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<journal-id journal-id-type="publisher-id">Front. Neurosci.</journal-id>
<journal-title>Frontiers in Neuroscience</journal-title>
<abbrev-journal-title abbrev-type="pubmed">Front. Neurosci.</abbrev-journal-title>
<issn pub-type="epub">1662-453X</issn>
<publisher>
<publisher-name>Frontiers Media S.A.</publisher-name>
</publisher>
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<article-meta>
<article-id pub-id-type="doi">10.3389/fnins.2024.1406814</article-id>
<article-categories>
<subj-group subj-group-type="heading">
<subject>Neuroscience</subject>
<subj-group>
<subject>Original Research</subject>
</subj-group>
</subj-group>
</article-categories>
<title-group>
<article-title>A multimodal dataset for investigating working memory in presence of music: a pilot study</article-title>
</title-group>
<contrib-group>
<contrib contrib-type="author">
<name><surname>Khazaei</surname> <given-names>Saman</given-names></name>
<xref ref-type="aff" rid="aff1"><sup>1</sup></xref>
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</contrib>
<contrib contrib-type="author">
<name><surname>Parshi</surname> <given-names>Srinidhi</given-names></name>
<xref ref-type="aff" rid="aff2"><sup>2</sup></xref>
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<contrib contrib-type="author">
<name><surname>Alam</surname> <given-names>Samiul</given-names></name>
<xref ref-type="aff" rid="aff2"><sup>2</sup></xref>
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<contrib contrib-type="author">
<name><surname>Amin</surname> <given-names>Md. Rafiul</given-names></name>
<xref ref-type="aff" rid="aff2"><sup>2</sup></xref>
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<contrib contrib-type="author" corresp="yes">
<name><surname>Faghih</surname> <given-names>Rose T.</given-names></name>
<xref ref-type="aff" rid="aff1"><sup>1</sup></xref>
<xref ref-type="aff" rid="aff2"><sup>2</sup></xref>
<xref ref-type="corresp" rid="c001"><sup>&#x0002A;</sup></xref>
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<aff id="aff1"><sup>1</sup><institution>Department of Biomedical Engineering, New York University</institution>, <addr-line>New York, NY</addr-line>, <country>United States</country></aff>
<aff id="aff2"><sup>2</sup><institution>Department of Electrical and Computer Engineering, University of Houston</institution>, <addr-line>Houston, TX</addr-line>, <country>United States</country></aff>
<author-notes>
<fn fn-type="edited-by"><p>Edited by: S. Abdollah Mirbozorgi, University of Alabama at Birmingham, United States</p></fn>
<fn fn-type="edited-by"><p>Reviewed by: Kyle Jaquess, Juniata College, United States</p>
<p>Xu Zhang, Boston Children&#x00027;s Hospital and Harvard Medical School, United States</p></fn>
<corresp id="c001">&#x0002A;Correspondence: Rose T. Faghih <email>rfaghih&#x00040;nyu.edu</email></corresp>
</author-notes>
<pub-date pub-type="epub">
<day>19</day>
<month>06</month>
<year>2024</year>
</pub-date>
<pub-date pub-type="collection">
<year>2024</year>
</pub-date>
<volume>18</volume>
<elocation-id>1406814</elocation-id>
<history>
<date date-type="received">
<day>25</day>
<month>03</month>
<year>2024</year>
</date>
<date date-type="accepted">
<day>30</day>
<month>05</month>
<year>2024</year>
</date>
</history>
<permissions>
<copyright-statement>Copyright &#x000A9; 2024 Khazaei, Parshi, Alam, Amin and Faghih.</copyright-statement>
<copyright-year>2024</copyright-year>
<copyright-holder>Khazaei, Parshi, Alam, Amin and Faghih</copyright-holder>
<license xlink:href="http://creativecommons.org/licenses/by/4.0/"><p>This is an open-access article distributed under the terms of the Creative Commons Attribution License (CC BY). The use, distribution or reproduction in other forums is permitted, provided the original author(s) and the copyright owner(s) are credited and that the original publication in this journal is cited, in accordance with accepted academic practice. No use, distribution or reproduction is permitted which does not comply with these terms.</p></license>
</permissions>
<abstract>
<sec>
<title>Introduction</title>
<p>Decoding an individual&#x00027;s hidden brain states in responses to musical stimuli under various cognitive loads can unleash the potential of developing a non-invasive closed-loop brain-machine interface (CLBMI). To perform a pilot study and investigate the brain response in the context of CLBMI, we collect multimodal physiological signals and behavioral data within the working memory experiment in the presence of personalized musical stimuli.</p>
</sec>
<sec>
<title>Methods</title>
<p>Participants perform a working memory experiment called the <italic>n</italic>-back task in the presence of calming music and exciting music. Utilizing the skin conductance signal and behavioral data, we decode the brain&#x00027;s cognitive arousal and performance states, respectively. We determine the association of oxygenated hemoglobin (HbO) data with performance state. Furthermore, we evaluate the total hemoglobin (HbT) signal energy over each music session.</p>
</sec>
<sec>
<title>Results</title>
<p>A relatively low arousal variation was observed with respect to task difficulty, while the arousal baseline changes considerably with respect to the type of music. Overall, the performance index is enhanced within the exciting session. The highest positive correlation between the HbO concentration and performance was observed within the higher cognitive loads (3-back task) for all of the participants. Also, the HbT signal energy peak occurs within the exciting session.</p>
</sec>
<sec>
<title>Discussion</title>
<p>Findings may underline the potential of using music as an intervention to regulate the brain cognitive states. Additionally, the experiment provides a diverse array of data encompassing multiple physiological signals that can be used in the brain state decoder paradigm to shed light on the human-in-the-loop experiments and understand the network-level mechanisms of auditory stimulation.</p>
</sec></abstract>
<kwd-group>
<kwd>multimodal dataset</kwd>
<kwd>brain-machine interface (BMI)</kwd>
<kwd>music</kwd>
<kwd>closed-loop systems</kwd>
<kwd>working memory</kwd>
<kwd>decoder design</kwd>
<kwd>cognitive arousal</kwd>
<kwd>cognitive performance</kwd>
</kwd-group>
<counts>
<fig-count count="8"/>
<table-count count="2"/>
<equation-count count="7"/>
<ref-count count="64"/>
<page-count count="15"/>
<word-count count="9445"/>
</counts>
<custom-meta-wrap>
<custom-meta>
<meta-name>section-at-acceptance</meta-name>
<meta-value>Neural Technology</meta-value>
</custom-meta>
</custom-meta-wrap>
</article-meta>
</front>
<body>
<sec sec-type="intro" id="s1">
<title>1 Introduction</title>
<p>Recent advances in physiological signal measurement techniques enlighten the non-invasive closed-loop brain-machine interface (BMI) design. Such signals can be used to infer individuals&#x00027; underlying cognitive brain states and regulate them via non-invasive interventions such as music (Fekri Azgomi et al., <xref ref-type="bibr" rid="B16">2023</xref>). The human brain state regulation via musical stimuli would have profound applications in closed-loop BMI (CLBMI) (Ehrlich et al., <xref ref-type="bibr" rid="B14">2019</xref>), neural rehabilitation (Ottonello et al., <xref ref-type="bibr" rid="B35">2019</xref>; Salas et al., <xref ref-type="bibr" rid="B40">2019</xref>), and cognitive impairment treatments (Ray and Mittelman, <xref ref-type="bibr" rid="B38">2017</xref>). As an instance of such applications, the well-known Yerkes-Dodson law, a.k.a. the inverted-U law, explains that optimal cognitive performance can be achieved by setting the cognitive arousal within a moderate level (Yerkes, <xref ref-type="bibr" rid="B60">1907</xref>; Yerkes and Dodson, <xref ref-type="bibr" rid="B61">1908</xref>). This inspires us to design a pilot study involving a human-subject working memory experiment in the presence of arousing music stimuli. We record the multimodal physiological and behavioral signals to investigate the feasibility of regulating one&#x00027;s cognitive arousal and performance via background music with calming and exciting contents.</p>
<p>Several studies have explored how the introduction of music can impact cognitive functioning (Parshi et al., <xref ref-type="bibr" rid="B36">2019</xref>; Khazaei et al., <xref ref-type="bibr" rid="B27">2021</xref>). Multiple studies have used music to influence driving performance (&#x000DC;nal et al., <xref ref-type="bibr" rid="B46">2012</xref>, <xref ref-type="bibr" rid="B45">2013</xref>). In Huang and Shih (<xref ref-type="bibr" rid="B24">2011</xref>) and Kuschpel et al. (<xref ref-type="bibr" rid="B29">2015</xref>), the positive effect of music on concentration and the effectiveness of using music to reduce cognitive stress in closed-loop systems have been shown. In our designed working memory experiment, two types of music are employed, namely, calming and exciting music. Notably, the calming and exciting music selected by participants such that the calming and exciting components are supposed to replicate the low and high arousing conditions, respectively. Here, we mainly focus on cognitive performance and arousal in the presence of calming and exciting music.</p>
