Unpacking Transient Event Dynamics in Electrophysiological Power Spectra
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Electrophysiological recordings of neuronal activity show spontaneous and task-dependent changes in their frequency-domain power spectra. These changes are conventionally interpreted as modulations in the amplitude of underlying oscillations. However, this overlooks the possibility of underlying transient spectral ‘bursts’ or events whose dynamics can map to changes in trial-average spectral power in numerous ways. Under this emerging perspective, a key challenge is to perform burst detection, i.e. to characterise single-trial transient spectral events, in a principled manner. Here, we describe how transient spectral events can be operationalised and estimated using Hidden Markov Models (HMMs). The HMM overcomes a number of the limitations of the standard amplitude-thresholding approach to burst detection; in that it is able to concurrently detect different types of bursts, each with distinct spectral content, without the need to predefine frequency bands of interest, and does so with less dependence on a priori threshold specification. We describe how the HMM can be used for burst detection and illustrate its benefits on simulated data. Finally, we apply this method to empirical data to detect multiple burst types in a task-MEG dataset, and illustrate how we can compute burst metrics, such as the task-evoked timecourse of burst duration.
KeywordsElectrophysiology Spectrum Dynamics Bursting Hidden Markov model
A wide range of brain regions generate spectrally specific rhythmic signatures in electrophysiology recordings. Whilst some of these ‘rhythms’ reflect genuinely sustained oscillatory activity, it has been raised that others may be better described as spectrally specific transient events (Jones 2016; van Ede et al. 2018). In the latter case, the dynamics may be better characterised by measures of the duration, rate, or amplitude of transient events, as they occur at the level of single trials, rather than standard static or trial-averaged estimates of power.
The transient perspective suggests that the typical picture of a persistent oscillatory response to, for example, a stimulus or during working memory, may be an artefact of averaging temporally variable, short-lived events across many trials (Lundqvist et al. 2016; Stokes and Spaak 2016). In some cases, the temporal dynamics of these spectrally specific events, rather than overall amplitude or power, may be the crucial variable. This perspective is prominent in several lines of research into the 13–30 Hz beta band. Visual attention is associated with increased beta activity consisting of 300–1000 ms bursts propagating throughout the visual stream (Wróbel 2000). Similarly, in motor cortex, single-trial analyses of 13–30 Hz beta power show motor task responses of several seconds that may be built from bursts of < 150 ms in both cortical and sub-cortical regions (Feingold et al. 2015; Sherman et al. 2016). The rate and timing of these burst-events predict somatosensory and motor performance (Little et al. 2018; Shin et al. 2017) suggesting that single-trial variability in these burst-parameters is likely to be more than noise. Finally, adaptive deep-brain stimulation targeted at reducing the duration of beta bursts, rather than continuous suppression of beta power in the subthalamic nucleus of patients with Parkinson’s Disease, may improve the efficacy and efficiency of DBS (Tinkhauser et al. 2017a, b). These converging findings provide evidence that the precise temporal dynamics underlying power changes in beta activity are functionally relevant across a range of brain regions, species and task contexts.
The temporal perspective that emphasises transient spectral events thus has a recognised value, but the estimation of their temporal metrics comes with a range of technical challenges. Accurate analysis of transient spectral events, or burst detection, necessitates the detection of power changes against background noise at the single-trial level. This is typically performed by thresholding the amplitude distribution of a bandlimited signal. For instance in two recent examples, Shin et al. (2017) used a threshold of six times the median beta power derived by wavelets, and Tinkhauser et al. (2017a) used the 75th percentile of the amplitude derived from the Hilbert transform. These thresholds are set to identify periods when a signal’s amplitude is in the long tail of a positively skewed amplitude distribution. However, a noisy signal is likely to have a near-Gaussian amplitude distribution with few outliers, which makes this threshold selection difficult or even arbitrary. In addition, the temporal dynamics of a signal are constrained by the time–frequency trade off in linear filters or time–frequency transforms (Aru et al. 2015; de Cheveigné and Nelken 2019). In other words, a high temporal resolution is desirable when analysing dynamics, but this leads to smearing in frequency, which makes it difficult to disambiguate between (potentially) different dynamics in neighbouring frequency bands.
