2.1.

Source of Signal

Single electrode recording has been in use for decades, but recent advances to multi-electrode arrays have enabled researchers to characterize the macroscopic dynamic patterns. Electrode arrays can be used as a tool to study spatiotemporal dynamics by measuring changes in local field potentials (LFPs). LFPs have several qualities that make them suitable for studying neural brain dynamics. LFPs represent the aggregate activity of small populations of neurons characterized by their extracellular potentials.³² A cardinal feature of this signal is that it represents activity from many neurons in the vicinity of the recording site. Thus, it samples local neuronal populations and captures network dynamics that would otherwise be missed by single-cell recordings.³³ These network dynamics are what define LFP, which has a spatial resolution of 200 to $400\mu \mathrm{m}$ and a temporal resolution on the order of millisecond. A drawback to LFPs is that the spatial coverage is limited to a single column or activity across distinct columns with multiple arrays. Because of this, most of the identified dynamic patterns inform the localized occurrence and spread of spontaneous activity rather than a brain-wide understanding of spatiotemporal dynamics.

2.2.

Dynamic Patterns

Electrode arrays have been used to identify recurring traveling waves in spontaneous activity in both cortical slices and surface recordings.^6,8–35

In vitro experiments have proven to be beneficial for elucidating the mechanism that drives the observed recurrent propagation. Slow rhythmic activity ($<1\mathrm{Hz}$) was generated in vitro when slices of the ferret neocortex were placed in a bathing medium that mimics the extracellular ionic composition in situ.⁶ The transition from a depolarized to hyperpolarized state recurred with a periodicity of once every $3.44\pm 1.76\mathrm{s}$.⁶ These oscillations were initiated by layer 5 excitatory interactions between pyramidal neurons. For in vitro slice preparation, the slow oscillation then propagates within these infragranular layers.⁶ These oscillations were further studied across cortical slices using multi-electrode arrays to investigate local and global network dynamics. It was found that activation waves systematically propagated parallel to the cortical surface, with wide variability in spatial source and speed.^6,8 Irrespective of their variability, wavefronts revealed loci across L4/L5, adding to the evidence that most excitable cell assemblies reside in L5.^6,7,8

Further evidence of the initiation souce in L5 was also found in vivo validating the role of layer ⅘ in “up” state initiation.^9,10 Ensemble spatiotemporal dynamics of spontaneous depolarizations were either brief and localized to an area of a barrel column or occurred as propagating waves dependent on local glutamatergic synaptic transmission in layer ⅔.¹¹ This flow of excitation is strictly feed forward from layer 4 neurons projecting to layer ⅔. Individual layer ⅔ pyramidal neurons are oriented preferentially along the rows of the barrel field, inducing preferential spread of excitation along the cortical axis.¹¹ Neurons in the rat somatosensory cortex revealed that “up” state onsets initiate a sequential spread of activity across the population as shown in Fig. 1(a).¹² They found that sequential structure was expressed only in the first $\sim 100\mathrm{ms}$ after the “up” state initiation and was most readily detected by the number of neurons with the highest firing rates ($>2\mathrm{Hz}$).¹² A subset of “up” states then propagated as traveling waves. Regardless of their propagation direction, these traveling waves initiated similar local sequences. These patterns were found in both anesthetized and unanesthetized conditions.¹² An observed difference between the two states was that the induced sequences under anesthesia lasted almost twice as long as those in unanesthetized animals.

Fig. 1

(a) Pseudocolor plot showing the normalized activity of a simultaneously recorded population triggered by “up” state onset, arranged vertically by latency. The dots indicate from which shank the neurons were recorded. Reprinted from Ref. 12 Copyright 2007 National Academy of Sciences. (b) Classification and detection of specific wave patterns at the cortex-wide scale. Reprinted from Ref. 15. (c) Spatial configuration of four microstate classes. SCH, individual with schizophrenia; HC, healthy controls; All, all participants in the study. Note how topographies extend over wide-scale areas representing global brain electrical events. Reprinted from Ref. 36.

Both in vitro and in vivo studies using electrode arrays have definitively demonstrated rhythmic activity that propagates along the cortex. These direct measurements of relatively localized neural activity help to validate the widespread patterns of propagation observed with other modalities and allow the mechanisms underlying the generation and coordination of such activity to be rigorously probed on a larger scale.

