 Research
 Open Access
 Published:
Datadriven visualization of multichannel EEG coherence networks based on community structure analysis
Applied Network Science volume 3, Article number: 41 (2018)
Abstract
An electroencephalography (EEG) coherence network is a representation of functional brain connectivity, and is constructed by calculating the coherence between pairs of electrode signals as a function of frequency. Typical visualizations of coherence networks use a matrix representation with rows and columns representing electrodes and cells representing coherences between electrode signals, or a 2D nodelink diagram with vertices representing electrodes and edges representing coherences. However, such representations do not allow an easy embedding of spatial information or they suffer from visual clutter, especially for multichannel EEG coherence networks. In this paper, a new method for datadriven visualization of multichannel EEG coherence networks is proposed to avoid the drawbacks of conventional methods. This method partitions electrodes into dense groups of spatially connected regions. It not only preserves spatial relationships between regions, but also allows an analysis of the functional connectivity within and between brain regions, which could be used to explore the relationship between functional connectivity and underlying brain structures. As an example application, the method is applied to the analysis of multichannel EEG coherence networks obtained from older and younger adults who perform a cognitive task. The proposed method can serve as a preprocessing step before a more detailed analysis of EEG coherence networks.
Introduction
EEG records the electrical activity of the brain by attaching electrodes to the scalp of a subject at multiple locations. Synchronous electrical activity in brain regions is generally assumed to imply functional integration. Such synchronization occurs over a large range of scales. For example, local synchronization occurs during visual processing, synchronization between neighboring temporal and parietal cortical regions is observed during multimodal semantic processing, and longrange frontoparietal interactions occur in working memory retention and mental imagery (von Stein and Sarnthein 2000). A large number of methods have been proposed to measure the synchrony between pairs of brain regions, and these measures are often closely correlated (Nunez et al. 1997). EEG coherence is one of these measures, which is calculated between pairs of electrode signals as a function of frequency (Halliday et al. 1995; Maurits et al. 2006).
Visualization provides a visual representation of the data to help people carry out analysis tasks effectively. It happens at an early stage in the process, usually before a statistical or computational analysis, and it allows people to explore their data before knowing exactly what kind of questions to ask (Munzner 2014). After the questions have been welldefined, existing methods such as machine learning can be used to answer them. For the case of brain connectivity, visualization can lead to the discovery of unanticipated patterns (Alper et al. 2013), thus providing insight into brain functioning. In this way it can help neuroscientists to understand how the brain works, especially for the case where no a priori assumptions or hypotheses about brain activity in specific regions are made (Ma et al. 2015; Li et al. 2012; Xia et al. 2013; Christodoulou et al. 2011; Gerhard et al. 2011; Fujiwara et al. 2017).
An EEG coherence network represents functional brain connectivity, more precisely, the coherences between pairs of signals recorded by the electrodes. However, visualization of highdensity or multichannel EEG (at least 64 electrodes) coherence networks is not always managed well (ten Caat et al. 2008). Typical visualizations of coherence networks are a matrix representation with rows and columns representing electrodes with cells representing coherences between electrode signals or a nodelink diagram with vertices representing electrodes and edges representing coherences (see Fig. 1). Edges are considered significant when their coherence passes a significance threshold (Halliday et al. 1995), see also the description of the experimental setup in the “Results” section. However, such representations can suffer from some drawbacks. The matrix representation is very effective for visualizing large and/or dense networks (Alper et al. 2013; Yi et al. 2010), but the relative spatial location of electrodes is hard to embed in this matrix. Therefore, brain connectivity network visualization is complex. The common focus on specific connections is often insufficient to explain all aspects of information contained in the network, because the spatial context of the connections is also crucial in the analysis of brain connectivity. In contrast, the nodelink diagram is a straightforward method of visualizing networks that preserves spatial information about the electrodes well. This visualization, however, suffers from the potentially large number of overlapping edges when visualizing dense networks, which makes it hard to distinguish connections (Kamiński et al. 1997).
To study connectivity patterns in the coherence graph, researchers often employ a hypothesisdriven or semidatadriven definition of certain regions of interest (ROIs), in which all electrodes are assumed to record similar signals because of volume conduction effects (Gladwin et al. 2006; Lachaux et al. 1999). However, these methods generally depend on certain assumptions or hypotheses, where an a priori selection of relevant electrodes is made. As a consequence, not all the available data is used and the underlying brain network is not fully explored.