Here, we briefly outline the challenges associated with inferring bursting events in time-series and how the problem may be approached with a Hidden Markov Model (HMM) in a data-driven manner. The HMM has previously been applied to MEG data acquired during a range of simple motor (Vidaurre et al. 2016), motor learning (Zich et al. 2018) and cognitive (Quinn et al. 2018) tasks. We expand on these papers by exploring the theory behind how an HMM might represent a transient spectral event in the context of the recent literature on bursting oscillations. We consider two HMM based methods which operationalise bursting phenomena in different ways and with different assumptions. The time-delay embedded HMM is then applied to a simple motor task to explore how temporal dynamics related to bursting might underlie electrophysiological power spectra. Firstly, in the case of between subject differences in beta power across a whole recording session and secondly for a contrast between pre-movement and post-movement time windows highlighting the post-movement beta rebound.
Materials and Methods
Temporal Dynamics and Spectral Power
Standard Fourier-based approaches describe times series with a set of pure sinusoids. This means that each frequency has a single amplitude and phase lag which is assumed to be constant over time. Following this, changes in spectral power are typically interpreted as a change in the magnitude or power of the underlying oscillation. This interpretation is unambiguous when comparing stationary sinusoids but can be misleading when the signals contain richer temporal dynamics. For instance, some oscillations particularly in the beta and gamma bands, may contain intermittent, ‘bursting’ activity; therefore it may be more appropriate to consider these as transient pulses of spectrally specific activity rather than tonic oscillations (van Ede et al. 2018). Crucially, changes in the temporal parameters of these spectral events, such as lifetime or rate of occurrence, may appear as changes in power in standard analyses. In comparing two signals, this may result in a false interpretation that one signal contains tonic oscillations with larger magnitude when instead it has longer or more frequent spectrally specific bursting events. Moreover, distinct changes in the underlying parameters (more bursts, longer bursts, or bursts with higher amplitude) may yield equivalent changes in trial-average power. Targeting the changes in the underlying parameters could therefore enrich our understanding (and help distinguish between alternative models) of power changes in various experimental conditions and clinical disorder.
A range of methods, including the HMM approach being proposed here, have been developed to describe the temporal dynamics that might underlie spectral power changes. These approaches are expository in their nature and, on their own, cannot unambiguously resolve the deeper question of whether the underlying physiology is comprised of transient events or oscillations occurring within noise. However, they can provide insight into the rich temporal structure that is missed with static or trial-averaged approaches.
The increases in power seen in Fig. 1b–d are not mathematically inaccurate, they are a complete representation of the data under the assumptions of the Fourier transform. However, our interpretation of the power change in this form is ambiguous; we cannot make a strong statement about the which feature lead to our power change from the (non-time-resolved or trial-averaged) power spectrum alone. We need access to the temporal dynamics to resolve the difference between our three cases.
Dynamics in Spectrally-Specific Events with Hidden Markov Models
One way to explore the temporal dynamics of transient events with specific spectral signatures, i.e. to do burst detection, is to use Hidden Markov Models. Our intention here is to provide an intuition into how the Hidden Markov Model can be used to operationalise and explore the temporal dynamics of transient spectral events, or bursts, rather than to make a formal comparison between all available alternative methodological approaches.
The Hidden Markov Model represents data as a system moving through a set of discrete states. Each state is an abstract representation linked to the data through a probabilistic observation model (Baker et al. 2014; Vidaurre et al. 2016). The observation model can take different forms to suit the data modality and features of interest (Vidaurre et al. 2018a). Previous applications of the HMM have used autoregressive models (Vidaurre et al. 2016) or multivariate Gaussian distributions (Baker et al. 2014; Quinn et al. 2018; Vidaurre et al. 2018a) as observation models describing multi-region or single-region data in human and animal data. This flexibility makes the HMM a practical choice for analysing a wide range of data types, by tuning the observation model whilst the essential mathematical framework and parameter inference remain the same.