3.1.

Source of Signal

An important component to studying the spatiotemporal dynamics of the brain is the understanding of the cellular mechanisms, something that cannot be done with LFPs. This includes the monitoring of membrane voltage at the cellular, circuit, and systems levels. A game-changing advance made in recent years using genetically engineered animal models has enabled the monitoring of these cellular mechanisms. These optical tools include voltage-sensitive dies and genetically encoded indicators of voltage (GEVIs) or calcium (GECIs). The set of optical imaging tools is cell type-specific, less invasive, and able to relate activity and anatomy and to facilitate long-term recordings of individual cell’s activities over weeks.³⁷ Due to their inherent properties, there are key conceptual differences between GEVI and GECI signals. Things that must be considered are (1) the mode (calcium or voltage), (2) site of protein expression, and (3) sensitivity to action potential versus synaptic potential. GEVI signals largely represent the synaptic input arriving into a neural circuit whereas GECI signals present the action potential output generated in the neural circuit.³⁸

Their differing sources, in turn, impact characteristics of the measured signal including the resolution and signal strength. The typical spatial resolution for population activity is 50 to $100\mu \mathrm{m}$.³⁸ The temporal resolution of calcium imaging is limited by calcium ion dynamics in the neurons and is usually too slow for following brain oscillations at frequencies $>10\mathrm{Hz}$, a limitation that is not shared by voltage imaging. Calcium indicators, however, usually produce larger fractional changes in fluorescence, whereas voltage-sensitive dyes provide smaller signals. For population imaging, with no cellular resolution, GECI optical signals showed an 8 to 20 times better signal-to-noise ratio (SNR) than GEVI signals.³⁸

These tools can be combined with intrinsic optical signal imaging (IOSI), which makes use of the spectral properties of hemoglobin (Hgb), which has different absorption properties when oxygenated or deoxygenated, to measure changes in brain activity.³⁹ IOSI benefits particularly from a relatively simplistic experimental setup in which there is no need for a genetically engineered animal. IOSI can provide information about hemodynamics that is complementary to the information about neural activity obtained with fluorescence imaging techniques.⁴⁰

3.2.

Dynamic Patterns

Optical imaging can measure activity from single neurons to cortex-wide spatiotemporal dynamics. Imaging cortex-wide patterns reveal critical neuronal dynamics that have unique spatiotemporal dynamics for slower and faster frequency bands of activity.^15,11,26,13

Spontaneous infraslow activity ($<0.1\mathrm{Hz}$) travels through the cerebral cortex along stereotypical spatiotemporal trajectories that are recapitulated in Hgb optical imaging. The spatiotemporal trajectories of the infraslow calcium signal and the Hgb signals prove to be highly similar, demonstrating that neurovascular coupling is preserved during spontaneous activity.¹³ The time scale for this activity ranges from $\pm 0.5\mathrm{s}$. Under anesthesia, infraslow calcium signals travel posterior–anterior with posterior leading anterior activity by $\sim 0.5\mathrm{s}$.¹³ This is consistent with other reports of correspondence between infraslow neural activity and hemodynamic signals.^41,42 This relationship does not hold for slightly higher frequency bands of 1 to 4 Hz (Delta Band).¹³

Delta band spontaneous activity ranges from $\pm 10\mathrm{ms}$ and travels in a reciprocal direction along the anterior–posterior axis of the mouse cortex. Under anesthesia, the anterior delta band leads the posterior delta by $\sim 100\mathrm{ms}$.¹³ This result is consistent with others that have shown that delta activity travels anterior–posterior in anesthesia and sleep.^43,14 Dynamics of the delta band were also investigated for anesthetized mice using voltage imaging.¹⁵ By treating the spontaneous neural activity as propagating waves, delta band activity is shown to propagate in heterogeneous directions. Specific wave patterns found included plane waves, standing waves, and source, sink, and saddle patterns [Fig. 1(b)]. Plane waves are those that travel anterior to posterior, whereas standing waves are defined as periods in which there is no apparent wave propagation across the analysis window.¹⁵ These patterns were observed globally and locally in mice, with local wave patterns of source, sink, or saddle emerging in preferred spatial locations.¹⁵

Most of the dynamic analysis that has been done so far using optical imaging has been confined to two frequency bands: infraslow activity and the delta band. It was found that infraslow motifs ($<0.1\mathrm{Hz}$) are analogous to cortical motifs observed from slow frequency spontaneous activity (0.5 to 6.0 Hz),²² in contrast to prior studies that showed the direction of propagation was different for delta and infraslow waves. A clear area for future research is determining how the spatiotemporal dynamics of these two bands interact. This is particularly important given that these slow frequencies are relevant for interpreting fMRI.