As an alternative to the hypothesisdriven and semidatadriven approaches, ten Caat et al. (2007a,, 2008) proposed a method for detection of datadriven ROIs, referred to as functional units (FUs). An FU is represented in the coherence graph by a spatially connected maximal clique (a clique is a vertex set in which every twoelement subset is connected by an edge). Because larger ROIs are assumed to correspond to stronger source signals, larger FUs are considered to be more interesting. Therefore, the maximal clique based (MCB) method of ten Caat et al. (2007a) focused on maximal cliques, for which vertex sets are as large as possible. Since the MCB method is very timeconsuming (time complexity O(3^{n/3}), with n the number of vertices), as an alternative a watershed based (WB) method was proposed that detects spatially connected cliques in a greedy way (ten Caat et al. 2007b). To reduce the potential oversegmentation of this approach, an improved watershed based method (IWB) (time complexity O(n^{2} logn)) was proposed that merges FUs if they are spatially connected and if their union is a clique (ten Caat et al. 2008). The WB and IWB methods are up to a factor of 100,000 faster than the MCB method for a typical multichannel setting with 128 EEG channels, thus making interactive visualization of multichannel EEG coherence possible. The FUs detected by the (I)WB method are similar but not identical to the FUs detected by the MCB method. To distinguish them we therefore denote the corresponding FUs by FU^{MCB} and FU^{IWB}, respectively.
To visualize the FUs, ten Caat et al. (2007a) introduced the concept of FU map, which represents the FUs as a set of Voronoi cells (one for each electrode) with identical gray value, with different gray values for adjacent FUs (see Fig. 7 in the “Method” section for an example). A colorcoded circle is placed at each FU center that represents the average coherence of this FU, and a colorcoded line is drawn between pairs of FU centers if the average coherence between these two FUs exceeds the coherence threshold. This visualization shows both synchronization within and between FUs.
A drawback of the MCB and IWB methods is that the analysis of local synchronization is difficult, since these methods detect maximal cliques, that is, groups of spatiallyconnected electrodes that are as large as possible. Specifically, the MCB method views coherences above or equal to the predefined threshold equally while the IWB method clusters electrodes based on their neighbours which have the largest coherence value with them, without considering how strong the electrodes are connected with the other members of the group. Therefore, in this paper we propose an alternative method, based on detecting densely interconnected groups of brain regions known as network communities, which can be observed either in anatomical or in functional networks (Honey et al. 2007; Rubinov and Sporns 2010). The composition of these individual groups, known as community structure, is usually obtained by optimizing the modularity measure, as proposed by Newman (2004). We use the community structure analysis of a network as a datadriven approach to facilitate the visual analysis and interpretation of multichannel EEG coherence networks. The proposed method, referred to as the community cliquebased (CCB) method, partitions the set of electrodes into several datadriven ROIs (communities) based on their connections and positions. As a result, electrodes within the same community are spatially connected and are more densely connected than electrodes in different communities. For brevity, the ROIs obtained by community detection will still be called “functional units”, but denoted by the symbol FU^{CCB} to distinguish them from the functional units obtained by the MCB and IWB methods. The functional units detected by the CCB method are visualized in an FU^{CCB} (functional unit) map, in exactly the same way as for the FU^{MCB} and FU^{IWB} maps.
A preliminary version of this paper appeared in Ji et al. (2018). In that paper, we briefly described the new method, and compared it with the other two methods. In this paper, we provide more algorithmic details about the three methods, compare the three methods when applied to synthetic and real EEG coherence networks, and apply the new method in one example application. This application shows the potential of our method for visualizing multichannel EEG coherence networks.
Overall, the new communitybased method for detecting functional units is not only expected to reduce the drawbacks of the conventional hypothesisbased approaches, but also to allow a more detailed analysis of the relationship between functional connectivity and underlying brain structure than the datadriven MCB and IWB methods.
Related work
The principal concept in our approach is to visualize brain connectivity, and to extract meaningful information from this representation for further analysis. The challenge in visualization often lies in the analysis of a huge amount of data, in our case the large number of EEG channels.
A straightforward method would be to visualize functional brain connectivity data as 3D nodelink diagrams: ROIs are shown as nodes and the relationships between these nodes are encoded in the edges. But this approach suffers from visual clutter, and side effects of 3D rendering such as occlusion are hard to remedy (Alper et al. 2013; Dosenbach et al. 2010).
An alternative approach is to depict the connectivity data by a 2D representation, which could reduce the work of 3D rendering. A wide variety of methods has been developed to map data on 2D space to visualize neuronal interactions or relations between brain regions. To preserve the spatial information of the data to some extent, a nodelink diagram based on a biologically meaningful layout has been used (Achard 2006). In this biological layout, planar projections are used for the 3D electrode locations on the surface of a head (see for example Fig. 2). Vertices are usually mapped according to a top view of the head, sometimes to two separate side views of the left and right hemispheres. However, such a visualization with edges representing connections may suffer from a large number of overlapping edges, resulting in a cluttered representation, especially for a large amount of data.