In this paper, we will consider two HMM approaches to operationalise the detection of bursts of spectrally specific activity in single-channel (i.e. single-region electrophysiological data). In these two approaches, we either conceptualise a burst as a period of high amplitude, or as a period with a distinct power spectra.
Periods of High Amplitude
In the first approach, we define a burst as a period of high instantaneous amplitude within a predefined frequency band. These can be identified using an HMM with a Gaussian observation model inferred on amplitude envelope time-courses of bandpass filtered data. We refer to this as the amplitude-envelope HMM (AE-HMM; Baker et al. 2014; Quinn et al. 2018). In this approach, we typically specify that there are two states, one corresponding to the ‘burst’ state (i.e. when there is high amplitude), and one corresponding to a low amplitude state. A specific visit to the burst state then equates to the occurrence of a burst event.
This HMM variant is the most similar to power thresholding methods, in which a ‘burst’ occurs when the envelope exceeds a critical amplitude threshold. However, there are two key differences Firstly, the HMM does not threshold the amplitude envelope directly. Instead, each state has a probability of being ‘on’ at each moment in time. Switching between states can then be computed analytically by the Viterbi algorithm, or through a manual thresholding of the probabilities. The distributions of posterior probabilities from a well-fitted HMM tend to be strongly bimodal with most samples having probabilities close to zero or one. When selecting a threshold for the posterior probabilities by hand, this means that a relatively wide range of thresholds (typically between .33 and .66) tend to give similar results.
Secondly, the HMM applies temporal regularisation to avoid overfitting to small changes in the envelope. That is, the effect of having a transition probability matrix discourages too many spurious state transitions. This is particularly relevant when small changes in the envelope close to the threshold could lead to many small bursts being identified by a strict threshold. In contrast, brief dips during periods of otherwise high amplitude are less likely to lead to state changes in the HMM.
Periods with Distinct Power Spectra
We may also define a burst as a period of time with a distinct pattern of spectral properties (e.g. power). These can be identified using a time-delay embedded HMM (TDE-HMM; Quinn et al. 2018; Vidaurre et al. 2018b), which uses an HMM with a multivariate Gaussian observation inferred on a time-delay embedding of the wide-band data (i.e. a cross-temporal Gaussian distribution over some prespecified window). Each state then captures periods of time that have distinct auto-covariance. Though defined in the time-domain, the auto-covariance of a time series is closely related to its frequency content; the Power Spectral Density of a time-series can be computed from the discrete Fourier transform or its autocovariance (as shown by the Wiener–Khinchin theorem).
In this approach, we typically specify more than two states in the HMM. Where each state represents a particular type of spectral event, or bursting. For example, one state may detect bursts in the beta band, another in the alpha band. A specific visit to a state then equates to the occurrence of a burst event of the type represented by that state.
In contrast to the AE-HMM, the TDE-HMM states are defined by the magnitude and shape of an entire spectrum rather than the magnitude within a specified frequency band. Bursts can then be operationalised as short-lived states containing clear spectral features. As the TDE-HMM works on the whole spectrum from raw time-courses, there is no need for the tight bandpass filtering needed prior to computing the Hilbert transform in envelope-based methods. These filters require a priori specification and can themselves affect the dynamics visible in the data (de Cheveigné and Nelken 2019). As with the AE-HMM, the TDE-HMM is able to infer bursts without defining a priori thresholds.
The general theory of Hidden Markov Modelling is explored in Rabiner and Juang (1986) and Bishop (2006). The code to run the following simulations and real data analyses can be found on https://github.com/OHBA-analysis/Quinn2019_BurstHMM. These analyses were carried out in Matlab 2019a using the Signal Processing and Wavelet toolboxes.
HMM analyses are carried out using the HMM-MAR toolbox (https://github.com/OHBA-analysis/HMM-MAR; Vidaurre et al. 2018a, 2016). Previous HMM applications have detected transient events in MEG (Baker et al. 2014; Quinn et al. 2018; Vidaurre et al. 2018b, 2016), fMRI (Vidaurre et al. 2017) and simultaneous EEG-fMRI (Hunyadi et al. 2019).