4.1.

Source of Signal

Due to its wide availability, intrinsic contrast mechanism, and ability to capture whole brain changes in activation, fMRI is one of the most widely used functional imaging techniques in humans and other animals.⁴⁴

Most fMRI studies rely on blood-oxygen-level-dependent, or BOLD contrast, as an indirect measure of neural activity in the brain.⁴⁵ The BOLD signal is a composite hemodynamic signal that is affected by factors including cerebral blood flow (CBF) and changes in the ratio of diamagnetic oxyhemoglobin to paramagnetic deoxyhemoglobin (HbR) in response to the increased metabolic demand of neurons and other cells in the brain. The increase of HbR in the wake of neural activity can be felt by the local protons in water, affecting their T2 and T2* relaxation times, resulting in an MRI-based signal that can be used for functional imaging.^44–47 In other words, the BOLD signal that is almost universally used in fMRI studies is an indirect measure of neural activity.

The BOLD signal directly constrains the temporal and spatial resolution of fMRI and has important implications for the use of fMRI to study the spatiotemporal dynamics of the brain. The BOLD signal has a temporal resolution on the scale of the hemodynamic response to neural activation, which occurs on the order of a few seconds after neural activity. In humans, the hemodynamic response typically has a width of about 3 s and peaks between 5 and 6 s, but this is variable across conditions and animal models.⁴⁴ The spatial resolution of BOLD fMRI (and the SNR) is dependent on the strength of the applied magnetic field.^44,48 The typical voxel size in fMRI can range from 3 to 4 mm in lower field strength (1.5 to 3 T) magnets and from 400 to $500\mu \mathrm{m}$ with field strengths of 7 T and above.^44,48

4.2.

Dynamic fMRI Patterns

4.2.1.

Quasi-periodic patterns

Quasi-periodic patterns, or QPPs, are reliably recurring spatiotemporal patterns of propagating activity.^16,17,18 The patterns are detected in fMRI data [typically resting state (rs)] using a correlation-based iterative approach without a user-defined start point (for more details, see Ref. 17). QPPs are an infraslow pattern (below 0.5 Hz), occurring on a timescale of 0.2 to 0.1 Hz, or 1 cycle every 5 to 10 s. QPPs can be thought of as rhythmic waves that are a combination of standing and traveling waves. Originally described in rats in Majeed et al.,¹⁷ QPPs have since been detected in several human datasets.

A major feature of QPPs is that they show a reliable anti-correlation in propagating activity between the well-described default mode networks (DMNs) and task-positive networks (TPNs) [Fig 2(b)].^16,19 The DMN and TPN are intrinsic connectivity networks that are traditionally associated with either introspective self-referential cognition (mind wandering) or with the conscious direction of attention or processing of incoming stimuli, respectively.^16,20 QPPs also contribute to normal functional connectivity and the level of anti-correlation typically seen between the DMN and TPN.¹⁶ The contribution of QPPs to typical functional connectivity in attentional networks may shed light on the etiology of diseases and brain states related to disrupted attention. Work by Abbas et al.,¹⁶ for example, found a reduced contribution of QPPs to functional connectivity in individuals with attention-deficit/hyperactivity disorder.

Fig. 2

(a) CAPs showing distinct co-activation in “task-positive” areas and consistent deactivation in “task-negative” areas. Reprinted from Ref. 23. (b) Spatiotemporal patterns seen in the resting-state QPP. Reprinted with permission from Ref. 16.

The neural origins and mechanisms underlying the generation of QPPs is an area of active research, but early work with local field potentials and resting-state fMRI (rs-fMRI) in rodents suggests that QPP activity is correlated to infraslow electrical activity.^18,21 Spontaneous infraslow patterns have also been detected in mice using wide-field voltage-sensitive dye imaging, but specific mechanisms underlying the generation of infraslow patterns are still unclear.²² A combination of multimodal and/or cell-type specific techniques in rodents may provide the best approach to better understanding the origins and role of QPPs in dynamics and functional connectivity.

