Brain-computer interface (BCI) technology aims at helping patients with severe neurofunctional disabilities to communicate with outer world without using the natural output channels of the brain. This technology is generally based on features extracted from EEG recordings and the designing of the classifier. Most of these neural features are evoked during visual stimulation paradigms such as the P300 matrix speller paradigm and the steady-state evoked potential paradigm (SSVEP) . However, a number of BCI end-users in complete paralysis state, loss of gaze control when performing visual BCI paradigms, thus new BCI paradigms only relying on brain response to auditory stimulation need to be established.
Recently, auditory BCI is usually performed as a P300 oddball paradigm; that is, visual stimuli are replaced by audio stimuli such as bells, buzzing, tones and spoken words or numbers. Halder et al.  proposed an auditory three stimulus oddball paradigm in which a series of frequent standard tones and two targets randomized in sequences of up to seven stimuli played to subjects. The results showed that the average accuracy of 78.5% was achieved. Höhne and Tangermann presented a streaming paradigm for auditory spelling . In this paradigm, the letters were presented in a constant auditory stream. The subject focused their attention to the target letter within this stream, the result showed that the average accuracy of 41%. Kleih et al.  proposed an auditory spelling paradigm the WIN-speller. In the WIN-speller letters were grouped by words, such as the word KLANG representing the letters A, G, K, L, and N. Thereby, the decoding step between perceiving a code and translating it to the stimuli it represents became superfluous. The average accuracy was 84%.
In this paper, we proposed a modified auditory oddball paradigm, in which the spoken digits (voices) are used to auditory stimulus. The subject need make a response to target digits and ignore non-target digits in experiment. Superposed average method was used to exact feature, fisher discriminant analysis was used to the target detection. With the increasing of trails, the EEG response to target voice could have already reached a discriminable level before all trials were presented. To speed up the decision, a stopping criterion should be set to terminate the stimulus repeating, so the Dynamic Stopping Criterion (DSC) was used as the experimental conditions to stop.
2.1. Subjects and Data Recording
Six healthy subjects, age 20 to 27 years, participated in the experiment. The experimental procedure was explained in detail to each subject. None of the subjects had a history of hearing loss and were all able to clearly hear and identify the different digits used in the experiment.
A standard EEG cap (Compumedics Neuroscan, USA) with 64 surface electrodes was used for recording EEG signals. EEG data were collected from Fz, FCz, Cz, CPz, Pz, Oz and sampled at 1000 Hz. The SynAmps 2 amplifier and data acquisition system (Com- pumedics Neuroscan, USA) was used for signal conditioning and data acquisition (band-width 0.05 - 200 Hz). All electrode impedances were kept below 5 KΩ during data recording.
2.2. Experimental Procedure
In this experiment, two mono stimulus sequences were played simultaneously. The sequence played in the left ear consisted of four spoken digits in Chinese, i.e., 1, 2, 3, 4. The sequence played in the right ear consisted of four spoken digits in Chinese, i.e., 5, 6, 7, 8. One target and seven non-target stimuli were delivered in each trail randomly. One trail of the sequence presented in the ear is shown in Figure 1. All voices were presented for 200 ms with a randomized inter stimulus interval (ISI) of 250 - 450 ms. The loudness was set to 75 dB sound pressure level (SPL). Each sequence consisted of 40 trails. The two sequences differed in the direction from which they were presented to the subject (either the right or left channel of stereo headphones) simultaneously. The task consisted of two sessions, in each of which the subject was requested to attend to a sequence in one direction and to count the target stimuli in the attended sequence. Before each task, the participant was asked a randomly selected “yes/no” question. If the subject selected “yes”, he was supposed to attend to left target (one of 1 - 4), and if the subject selected “no”, to instead attend to right target (one of 5 - 8).
2.3. Data Analysis
The raw EEG data were filtered using a 0.5 - 10 Hz digital band-pass filter. The data epochs were extracted from 200 ms before the stimulus-onset to 800 ms after the stimulus-onset. Then, all epochs were referred to the mean amplitude of the prestimulus baseline. There were 40 trials each task, with eight stimuli in each trial, 320 epochs were extracted from each task. To determine EEG responses differences between the target and non-target, grand average analysis was used to extract the features. Fisher discriminant analysis was adopted to discriminate between EEG responses for target and non-target.