The AE- and TDE-HMMs are illustrated with a simulation. A noise time-course with a 1/f like profile is generated using direct-pole placement to define an order-1 AR model. Spectrally specific bursting events at either 20 or 35 Hz are added to this noise time-course at random intervals.
High amplitude burst events are detected using either a standard thresholding approach or a Gaussian HMM on the amplitude envelope estimated with the Hilbert transform after a narrow (15–20 Hz) or a wide (15–35 Hz) bandpass filter. For an informal comparison, a standard threshold is selected as twice the median amplitude envelope value in each example. The Gaussian HMM is specified to have two-states with the intention that the state with the higher mean amplitude reflects the bursting periods.
The same simulated time-course is used to illustrate the use of the TDE-HMM. In contrast to the AE-HMM, the TDE-HMM works on the raw time-courses, adaptively learning the spectral content, and therefore does not require a priori specification of the frequency bands of interest. A time delay embedding with lags from − 7:7 (58 ms) is defined, which means that each state has a [15 × 15] auto-covariance matrix as its observation model (the HMM state observation model means are set to zero). We fit the HMM with three states to reflect the periods of noise, low frequency bursts and high frequency bursts. State specific power spectra are computed for the TDE-HMM using a post hoc multi-taper spectral analysis (Vidaurre et al. 2016). The multitaper method computes the power spectrum multiplying the raw data with a set of seven orthogonal two-second data tapers (discrete prolate spheroidal sequences with a time-bandwidth product of 4) and taking the average spectrum over all the tapers (www.chronux.org; Mitra and Bokil 2007). The HMM-based multitaper approach used extends this method by weighing the contribution of each data point to the final spectral estimation using the state probabilities that the HMM inference provides for each time point in the dataset.
Empirical Source-Space MEG Data
The TDE-HMM is applied to MEG sensor-space data acquired from 33 participants whilst completing a Go-NoGo task [full experimental details can be found in (Nowak et al. 2017)]. During each trial, participants prepare to make an abduction movement of the right index finger. On 80% of trials (Go trials) this movement is completed as expects and on the remaining 20% (NoGo trials) the prepared movement is no performed. Here we analysed the Go trials containing a valid finger movement. The sensor data were preprocessed with Signal-Space Separation Maxfilter before being converted to SPM12 format for processing in the OSL toolbox in MatLab. Each session is bandpass filtered between 1 Hz and 48 Hz and downsampled to 500 Hz. Independent Component Analysis (ICA) is used to identify and reject components of the sensor data relating to ECG and EOG. A single time-course is taken from the first principal component of 12 sensors over the left motor cortex as defined in (Nowak et al. 2017). This time course is epoched to the offset of the finger movement (identified from concurrent EMG recordings) to focus the analysis on the beta rebound. Finally, outlier trials are rejected from further analysis using an automated generalized extreme studentized deviate (GESD) algorithm.
Prior to HMM inference, the epoched data are downsampled by a factor of six to 83.3 Hz. This is as the TDE spectra will span the whole range from zero to Nyquist frequency. Therefore, downsampling will ensure that this range is focused on the frequency range of the physiological oscillations of interest. The TDE-HMM is inferred on the epoched data with six states and an embedding window of 23 samples (276 ms). We use a longer window here than for the simulations to allow the model to capture a greater range of auto-covariance structures in the data.
Once the HMM state time-courses and observation model have been inferred, we compute a range of temporal statistics from the state time-courses and extract the auto-covariance matrices from the observation models. The state-specific power spectra are computed directly from the observation model by taking the fast-Fourier transform (fft) of the middle row of the inferred autocovariance matrix. Next, the state time-courses are averaged across trials to compute a task-evoked fractional occupancy. HMM-regularised time–frequency transforms are computed from the outer product of the task-evoked fractional occupancy and the state-wise power spectra. This provides an alternative time–frequency transform of the data as seen by the inferred HMM. Finally, other task dynamics describing the transient spectral events, or bursts, can be computed. For example, we computed the task-evoked change in lifetimes for a state by creating a vector containing ‘NaNs’ (i.e. Not-a-Numbers) when the state is off, and the lifetime of the state visit when the lifetime is on. The average of these lifetimes across trials then summarises how the duration of state visits change over a trial.