4.3.

Spatiotemporal fMRI Pattern Summary

Dynamic fMRI analysis of QPPs, CAPs, and other spatiotemporal trajectories already shows great promise in detecting unique spatiotemporal patterns that are missed by traditional static fMRI analysis. Each of these approaches has led to new insights into spatiotemporal dynamics and has generated a validation of the findings shared between the approaches. For example, QPPs, CAPs, and the variational autoencoder approach to spatiotemporal patterns all validate some aspects of DMN/TPN anti-correlation. A common drawback of all of these spatiotemporal analysis methods is a lack of understanding of the origins of the patterns.

As previously mentioned, multimodal approaches in animals and humans provide the most promising route to a better understanding of the neural basis of these patterns and to a translational impact. Pairing fMRI with cell-type-specific imaging techniques such as optical imaging, opto/chemo-genetics, or electrophysiology in animal models will lead to better models of the neural substrates of cortex-wide spatiotemporal patterns and give experimental insight into circular causality across scales.

5.1.

Source of Signal

The primary source of the signal captured by electroencephalography (EEG) recordings is the electrical activity generated by postsynaptic potentials in the apical dendrites of cortical pyramidal neurons.^51,52 Because the sensors are located relatively far from the neurons, the EEG signal represents the summed activity of a large number of neurons spread across the cortex.

EEG’s sensitivity to electrical events on the order of postsynaptic potentials means it has significantly higher temporal resolution than fMRI. EEG can capture electrical events ranging from millisecond to hundreds of milliseconds.⁴⁴ Although the temporal resolution of EEG is very fast, the spatial resolution of EEG is one of its major drawbacks. EEG relies on the placement of scalp electrodes, with a higher number of electrodes resulting in better signal localization and resolution.⁵² Even with a high number of scalp electrodes (ranging from 4 to 256 electrodes in some studies⁵³), the spatial resolution of EEG is limited to between 10 and 20 mm and is limited to electrical activity at the cortical surface, as the sources rely on superficial postsynaptic potentials.^44,51

Individual postsynaptic potential events as measured with EEG are extremely small and do not result in a large signal.⁵¹ However, when a large number of excitatory or inhibitory postsynaptic potentials [excitatory post - synaptic potentials (EPSPs) or inhibitory post - synaptic potentials (IPSPs], respectively) occur with synchrony, the effects summate and can result in detectable EEG waves. The frequency and amplitude of such waves due to variation in underlying synchrony constitute the primary signal that can be used in EEG to measure differences across brain states or disease states.⁵¹ A number of important waveforms and patterns have been detected with EEG that correlate with different brain states, levels of consciousness, sensory inputs, or disease states. However, the canonical oscillatory bands of EEG such as delta, theta, alpha, or beta waves are not the focus of this review. Instead, EEG microstates will be discussed, as their spatiotemporal characteristics are similar to CAPs and comparable optical spatial patterns.

5.2.

Dynamic Patterns

EEG microstates are spontaneous spatiotemporal patterns of electrical activity occurring on the sub-second timescale and lasting between 80 and 120 ms.^26,54 These microstates are described as being quasi-stable for those brief sub-second periods. In other words, EEG microstates are a form of standing wave. EEG microstates are normally measured during rs (eyes closed). Somewhat similar to QPPs or CAPs observed in rs-fMRI, EEG microstates are global patterns that reliably recur temporally and topographically across subjects.^26,27

Similar to functional networks such as the DMN or TPN, defined in fMRI studies, EEG microstates have also led to the description of canonical brain states. Four canonical classes of microstate maps that are reliable across studies have emerged over time.^54,55,28 Changes in the typical spatiotemporal configuration of these activation maps have been observed during different cognitive and neurological states [Fig 1(c)]. For example, a 1998 study by Lehmann et al.⁵⁶ presented human subjects with a tone at a random interval and then asked them to relay what was going through their mind just before they heard the tone. Thoughts were then classified as visual or abstract thinking and then compared with the EEG microstate topography at the moment preceding the report of visual or abstract thinking. The microstate associated with visual thoughts closely resembled the second canonical EEG microstate, which has been implicated in resting visual network activity.^54,56 In a related study, EEG microstates were found to differ significantly when subjects were presented with words associated with either imagery or abstract meaning.⁵⁵ Studies such as these have led to the suggestion that microstates may be the fundamental building blocks or units of cognition or mentation.⁵⁴ In addition to normal cognition or mentation, EEG microstates have also been shown to differ in psychiatric disease states such as schizophrenia [also see Fig 1(c)].²⁸

