Abstract
Purpose
Recent studies have analyzed steady-state visual evoked potentials (SSVEPs) measured on belowthe-hairline areas, such as behind-the-ears (temporal area) and face (frontal area) using different montages of channels and frequency bands. This study aims to investigate how both reference electrode and frequency ranges (low, medium, and high bands) affect the SSVEP measured on hairless areas of temporal and frontal.
Methods
The EEG signals were acquired from 12 individuals, and the elicited SSVEP was evaluated in terms of amplitude and signal-to-noise ratio (SNR).
Results
The best electrode combinations for measuring SSVEP on hairless areas are obtained with Fpz-Tp9 and Fpz-Tp10 (up to 40 Hz); however, for stimuli frequencies higher than 40 Hz, the best result is obtained with the temporal area and with the reference electrode located on the ear.
Conclusion
The SSVEP amplitude and the SNR depend on the combination of the electrode reference and the range of visual stimulus frequency. These findings can aid in the development of more practical and comfortable SSVEP-based BCIs.
Similar content being viewed by others
Avoid common mistakes on your manuscript.
Introduction
Steady-state visual evoked potentials (SSVEPs) are responses of the visual cortex to visual stimuli at specific frequencies. When the retina is excited by a visual stimulus, the brain generates electrical activity at the same frequency (and/or harmonics) of the visual stimulus. In the electroencephalogram (EEG), three bands can be identified: low- (up to 12 Hz), medium- (12–30 Hz), and high-frequency (≥ 30 Hz) (Zhu et al. 2010).
SSVEP response is often maximal in occipital area; consequently, this region is normally used to measure SSVEPs (Vialatte et al. 2010). In fact, generally, brain-computer interfaces (BCIs) based on SSVEP use electrodes located at occipital positions (O1, O2, and/or Oz) (Muller-Putz and Pfurtscheller 2008, Diez et al. 2011). However, this area is generally covered by hair, which causes bad impedance matching between the electrode contact and the skin (Wang et al. 2017). On the other hand, neuroscience studies based on EEG and other techniques (like MEG, PET, fMRI) reported that SSVEP response also occurs in other brain areas, including parietal, temporal, frontal, and prefrontal (Vialatte et al. 2010; Di Russo et al. 2007; Pastor et al. 2007; Floriano et al. 2018; Srinivasan et al. 2007, Sammer et al. 2005, Fawcett et al. 2004). However, after years of research, the complex mechanisms behind SSVEP distribution are not yet fully understood; details about proposed theories can be found in (Vialatte et al. 2010).
Thus, towards a more practical BCI, recent researches have analyzed SSVEP measured from below-the-hairline areas using some montages of EEG channels and frequency bands. For example, Norton et al. (2015) measured SSVEPs with an electrode positioned behind-the-ear with ear-referenced electrode. Hsu et al. (2016) obtained medium-frequency range SSVEP on the forehead with reference electrode on the behind-the-ear area. In a recent study using low- and medium-frequency band, it was found that behind-the-ear areas have better SNR in comparison to other hairless areas (Wang et al. 2017).
The reference electrode position and the stimulation frequency affect the SSVEP measured on the scalp (occipital area). However, the influence of these factors on SSVEP from below-the-hairline areas in the three frequency bands was not addressed. Thus, this study aims to investigate how reference electrode and the frequency bands (low, medium, and high bands) affect the SSVEP measured on hairless areas.
Materials and methods
EEG acquisition and experimental protocol
EEG signals were acquired with a Grass 15LT amplifier system and digitalized with a NI-DAQ-Pad6015. The sampling frequency was set at 256 Hz. The cutoff frequencies of the analog band-pass filter were set to 1 and 100 Hz. Additionally, a notch filter for 50 Hz (Argentinian power supply) was applied. Figure 1a presents the positions where the electrodes were located.