<p>Cognitive performance is a hidden brain state that demonstrates the general performance of one&#x00027;s cognitive functions (Khazaei et al., <xref ref-type="bibr" rid="B28">2024</xref>). The cognitive functions of humans can be divided into two groups, namely, basic cognitive functions and higher-level cognitive functions. Working memory is one of the basic cognitive functions that provides temporary storage and allows the manipulation of information (Baddeley, <xref ref-type="bibr" rid="B5">1992</xref>). Here, the <italic>n</italic>-back task serves as a cognitive task of interest, which encourages working memory usage by inducing different cognitive loads (von Janczewski et al., <xref ref-type="bibr" rid="B48">2021</xref>; Fekri Azgomi et al., <xref ref-type="bibr" rid="B16">2023</xref>). Decoding the underlying cognitive performance in a continuous manner is one of the challenges in this paradigm, which can be addressed by employing informative data and applying decoding approaches. One of the most accessible and informative data in this context would be the behavioral data recorded during the cognitive task of interest. We consider the sequence of responses as well as the reaction time of participants as the available behavioral observation and quantify the cognitive performance using Bayesian filters within an expectation-maximization (EM) framework (Amin et al., <xref ref-type="bibr" rid="B2">2021</xref>; Khazaei et al., <xref ref-type="bibr" rid="B27">2021</xref>).</p>
<p>Another hidden brain state that may have impact on cognitive performance is the underlying arousal state. In particular, the amygdala plays a crucial role in connecting arousal to memory formation (McGaugh, <xref ref-type="bibr" rid="B32">2004</xref>). Typically, the arousal state is linked to the degree of physiological alertness (Cudo et al., <xref ref-type="bibr" rid="B11">2018</xref>), and variation in arousal is mainly due to the exogenous and endogenous stimulation, which can be accompanied by neural, hormonal, and other biochemical changes (Hobson and Lindsley, <xref ref-type="bibr" rid="B22">1988</xref>). Specifically, previous research on the autonomic nervous system (ANS) inference presents the electrodermal activity (EDA) as an informative measurement of cognitive arousal (Wickramasuriya et al., <xref ref-type="bibr" rid="B57">2018</xref>; Wickramasuriya and Faghih, <xref ref-type="bibr" rid="B54">2020a</xref>). In particular, the skin conductance (SC) signal (a measure of EDA) reflects the sweat secretions process, which is firmly linked to the underlying ANS activity inside the brain (Amin and Faghih, <xref ref-type="bibr" rid="B3">2022</xref>). The variation in skin conductivity can be used as a quantitative index of arousal during a cognitive task (Khazaei et al., <xref ref-type="bibr" rid="B27">2021</xref>).</p>
<p>When it comes to designing a CLBMI architecture for human cognitive functions, it would be crucial to investigate how the environment and interactions affect the cognitive capacity of the human operator (Cain, <xref ref-type="bibr" rid="B10">2007</xref>). To gain a better insight into BMI design procedures and analyze how different regions of the brain react to the stimuli, neuroimaging methods with relatively high spatial resolution can play a crucial role. These neuroimaging methods include but are not limited to magnetoencephalography (MEG), electroencephalography (EEG), functional magnetic resonance imaging (fMRI), and functional near-infrared spectroscopy (fNIRS) (Berka et al., <xref ref-type="bibr" rid="B8">2007</xref>; Wendel et al., <xref ref-type="bibr" rid="B49">2009</xref>; Baldwin and Penaranda, <xref ref-type="bibr" rid="B6">2012</xref>; Fyshe et al., <xref ref-type="bibr" rid="B18">2012</xref>). The fNIRS is a relatively new neuroimaging technique that can show significant spatiotemporal changes for memory tasks in the prefrontal cortex (PFC) (Hoshi et al., <xref ref-type="bibr" rid="B23">2003</xref>). Also, the fNIRS has a higher spatial resolution than EEG, and it is practical for unobtrusive applications. In the designed experiment, we use the fNIRS and collect data from the prefrontal cortex (PFC) and occipital (OC) areas of the participant.</p>
<p>Multiple studies investigate the brain neural activity in the course of <italic>n</italic>-back tasks via fNIRS (Ayaz et al., <xref ref-type="bibr" rid="B4">2007</xref>; Roy et al., <xref ref-type="bibr" rid="B39">2013</xref>; Fishburn et al., <xref ref-type="bibr" rid="B17">2014</xref>; Herff et al., <xref ref-type="bibr" rid="B21">2014</xref>). In Ayaz et al. (<xref ref-type="bibr" rid="B4">2007</xref>) and Herff et al. (<xref ref-type="bibr" rid="B21">2014</xref>), the cognitive loads and hemodynamic responses association is considered, and the hemodynamic responses are classified accordingly. Another study considers the <italic>n</italic>-back tasks and presents the fNIRS sensitivity to cognitive load and transitioning from a resting state to a task (Fishburn et al., <xref ref-type="bibr" rid="B17">2014</xref>). While the link between the cognitive load of <italic>n</italic>-back task and corresponding hemodynamic responses is studied vastly, the study of association between the continuous cognitive performance signal and fNIRS data in the presence of music is investigated relatively sparsely. Previous studies such as Meidenbauer et al. (<xref ref-type="bibr" rid="B33">2021</xref>) and Struckmann et al. (<xref ref-type="bibr" rid="B44">2021</xref>) have considered the distinctive measures of cognitive performance, like the number of correct/incorrect responses and reaction time, and investigated the hemodynamic response data association. While this set of measurements can be an informative index of performance, it merely presents a distinct measure of performance, and might not fully capture the underlying dynamic of the brain&#x00027;s cognitive state (Basu et al., <xref ref-type="bibr" rid="B7">2023</xref>). In this research, we study the association between the oxygenated hemoglobin (HbO) concentration and the continuous performance state decoded from behavioral data. In particular, we employ a Bayesian-based performance decoder that accounts for the underlying dynamic of this brain state, and tracks its continuous trajectory using behavioral data. Also, we evaluate the energy of total hemoglobin (HbT) signal within each music session.</p>
<p>To summarize, the primary purpose of this pilot study is to provide a multimodal database and examine the viability of using music as an intervention. The database includes a diverse array of data encompassing multiple physiological measurements to shed light on the human-subject experiments using music intervention. The available signals include SC data, electrocardiogram (ECG), skin surface temperature, respiration, photoplethysmography (PPG), functional near-infrared spectroscopy (fNIRS), electromyogram (EMG), de-identified facial expression scores, sequence of correct/incorrect responses, and reaction time recorded during the <italic>n</italic>-back task. In this research, we focus on cognitive performance and arousal, and we present how the HbO concentration is correlated with cognitive performance. Also, the energy of the HbT signal is evaluated with respect to each music. We represent how the arousal and performance indices vary with respect to task difficulty and music type. Then, we discuss our findings and provide a summary of our approach, followed by future directions of this research.</p>
</sec>
<sec sec-type="materials and methods" id="s2">
<title>2 Materials and methods</title>
<sec>
<title>2.1 Cognitive task overview</title>
<p>We designed the experiment centered on the working memory task called the <italic>n</italic>-back task (Herff et al., <xref ref-type="bibr" rid="B21">2014</xref>; Shin et al., <xref ref-type="bibr" rid="B43">2018</xref>). Here, the participant was shown a series of alphabets as stimuli, and the participant had to identify if the most recently displayed alphabet was the same as the alphabet displayed at the <italic>n</italic><sup><italic>th</italic></sup> previous iteration (Herff et al., <xref ref-type="bibr" rid="B21">2014</xref>; Shin et al., <xref ref-type="bibr" rid="B43">2018</xref>; Khazaei et al., <xref ref-type="bibr" rid="B27">2021</xref>). In this type of experiment, the cognitive workload increases with <italic>n</italic>, and the participant has to recall more of the stimuli with higher values of <italic>n</italic>. Here, the experiment was conducted within two sessions; session one was accompanied by calming background music, and session two was accompanied by exciting background music. The participants were requested to share their own music with &#x0201C;calming&#x0201D; and &#x0201C;exciting&#x0201D; content to be played during the experiment. We employ this strategy first to enhance the ecological validity, as people often listen to their own music (&#x000DC;nal et al., <xref ref-type="bibr" rid="B46">2012</xref>); secondly, this strategy aims to ensure that any behavior observed in brain activity is not attributable to disliking the music (&#x000DC;nal et al., <xref ref-type="bibr" rid="B46">2012</xref>). Finally, this strategy enables us to incorporate the person-specific closed-loop system with personalized intervention. We delivered the background music via an external speaker. The music stimulation started at the beginning of each session, and it continuously played until the end of the session (i.e., 964 s). We performed the experiment in a closed experiment room to minimize the impact of external variables. Each session in the experiment included 8 blocks for each type of <italic>n</italic>-back task (2 types of <italic>n</italic>-back task &#x000D7; 8 = 16 blocks within one session). Hence, we have 16 blocks at each session and 32 blocks during the whole experiment. We decided to keep the experimental duration time for a bit longer than half an hour. This ensures that the collected SC signals do not show a lot of relative drift over time due to the accumulation of sweat or shift in the position of electrodes.</p>