Some methods were proposed to remedy the visual clutter by eliminating overlaps and reducing the number of longdistance edges employing graph drawing. For example, for 2D nodelink diagrams the layout can be calculated by multidimensional scaling or forcedirected algorithms (Fruchterman and Reingold 1991). However, such methods usually change the layout of the vertices to reduce visual clutter. Yet, the spatial context of the data is still vital for facilitating the interpretation of the data by neuroscientists, who are trained in reasoning with respect to spatial brain regions. Hence, nodelink diagrams are often accompanied by a separate picture showing the position of nodes, with nodes on the two representations being matched by color encoding or labeling (Nelson et al. 2010). In this approach, information about spatial context is not presented in a single image. Matrix representations are also popular to represent functional connectivity networks. This approach outperforms the nodelink diagram in visualizing large networks. By arranging ROIs along the rows and columns of a matrix, their spatial relations are, however, lost (Kamiński et al. 1997).
Some studies explored the capabilities of nodelink diagrams and matrix representations, and these suggested that the matrix representations outperform nodelink diagrams for most tasks when the number of nodes becomes very large (Alper et al. 2013; Ghoniem et al. 2005).
Based on the basic nodelink and matrix representations, several other useful tools have been developed for visualizing brain networks. To take advantage of both nodelink diagrams and matrix representations, some visualization methods provide a dual representation to explore networks (Ma et al. 2015; Henry and Fekete 2006). Christodoulou et al. present BrainNetVis to support brain network modelling and visualization by providing both quantitative and qualitative network measures of brain connectivity (Christodoulou et al. 2011). Gerhard et al. introduce the Connectome Viewer Toolkit for connectome mapping, analysis, and visualization (Gerhard et al. 2011). Xia et al. present BrainNet Viewer to display brain surfaces, nodes and edges as well as properties of the network (Xia et al. 2013). Fujiwara et al. introduce a visual analytics system for comparison of brain connectivity across individuals, groups, and time points (Fujiwara et al. 2017). However, none of these methods can completely overcome the intrinsic drawbacks of nodelink diagrams and matrix representations. To present brain connectivity in a single image and overcome the drawbacks of conventional methods, we reduce the visual clutter by putting nodes with specific properties, based on their spatial information and topological network properties, into the same group. This presentation then serves as a first step before a more detailed analysis of EEG coherence networks.
Method
Although there are many unsupervised graph clustering methods, they either aim to find a predetermined number of clusters or do not consider the spatial information of the data (Ahmadlou and Adeli 2011; Kirschner et al. 2012; Schaeffer 2007). ten Caat et al. proposed a method considering the functional connections and spatial information of nodes together (ten Caat et al. 2008). This method assumes that a spatially connected set of electrodes records similar signals as a result of volume conduction (ten Caat et al. 2008; 2007a). However, one potential drawback of this method is that it is not easy to analyze local synchronization since the method tries to find groups of electrodes that are as large as possible.
In this section, we first provide some background on EEG coherence and the data representation of the EEG coherence network. Then we describe the community cliquebased method of detecting dense spatiallyconnected groups of electrodes. Then, we briefly describe the MCB and IWB methods for later comparison in the “Results” section.
EEG coherence
During an EEG experiment, brain activity is recorded by electrodes attached to the scalp of a subject at different locations. The electrodes are placed based on the 10/20 system and the position of an electrode is indicated by its label which is a combination of letters indicating brain regions (e.g., F for frontal), and digits indicating lateralization (odd numbers for left, even for right) and distance from the midline (higher numbers are farther away) (see Fig. 2) (Luck 2005; Oostenveld and Praamstra 2001). A conductive gel is applied between electrodes and skin for reducing impedance. EEG provides highresolution temporal information about brain activity, and the electrical potential is typically measured at sampling rates up to 2000Hz. The measured signal that is recorded from each site is amplified, resulting in one recording channel for every electrode. If there are many electrodes, e.g., 64 or 128, the term “multichannel” or “highdensity” EEG is used.
Activity from one source can result in a strong signal recorded by multiple electrodes, and nearby electrodes usually record similar signals due to volume conduction and reference electrode effects (Holsheimer and Feenstra 1977; Nunez et al. 1997). Often, there are several sources of activity at different locations, and these sources can be synchronized. Consequently, signals recorded by electrodes that are far apart can also be similar. The degree of interaction between two signals can be measured by coherence which is a measure for the similarity of signals as a function of frequency.
The coherence c_{λ} as a function of frequency λ for two continuous time signals x and y is defined as the absolute square of the crossspectrum f_{xy} normalized by the autospectra f_{xx} and f_{yy} (Halliday et al. 1995), having values in the interval [0, 1]: \(c_{\lambda }(x,y) = \frac { f_{xy}(\lambda)^{2} } {f_{xx}(\lambda)f_{yy}(\lambda)}\).
Data representation and EEG coherence network
A network is simply a collection of connected objects. We refer to the objects as nodes or vertices and the connections between the nodes as edges. In mathematics, networks are often referred to as graphs, and the area of mathematics concerning the study of graphs is called graph theory. In this paper, we use the terms network and graph interchangeably.