As with fMRI, combining multiple modalities in both humans and animals may be the most promising route to an integrated understanding of the origins of spatiotemporal patterns such as microstates detected in EEG. In humans, studies have paired EEG with simultaneous fMRI to compare EEG microstates with BOLD activation maps, giving some insight into the source localization of EEG microstates.^29,30 To better understand the neural origins of EEG microstates, EEG could also potentially be paired with fMRI or other more invasive and cell-type-specific approaches in transgenic animal models. Multimodal animal approaches could shed light on the cross-species persistence of the four canonical EEG microstates seen in human studies and provide experimental tools to investigate their origins.

7.1.

Complementary Multimodality Studies

Each of the aforementioned modalities has its own strengths and weaknesses as outlined in Table 1. To leverage their individual strengths, multimodal imaging approaches have become increasingly popular. Multimodal imaging has the promise of allowing for not only the study of how different signals are related across scales but also a better understanding of how the observed dynamic patterns are influenced across these scales. There is also no known timing for wide-scale intrinsic brain activity, and simultaneous measurement at different spatial and temporal scales is needed to bridge this gap.

EEG is a valuable multimodal tool for correlating electrophysiological events with dynamic patterns. Recent efforts to better understand the origins of EEG microstates have paired EEG with fMRI, in which source localization of microstates can be inferred by comparing simultaneously measured BOLD activation.^29,30 Simultaneous recordings of EEG microstates and BOLD fMRI show that some canonical rs networks from fMRI such as the DMN correspond to microstate associated networks as measured with EEG.^29,30 Beyond microstates, other multimodal studies have compared the infraslow dynamics of multichannel EEG with BOLD fMRI. For example, using a multimodal approach with simultaneous EEG and fMRI in human subjects, it is possible to correlate the infraslow dynamics of scalp potentials (0.01 to 0.1 Hz) with the infraslow dynamics of the BOLD signal. Using this approach, it has been shown that scalp potentials from EEG correlated strongly to fMRI/BOLD dynamics temporally and spatially.^65,66 Anatomically, EEG dynamics correlate with the BOLD activity of well-defined intrinsic connectivity networks in fMRI including the DMN and the TPN.⁶⁵ Infraslow dynamics have also been studied using simultaneous LFP and fMRI.⁴² A spontaneous BOLD signal at the recording sites was found to exhibit significant localized correlation with the infraslow LFP signals as well as with the slow power modulations of higher-frequency LFPs (1 to 100 Hz) with a delay comparable to the hemodynamic response time.⁴²

Simultaneous multimodal methods to measure complementary features of activity using optical imaging and fMRI have also been described.^81–70,71 Wide-field optical imaging provides the advantage of covering a large field of view while measuring cell-type-specific signals.^67,69,70 There have been great advances made in understanding the functional roles of different cell types, but what remains unknown is how the activity at the cellular scale affects the activity measured at a global scale recorded with fMRI. Because the brain exhibits structured activity at all scales, a better understanding of how different levels contribute to the system as a whole is still needed. The combination of wide-field optical imaging with fMRI to study how different cell types influence hemodynamic regulation is particularly promising.^67,70,72 Another potential benefit of simultaneous optical imaging and fMRI is that the whole brain coverage of fMRI provides some information about activity in subcortical areas, which cannot be observed optically but which plays an important role in the generation of coordinated brain activity.

One of the main limitations of wide-field optical imaging is that it does not allow for the resolution of single neurons, capillaries, or subcortical nuclei.⁶⁹ Fiber photometry is another promising approach that has been increasingly used for multimodal fMRI studies.^72–76 Fiber photometry allows for cell-type-specific fluorescence imaging such as wide-field optical imaging with the placement of one or more fibers that can target specific neural populations or regions of interest.