<p>Each block includes 5 s instruction followed by 22 trial windows in which a letter stimulus was displayed for 0.5 s and a cross was presented for 1.5 s, which resulted in a total 2 s trial window that participant could deliver the response via Chronos Keypad. Thus, the total duration of each task block was 49 s (5&#x0002B;22 &#x000D7; 2 &#x0003D; 49). In each task block, 30% of the stimuli were a target. The task block of each <italic>n-</italic>back task was randomized. At the end of each block, a 10 s &#x0201C;RELAX&#x0201D; segment was presented where a resting cross was displayed on the screen. After 8 task blocks (the halfway mark for each session), a 20 s &#x0201C;RELAX&#x0201D; section was presented where a resting cross is displayed on a smart 65 inch TV screen connected via HDMI to a laptop. The duration of each session was 964 s, which is &#x0007E;16 min. After each session, there was a 2 min relaxation break in which the participant was allowed to relax. A resting cross was displayed on the screen during this time. <xref ref-type="fig" rid="F1">Figure 1</xref> describes the timing of one session with randomized trials. The experiment took a total of 2, 168 s (calming session duration 964&#x0002B; intersession break 120&#x0002B; exciting session duration 964&#x0002B; after the session rest period 120 &#x0003D; 2, 168 s), i.e., approximately half an hour. Participants were comfortably seated with the attached non-invasive sensors, and a display screen was placed &#x0007E;1&#x02013;2 m in front of them. The only required movement was pressing one of two buttons on a Chronos Keypad: the target and non-target buttons. Participants were required to press one of the buttons for each stimulus displayed.</p>
<fig id="F1" position="float">
<label>Figure 1</label>
<caption><p>The experimental setup for multimodal physiological data collection from a female participant during the <italic>n</italic>-back task. An overview of the physiological sensors&#x00027; placement during the <italic>n</italic>-back task session.</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0001.tif"/>
</fig>
</sec>
<sec>
<title>2.2 Experimental procedures</title>
<p>The experimental procedures in this study were approved by the institutional review board at the University of Houston, TX, USA (STUDY00002013). Only participants who were 18 years or older and were able to provide consent were permitted to participate in this experiment. Anyone suffering from known cardiac ailments or psychological disorders was excluded. Adults unable to consent, anyone below age 18, pregnant women, prisoners, students whose grades may be influenced and, economically and/or educationally disadvantaged persons were excluded from the study. A total number of 11 healthy participants (five male and six female) between the ages of 22&#x02013;25 participated in this study. Six participants with measurement error, data corruption, and small modalities were removed. Hence, the studied sample size here is five (two male and three female) while the de-identified facial expression scores for four participants are included in the main database. All identifiable aspects of the data were removed to ensure privacy. This includes any data that may be used to identify the original participants. The experiment focused on collecting multimodal data to investigate the feasibility of using music as an intervention. The experiment was conducted with a multitude of sensors. We describe the sensors applied in the following subsections.</p>
<sec>
<title>2.2.1 Functional near infrared spectroscopy</title>
<p>The near-infrared region (620&#x02013;1, 000 nm) of the electromagnetic spectrum is scattered by biological tissue but absorbed by hemoglobin (Villringer et al., <xref ref-type="bibr" rid="B47">1993</xref>); by measuring the amount of absorbed near-infrared light and using the modified Beer-Lambert law (Sassaroli and Fantini, <xref ref-type="bibr" rid="B42">2004</xref>), fNIRS measures changes in oxygenated hemoglobin (HbO), deoxygenated hemoglobin (HbR), and total hemoglobin (HbT). The fNIRS demonstrates excellent spatial resolution but relatively poor temporal resolution (Fazli et al., <xref ref-type="bibr" rid="B15">2012</xref>). The spatial resolution of fNIRS can be used to obtain the functional connectivity map of the brain (Santosa et al., <xref ref-type="bibr" rid="B41">2018</xref>). The fNIRS optodes can be placed according to the international 10 &#x02212; 5 system (Oostenveld and Praamstra, <xref ref-type="bibr" rid="B34">2001</xref>), and readings can be taken from the whole scalp. The fNIRS channels placed during this experiment collected hemodynamic data from the PFC and the OC areas of the brain. In particular, the employed fNIRS sensor is <italic>NIRSport 2</italic>, configured as shown in <xref ref-type="fig" rid="F4">Figure 4</xref>. The sources (S) and detectors (D) were placed according to the positions depicted in the figure (on a head cap worn by the participants). There were 16 sources and 14 detectors located on PFC and OC areas, and signals were recorded from 44 channels. The sampling frequency is 7.81 Hz.</p>
</sec>
<sec>
<title>2.2.2 Electrocardiogram</title>
<p>ECG is the electrogram of the heart. Specifically, it is the electrical signal that correlates with the expansion and contraction of the heart muscle, and it is used to detect heart problems such as arrhythmia. In our experiment, ECG sensors were placed on the torso of the participants, as shown in <xref ref-type="fig" rid="F2">Figure 2</xref>. We collected the ECG data with the <italic>MP160 BioPac</italic> system and the <italic>BioNomadix</italic> wireless devices. The <italic>EL503 BioPac</italic> general-purpose disposable electrodes were used on the torso region. The sampling frequency is 2, 000 Hz.</p>
<fig id="F2" position="float">
<label>Figure 2</label>
<caption><p>The electrocardiogram (ECG) and respiration sensors configuration. Electrode placements of Electrocardiogram sensors (indicated by blue lines) and respiration belt on the front torso (shown with black lined indicators).</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0002.tif"/>
</fig>
</sec>
<sec>
<title>2.2.3 Respiration</title>
<p>The respiration belt sensor of the <italic>MP160 BioPac</italic> system was placed on the abdomen of the participant in contact with the torso as described in the <italic>BioPac</italic> manual and depicted in <xref ref-type="fig" rid="F2">Figure 2</xref>. The contraction and expansion of the lungs are captured by the belt. The sampling frequency is 2, 000 Hz.</p>
</sec>
<sec>
<title>2.2.4 Skin surface temperature</title>
<p>As portrayed in <xref ref-type="fig" rid="F3">Figure 3</xref>, the skin surface temperature data is collected from the minimus digitus (little finger) of the non-dominant hand using the MP160 BioPac system with the <italic>BioNomadix</italic> wearable device coupled with the <italic>BN-TEMP-A-XDCR BioPac</italic> sensor. Also, the <italic>Empatica E4</italic> wearable wristband worn by the participant collected skin temperature data. The sampling frequency for BioPac is 2, 000 Hz, and for <italic>Empatica E4</italic> is 4 Hz.</p>
<fig id="F3" position="float">
<label>Figure 3</label>
<caption><p>The electrodermal activity (EDA), photoplethysmography (PPG), and electromyogram (EMG) sensors configuration. <bold>(A)</bold> Sensor placements on the hand for PPG, EDA, and Skin Temperature. <bold>(B)</bold> EMG sensors were placed on the participant&#x00027;s trapezius muscles to detect stress states from muscle movements.</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0003.tif"/>
</fig>
</sec>
<sec>
<title>2.2.5 Electrodermal activity</title>
<p>Sensors from both the <italic>MP160 BioPac</italic> system and <italic>Empatica E4</italic> wearable wristband were used to record EDA. The <italic>Empatica E4</italic> wearable wristband was worn on the wrist by the participant. The <italic>M160 BioPac</italic> system sensors were placed over the digitus quartus manus (ring finger) and digitus medius manus (middle finger) of the participant, as shown in <xref ref-type="fig" rid="F3">Figure 3</xref>. The BioPac EL507 disposable electrodes are used as the leads for EDA. The sampling frequency for <italic>BioPac</italic> is 2, 000 Hz, and for <italic>Empatica E4</italic> is 4 Hz.</p>
</sec>
<sec>
<title>2.2.6 Photoplethysmography</title>
<p>Wearable physiological sensor <italic>BN-PULSE-XDCR</italic> coupled with <italic>BioNomadix</italic> unit is placed on the digitus secundus manus (index finger) of the non-dominant hand (<xref ref-type="fig" rid="F3">Figure 3</xref>) to obtain PPG data with the <italic>M160 BioPac</italic> system. Also, the <italic>Empatica E4</italic> wearable wristband (worn on the wrist) collected PPG data. PPG is an optical means to detect changes in blood volume in a tissue. PPG is generally used to monitor cardiac health and heart rate. The sampling frequency for the <italic>BioPac</italic> system is 2, 000 Hz. The sampling frequency for the <italic>Empatica E4</italic> wristband is 4 Hz.</p>
</sec>
<sec>
<title>2.2.7 Electromyogram</title>
<p>As depicted in <xref ref-type="fig" rid="F3">Figure 3</xref>, sensors from the <italic>MP160 BioPac</italic> system are placed on the participant&#x00027;s trapezius muscle for EMG recordings. The <italic>EL503</italic> general-purpose electrodes are used in this case. EMG is used to detect the health of muscles and the nerves that control them. In this experiment, the placement of EMG electrodes provides data about the tensing of a participant&#x00027;s shoulders and back while performing a cognitive stress task. The sampling frequency is 2, 000 Hz.</p>