Functional brain connectivity obtained from EEG data is represented by an undirected coherence graph G=(V,E), defined by a set of vertices V and a set of edges E⊆V×V where vertices represent electrodes. Since weak coherences may represent spurious connections and these connections tend to obscure the topology of strong and significant connections (Rubinov and Sporns 2010), we only consider coherences with values above a predefined significance threshold (Halliday et al. 1995; ten Caat et al. 2008). Coherences above the significance threshold are represented by edges, whereas coherences below the threshold are ignored (see Fig. 3c). Vertices are not selfconnected. To determine spatial relationships between electrodes, a Voronoi diagram is employed, which partitions the plane into regions of points with the same nearest vertex (for a simple example, see Fig. 3a. For EEG data, the vertex set is equal to the set of electrode positions. The vertices are referred to as (Voronoi) centers, and the region boundaries as (Voronoi) polygons. The area enclosed by a polygon is called a (Voronoi) cell. We call two cells Voronoi neighbors if they have a boundary in common. A collection of cells is called Voronoi connected if for a pair ϕ_{0},ϕ_{n}∈C, there is a sequence ϕ_{0},ϕ_{1},...,ϕ_{n} of cells in C, with each pair ϕ_{i−1},ϕ_{i} consisting of Voronoi neighbors. Cells, vertices, nodes, and electrodes are interchangeable in this paper.
Community clique detection
We now introduce the CCB approach to find dense spatiallyconnected cliques from an EEG coherence network based on community structure. Such a clique is a set of electrodes that are spatially connected, and signals recorded by these electrodes are more densely connected within the same clique than with signals that are recorded by electrodes in other cliques.
Community structure
The community structure of a network is defined as groups of nodes with a high density of withingroup connections and a lower density of betweengroup connections. Such structures have been observed in many different types of networks including social, biological, and telecommunication networks (Danon et al. 2005; Newman 2006). In particular, the community structure of a brain functional connectivity network shows the groups of neuronal areas where there is more synchronous activity within a group and less synchronous activity between groups. These communities may be considered as functional areas in the brain (Ahmadlou and Adeli 2011).
Various algorithms have been proposed for the identification of community structure from complex networks. Many of these algorithms are based on the idea of optimizing the socalled modularity index Q of the partition of a network (Newman and Girvan 2004; Newman 2006). In the case of a weighted network, this index is defined as follows (Blondel et al. 2008):
where c(v,v^{′}) represents the weight (in our case the coherence value) of the edge between nodes v and v^{′}, \(K_{v} = \sum _{l}c(v,l)\) is the sum of weights of the edges incident to vertex v, L(v) is the community label of vertex v, the δ−function δ(i,j) is 1 if i=j and 0 otherwise, and \(m=\frac {1}{2}\sum _{v, v'}c(v, v')\). The modularity Q is equal to the fraction of the sum of weights of edges that connect nodes in the same community minus what that fraction would be on average if the communities remained fixed but the edge weights were randomly distributed. The higher the value of Q, the more confident one can be that a significant community structure has been found (Newman 2006). So, the procedure of detecting community structure is usually based on maximizing the modularity index Q.
The optimal community structure for a given network is typically estimated with optimization algorithms rather than computed exactly (Danon et al. 2005; Rubinov and Sporns 2010)). A simple and efficient method of optimizing modularity was proposed by Blondel et al. (2008). It involves the local movement of nodes, and proceeds in two phases. In the first phase, each node of the network is initialized as a singleton community. Then, for each node v, the modularity gain ΔQ is evaluated that would result from removing v from its community C_{L(v)} and placing it in one of the other communities. The node v is then placed in the community for which this gain is maximum and positive. If no positive gain is possible, nothing is done. This process is applied repeatedly and sequentially for all nodes until no further improvement can be achieved and the first phase is then complete.
Equation 2 can be used to calculate the modularity gain ΔQ when removing one node v from its community C_{L(v)} to an arbitrary community C_{i} (Blondel et al. 2008; Rubinov and Sporns 2010; Sun et al. 2009):
where \(K_{C_{L(v)}}\) is the sum of the weights of the links incident to nodes in C_{L(v)}, \(K_{C_{i}}\) is the sum of the weights of the links incident to nodes in C_{i}, and K_{v} is the sum of the weights of the links incident to node v.
The second phase of the algorithm consists of building a new network whose nodes are the communities found in the first phase. To do so, the weights of the links between the new nodes are given by the sum of the weights of the links between nodes in the corresponding two communities. Links between nodes of the same community lead to selfloops for this community in the new network. Once this second phase is completed, the first phase of the algorithm is reapplied to the new network. The combination of both phases is called a “pass”. The passes are iterated until there are no more changes.
Community clique detection method
Here, we extend the method proposed by Blondel et al. (2008) to obtain dense spatiallyconnected cliques, the community clique, consisting of Voronoiconnected vertices of the EEG coherence network.
The outline of our method can be summarized as follows. The difference with Blondel’s method is in step 2, the calculation of the modularity gain, where an extra condition is applied which ensures that the resulting communities are spatially connected cliques (see the introduction for the motivation):