Twelve healthy subjects (ages 26.1 ± 4.1; 6 F and 6 M) with normal or corrected to normal vision participated in this study. The EEG recordings were conducted in a laboratory with low background noise and dim luminance. The study was approved by the Ethics Committee of the School of Exact, Physical and Natural Sciences of the National University of San Juan Argentina (act #7). Before participating in this study, all volunteers read an information sheet and signed a consent form.
Each subject sat in a chair at 60 cm from the stimulus. The experiment consisted of five runs, and each run was composed of 12 trials, one per stimulation frequency (Fig. 1c). The stimulation frequencies were presented in random order to each volunteer. Each trial lasted 7 s, with a variable separation between trials from 2 to 4 s, to avoid expectation effect (Fig. 1d). The trial begins with a beep (at t = 0 s) and 2 s later the stimulus is turned on. The stimulus stays on until the end of the trial at t = 7 s. At this moment, a feedback is presented to the volunteer, indicating whether the SSVEP was detected or not. The feedback is important to maintain the interest of the volunteer in the test. The subject was recommended relax for 2–5 min before beginning the next run. The advantage of using a short-time trial (7 s) in this study is due to potential real-time applications, such as, for example, control of a wheelchair.
The visual stimulus was composed of a light-emitting diode (LED) that illuminates a diffusion board of 4 cm × 4 cm. The LED can flick at different frequencies, from 5 to 65 Hz, with intervals of 5 Hz, comprising 12 frequencies, similarly as done by (Lin et al. 2012). Notice that 50 Hz was not used as stimulation frequency because this is the power line frequency in Argentina. Therefore, the stimuli range covers the three SSVEP bands (low-, medium-, and high-frequency).
In order to evaluate how the electrode montage affects the measurement of SSVEP, 19 channel configurations were evaluated, such as shown in Table 1. The ground electrode (GND) was placed at A2 (see Fig. 1b).
The linked reference consists of a virtual reference obtained by averaging the potentials recorded at the left and right mastoids (LKT) or ears (LKE).
EEG data analysis
First, the EEG was digitally filtered with a Butterworth filter, order 6, bandwidth 3–70 Hz. Then, an EEG segment of 5 s was extracted between t = 2 s and t = 7 s and the magnitude of the frequency components of the signal was calculated based on the discrete Fourier transform (DFT) of the signal x[n], defined as
where F(f) is the magnitude of the signal, Ts is the sampling period, N is the total number of samples of the signal, and f is the frequency.
The SNR was computed in (2) based on the values extracted from Eq. (1). The SNR of the SSVEP at a single channel is defined as the ratio of F(f) to the mean amplitude of the K neighboring frequencies (Wang et al. 2017):
where ∆f is the frequency resolution (0.2 Hz in this study) and K was set to 8 (i.e., four frequencies on each side) (Chen et al. 2014). These parameters F(f) and SNR(f) were calculated using the 19 channels shown in Table 1.
Also, in order to have an overview of the distribution of the most relevant frequencies to each channel, the 12 frequencies (5–65 Hz) were ranked using the SNR value, according to (Müller-Putz et al. 2008, Müller et al. 2015). The frequency with the highest SNR received the score 12, the second the score 11, and so forth. Then, the scores of each frequency were summed up over the subjects (maximum is 144, i.e., 12 subjects × 12 (highest score)). The final result is the selection of a group of frequencies with the best SNR to each channel.
Statistical analysis
The one-way analysis of variance (ANOVA) was applied to the data. The statistical tests were run for each stimulation frequency, and then we analyzed the behavior of the SSVEP from every channel in each frequency. Following, the Tamhane T2 was used for post hoc tests.
Results
Figure 2 shows the mean amplitude of the SSVEP calculated at each stimulation frequency. The mean SNR of the three groups is depicted in Fig. 3.
The best channel from each group is presented in Fig. 4, i.e., Oz-LKT (from the occipital group), Tp9-LKE and Tp10-LKE (from the temporal group), and Fpz-LKT (from the frontal group). Additionally, Fig. 5 shows the result of score evaluation to each channel.