</sec>
<sec>
<title>2.2.8 Facereader</title>
<p>Facial expression data were recorded via a dedicated camera. Then, the facial expression scores were obtained using Face Reader software. De-identified facial expression scores for four participants are included in the multimodal dataset.</p>
</sec>
<sec>
<title>2.2.9 Synchronization and behavioral data recording</title>
<p>The experimental design, timing, and triggers for different equipment have been executed using the <italic>Chronos</italic> input device and <italic>E-Prime</italic> software. The <italic>Chronos</italic> and <italic>E-Prime</italic> offer a script-free way to synchronize data with task events. The participant&#x00027;s behavioral signals, including the number of correct and incorrect responses along with reaction times, were collected.</p>
</sec>
</sec>
<sec>
<title>2.3 Data analysis methods</title>
<p>To decode the cognitive state of interest, we employ the Bayesian filtering approach within the expectation-maximization framework. We utilize the SC signal collected via MP160 BioPac system to decode a cognitive arousal state. This is done by considering the arousal events occurrences and their amplitudes as the available observation (Wickramasuriya et al., <xref ref-type="bibr" rid="B57">2018</xref>, <xref ref-type="bibr" rid="B50">2019</xref>, <xref ref-type="bibr" rid="B51">2022</xref>; Wickramasuriya and Faghih, <xref ref-type="bibr" rid="B52">2019a</xref>,<xref ref-type="bibr" rid="B53">b</xref>, <xref ref-type="bibr" rid="B54">2020a</xref>,<xref ref-type="bibr" rid="B55">b</xref>). Also, to quantify the hidden performance state, we use the sequence of correct and incorrect responses and the reaction time as binary and continuous observations, respectively (Prerau et al., <xref ref-type="bibr" rid="B37">2009</xref>).</p>
<sec>
<title>2.3.1 Arousal state estimation</title>
<p>The arousal state (<italic>x</italic><sub><italic>j</italic></sub>) can be modeled as a random walk process (Wickramasuriya and Faghih, <xref ref-type="bibr" rid="B54">2020a</xref>):</p>
<disp-formula id="E1"><label>(1)</label><mml:math id="M1"><mml:mtable class="eqnarray" columnalign="left"><mml:mtr><mml:mtd><mml:msub><mml:mrow><mml:mi>x</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub></mml:mtd><mml:mtd><mml:mo>=</mml:mo><mml:msub><mml:mrow><mml:mi>x</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi><mml:mo>-</mml:mo><mml:mn>1</mml:mn></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003F5;</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub><mml:mo>,</mml:mo></mml:mtd></mml:mtr></mml:mtable></mml:math></disp-formula>
<p>where <inline-formula><mml:math id="M2"><mml:msub><mml:mrow><mml:mi>&#x003F5;</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0007E;</mml:mo><mml:mrow><mml:mi mathvariant="script">N</mml:mi></mml:mrow><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:mn>0</mml:mn><mml:mo>,</mml:mo><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>&#x003F5;</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:math></inline-formula> is the process noise and <italic>j</italic> stands for the time index. Following the marked point process filtering approach (Wickramasuriya and Faghih, <xref ref-type="bibr" rid="B54">2020a</xref>), we consider Bernoulli distribution for neural impulse occurrence (arousal events) <italic>n</italic><sub><italic>j</italic></sub> with probability mass function <inline-formula><mml:math id="M3"><mml:msubsup><mml:mrow><mml:mi>a</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow><mml:mrow><mml:msub><mml:mrow><mml:mi>n</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub></mml:mrow></mml:msubsup><mml:msup><mml:mrow><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:mn>1</mml:mn><mml:mo>-</mml:mo><mml:msub><mml:mrow><mml:mi>a</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:mrow><mml:mrow><mml:mn>1</mml:mn><mml:mo>-</mml:mo><mml:msub><mml:mrow><mml:mi>n</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub></mml:mrow></mml:msup></mml:math></inline-formula> such that <italic>P</italic>(<italic>n</italic><sub><italic>j</italic></sub> &#x0003D; 1) &#x0003D; <italic>a</italic><sub><italic>j</italic></sub>.</p>
<p>We can relate <italic>x</italic><sub><italic>j</italic></sub> to <italic>a</italic><sub><italic>j</italic></sub> by applying a sigmoid transform (Young et al., <xref ref-type="bibr" rid="B62">2004</xref>). Thus,</p>
<disp-formula id="E2"><label>(2)</label><mml:math id="M4"><mml:mtable class="eqnarray" columnalign="left"><mml:mtr><mml:mtd><mml:msub><mml:mrow><mml:mi>a</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub></mml:mtd><mml:mtd><mml:mo>=</mml:mo><mml:mfrac><mml:mrow><mml:mn>1</mml:mn></mml:mrow><mml:mrow><mml:mn>1</mml:mn><mml:mo>&#x0002B;</mml:mo><mml:msup><mml:mrow><mml:mi>e</mml:mi></mml:mrow><mml:mrow><mml:mo>-</mml:mo><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:msub><mml:mrow><mml:mi>x</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:mi>&#x003B2;</mml:mi></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:mrow></mml:msup></mml:mrow></mml:mfrac><mml:mo>,</mml:mo></mml:mtd></mml:mtr></mml:mtable></mml:math></disp-formula>
<p>where &#x003B2; is a constant that can be derived from <inline-formula><mml:math id="M5"><mml:mi>&#x003B2;</mml:mi><mml:mo>&#x02248;</mml:mo><mml:mo class="qopname">log</mml:mo><mml:mstyle mathsize="2.03em"><mml:mrow><mml:mtext>&#x000A0;</mml:mtext></mml:mrow></mml:mstyle><mml:mfrac><mml:mrow><mml:msub><mml:mrow><mml:mi>a</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub></mml:mrow><mml:mrow><mml:mn>1</mml:mn><mml:mo>-</mml:mo><mml:msub><mml:mrow><mml:mi>a</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub></mml:mrow></mml:mfrac><mml:mstyle mathsize="2.03em"><mml:mrow><mml:mtext>&#x000A0;</mml:mtext></mml:mrow></mml:mstyle></mml:math></inline-formula>, and <italic>a</italic><sub>0</sub> is the average probability of observing an impulse during the experiment. As described in Wickramasuriya and Faghih (<xref ref-type="bibr" rid="B54">2020a</xref>), the continuous-valued amplitude <italic>r</italic><sub><italic>j</italic></sub> of each neural impulse can be represented as</p>
<disp-formula id="E3"><label>(3)</label><mml:math id="M6"><mml:mtable class="eqnarray" columnalign="left"><mml:mtr><mml:mtd><mml:msub><mml:mrow><mml:mi>r</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub></mml:mtd><mml:mtd><mml:mo>=</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B3;</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B3;</mml:mi></mml:mrow><mml:mrow><mml:mn>1</mml:mn></mml:mrow></mml:msub><mml:msub><mml:mrow><mml:mi>x</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:msub><mml:mrow><mml:mi>v</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub><mml:mo>,</mml:mo></mml:mtd></mml:mtr></mml:mtable></mml:math></disp-formula>
<p>where <inline-formula><mml:math id="M7"><mml:msub><mml:mrow><mml:mi>v</mml:mi></mml:mrow><mml:mrow><mml:mi>j</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0007E;</mml:mo><mml:mrow><mml:mi mathvariant="script">N</mml:mi></mml:mrow><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:mn>0</mml:mn><mml:mo>,</mml:mo><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>v</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:math></inline-formula> presents the sensor noise, &#x003B3;<sub>0</sub> and &#x003B3;<sub>1</sub> are the unknown model parameters in arousal state model in <xref ref-type="disp-formula" rid="E1">Equations (1)</xref>&#x02013;<xref ref-type="disp-formula" rid="E4">(4)</xref>, to be determined. Consequently, the joint density function for the observed neural impulse is</p>
<disp-formula id="E4"><label>(4)</label><mml:math id="M8"><mml:mrow><mml:mtable columnalign='left'><mml:mtr columnalign='left'><mml:mtd columnalign='left'><mml:mrow><mml:mo stretchy='false'>(</mml:mo><mml:msub><mml:mi>n</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mo>&#x02229;</mml:mo><mml:msub><mml:mi>r</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mo>&#x0007C;</mml:mo><mml:msub><mml:mi>x</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mo stretchy='false'>)</mml:mo><mml:mo>=</mml:mo><mml:mrow><mml:mo>{</mml:mo><mml:mrow><mml:mtable columnalign='left'><mml:mtr columnalign='left'><mml:mtd columnalign='left'><mml:mrow><mml:mn>1</mml:mn><mml:mo>&#x02212;</mml:mo><mml:msub><mml:mi>a</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mtext>&#x02003;&#x02003;&#x02003;&#x02003;&#x02003;&#x02003;</mml:mtext></mml:mrow></mml:mtd><mml:mtd columnalign='left'><mml:mrow><mml:mtext>if&#x000A0;</mml:mtext><mml:msub><mml:mi>n</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mtext>=0</mml:mtext></mml:mrow></mml:mtd></mml:mtr><mml:mtr columnalign='left'><mml:mtd columnalign='left'><mml:mrow><mml:msub><mml:mi>a</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mfrac><mml:mn>1</mml:mn><mml:mrow><mml:msqrt><mml:mrow><mml:mn>2</mml:mn><mml:mi>&#x003C0;</mml:mi><mml:msubsup><mml:mi>&#x003C3;</mml:mi><mml:mi>v</mml:mi><mml:mn>2</mml:mn></mml:msubsup></mml:mrow></mml:msqrt></mml:mrow></mml:mfrac><mml:msup><mml:mi>e</mml:mi><mml:mrow><mml:mfrac><mml:mrow><mml:mo>&#x02212;</mml:mo><mml:msup><mml:mrow><mml:mo stretchy='false'>(</mml:mo><mml:msub><mml:mi>r</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mo>&#x02212;</mml:mo><mml:msub><mml:mi>&#x003B3;</mml:mi><mml:mn>0</mml:mn></mml:msub><mml:mo>&#x02212;</mml:mo><mml:msub><mml:mi>&#x003B3;</mml:mi><mml:mn>1</mml:mn></mml:msub><mml:msub><mml:mi>x</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mo stretchy='false'>)</mml:mo></mml:mrow><mml:mn>2</mml:mn></mml:msup></mml:mrow><mml:mrow><mml:mn>2</mml:mn><mml:msubsup><mml:mi>&#x003C3;</mml:mi><mml:mi>v</mml:mi><mml:mn>2</mml:mn></mml:msubsup></mml:mrow></mml:mfrac></mml:mrow></mml:msup></mml:mrow></mml:mtd><mml:mtd columnalign='left'><mml:mrow><mml:mtext>if&#x000A0;</mml:mtext><mml:msub><mml:mi>n</mml:mi><mml:mi>j</mml:mi></mml:msub><mml:mtext>=1</mml:mtext></mml:mrow></mml:mtd></mml:mtr></mml:mtable></mml:mrow></mml:mrow><mml:mo>.</mml:mo></mml:mrow></mml:mtd></mml:mtr></mml:mtable></mml:mrow></mml:math></disp-formula>