1
Assign a unique community to each node of the network.

2
Use 2 to calculate the modularity gain ΔQ for node v caused by removing node v from its community and placing it in another community such that the node v is connected to each node of that community and has at least one Voronoi neighbour in that community.

3
Place the node v in the community for which the gain is the highest and positive. If no positive gain is available, nothing is done.

4
Continue repeating steps (2) and (3) until every node is processed.

5
Repeat steps (2) (4) until no further improvement of the modularity index Q is achieved.
Note that the algorithm’s output depends on the order in which the nodes are processed in step (2). The ordering does not have a significant influence on the modularity that is obtained, but can influence the computation time (Blondel et al. 2008). In our case, a decreasing order is chosen based on the average local coherence of vertices, which is also used to detect basins in the IWB method (ten Caat et al. 2008).
Algorithm 1 shows the pseudocode of the community clique detection procedure. It maintains the following dynamic vertex sets in the coherence graph of significant electrode connections:

C_{i} contains a sorted list of the vertices in community i;

L(v) is the community label of vertex v;

H_{i} contains a list of vertices (sorted by vertex number) that are connected to each of the vertices in C_{i};

R_{i} contains a list of vertices which have at least one Voronoi neighbor in C_{i}.
The operation remove(v,C_{L(v)}) removes the node v from the community C_{L(v)} and returns a set consisting of the remaining nodes. Similarly, add(v,C_{i}) inserts node v into the community C_{i} and returns the updated community. The operation isVor(C_{i}) returns “true” if the community C_{i} is empty, or if it only has one vertex, or if each pair of vertices in C_{i} is Voronoiconnected when C_{i}>1; and it returns “false” if not. The size of a vertex set is denoted by ·.
We now turn to a more precise analysis of the algorithm:

Initialization (lines 17).


Initially, every node of the network is a singleton community (line 3).


The set of vertices which are connected to vertices of community C_{i} is identical to the set of vertices which are connected to the node v=V(i) (line 5)


The set of vertices which are connected Voronoineighbours of vertices of community C_{i} is the set of vertices that are connected Voronoineighbours of the node v=V(i) (line 6).


Set flag as true (line 8). flag is used to indicate that the modularity can be improved. If flag is false, there is no improvement of modularity.



Main Procedure (line 8line 37). This consists of the following steps.


Take the ith node v=V(i) from V. If after removing v from its original community C_{L(v)} any pair of remaining vertices is not Voronoiconnected, nothing is done, and the procedure continues with a new node (line 13). Otherwise, set the maximal gain of modularity maxΔQ to zero, and take the jth community C_{j}.


In case C_{j} is empty or v is not connected to any nodes of C_{j} or v has no Voronoi neighbors in C_{j}, nothing is done, and the procedure continues with a new community (line 16). Otherwise, compute the modularity gain ΔQ (line 17).


If the current gain ΔQ is higher than maxΔQ, which means the modularity can be improved, set the label of the current community j to the destination community label d to which community the node v will move (line 21). Otherwise, nothing is done, and the procedure continues with a new community.


