R-peak locations.
Figure 3. An example of an ECG signal (blue line), GCG signal (green line), and selected template (red line) from subject #CP-63. The template corresponds to that highlighted in Figure 2. Red points mark R-peak locations.
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Figure 4. Some excerpts of ECG (blue line), GCG (green line), and NCC (orange line) signals from subjects: (a) #CP-08 and (b) #CP-63. Red and black points mark the temporal locations of R peaks and NCC peaks, respectively.
Figure 4. Some excerpts of ECG (blue line), GCG (green line), and NCC (orange line) signals from subjects: (a) #CP-08 and (b) #CP-63. Red and black points mark the temporal locations of R peaks and NCC peaks, respectively.
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Figure 5. An example of inter-beat interval estimation from subject #CP-63 on ECG (blue line) and NCC (orange line) signals. For the ECG signal, the inter-beat interval was estimated as the temporal difference between two consecutive R-peaks (grey double arrow). For the NCC signal, the inter-beat interval measurement was obtained as the temporal difference between two consecutive NCC peaks (electric blue double arrow).
Figure 5. An example of inter-beat interval estimation from subject #CP-63 on ECG (blue line) and NCC (orange line) signals. For the ECG signal, the inter-beat interval was estimated as the temporal difference between two consecutive R-peaks (grey double arrow). For the NCC signal, the inter-beat interval measurement was obtained as the temporal difference between two consecutive NCC peaks (electric blue double arrow).
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Figure 6. Statistical analyses on inter-beat intervals obtained from GCG signals of the 95 VHD patients included in the dataset: (a) results of the regression and correlation analysis and (b) results of the Bland–Altman analysis.
Figure 6. Statistical analyses on inter-beat intervals obtained from GCG signals of the 95 VHD patients included in the dataset: (a) results of the regression and correlation analysis and (b) results of the Bland–Altman analysis.
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Figure 7. Statistical analyses on inter-beat intervals obtained from GCG signals of the 76 VHD patients: (a) results of the regression and correlation analysis and (b) results of the Bland–Altman analysis.
Figure 7. Statistical analyses on inter-beat intervals obtained from GCG signals of the 76 VHD patients: (a) results of the regression and correlation analysis and (b) results of the Bland–Altman analysis.
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Table
Table 1. Results of statistical analyses on the GCG signals of the 95 VHD patients included in the dataset: 95% CIbias is the 95% confidence interval of the bias and 95% CILoA is the 95% confidence interval of the limits of agreement.
Table 1. Results of statistical analyses on the GCG signals of the 95 VHD patients included in the dataset: 95% CIbias is the 95% confidence interval of the bias and 95% CILoA is the 95% confidence interval of the limits of agreement.
Sample sizeN° of subjects95
N° of compared inter-beat intervals31,831
Performance of heartbeat detectionSensitivity (%)87
PPV (%)92
Results of regression analysisSlope0.995
Intercept (ms)4.06
R20.9985
Results of correlation analysisr0.9993 (p < 0.001)
Results of Bland-Altman analysisBias (ms)0.15 (p < 0.001)
95% CIbias (ms)[0.08, 0.22]
LoA (ms)[−12.85, 13.15]
95% CILoA (ms)[−12.97, 13.27]
Table
Table 2. Results of statistical analyses performed on GCG and SCG signals from the same 76 VHD patients: 95% CIbias is the 95% confidence interval of the bias and 95% CILoA is the 95% confidence interval of the limits of agreement.
Table 2. Results of statistical analyses performed on GCG and SCG signals from the same 76 VHD patients: 95% CIbias is the 95% confidence interval of the bias and 95% CILoA is the 95% confidence interval of the limits of agreement.
GCGSCG
Sample sizeN° of subjects7676
N° of compared inter-beat intervals26,30826,913
Performance of heartbeat detectionSensitivity (%)8990
PPV (%)9391.5
Results of regression analysisSlope0.9950.995
Intercept (ms)4.513.92
R20.99870.9986
Results of correlation analysisr0.9993
(p < 0.001)		0.9993
(p < 0.001)
Results of Bland-Altman analysisBias (ms)0.16
(p < 0.001)		0.09
(p = 0.09)
95% CIbias (ms)[0.09, 0.23][0.01, 0.17]
LoA (ms)[−11.84, 12.16][−12.91, 13.09]
95% CILoA (ms)[−11.97, 12.29][−13.05, 13.23]
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Parlato, S.; Centracchio, J.; Esposito, D.; Bifulco, P.; Andreozzi, E. Heartbeat Detection in Gyrocardiography Signals without Concurrent ECG Tracings. Sensors 2023, 23, 6200. https://doi.org/10.3390/s23136200

AMA Style

Parlato S, Centracchio J, Esposito D, Bifulco P, Andreozzi E. Heartbeat Detection in Gyrocardiography Signals without Concurrent ECG Tracings. Sensors. 2023; 23(13):6200. https://doi.org/10.3390/s23136200

Chicago/Turabian Style

Parlato, Salvatore, Jessica Centracchio, Daniele Esposito, Paolo Bifulco, and Emilio Andreozzi. 2023. "Heartbeat Detection in Gyrocardiography Signals without Concurrent ECG Tracings" Sensors 23, no. 13: 6200. https://doi.org/10.3390/s23136200

APA Style

Parlato, S., Centracchio, J., Esposito, D., Bifulco, P., & Andreozzi, E. (2023). Heartbeat Detection in Gyrocardiography Signals without Concurrent ECG Tracings. Sensors, 23(13), 6200. https://doi.org/10.3390/s23136200

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