<p>The unknown parameters <inline-formula><mml:math id="M9"><mml:msub><mml:mrow><mml:mi>&#x003B8;</mml:mi></mml:mrow><mml:mrow><mml:mi>A</mml:mi></mml:mrow></mml:msub><mml:mo>=</mml:mo><mml:mrow><mml:mo>{</mml:mo><mml:mrow><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>&#x003F5;</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup><mml:mo>,</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B3;</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub><mml:mo>,</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B3;</mml:mi></mml:mrow><mml:mrow><mml:mn>1</mml:mn></mml:mrow></mml:msub><mml:mo>,</mml:mo><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>v</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup></mml:mrow><mml:mo>}</mml:mo></mml:mrow></mml:math></inline-formula>, and hidden arousal state <italic>x</italic><sub><italic>j</italic></sub> can be decoded at the same time using an expectation-maximization (EM) framework (Wickramasuriya and Faghih, <xref ref-type="bibr" rid="B54">2020a</xref>). A description of the applied arousal state decoder is available in the <xref ref-type="supplementary-material" rid="SM1">Supplementary material</xref>.</p>
</sec>
<sec>
<title>2.3.2 Performance state estimation</title>
<p>Inspired by the proposed state-space model in Prerau et al. (<xref ref-type="bibr" rid="B37">2009</xref>), we model the cognitive performance state as</p>
<disp-formula id="E5"><label>(5)</label><mml:math id="M10"><mml:mtable class="eqnarray" columnalign="left"><mml:mtr><mml:mtd><mml:msub><mml:mrow><mml:mi>z</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>=</mml:mo><mml:msub><mml:mrow><mml:mi>z</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi><mml:mo>-</mml:mo><mml:mn>1</mml:mn></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:msub><mml:mrow><mml:mi>w</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>,</mml:mo></mml:mtd></mml:mtr></mml:mtable></mml:math></disp-formula>
<p>where <italic>z</italic><sub><italic>k</italic></sub> is the performance state, <inline-formula><mml:math id="M11"><mml:msub><mml:mrow><mml:mi>w</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0007E;</mml:mo><mml:mrow><mml:mi mathvariant="script">N</mml:mi></mml:mrow><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:mn>0</mml:mn><mml:mo>,</mml:mo><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>w</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:math></inline-formula> stands for the process noise and <italic>k</italic> is the trial number during the experiment.</p>
<p>Similar to Prerau et al. (<xref ref-type="bibr" rid="B37">2009</xref>), we can form the observation model by specifying one binary observation (correct/incorrect response at <italic>k</italic><sup><italic>th</italic></sup> trial) and one continuous observation (reaction time of the corresponding response). The Bernoulli probability model is assumed for the binary responses with the probability mass function of <inline-formula><mml:math id="M12"><mml:msubsup><mml:mrow><mml:mi>p</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow><mml:mrow><mml:msub><mml:mrow><mml:mi>m</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub></mml:mrow></mml:msubsup><mml:msup><mml:mrow><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:mn>1</mml:mn><mml:mo>-</mml:mo><mml:msub><mml:mrow><mml:mi>p</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:mrow><mml:mrow><mml:mn>1</mml:mn><mml:mo>-</mml:mo><mml:msub><mml:mrow><mml:mi>m</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub></mml:mrow></mml:msup></mml:math></inline-formula>. Applying sigmoid transform we express the <italic>p</italic><sub><italic>k</italic></sub> in terms of <italic>z</italic><sub><italic>k</italic></sub> such that</p>
<disp-formula id="E6"><label>(6)</label><mml:math id="M13"><mml:mtable class="eqnarray" columnalign="left"><mml:mtr><mml:mtd><mml:msub><mml:mrow><mml:mi>p</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub></mml:mtd><mml:mtd><mml:mo>=</mml:mo><mml:mfrac><mml:mrow><mml:mn>1</mml:mn></mml:mrow><mml:mrow><mml:mn>1</mml:mn><mml:mo>&#x0002B;</mml:mo><mml:msup><mml:mrow><mml:mi>e</mml:mi></mml:mrow><mml:mrow><mml:mo>-</mml:mo><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:msub><mml:mrow><mml:mi>z</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:mi>&#x003BC;</mml:mi></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:mrow></mml:msup></mml:mrow></mml:mfrac><mml:mo>.</mml:mo></mml:mtd></mml:mtr></mml:mtable></mml:math></disp-formula>
<p>The constant term &#x003BC; can be derived from <inline-formula><mml:math id="M14"><mml:mi>&#x003BC;</mml:mi><mml:mo>&#x02248;</mml:mo><mml:mo class="qopname">log</mml:mo><mml:mstyle mathsize="2.03em"><mml:mrow><mml:mtext>&#x000A0;</mml:mtext></mml:mrow></mml:mstyle><mml:mfrac><mml:mrow><mml:msub><mml:mrow><mml:mi>p</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub></mml:mrow><mml:mrow><mml:mn>1</mml:mn><mml:mo>-</mml:mo><mml:msub><mml:mrow><mml:mi>p</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub></mml:mrow></mml:mfrac><mml:mstyle mathsize="2.03em"><mml:mrow><mml:mtext>&#x000A0;</mml:mtext></mml:mrow></mml:mstyle></mml:math></inline-formula> where <italic>p</italic><sub>0</sub> is the average probability of having a correct response.</p>
<p>The reaction time <italic>t</italic><sub><italic>k</italic></sub> can be related to the performance state as</p>
<disp-formula id="E7"><label>(7)</label><mml:math id="M15"><mml:mtable class="eqnarray" columnalign="left"><mml:mtr><mml:mtd><mml:msub><mml:mrow><mml:mi>I</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub></mml:mtd><mml:mtd><mml:mo>=</mml:mo><mml:mo class="qopname">log</mml:mo><mml:msub><mml:mrow><mml:mi>t</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>=</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B1;</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B1;</mml:mi></mml:mrow><mml:mrow><mml:mn>1</mml:mn></mml:mrow></mml:msub><mml:msub><mml:mrow><mml:mi>z</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0002B;</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B4;</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>,</mml:mo></mml:mtd></mml:mtr></mml:mtable></mml:math></disp-formula>
<p>where we consider the log of reaction time at each trial (<italic>I</italic><sub><italic>k</italic></sub>) to follow the linear model with the Gaussian noise term <inline-formula><mml:math id="M16"><mml:msub><mml:mrow><mml:mi>&#x003B4;</mml:mi></mml:mrow><mml:mrow><mml:mi>k</mml:mi></mml:mrow></mml:msub><mml:mo>&#x0007E;</mml:mo><mml:mrow><mml:mi mathvariant="script">N</mml:mi></mml:mrow><mml:mrow><mml:mo stretchy="false">(</mml:mo><mml:mrow><mml:mn>0</mml:mn><mml:mo>,</mml:mo><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>&#x003B4;</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup></mml:mrow><mml:mo stretchy="false">)</mml:mo></mml:mrow></mml:math></inline-formula>; the vector of unknown model parameters in performance state model in <xref ref-type="disp-formula" rid="E5">Equations (5)</xref>&#x02013;<xref ref-type="disp-formula" rid="E7">(7)</xref>, <inline-formula><mml:math id="M17"><mml:msub><mml:mrow><mml:mi>&#x003B8;</mml:mi></mml:mrow><mml:mrow><mml:mi>P</mml:mi></mml:mrow></mml:msub><mml:mo>=</mml:mo><mml:mrow><mml:mo>{</mml:mo><mml:mrow><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>w</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup><mml:mo>,</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B1;</mml:mi></mml:mrow><mml:mrow><mml:mn>0</mml:mn></mml:mrow></mml:msub><mml:mo>,</mml:mo><mml:msub><mml:mrow><mml:mi>&#x003B1;</mml:mi></mml:mrow><mml:mrow><mml:mn>1</mml:mn></mml:mrow></mml:msub><mml:mo>,</mml:mo><mml:msubsup><mml:mrow><mml:mi>&#x003C3;</mml:mi></mml:mrow><mml:mrow><mml:mi>&#x003B4;</mml:mi></mml:mrow><mml:mrow><mml:mn>2</mml:mn></mml:mrow></mml:msubsup></mml:mrow><mml:mo>}</mml:mo></mml:mrow></mml:math></inline-formula> and the performance state <italic>z</italic><sub><italic>k</italic></sub> can be decoded using the EM approach (Prerau et al., <xref ref-type="bibr" rid="B37">2009</xref>; Khazaei et al., <xref ref-type="bibr" rid="B27">2021</xref>). A description of the applied performance state decoder is available in the <xref ref-type="supplementary-material" rid="SM1">Supplementary material</xref>.</p>
</sec>
<sec>
<title>2.3.3 fNIRS processing</title>
<p>Similar to Yaghmour et al. (<xref ref-type="bibr" rid="B59">2021</xref>) and Parshi et al. (<xref ref-type="bibr" rid="B36">2019</xref>), we preprocess the collected hemodynamic data using the Nirslab software (Xu et al., <xref ref-type="bibr" rid="B58">2014</xref>). The preprocessing steps include bandpass filtering and converting the light intensity data to HbO, HbR, and HbT concentrations (Yaghmour et al., <xref ref-type="bibr" rid="B59">2021</xref>).</p>