After all communities are traversed, select the first community which has the highest ΔQ, and update community C_{L(v)} by removing node v from its original community C_{L(v)} (line 26); replace H_{L(v)} by vertices that are connected to each node of the updated community C_{L(v)} (line 27); replace R_{L(v)} by the vertices that are connected Voronoi neighbours of nodes of the updated community C_{L(v)} (line 28); move node v into the destination community C_{d} (line 29); replace H_{L(v)} by its intersection with the set of vertices that are connected with v in the coherence graph (line 30); replace R_{L(v)} by its union with the vertices that are connected Voronoi neighbours of v (line 31); v receives label d (line 32).


This procedure is repeated until no improvement is obtained, which means flag=false after all nodes have been processed.


Figure 4 illustrates the procedure of community clique detection for an EEG coherence network, with the coherence matrix shown in Table 1. Table 1 shows a synthetic coherence network, and we use it to illustrate the procedure of the three methods. The following detailed description contains references to Fig. 4. For a dataset of 119 electrodes, the computing time was around 0.84 s on a modern desktop computer (Intel 3.2 GHz, 8 GB RAM).
At T1, the initial stage, each of these twelve vertices correspond to a unique community represented by a specific colored symbol: L(a)=1, L(b)=2, L(c)=3, L(d)=4, L(e)=5, L(f)=6, L(g)=7, L(h)=8, L(i)=9, L(j)=10, L(k)=11, L(l)=12. Then, we calculate the modularity gain ΔQ caused by removing k (since k has the highest local average coherence, and the descending order of vertices based on their local average coherence is: h,a,f,e,b,l,d,g,i,j,c,k) from its community to the other communities; all the values of ΔQ are listed on the right in Fig. 4.
T2T12. At every next step, the next vertex v will be chosen and the gain of removing v from its community C_{L(v)} to the remaining communities will be computed. If the positive highest gain maxΔQ results from the movement of node v to the community in which v has at least one Voronoi neighbour and is connected with each vertex in that community, then the vertex v will be removed from its original community to the destination community C_{Des}, C_{L(v)} is updated by deleting v from C_{L(v)} and C_{Des} is replaced by the union of itself with v. At T2, v=h, C_{L(v)}=C_{8}=∅, C_{Des}=C_{12}={h,l}. At T3, v=a, C_{L(v)}=C_{1}=∅, C_{Des}=C_{5}={a,e}. At T4, v=f, C_{L(v)}=C_{6}=∅, C_{Des}=C_{5}={a,e,f}. At T5, v=e, nothing is done since maxΔQ is negative when merging e and i into one community. At T6, v=b, C_{L(v)}=C_{2}=∅, C_{Des}=C_{5}={a,b,e,f}. At T7, v=l, nothing is done since all the communities except C_{12}, the original community, have no connected Voronoi neighbours of l. At T8, v=d, C_{L(v)}=C_{4}=∅, C_{Des}=C_{12}={d,h,l}. At T9, v=g, C_{L(v)}=C_{7}=∅, C_{Des}=C_{12}={g,d,h,l}. At T10, v=i, C_{L(v)}=C_{9}=∅, C_{Des}=C_{5}={a,b,e,f,i}. At T11, v=j, C_{L(v)}=C_{10}=∅, C_{Des}=C_{5}={a,b,e,f,i,j}. At T12, v=c, and at T13, v=k, nothing is done since the vertex v has no connected Voronoineighbours.
From T14 on, all vertices will be traversed again. The gain ΔQ can be easily computed and it can be observed that there is no more positive gain, which means the modularity can not be improved anymore. So the detection procedure stops. Finally, we obtain two community cliques {a,b,e,f,i,j} and {g,d,h,l} at T25.
FU detection using the MCB and IWB method
MCB method
The maximal clique based (MCB) method (ten Caat et al. 2007a) is an extension of the method proposed by Bron and Kerbosch (1973). It detects maximal cliques consisting of Voronoiconnected vertices. Its recursive procedure maintains four dynamic vertex sets (ten Caat et al. 2008):

The set compsub contains an increasing or decreasing clique.

The set currentcand contains the candidates that are a Voronoi neighbor of at least one element in compsub, and only these can be added to compsub at the current step.

The set complcand is the complement of currentcand in candidates containing vertices that are connected to all vertices in compsub.