Discussion
In our research, the SSVEP on Oz electrode was acquired for comparison purposes. Generally, the occipital group achieved higher SSVEP amplitudes and higher SNR than the other groups.
The temporal group presented the lowest amplitude values. Within the temporal group, between 5 and 20 Hz, Tp9-RE and Tp10-LE channels showed higher SSVEP amplitudes (Fig. 2). On the other hand, in evaluating the SSVEP amplitudes on the frontal group, no pattern was found, as all channels presented similar amplitudes at each frequency.
Figure 3b shows a peak at 35 Hz and, curiously, an increment of the SNR as the frequency increases. In this case, Tp9-LE achieved the best SNR for the range of 5 to 20 Hz, and Tp10-LKE presented the best SNR between 25 and 65 Hz.
In Fig. 4, Fpz-LKT presented higher SNR between 5 and 35 Hz than for the temporal group. On the other hand, from 40 Hz, the temporal group is a better option. Particularly, Tp10-LKE presented higher SNR values than Tp9-LKE.
The occipital group achieved higher SNR, particularly up to 40 Hz, which was statistically significant (p value < 0.05). On higher stimulation frequencies, this superiority is not so evident and, indeed, some non-hair positions achieved similar SNR.
Our findings are consistent to that found by Norton et al. (2015), which used low stimuli frequency (range of 6–10 Hz), as they reported high SNR for the channel closest to the reference on the ear. In our study, the behind-the-ear (Tp9-LE) position achieved a good SNR in low- and medium-frequency range (5–20 Hz) (see Fig. 3b). In addition, our results show a peak at 35 Hz and, curiously, an increment of the SNR as the frequency increases. On the other hand, Hsu et al. (2016) measured SSVEP on Fpz referenced to left mastoid (Tp9), with stimulation frequency from 13 to 31 Hz. They found similar SSVEP amplitudes to the ones depicted in Fig. 2. Moreover, they reported higher SNR between 17 and 21 Hz, decreasing further. Similarly, we obtained higher SNR between 10 and 20 Hz (Fig. 3c), but we found an additional peak at 35 Hz. However, different of our study, high-frequency stimulation (≥ 35 Hz) was not analyzed in Hsu et al. (2016), where the SSVEP presents a different behavior and the differences among channels are reduced. According to our results, a better result may be obtained if Fpz-LKT is used instead of Fpz-Tp9.
Conclusion
In this work, we presented a study about the characteristics of the amplitudes and SNR of SSVEP elicited on the three frequency ranges (low, medium, and high), which were evaluated on hairless areas. It was found that occipital area in fact presents the best SNR, but only up to 40 Hz. Beyond 40 Hz according our study, this superiority is not observed. On the other hand, the best electrode combinations for measuring SSVEP on hairless areas are obtained with Fpz-Tp9 and Fpz-Tp10 (up to 40 Hz). At frequencies higher than 40 Hz, the temporal positions referenced at the ear are the best options. As a contribution to the state-of-art, our study provides results that can aid in the setup of new SSVEP-based BCIs.
References
Chen X, Chen Z, Gao S, Gao X. A high-ITR SSVEP-based BCI speller. Brain-Computer Interfaces. 2014;1(3–4):181–91.
Di Russo F, Pitzalis S, Aprile T, Spitoni G, Patria F, Stella A, et al. Spatiotemporal analysis of the cortical sources of the steady-state visual evoked potential. Hum Brain Mapp. 2007;28(4):323–34.
Diez PF, Mut VA, Perona EMA, Leber EL. Asynchronous BCI control using high-frequency SSVEP. J Neuroeng Rehabil. 2011;8(1):39.
Fawcett IP, Barnes GR, Hillebrand A, Singh KD. The temporal frequency tuning of human visual cortex investigated using synthetic aperture magnetometry. NeuroImage. 2004;21(4):1542–53.
Floriano A, Diez FP, Freire Bastos-Filho T. Evaluating the influence of chromatic and luminance stimuli on SSVEPs from behind-the-ears and occipital areas. Sensors. 2018;18(2):615.