<p>We first analyze the HbO data. To study the PFC and OC areas, the combinations of HbO channels are considered such that we cover 16 different brain regions. These brain regions are distributed within the right and left sides of the PFC and OC areas (Donadel et al., <xref ref-type="bibr" rid="B13">2021</xref>). As depicted in <xref ref-type="fig" rid="F4">Figure 4B</xref>, each of the studied areas is surrounded by four channels, and the average HbO concentration can be derived accordingly. We evaluate the epoch of HbO signal over 22 trials (within each task block) of the <italic>n</italic>-back task with respect to the task difficulty (e.g., 1-back) and music session. The epoch of a signal can be defined as a signal segment within a specific time window. Such evaluation is inspired by the event-related potential (ERP) study, which analyzes a brainwave in response to the stimuli (Luck, <xref ref-type="bibr" rid="B30">2014</xref>). Here, we consider the signal segment over 22 trials (&#x02248;44 s), and we perform a similar ERP-like study to derive an epoch of performance state with respect to the type of task (i.e., task difficulty) and music session. Then, we find the Pearson correlation coefficient between the epoch of HbO and continuous performance.</p>
<fig id="F4" position="float">
<label>Figure 4</label>
<caption><p>The Functional Near Infrared Spectroscopy (fNIRS) sensor configuration. <bold>(A)</bold> Optode layout of the fNIRS sources (red), detectors (blue), and channels (green) used during the experiment. The Nasion (Nz, the intersection point of the frontal and nasal bones), Inion (Iz, the occipital protuberance behind the scalp), and Left and Right Pre-auricular points (LPA, RPA, the points anterior to the ears in front of the upper end of the tragus) are labeled accordingly. <bold>(B)</bold> The channel numbers and studied regions of PFC and OC areas located on right and left hemisphere: LF1- to LF4, RF1 to RF4, LB1 to LB4, and RB1 to RB4.</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0004.tif"/>
</fig>
<p>Additionally, inspired by the study in Wickramasuriya et al. (<xref ref-type="bibr" rid="B56">2023</xref>), we investigate HbT signal energy with respect to the presented music types. Particularly, we consider the collected signal from the PFC channels (i.e., channels 23&#x02013;44) and smooth the signal using a 10 <italic>s</italic> sample-by-sample running average filter.</p>
</sec>
<sec>
<title>2.3.4 Statistical analysis</title>
<p>The differences in human brain structure can lead to variation in behaviors, cognitive abilities, and mental and physical health (Gu and Kanai, <xref ref-type="bibr" rid="B20">2014</xref>). To have a general and person-specific index of cognitive states with respect to an individual&#x00027;s baseline, we formulate the metrics called high arousal index (HAI) and high performance index (HPI) (Wickramasuriya and Faghih, <xref ref-type="bibr" rid="B54">2020a</xref>). These arousal and performance indices can be calculated from <italic>prob</italic>(state<sub><italic>j</italic></sub>&#x0003E;threshold) where the threshold has been set to the median of the state values. Here, we decode the hidden arousal and performance state merely based on the SC and behavioral data (Fekri Azgomi et al., <xref ref-type="bibr" rid="B16">2023</xref>). The HAI and HPI are evaluated with respect to task difficulty and music sessions. In particular, we perform the two-sided sign test to compare the 1-back task and 3-back task data (i.e., 1-back vs. 3-back) during each music session (<italic>N</italic> &#x0003D; 176); similarly, the two-sided sign test is executed to compare the HAI and HPI associated with calming and exciting sessions (calming vs. exciting) during each task difficulty level. We consider 0.01 as the significance level (99% confidence), and the <italic>p</italic>&#x02212;values are reported in <xref ref-type="table" rid="T1">Tables 1</xref>, <xref ref-type="table" rid="T2">2</xref>.</p>
<table-wrap position="float" id="T1">
<label>Table 1</label>
<caption><p>The performed signrank test with respect to music sessions and <italic>n</italic>-back difficulty levels given the decoded high arousal index (HAI).</p></caption>
<table frame="box" rules="all">
<thead>
<tr style="background-color:#919498;color:#ffffff">
<th valign="top" align="center" colspan="6"><italic><bold>p</bold></italic><bold>-values</bold></th>
</tr>
</thead>
<tbody>
<tr style="background-color:#919498;color:#ffffff">
<td valign="top" align="left"><bold>Groups</bold></td>
<td valign="top" align="center"><bold>Participant 1</bold></td>
<td valign="top" align="center"><bold>Participant 2</bold></td>
<td valign="top" align="center"><bold>Participant 3</bold></td>
<td valign="top" align="center"><bold>Participant 4</bold></td>
<td valign="top" align="center"><bold>Participant 5</bold></td>
</tr>
<tr>
<td valign="top" align="left">Calming session trials (1-back vs. 3-back)</td>
<td valign="top" align="center">0.0595</td>
<td valign="top" align="center">0.2582</td>
<td valign="top" align="center">1</td>
<td valign="top" align="center">0.3271</td>
<td valign="top" align="center">0.0129</td>
</tr>
<tr>
<td valign="top" align="left">Exciting session trials (1-back vs. 3-back)</td>
<td valign="top" align="center">0.821</td>
<td valign="top" align="center">0.0288</td>
<td valign="top" align="center">1.7349e-05</td>
<td valign="top" align="center">0.0012</td>
<td valign="top" align="center">0.5977</td>
</tr>
<tr>
<td valign="top" align="left">1-back trials (calming vs. exciting)</td>
<td valign="top" align="center">8.4957e-14</td>
<td valign="top" align="center">5.1376e-30</td>
<td valign="top" align="center">2.6388e-13</td>
<td valign="top" align="center">2.3808e-12</td>
<td valign="top" align="center">9.8706e-40</td>
</tr>
<tr>
<td valign="top" align="left">3-back trials (calming vs. exciting)</td>
<td valign="top" align="center">4.3804e-18</td>
<td valign="top" align="center">2.3884e-22</td>
<td valign="top" align="center">9.8706e-40</td>
<td valign="top" align="center">2.2015e-26</td>
<td valign="top" align="center">9.8706e-40</td>
</tr></tbody>
</table>
</table-wrap>
<table-wrap position="float" id="T2">
<label>Table 2</label>
<caption><p>The performed signrank test with respect to music sessions and <italic>n</italic>-back difficulty levels given the decoded high performance index (HPI).</p></caption>
<table frame="box" rules="all">
<thead>
<tr style="background-color:#919498;color:#ffffff">
<th valign="top" align="center" colspan="6"><italic><bold>p</bold></italic><bold>-values</bold></th>
</tr>
</thead>
<tbody>
<tr style="background-color:#919498;color:#ffffff">
<td valign="top" align="left"><bold>Groups</bold></td>
<td valign="top" align="center"><bold>Participant 1</bold></td>
<td valign="top" align="center"><bold>Participant 2</bold></td>
<td valign="top" align="center"><bold>Participant 3</bold></td>
<td valign="top" align="center"><bold>Participant 4</bold></td>
<td valign="top" align="center"><bold>Participant 5</bold></td>
</tr>
<tr>
<td valign="top" align="left">Calming session trials (1-back vs. 3-back)</td>
<td valign="top" align="center">1.0693e-34</td>
<td valign="top" align="center">4.2545e-33</td>
<td valign="top" align="center">8.2346e-15</td>
<td valign="top" align="center">8.3044e-28</td>
<td valign="top" align="center">2.4552e-36</td>
</tr>
<tr>
<td valign="top" align="left">Exciting session trials (1-back vs. 3-back)</td>
<td valign="top" align="center">5.3702e-23</td>
<td valign="top" align="center">4.2647e-06</td>
<td valign="top" align="center">8.2346e-15</td>
<td valign="top" align="center">4.2545e-33</td>
<td valign="top" align="center">3.7427e-08</td>
</tr>
<tr>
<td valign="top" align="left">1-back trials (calming vs. exciting)</td>
<td valign="top" align="center">3.3866e-05</td>
<td valign="top" align="center">0.0033</td>
<td valign="top" align="center">4.4108e-07</td>
<td valign="top" align="center">3.9597e-04</td>
<td valign="top" align="center">0.8211</td>
</tr>
<tr>
<td valign="top" align="left">3-back trials (calming vs. exciting)</td>
<td valign="top" align="center">2.3808e-12</td>
<td valign="top" align="center">1.6276e-17</td>
<td valign="top" align="center">0.0053</td>
<td valign="top" align="center">2.1008e-16</td>
<td valign="top" align="center">1.1527e-18</td>
</tr></tbody>
</table>
</table-wrap>
</sec>
</sec>
</sec>
<sec sec-type="results" id="s3">
<title>3 Results</title>
<p>Given the HAI boxplots in <xref ref-type="fig" rid="F5">Figure 5</xref>, a higher variation in the arousal matrices with respect to the calming and exciting session is noted, while such variation can not be observed with respect to the task difficulty. The median values of HAI in 1-back and 3-back (1-back vs. 3-back) tasks do not diverge considerably. However, considering the music sessions (calming vs. exciting), the median values associated with the calming sessions do not fall within the range of exciting session boxes. According to the reported <italic>p</italic>-values and boxplots (<xref ref-type="table" rid="T1">Table 1</xref>), there is no significant difference between the HAI in calming session 1-back tasks and 3-back ones. In regards to HAI associated with exciting sessions, participants 3 and 4 are the only ones who depict a significant difference between the 1-back task and 3-back task data (<xref ref-type="table" rid="T1">Table 1</xref>). Considering the HAI with respect to the music, all the participants present significant differences when shifting from a calming to an exciting session (<xref ref-type="table" rid="T1">Table 1</xref>).</p>
<fig id="F5" position="float">
<label>Figure 5</label>
<caption><p>Distribution of high arousal index (HAI) within trials with respect to task difficulties and music sessions. Each sub-plot shows the box plot of the average HAI data within the trials with respect to 1-back task in the calming session (green box), 3-back task in the calming session (blue box), 1-back task in the exciting session (gray box), and 3-back task in the exciting session (red box).</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0005.tif"/>