The DSC algorithm is illustrated in Figure 2. Fisher discriminant analysis was used with this algorithm, the classifier responses for target and non-target digits were grouped. The training data consisted of 20 target digits for each of which twenty trails were measured. Thus, the non-target group would consist of classifier responses to 140 non-target digits while the target group would consist of classifier responses to 20 target digits. Kernel density estimates using a Gaussian kernel  were calculated for each group to estimate the probability density function of the likelihood. These participant-specific likelihoods are the only requirement for the algorithm to control data collection in real time. The method for updating the probability that a digit is the target
Figure 1. One trail of the sequence.
Figure 2. DSC algorithm.
digit based on previous classifier responses is based on Bayes rule.
where is the current estimate of the digit’s probability of being the target given all of the classifier responses, , observed previously; is the prior probability for the digit; is the likelihood of the classifier responses; and is the probability of the classifier responses. For an online algorithm, the posterior probabilities need to be updated after each stimulus. Hence, sequential updating of the digit probabilities was carried out using the following:
where is the current estimate of the digit’s probability of being the target given all of the classifier responses observed previously; is the likelihood of the current classifier response, given that the digit was/was not in the currently presented set of digits; and the denominator normalizes the updated probabilities by dividing by the sum over all digits probabilities.
After each Bayesian update, the spoken digit probabilities are compared to a threshold to determine if the target digit can be selected. The threshold indicates the confidence that the correct digit has been chosen, and in this study, it was set to 90%. Once a target digit is selected, the process begins again for the next target digit by reinitializing all of the digit probabilities.
3.1. Auditory ERP
Figure 3 shows one an example of average ERP response to target stimuli and non- target stimuli. A negative peak with latency around the 100 - 200 ms period (N200) was showed in the target stimuli response. In addition, the P300 component was elicited by target stimuli, but absent in response to non-target stimuli.
3.2. Results of DSC Algorithm
DSC algorithm was used to establish the dynamic model, and the off-line data were simulated, and the adaptive stopping criterion was obtained. Figure 4 is the distribution of target and non-target probability density using kernel algorithm to estimate the
Figure 3. Grand average waveform.
Figure 4. Likelihoods of classifier response.
output of the classifier results, in which the dotted line represents the output possibility of target digital stimulation while solid line represent the non-target. Figure 5 shows stopping criteria probability curve, it is apparent that target stimuli are able to be selected with fewer trails. The comparison of communication rate between DSC algorithm and traditional static algorithm is presented in Figure 6. In this part, the communication rate was calculated using 10 trails. We found that the communication rate based on DSC condition can exceed the result of traditional static algorithm.
Figure 5. DSC model.
Figure 6. The comparison of communication rate between DSC algorithm and traditional static algorithm.
In this paper we presented a novel auditory BCI paradigm and acquired the EEG data from six subjects. Dynamic stopping standard based on Bayes algorithm was applied for the experiments data. In our DSC algorithm, the threshold was set as the probability of target detection and was estimated from training data, which is a reasonable prediction for final detection accuracy. The results showed that the target stimuli in the paradigm evoked obvious N200 and P300 response. Adaptive way in terms of time performance was superior to the traditional static way with higher accuracy. In a short word, the DSC algorithm of deciding the optimal number of averaging trials can improve the accuracy and communication rate of an auditory BCI.
In conclusion, the result of experiments suggests that this auditory paradigm and DSC algorithm are feasible for an auditory BCI system. Thus, it is possible to further implement an auditory BCI system with high accuracy and communication rate.
This study was supported by the National Natural Science Foundation of China, No. 31300818 and the Foundation of Hebei Province Department of Education, No. QN2016097.
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 Halder, S., Rea, M., Andreoni, R., et al.. (2010) An Auditory Oddball Brain-Computer Interface for Binary Choices. Clinical Neurophysiology, 121, 516-523. http://dx.doi.org/10.1016/j.clinph.2009.11.087
 Höhne, J. and Tangermann, M. (2014) Towards User-Friendly Spelling with an Auditory Brain-Computer Interface: The Charstreamer Paradigm. PloS One, 9, e98322. http://dx.doi.org/10.1371/journal.pone.0098322
 Kleih, S.C., Herweg, A., Kaufmann, T., et al.. (2015) The WIN-Speller: A New Intuitive Auditory Brain-Computer Interface Spelling Application. Frontiers in Neuroscience, 9. http://dx.doi.org/10.3389/fnins.2015.00346