Multimodal fiber photometry has been successfully paired with fMRI in rats, as in Liang et al.⁷⁵ and Tong et al.,⁷³ and in mice, as in Wang et al.⁷² and Schlegel et al.⁷⁶ The targeting specificity and subcortical reach of fiber photometry mean that it can be used to compare multimodal signals obtained in different nuclei of interest. This can be done in parallel animals or with multiple fibers within one animal.⁷⁷ Fiber photometry tracts can be multichannel and capture signals from multiple fluorophores or physiological sources at once.⁷⁴ Chao et al.⁷⁴ recently used a fiber photometry/fMRI approach to simultaneously measure GCaMP6f fluorescence, photometry-based cerebral blood volume (CBV), and fMRI CBV. This fiber photometry approach allowed them to estimate hemodynamic response functions in different subcortical nuclei, an analysis that could not be made with a superficial approach such as wide-field optical imaging.

A multimodal fiber-optics approach was used in Schwalm et al.⁷⁸ to study slow-wave brain dynamics. Using fiber photometry to record calcium indicators in populations of the cortex and thalamus in anesthetized rats with simultaneous BOLD fMRI, they found that the calcium activity of the entire cortex was related to the generation of slow-wave BOLD activity.⁷⁸ In another fiber optics example, Pais-Roldán et al.⁷⁹ used fiber photometry Ca+2 imaging and BOLD fMRI to relate pupil dynamics to the global fMRI signal and found a positive correlation between pupil dilation and the activity of a population of noradrenergic cells in the ventral brainstem. He et al.⁸⁰ used fiber optics with simultaneous fMRI to investigate the relationship between BOLD, CBV, and neuronal activity and found that the Ca+2 signal from neurons is linked to intrinsic cerebral vascular oscillations.

Given that complex brain-wide spatiotemporal patterns are unlikely to be driven by the activity of a single brain’s nuclei, the advantage of targeting multiple subcortical nuclei makes multimodal fiber photometry fMRI studies an excellent multimodal approach to studying brain dynamics. (For a more in-depth review of the multi-modal application of fiber optics and optogenetics in fMRI studies, see Albers et al.⁸¹)

An alternative approach that has been used to track Ca+2 activity in relation to the BOLD fMRI signal is the use of magnesium-enhanced MRI (MEMRI) ion imaging.⁸² For example, Duong et al.⁸² used anesthetized rats and MEMRImagnesium Ca+2 imaging to show that synapse dependent Ca+2 signal was correlated with BOLD and cerebral blood flow. The changes detected with MEMRI are much slower than those observed with methods such as optical imaging, often taking 24 to 48 h to show the enhancement throughout a pathway.⁸³ The slower time scale makes it better suited to imaging long-term changes rather than the fast intrinsic dynamics that are the primary focus of this review.

7.2.

New Imaging Tools

Ideally, to understand the relationship of neural activity across spatial and temporal scales, recordings should be made simultaneously from all neurons in the brain. To date, no imaging modality is capable of this task. Some, such as fMRI, obtain whole-brain coverage but lack sensitivity to individual neurons; others, such as electrophysiology, can detect activity in a single neuron but have limited spatial coverage. This gap is well-recognized in the field of neuroimaging, and improved methods that more closely approach the ideal case are constantly being developed, in part due to support from the BRAIN initiative. Larger microelectrode arrays, optical reporters that provide greater depth sensitivity, and higher resolution fMRI studies have all had a positive impact on the coverage and/or resolution that can be obtained.

Functional ultrasound (fUS) also presents a unique and promising approach to studying large-scale spatiotemporal patterns. Initially developed in rats,⁸⁴ and relying on a thinned-skull cranial window, Osmanski et al.⁸⁴ found that fUS is capable of increased spatial and temporal resolution compared with fMRI, with spatial resolution on the order of $100\mu \mathrm{m}$ and a temporal resolution of 2 ms. The equipment for fUS is also significantly more portable and less expensive than fMRI. Recently, fUS has been successfully used in mice to measure the activity of the default mode network.⁸⁵ Ferrier et al.⁸⁵ found that, under an awake or slightly sedated state, mice showed deactivation of hubs of the DMN, including the retrosplenial cortex, validating the use of fUS to study functional networks and spatiotemporal dynamics in mouse models. fUS has also been used in human neonates.⁸⁶ Baranger et al.⁸⁶ showed that fUS can be used as an effective and portable bedside method for measuring functional connectivity in human neonates in both healthy and diseased states. fUS has also been combined with EEG in human neonates to study sleep phases and epilepsy.⁸⁷ In both animal models and human neonates, fUS provides a portable and cost-effective alternative to fMRI that offers improved spatial and temporal resolution. However, fUS is limited in its potential to capture whole-brain activity in adult humans because of its poor penetration through the skull, and it is better suited to rodents with a cranial window or human neonates before the adult formation of the skull is complete.