Amplitude-Envelope HMM (AE-HMM) Simulation
First, results are shown when a narrow-band filter is applied prior to computing the amplitude envelope, such that the 35 Hz bursts are excluded. Figure 2b shows how both the HMM and the amplitude threshold are correctly able to identify periods of oscillatory activity for the remaining 20 Hz bursts, though the HMM’s performance does not critically depend on the pre-specification of a threshold value. The state-wise and thresholded amplitude distributions for the two approaches are shown in 2c. Whilst the amplitude threshold splits this distribution at a critical value (vertical dashed line), the two HMM state distributions (i.e. burst state in red, non-burst state in grey) are slightly overlapping reflecting the effects of the temporal regularisation in the HMM. This suggests that a brief period of lower amplitude during a high amplitude burst may not be enough for the AE-HMM to change state.
Next, results are shown when a wider-band filter is applied prior to computing the amplitude envelope, such that the both burst types are included. Figure 2d shows how both the HMM and amplitude threshold are able to identify general bursting around the correct time-periods, though the simple threshold provides a noisier estimate than the HMM in this wider band case. In Fig. 2d more high-frequency dynamics are present in the filtered envelope as this filter has a wider pass-band. This leads to the simple thresholding approach detecting many short bursts, or burst-splits, when the amplitude envelope dips below threshold. In contrast, the HMM is able to identify these as continuous periods of high spectral amplitude. This is further illustrated in Fig. 2e, in which the HMM state amplitude distributions are overlapping between the low and high-power states. This reflects the effects of the temporal regularisation within the HMM. When the envelope is close to the threshold, the HMM will not change state for a tiny fluctuation above or below it. This prevents a long but small amplitude event being split into several shorter events, which can occur when using standard thresholding methods.
While the AE-HMM approach does not require definition of the threshold a priori, neither AE-HMM nor amplitude thresholding is able to distinguish between the two different types of bursts, with their different carrier frequencies. This requirement of correctly specifying the frequency band(s) of interest a priori when using the AE-HMM is a limitation shared with standard thresholding methods.
Time Delay Embedded HMM (TDE-HMM) Simulation
The wider band state-specific spectra inferred with the time-delay embedded HMM allows us to extend the definition of a burst to a period with a distinct power spectrum rather than a period of high amplitude. This enables us to distinguish between events with different frequency profiles within the same model.
Application to Empirical Source-Space MEG Data
TDE-HMM States Describe Time-Windows with Distinct Power Spectra
HMM State Visits Show Rapid Dynamics Which Contribute to the Overall Power Spectrum
As suggested by the simulation in Fig. 1, these temporal statistics can directly relate to the standard power spectrum. Cross-subject variability in 15–30 Hz beta band power (Fig. 5e) is strongly correlated with cross-subject variability in the fractional occupancy of states 4 and 5 (Fig. 5f, g respectively). This suggests that participants with the strongest overall beta power also spend the longest time in the states with strong beta power.
Task Evoked Dynamics in HMM States
Temporal Dynamics in HMM States Contribute to Movement Induced Power Changes
The trial-wise dynamics of the temporal statistics estimated from the HMM allow us to probe the potential scenarios in Fig. 1 in a task setting. Here, we focus on how two states with peaks in the 15–30 Hz beta band (see Fig. 4a) change between a baseline (− 1500 to 750 ms, relative to movement offset) and post-movement beta rebound (500–1500 ms, relative to movement offset) window. Figure 7a, b show a strong increase in beta power between these windows, though they do not tell us which dynamic features underly this change. Here, we explore the beta rebound, an increase in 15–30 Hz power after the offset of a movement typically described with trial-averaged wavelet transforms. Using the HMM states we look at whether this power change could arise from a change in the amplitude, duration or rate of occurrence of bursting events (see Fig. 1) described by the HMM.