</fig>
<p>We evaluate the HPI in a similar manner, and as expected, we find that the median of HPI within the 1-back task trials is considerably higher than in 3-back task trials (<xref ref-type="fig" rid="F6">Figure 6</xref>). Also, the HPI median values among all the participants are higher within the 3-back task trials during the exciting session compared to the calming session (<xref ref-type="fig" rid="F6">Figure 6</xref>). The reported <italic>p</italic>&#x02212;values in <xref ref-type="table" rid="T2">Table 2</xref> depict the significant difference in HPI with respect to the task difficulty as well as music session in most of the cases.</p>
<fig id="F6" position="float">
<label>Figure 6</label>
<caption><p>Distribution of high performance index (HPI) within trials with respect to task difficulties and music sessions. Each sub-plot shows the box plot of the HPI data within the trials with respect to 1-back task in the calming session (green box), 3-back task in the calming session (blue box), 1-back task in the exciting session (gray box), and 3-back task in the exciting session (red box).</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0006.tif"/>
</fig>
<p><xref ref-type="fig" rid="F7">Figure 7</xref> presents the epochs of HbO concentration and performance across the task blocks for participant 2. As noted earlier, 16 specific brain regions from the left and right sides of the PFC and OC areas are considered. The correlation between the HbO epochs and performance epochs with respect to the types of the <italic>n</italic>-back task and the played music is illustrated. In particular, <xref ref-type="fig" rid="F7">Figure 7A</xref> displays the correlation in the 1-back task blocks within the calming session; <xref ref-type="fig" rid="F7">Figure 7B</xref> pays attention to the 3-back task blocks within the calming session; <xref ref-type="fig" rid="F7">Figure 7C</xref> addresses the 1-back task blocks within the exciting session; <xref ref-type="fig" rid="F7">Figure 7D</xref> considers the 3-back task blocks within the exciting session. The Pearson correlation coefficient (<italic>r</italic>) of performance and HbO concentration for each studied brain region is reported in a box next to each subplot. The highest HbO and performance positive correlation for participant 2 corresponds to the RF1 region (right side of the PFC) during the 3-back task blocks within the exciting session. Similar demonstrations for the other participants can be found in the <xref ref-type="supplementary-material" rid="SM1">Supplementary material</xref>. Also, the highest positive correlation can be observed within the 3-back task blocks for all participants. In particular, we can see that the highest correlation in participants 1&#x02013;5 corresponds to LB1, RF1, LF4, LF3, and LF2, respectively. Four out of five participants presented the highest performance-HbO correlation with the acquired HbO signal from the left hemisphere. A similar trend can be noted concerning the PFC areas.</p>
<fig id="F7" position="float">
<label>Figure 7</label>
<caption><p>The correlation study for the epoch of HbO and performance state across the task blocks for one participant. The sub-figures present the epochs of HbO and performance data recorded within: <bold>(A)</bold> the 1-back task blocks within the calming music. <bold>(B)</bold> the 3-back task blocks within the calming music. <bold>(C)</bold> the 1-back task blocks within the exciting music. <bold>(D)</bold> the 3-back task blocks within the exciting music. The sub-plots in each sub-figure, from top to bottom, represent: the HbO data collected from the left side of the PFC, right side of the PFC, left side of the OC area, and right side of the OC area. The boxes on the right side of subplots present the Pearson correlation coefficients (<italic>r</italic>) within the studied brain regions.</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0007.tif"/>
</fig>
<p>In <xref ref-type="fig" rid="F8">Figure 8</xref>, we present the mean energy (black) and mean envelope (blue) of smoothed HbT signal collected from the PFC channels (i.e., channels 23&#x02013;44). The <xref ref-type="supplementary-material" rid="SM1">Figure 8A</xref> presents the results within the calming session (green), and <xref ref-type="supplementary-material" rid="SM1">Figure 8B</xref> is related to the exciting session (red). The 1-back task blocks are indicated with lighter colors, while the 3-back ones are represented with more intense background colors. Aside from participant 3, it can be seen that the peak of the HbT energy is located within the exciting session.</p>
<fig id="F8" position="float">
<label>Figure 8</label>
<caption><p>The mean energy and mean envelope of smoothed HbT signal collected from PFC channels. The sub-figures present: <bold>(A)</bold> The mean energy (black) and mean envelope (blue) of smoothed HbT signal collected from PFC channels within the calming music for participants 1&#x02013;5. <bold>(B)</bold> The mean energy (black) and mean envelope (blue) of smoothed HbT signal collected from PFC channels within the exciting music for participants 1&#x02013;5. The background colors in each sub-panel indicate: the 1-back task during the calming session (light green); the 3-back task during the calming session (dark green); the 1-back task during the exciting session (light red); the 3-back task during the exciting session (dark red).</p></caption>
<graphic mimetype="image" mime-subtype="tiff" xlink:href="fnins-18-1406814-g0008.tif"/>
</fig>
</sec>
<sec sec-type="discussion" id="s4">
<title>4 Discussion</title>
<p>We have performed a working memory experiment in the presence of musical stimuli to collect multimodal physiological signals along with brain hemodynamic response signals of participants and evaluate the possibility of using music as an intervention. Participants were asked to perform a working memory task with different difficulty levels and music types (i.e., calming and exciting). The difficulty levels were included to ensure different cognitive loads during the experiment. We have used fNIRS to record the brain hemodynamic response. By incorporating multiple physiological signals in the experimental data collection, we have derived a rich neuro-physiological dataset that could offer a more comprehensive picture of the body and brain&#x00027;s reaction to music and cognitive load. In this dataset, we have implemented the musical stimuli by conducting the cognitive task in two sessions&#x02013;one with calming music content and the other with exciting music content. The presence of calming music was supposed to mimic the low arousal condition, while the exciting one was simulating the high arousal one. To incorporate the personalized version of CLBMI, we have used personalized music selected by the participants for calming and exciting music. While the applied music intervention offers us a personalized closed-loop architecture, it can induce the subject familiarity with the experiment environment. One possible approach to preserve the person-specific nature of the intervention and reduce the impact of the subject&#x00027;s familiarity is to employ newly generated music based on the subject&#x00027;s preference in future studies (Fekri Azgomi et al., <xref ref-type="bibr" rid="B16">2023</xref>).</p>
<p>In the presented research, we have collected data using both research grade (e.g., Biopac) and wearable devices (e.g., Empatica E4). While wearable devices can be implemented in everyday life settings and they seem to be more aligned with the future closed-loop architecture, the employed signal processing algorithms and estimation framework are more compatible with the research grade devices, and they outperform in the lab settings. Hence, we perform our in-depth analysis based on the data collected using research-grade devices. Although the presented framework includes a multimodal measurement that can be used concurrently for brain state estimation and classification, here, we analyze the SC data, oxygenated hemoglobin, total hemoglobin, and behavioral signals. However, we deliver complete dataset and experimental settings to provide a framework for any researcher who is interested in performing research in this paradigm. Particularly, the collected data presents a unique opportunity for future investigations, and it holds the potential to unlock groundbreaking insights and guide future data collection in this context.</p>
<p>Recording multimodal physiological signals within a cognitive task can provide an opportunity to explore cutting-edge strategies that may extend human cognitive capacities (Mangaroska et al., <xref ref-type="bibr" rid="B31">2021</xref>). However, multimodal physiological data collection comes with certain challenges (Cukurova et al., <xref ref-type="bibr" rid="B12">2020</xref>). Specifically, a suboptimal sensor connection or the presence of motion artifact in the modalities can lead to data corruption (Mangaroska et al., <xref ref-type="bibr" rid="B31">2021</xref>; Fekri Azgomi et al., <xref ref-type="bibr" rid="B16">2023</xref>). Consequently, the participant removal rate in this form of research, as observed in this experiment, can be high. Given the fast-paced advances in biomedical sensor development, one potential approach to address this concern is to use a more advanced setup that employs a lower number of sensors with a more robust connection to collect the signal of interest. Employing the recently developed sensors may pave the way for future data collection in a more practical and efficient manner.</p>