Hsu HT, Lee IH, Tsai HT, Chang HC, Shyu KK, Hsu CC, … Lee PL. Evaluate the feasibility of using frontal SSVEP to implement an SSVEP-based BCI in young, elderly and ALS groups. IEEE Trans Neural Syst Rehabil Eng. 2016;24(5):603–615.
Lin FC, Zao JK, Tu KC, Wang Y, Huang YP, Chuang CW, … Jung TP. SNR analysis of high-frequency steady-state visual evoked potentials from the foveal and extrafoveal regions of human retina. Proceedings of the 34th IEEE EMBS Conf.; 2012, 28 Aug-1 Sept; San Diego, USA. IEEE; 2012. pp. 1810–1814.
Müller SMT, Bastos-Filho TF, Sarcinelli-Filho M. Monopolar and bipolar electrode settings for SSVEP-based brain-computer interface. J Med Biol Eng. 2015;35(4):482–91.
Muller-Putz GR, Pfurtscheller G. Control of an electrical prosthesis with an SSVEP-based BCI. IEEE Trans Biomed Eng. 2008;55(1):361–4.
Müller-Putz GR, Eder E, Wriessnegger SC, Pfurtscheller G. Comparison of DFT and lock-in amplifier features and search for optimal electrode positions in SSVEP-based BCI. J Neurosci Methods. 2008;168(1):174–81.
Norton JJ, Lee DS, Lee JW, Lee W, Kwon O, Won P, …, Umunna S. Soft, curved electrode systems capable of integration on the auricle as a persistent brain–computer interface. Proc Natl Acad Sci. 2015;112(13):3920–3925.
Pastor MA, Valencia M, Artieda J, Alegre M, Masdeu JC. Topography of cortical activation differs for fundamental and harmonic frequencies of the steady-state visual-evoked responses. An EEG and PET H215O study. Cereb Cortex. 2007;17(8):1899–905.
Sammer G, Blecker C, Gebhardt H, Kirsch P, Stark R, Vaitl D. Acquisition of typical EEG waveforms during fMRI: SSVEP, LRP, and frontal theta. NeuroImage. 2005;24(4):1012–24.
Srinivasan R, Fornari E, Knyazeva MG, Meuli R, Maeder P. fMRI responses in medial frontal cortex that depend on the temporal frequency of visual input. Exp Brain Res. 2007;180(4):677–91.
Vialatte F-B, Maurice M, Dauwels J, Cichocki A. Steady-state visually evoked potentials: focus on essential paradigms and future perspectives. Prog Neurobiol. 2010;90(4):418–38.
Wang YT, Nakanishi M, Wang Y, Wei CS, Cheng CK, Jung TP. An online brain-computer interface based on SSVEPs measured from non-hair-bearing areas. IEEE Trans Neural Syst Rehabil Eng. 2017;25(1):14–21.
Zhu D, Bieger J, Molina GG, Aarts RM. A survey of stimulation methods used in SSVEP-based BCIS. Comput Intell Neurosci. 2010:1.
Acknowledgments
The authors acknowledge the technical support from the Federal University of Espirito Santo (UFES/Brazil) and the National University of San Juan (Argentina).
Funding
This study was financed in part by the CAPES/Brazil - Finance Code 88887.095636/2015-01.
Author information
Authors and Affiliations
Corresponding author
Ethics declarations
The study was approved by the Ethics Committee of the School of Exact, Physical and Natural Sciences of the National University of San Juan Argentina (act #7).
Additional information
Publisher’s note
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Rights and permissions
About this article
Cite this article
Floriano, A., Carmona, V.L., Diez, P.F. et al. A study of SSVEP from below-the-hairline areas in low-, medium-, and high-frequency ranges. Res. Biomed. Eng. 35, 71–76 (2019). https://doi.org/10.1007/s42600-019-00005-2
Received:
Accepted:
Published:
Issue Date:
DOI: https://doi.org/10.1007/s42600-019-00005-2