The task evoked fractional occupancy is computed by averaging the state post-probabilities across trials (Fig. 7c). In this case, the evoked fractional occupancy tells us the proportion of trials in which each state was active at each given time point. Both states show a significant increase in fractional occupancy in the rebound window compared to baseline, suggesting that an increased number of state events is contributing to the increased power in the beta rebound. Both states show a sharp drop in occupancy during the movement time itself. We further investigate how state lifetime changes over the trial by taking the state time course (containing ones when the state is ‘on’ and nans when the state is ‘off’) and replacing the ones in each state visit with the lifetime of that visit. We can then average this across trials to get a task-evoked state lifetime, similar to the evoked fractional occupancy. State 4 shows a sharp decrease in lifetime during movement and a significant increase during the rebound. In contrast, state 5 has modest but not significant changes between the baseline and rebound windows. The trial average perspective shows that the beta rebound continues for 1.5 s after movement offset (limited by the duration of our trial) the HMM suggests that this is built from brief state visits of 200–500 ms. Finally, we can compute a state-amplitude time-course similar to the evoked lifetimes. Here we replace the ones in the state time course with the observed beta power from a wavelet transform during each visit. Neither state shows a significant change in amplitude between the baseline and rebound windows.
In sum, the HMM representation allows us to explore the temporal dynamics underlying change in power during a task response. In this case, we can show that increased 15-30 Hz power during the beta rebound arises from increased number of visits to states 4 and 5, and an increased lifetime of visits to state 4. This analysis, alongside previous findings, shows that HMM state dynamics can describe complex task dynamics with transient spectrally-specific events such as the ones in this paper (Quinn et al. 2018; Vidaurre et al. 2016). Critically, by targeting the single-trial events, they also allow an analysis of the single-trial parameters that constitute such dynamics, providing greater granularity at the individual trial level than conventional measures of time-resolved trial-average spectral power.
The Hidden Markov Model provides a powerful approach for operationalising the detection of transient spectral events, or bursts of activity, in neuronal time-courses. The time-delay embedded (TDE) HMM is able to concurrently detect different types of bursting across a wide frequency range without the need to predefine a frequency bands of interest, and in general the HMM is able to detect events without a priori threshold specification. The model provides a rich description of both spectral content and temporal dynamics, which can be interrogated to explore the single-trial constituents of trial-averaged neural activity and how they are modulated by different experimental and clinical conditions.
Selecting Between HMM Variants
Several factors affect the choice of which HMM variant to use for a given analysis. The AE-HMM is sufficient for cases when interrogating amplitude dynamics within a known frequency band, but the spectrally-resolved approach of the TDE-HMM case is preferred where the precise spectral content of interest is not known and where there may be multiple burst types. The present applications are limited to detecting events in the 1–48 Hz frequency range as higher frequency gamma oscillations can be challenging to detect. Future work will extend the use of the TDE-HMM and HMM-MAR to detect transient events in the gamma range from broadband signals.
As an alternative, the autoregressive HMM can also be used to explore spectrally specific state dynamics (HMM-MAR; Vidaurre et al. 2016). This defines observed states with distinct autoregressive coefficients (AR). Like the auto-covariance, the AR coefficients are closely related to the power spectrum of the data and can be used to directly compute the Power Spectral Density (PSD). As the HMM-MAR states are defined by distinct autoregressive models, they will also have distinct power spectra. We would expect similar results from the HMM-AR approach. We have used the TDE as it typically performs more robustly, in particular with the shorter time-courses that we have in the MEG dataset used here.
HMM Hyperparameter Selection
A few parameters need to be pre-specified prior to HMM inference. Firstly, a fixed number of states to infer must be defined. A larger number of states provides a finer-grained description of the data but may be more difficult for the software to infer and for us to interpret. This choice should be informed by the question at hand and the level of detail required by the analysis. For instance, two states are sufficient and provide the most straightforward approach for describing changes in narrow-band amplitude envelopes (as in the case of the AE-HMM), treating these like ‘on’ and ‘off’ states. However, allowing only two states would be limiting for the more complex full-spectrum states in the TDE-HMM (in our example we used six). The number of delay-embeddings in the auto-covariance to include in the TDE states must also be defined. Larger auto-covariance matrices allow for more time lags and therefore more structure in the data to be revealed.