The set not contains vertices that are connected to all vertices in compsub and that were added to compsub previously.
At each call, the element from currentcand that has the largest number of connections with the other candidates (currentcand∪complcand) is added to compsub. Let this element be v (in the coherence graph). The set newcurrentcand is the intersection of currentcand and the neighborhood of v (in the coherence graph), united with the Voronoi neighbors of v in complcand. The set newcomplcand is the intersection of complcand and the neighborhood of v (in the coherence graph), minus the Voronoi neighbors of v in complcand. The set (new)not is the intersection of not and the neighborhood of v. This is repeated until newcurrentcand is empty. If newnot is also empty, then compsub is a Voronoiconnected maximal clique.
Figure 5 illustrates Voronoiconnected maximal clique detection using the MCB method for a coherence network, with the coherence matrix shown in Table 1. Its adjacency matrix is shown in Table 2 (here, we set the threshold at 0.2), and the Voronoi diagram is shown in Fig. 3a.
The following detailed description contains (row and column) references to Fig. 5. The procedure A. starts with all twelve vertices in the set candidates (not illustrated), and with not=∅. A1. Then, the vertex g with the highest degree (following Table 2) is first added to compsub. Its adjacent vertices in the coherence graph are in currentcand if they are spatial neighbours ({f,h}); otherwise, they are in complcand ({a,b,d,e,i,j,l}). A2A6. At every step, the element, say, v, from currentcand that has the largest number of connections in the coherence graph with the other candidates (currentcand∪complcand) is added to compsub. In case of ties, one vertex is selected randomly. The spatial neighbours of v in complcand, denoted by Λ(v), are moved from complcand to currentcand. Furthermore, vertices not adjacent to v in the coherence graph, denoted by Γ^{c}(v), are removed from both currentcand and complcand. This continues until currentcand is empty. At A2, v=f, Λ(v)={b,e,j}, and Γ^{c}(v)={d,h,l}. At A3, v=e, Λ(v)={a,i}, and Γ^{c}(v)=∅. At A4, v=a, Λ(v)=∅, and Γ^{c}(v)=∅. At A5, v=b, Λ(v)=∅, and Γ^{c}(v)=∅. At A6, v=i, Λ(v)=∅, and Γ^{c}(v)=∅. At A7, v=j, Λ(v)=∅, Γ^{c}(v)=∅, and compsub={a,b,e,f,i,j,g} is a Voronoiconnected maximal clique, because currentcand=∅ (and not=∅).
B. A later iteration for the MCB method returns to the situation preceding A2, with vertex g in the compsub, and vertex f put into the set of not. Then, at B1. only the vertex h is retained in currentcand, and complcand is the same as in A1. ({a,b,e,i,j,d,l}). At B2, v=h, Λ(v)={d,l}, Γ^{c}(v)={a,b,e,i,j}, and not=∅. At B3, v=d, Λ(v)=∅, Γ^{c}(v)=∅, and not=∅. At B4, v=l, Λ(v)=∅, Γ^{c}(v)=∅, not=∅, and compsub={g,d,h,l} is a Voronoiconnected maximal clique, because currentcand=∅ (and not=∅).
As it can be seen from the above example, every vertex can be part of multiple (Voronoiconnected) maximal cliques. (In the above example, vertex g belongs to Voronoiconnected maximal cliques {a,b,e,f,i,j,g} and {g,d,h,l}). To assign a unique label to every vertex, a quantity total strength is defined for a (sub)graph G=(V,E) as the sum of all edge values. For a vertex detected in more than one clique, it will be assigned to the clique which has the largest total strength. Then, the final cliques in above example are {a, b, e, f, i, j, g}and {d, h, l } (see C1).
IWB method
The IWB method is an alternative to the MCB method. It is a greedy method, approximating Voronoi connected maximal cliques on the basis of an edgebased watershed transform (ten Caat et al. 2007b).
This IWB method contains two main steps:

Initialization. An edge queue is initialized with edges (corresponding with a significant coherence) between markers, which are defined as nodes having locally maximal average coherence, and their Voronoi neighbors. These edges are sorted in a descending order based on their values. Each marker corresponds to a basin and is assigned a unique label.