<p>Based on our analysis on the SC signal, we can observe that the HAI level varies significantly within the music sessions, while the task-wise perspective does not reveal a significant variation. One may interpret that the difference in the induced cognitive load by 1-back and 3-back tasks is not significantly high enough to be reflected in the HAI signal. Another interpretation, though less probable, is that the impact of cognitive load on the arousal level is not as much as the effect of music type, and the cognitive load does not seem to have a mediating effect on arousal. Determining a general relationship that holds out of the scope of this dataset requires a comprehensive causality analysis, which is not the main focus of this study.</p>
<p>It should be noted that the HAI for participants 4 and 5 was reduced within the exciting session. This is the opposite of what the exciting content of music is supposed to elicit. This is a notable counterexample and demonstrates that the skin conductance response does not agree with the emotional content of music for participants 4 and 5. On the other hand, we can see that the HbT energy signal reaches its peak within the exciting session in both participant 4 and 5 cases. While the SC is a long-standing index of arousal (Greco et al., <xref ref-type="bibr" rid="B19">2016</xref>), we can observe that decoding the arousal from a single SC measurement might lack the robustness needed to explain the observed behavior. To address this concern in future investigations and experiment designs, the graphene e-tattoos (GET) sensors can be applied (Jang et al., <xref ref-type="bibr" rid="B26">2022</xref>), and the SC data can be collected and analyzed in a multichannel manner (Alam et al., <xref ref-type="bibr" rid="B1">2023</xref>).</p>
<p>According to the presented HPI, except for participant 2, we can see that the performance indices are elevated within the second session, in which the exciting music was presented. While one may hypothesize that the improved performance is a result of establishing the arousal within a moderate range using the exciting music, other factors such as the learning impact and participant&#x00027;s familiarity with the environment can be influential, and we should avoid making any definite conclusion on the impact of music. Here, findings may suggest the potential for integrating music into the closed-loop system. Given the low sample size, the absence of any mental state score, and the possible confounding factors, further studies with a higher number of subjects, mental state annotation, inclusion of a control group, and shuffled task difficulty as well as music sessions are required for a decisive resolution.</p>
<p>In the context of BMI, users may experience various cognitive loads and emotional states during the interaction with a technical system (Herff et al., <xref ref-type="bibr" rid="B21">2014</xref>). Both cognitive load and emotion status can trigger a particular brain response followed by variation in the cognitive performance (Fishburn et al., <xref ref-type="bibr" rid="B17">2014</xref>; Bigliassi et al., <xref ref-type="bibr" rid="B9">2015</xref>). Hence, it is crucial to understand the relation between the brain response under different cognitive loads and environmental stimuli to potentially optimize performance. The performed experiment provides an opportunity to study the hemodynamic response within different cognitive loads and music sessions. The highest HbO and performance positive correlation for participants 1&#x02013;5 can be seen during the 3-back task blocks (<xref ref-type="supplementary-material" rid="SM1">Supplementary material</xref>). One may interpret that the HbO data has the potential to be applied as an informative biomarker of performance within high cognitive loads. Also, the observed high HbT energy over the PFC within exciting sessions may be interpreted as participants&#x00027; higher brain activities within the exciting session compared to the calming session. This conforms with the findings in Zheng et al. (<xref ref-type="bibr" rid="B64">2020</xref>). Perhaps the participants had to concentrate more within higher arousal levels (Wickramasuriya et al., <xref ref-type="bibr" rid="B56">2023</xref>). Overall, these findings may be an indication of a new avenue for decoder design research, leading to innovative fNIRS feature extraction to decode the hidden arousal and performance states. It is important to highlight that due to the small sample size, further studies with a higher number of participants and more interventions as well as cognitive loads would be beneficial in drawing a final conclusion.</p>
<p>It would be vital to note that the experiment serves as a pilot study to investigate the viability of using music as the brain state regulator. In general, our findings show variation in collected signals as well as decoded brain states between different music sessions. According to each person&#x00027;s unique physiology and the applied personalized intervention, we are interested in having a personalized perspective rather than a general view. Particularly, the brain structure of individuals and the network-level interaction between cognitive brain states of individuals can be studied independently regardless of the sample size (Hurlburt et al., <xref ref-type="bibr" rid="B25">2015</xref>). The preliminary findings show that music may potentially have ramifications in the BMI system as a form of background stimulation, while more in-depth research is required to fully understand the role of music on arousal and performance. Specifically, in the CLBMI realm, it is crucial to have precise and robust measurements as well as feedback mechanisms. The presented pilot study should be improved to ensure the robustness of the CLBMI pathways. In the future, magnetoencephalography (MEG) can be employed in parallel with fNIRS technique to improve the spatial and temporal resolution of the brain recordings and implement the neurofeedback in our setup (Yucha and Montgomery, <xref ref-type="bibr" rid="B63">2008</xref>). We intend this study to be a stepping stone for formulating such studies and developing more comprehensive experiments.</p>
</sec>
<sec sec-type="data-availability" id="s5">
<title>Data availability statement</title>
<p>The raw data supporting the conclusions of this article will be made available by the authors, without undue reservation.</p>
</sec>
<sec sec-type="ethics-statement" id="s6">
<title>Ethics statement</title>
<p>The studies involving humans were approved by Institutional Review Board at the University of Houston, TX, USA. The studies were conducted in accordance with the local legislation and institutional requirements. The participants provided their written informed consent to participate in this study.</p>
</sec>
<sec sec-type="author-contributions" id="s7">
<title>Author contributions</title>
<p>SK: Data curation, Investigation, Methodology, Software, Visualization, Writing &#x02013; original draft, Writing &#x02013; review &#x00026; editing, Formal analysis, Validation. SP: Investigation, Methodology, Visualization, Writing &#x02013; original draft, Writing &#x02013; review &#x00026; editing. SA: Data curation, Writing &#x02013; original draft, Writing &#x02013; review &#x00026; editing. MA: Data curation, Investigation, Methodology, Writing &#x02013; review &#x00026; editing. RF: Conceptualization, Funding acquisition, Investigation, Methodology, Resources, Supervision, Writing &#x02013; review &#x00026; editing.</p>
</sec>
</body>
<back>
<sec sec-type="funding-information" id="s8">
<title>Funding</title>
<p>The author(s) declare financial support was received for the research, authorship, and/or publication of this article. This work was supported in part by the U.S. National Science Foundation under grants 1942585/2226123 - CAREER: MINDWATCH: Multimodal Intelligent Noninvasive brain state Decoder for Wearable AdapTive Closed- loop arcHitectures, 1755780 - CRII: CPS: Wearable-Machine Interface Architecture, and in part by the New York University (NYU) start-up funds to RF.</p>
</sec>
<ack><p>We would like to extend our gratitude to Dilranjan S. Wickramasuriya for his valuable contribution to data collection.</p>
</ack>
<sec sec-type="COI-statement" id="conf1">
<title>Conflict of interest</title>
<p>RF and MA are co-inventors of a patent application filed by the University of Houston based on this research.</p>
<p>The remaining authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.</p>
</sec>
<sec sec-type="disclaimer" id="s9">
<title>Publisher&#x00027;s note</title>
<p>All claims expressed in this article are solely those of the authors and do not necessarily represent those of their affiliated organizations, or those of the publisher, the editors and the reviewers. Any product that may be evaluated in this article, or claim that may be made by its manufacturer, is not guaranteed or endorsed by the publisher.</p>
</sec>
<sec sec-type="supplementary-material" id="s10">
<title>Supplementary material</title>
<p>The Supplementary Material for this article can be found online at: <ext-link ext-link-type="uri" xlink:href="https://www.frontiersin.org/articles/10.3389/fnins.2024.1406814/full#supplementary-material">https://www.frontiersin.org/articles/10.3389/fnins.2024.1406814/full#supplementary-material</ext-link></p>
<supplementary-material xlink:href="Data_Sheet_1.pdf" id="SM1" mimetype="application/pdf" xmlns:xlink="http://www.w3.org/1999/xlink"/></sec>
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