7.3.

Role of Spontaneous Activity in Brain Function

Many experimental approaches to understanding functional aspects of different stimuli or tasks rely on averaging large numbers of trials to effectively suppress background activity and highlight only activity that is repeatable across trials. However, there is growing appreciation that the dynamics of ongoing, systems-level activity influence activity in different trials and account for much of the variability that is observed. As an example, infraslow dynamic patterns detected with EEG have been shown to have predictive power for the response to incoming somatosensory input. In a 2008 study by Monto et al.,⁸⁸ human subjects received a weak electrical stimulus to the right index finger and their ability to detect the stimulus was correlated with the phase and amplitude of infraslow EEG dynamics. It was found that the likelihood of a subject perceiving a weak stimulus was significantly higher during the rising phase of the infraslow EEG fluctuations compared with the other phases.⁵² Studies such as this demonstrate the influence of spontaneous dynamics on perception and task performance and make it clear that the “circular causality” between dynamics at different scales has important implications for human behavior.

More recently, Iemi et al.⁸⁹ also used EEG to study the variation in response to stimuli based on internal states. Specifically, Iemi et al.⁸⁹ measured the variation in the event-related potential (ERP) compared with the EEG waveform present in the subject when the stimulus was received. They found that the ERP changed if the stimulus (black and white checkerboard images) was applied during strong alpha or beta waves.⁸⁹ In rodent studies of the role of spontaneous activity in modulating stimulus-response, Karvat et al.⁹⁰ used a closed-loop LFP system to test the hypothesis that beta-band activity can mask the response to an externally applied stimulus. Using LFP, beta-band activity was measured and compared with sensory-evoked responses in rats. It was found that beta-power activity in the rat somatosensory cortex was anti-correlated with sensory-evoked responses. In other words, the incoming sensory input could be masked depending on the band of spontaneous background activity occurring in the somatosensory cortex.

Studies such as these provide further evidence that spontaneous background activity heavily modulates or even masks perception and reaction to external stimuli. Further work is needed across modalities and models to better characterize the interplay between multiscale, ongoing activity and behavioral outcomes such as perception or task performance.

7.4.

Astrocytic Contribution to Brain Wide Patterns

Recently, GECIs have been combined with fiber photometry and fMRI in mouse models to explore the contribution of astrocytic activity to the BOLD signal and brain-wide patterns. For example, Gray et al.⁷⁷ used simultaneous fiber photometry in the cerebellum and V1 of anesthetized mice to show that astrocytic calcium signaling tracks the dynamics of noradrenergic neurons in response to stimuli and that astrocytes may act as amplifiers of vigilance states. In the thalamus, Wang et al.⁷² used simultaneous GECI optical fiber recording and fMRI in anesthetized rats to relate astrocytic calcium signal to the BOLD signal both at rest and in response to a stimulus. They found that the evoked astrocytic Ca+2 signal positively correlated with the BOLD signal, whereas the rs or intrinsic Ca+2 signal negatively correlated with the BOLD signal.⁷²

Going forward, multimodal fMRI approaches are the most promising route to a better understanding of the role of astrocytes in brain-wide spatiotemporal dynamics. In addition to pairing cell-type-specific fiber photometry and optical imaging with fMRI, chemogenetics and optogenetics provide experimental options to drive the activity of astrocytic Ca+2 signals and study their role in brain-wide dynamics.

7.5.

Complex Systems Analysis

With coordinated patterns of activity at multiple spatial and temporal scales, the brain has all of the hallmarks of a complex system and shares features with other complex systems (e.g., global climate). New methods for characterizing these complex systems and their cross-scale interactions are continually being developed, and each new tool provides another view of the functional organization of the brain. For example, some research suggests that the brain as a complex system self organizes into a critical state. In this state interactions between system components lead to scale-invariant events that are beneficial for the system performance by obtaining an optimal balance of stability and flexibility.^91,92 These tools and concepts can inform further research that aims to drive an individual brain into particular states using invasive or noninvasive brain stimulation technology, moving the field closer to truly personalized medicine.