The HMM can be sensitive to relatively subtle noise sources. Change in non-neuronal noise or variance in the time-course are likely to be modelled by one or more HMM states. Therefore, particular care should be taken during data pre-processing to ensure that the HMM states are characterising the interesting, neuronal variance in the signal (Quinn et al. 2018). Finally, as it happens with other models (e.g. ICA), the HMM inference has some stochasticity; therefore, the results can slightly vary between inference runs. It is advised to repeat the HMM inference several times to ensure that specific results are consistent.
Statistical testing of the HMM derived burst features can be carried out straightforwardly. Typically focusing on either group differences or task evoked changes in temporal dynamics. Group differences in temporal dynamics can be computed between different scan sessions or subjects within the dataset. Single subject features such as fractional occupancy or state lifetime can be computed from the inferred HMM and carried forward into group level statistics in the same way as standard between-subject variables. For example, this approach has been applied to identify group differences between patients with Alzheimer’s disease and healthy controls in a whole-brain AE-HMM (Sitnikova et al. 2018). Secondly, task or stimulus evoked changes can be computed by epoching the state time-courses and computing evoked state features. Group level GLM analysis of task evoked-fractional occupancies computed from MEG data during a face-perception task show rapid task responses which distinguish between face and non-face stimuli (Quinn et al. 2018).
Summary and Conclusions
We have illustrated the use of an amplitude-envelope HMM to detect periods of high amplitude without pre-specification of an a priori amplitude threshold. Further, the time-delay embedded HMM was shown to be able to concurrently detect multiple types of bursting, each with distinct spectral profiles. Each of these methods estimate the temporal dynamics of spectrally specific events as a state time-course, where each state represents a distinct type of bursting, and each state-visit represents an individual burst event. This can then be used to estimate task response time-courses of burst metrics such as the rate of burst occurrence, burst duration, burst amplitude and interval time.
Whether this temporal dynamic perspective resembles underlying neuronal physiology more closely than sustained oscillation is the subject of ongoing research (van Ede et al. 2018). Nevertheless, there is utility in characterising the rapid temporal features of underlying frequency domain effects with models assuming transient state-visits rather than sustained effects (Quinn et al. 2018; Vidaurre et al. 2016). Novel burst-specific parameters such as rate of occurrence, duration and amplitude are being shown to have clinical (Tinkhauser et al. 2017a) and cognitive (Feingold et al. 2015; Shin et al. 2017) relevance. Finally, the spectrally-resolved HMM variants allow us to compute HMM-regularised time–frequency transforms which recreate reasonable time–frequency responses build from transient spectrally-specific events.
The HMM provides an effective technique for characterising such transient spectrally-specific events, bypassing some of the limitations of amplitude-thresholding approaches. Here, we have presented the relevant theory and motivations behind the use of the HMM as a potential ‘burst-detector’, and have presented an introduction to the available analysis scripts associated with this approach using the HMM-MAR toolbox.
The authors would like to thank Charlotte Stagg and Emily Hinson for collecting and providing access to the MEG data.
This research was supported by the NIHR Oxford Health Biomedical Research Centre, a Wellcome Trust Strategic Award (Grant 098369/Z/12/Z), Wellcome Investigator Awards to MWW (106183/Z/14/Z) and ACN (104571/Z/14/Z) and a James S. McDonnell Foundation Understanding Human Cognition Collaborative Award (220020448). The Wellcome Centre for Integrative Neuroimaging is supported by core funding from the Wellcome Trust (203139/Z/16/Z). MB is supported by the UK Quantum Technology Hub for Sensors and Metrology, funded by the Engineering and Physical Sciences Research Council (EPSRC) (EP/M013294/1). ZAS is supported by a studentship from the Oxford Nottingham Biomedical Imaging Centre for Doctoral Training Centre (EPSRC/MRC - EP/L016052/1).
Compliance with Ethical Standards
Conflict of interest
The authors declare that they have no conflict of interest.
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