Main Procedure. Remove the first edge, e=(v,v^{′}), from the queue, and determine the label of node v^{′}. In case the node v^{′} is unlabelled, v^{′} receives the label of v and the queue is extended with the edges between v^{′} and its unlabelled connected Voronoineighbours, if v^{′} is connected to every node of the basin where v is in. In case v^{′} was also labelled, check if the two basins that contain v and v^{′} can merge into a single basin. If so, then merge them, otherwise nothing is done.
The main procedure is repeated until queue is empty. Each basin then corresponds to an FU^{IWB}.
Figure 6 illustrates FU detection with the IWB method for a coherence network, with the coherence matrix shown in Table 1 and the Voronoi diagram shown in Fig. 3a. The following detailed description contains references to Fig. 6.
At S1, three markers, a,f,h, are detected, and they are represented by a green diamond, red star, and magenta uptriangle, respectively. Each is then assigned a unique number: L(a)=1, L(f)=2, L(h)=3; edges (corresponding to significant coherences) between markers and their unlabelled Voronoi neighbours represented by blue squares are added in the queue; the edge with the highest value in the queue is c(h,l) and is shown at the top on the right of S1.
S2S11. At every next step, the edge, say, c(v,v^{′}), with the highest value in the queue is removed. Then, the vertex v^{′} is labelled. The edges (denoted by Φ(v^{′})) between v^{′} and its unlabelled Voronoineighbours are inserted in the queue and will be highlighted in bold. At S2, v=h, v^{′}=l, L(v^{′})=L(h)=3, and Φ(v^{′})=∅. At S3, v=h, v^{′}=d, L(v^{′})=L(h)=3, and Φ(v^{′})=∅. At S4, v=f, v^{′}=g, L(v^{′})=L(f)=2, and Φ(v^{′})=∅. At S5, v=h, v^{′}=g, h which was labelled already in the previous stage. But, the basin of g and the basin of h can not merge since their union is not a clique in the coherence graph (h,d,l are not significantly connected with f, which can be derived from 1). Hence, nothing will be done at this stage. At S6, v=a, v^{′}=b, L(v^{′})=L(a)=1, and Φ(v^{′})=∅. At S7, v=a, v^{′}=e, L(v^{′})=L(a)=1, and Φ(v^{′})={(e,i)}. At S8, v=f, v^{′}=b, b was labelled already in the previous stage. But the basins of f and b can merge since their union is a clique in the coherence graph. Hence, vertices in the basin of b will be moved to the basin of f. L(v^{′})=L(f)=3, L(a)=L(f)=3, L(e)=L(f)=3, and Φ(v^{′})=∅. At S9, v=f, v^{′}=e, L(v^{′})=L(e)=3, and Φ(v^{′})=∅. At S10, v=e, v^{′}=i, L(v^{′})=L(e)=3, and Φ(v^{′})=∅. At S11, v=i, v^{′}=j, L(v^{′})=L(j)=3, and Φ(v^{′})=∅. At S12, v=f, v^{′}=j, L(v^{′})=L(j)=3, and Φ(v^{′})=∅. Now, two basins have been detected, { a, b, e, f, i, j, g} and { d, h, l}, because the queue is empty.
FU visualization
Given FUs, the interFU coherence\(c^{\prime }_{\lambda }\) at frequency λ between two FUs C_{1} and C_{2} is defined as the sum of coherence values between one vertex in C_{1} and the other vertex in C_{2}, divided by the maximal number of edges between C_{1} and C_{2}:
Note that coherences between any pair of vertices are taken into account to normalize for the size of the FUs even if their coherence is below the predefined threshold.
An FU map visualizes each FU as a set of Voronoi cells with identical gray values and with different gray values for adjacent FUs. See Fig. 7 for an example. The colour of the circle over the geographic centre of FU C_{1} reflects its average coherence\(\hat {c}_{\lambda } (C_{1})\), which is defined as \(\hat {c}_{\lambda } (C_{1}) = \frac {\sum _{i,j} \{ c_{\lambda } (v_{i}, v_{j}) v_{i} \in C_{1}, v_{j} \in C_{1} \} }{C_{1} (C_{1}1)}\). Note that the geographic centre of an FU can be located in a cell not belonging to the corresponding FU. A line is drawn between FU centres if the corresponding interFU coherence exceeds a predefined threshold.
In our case, only FUs larger than five cells are considered. White Voronoi cells are part of smaller FUs.
Comparison of methods applied to synthetic EEG coherence networks
In this subsection, we will first compare the proposed method with two other methods using a synthetic EEG coherence network (see Fig. 3 and Table 1). The comparison between the three methods applied to real functional brain networks is described in the “Results” section.
For the MCB method, at the stage of (Voronoiconnected) maximal clique detection, coherences are considered equally when their values are above or equal to the threshold. This method intends to find all possible maximal cliques in a coherence network. Then, at the stage of vertex assignment, the vertex is assigned to the clique which has the highest total strength when it is part of multiple cliques, no matter how strong the vertex is connected to these cliques. Hence, the vertex will be placed in the clique with more vertices when two cliques have an equal average coherence. For example, at the stage of maximal clique detection, we found two overlapping maximal cliques, {a,b,e,f,i,j,g} and {g,d,h,l}, in Fig. 5. But the former has a higher total strength, so g is removed from {g,d,h,l} at the assignment stage, and the final cliques are shown in C1.
For the IWB method, the edges connecting a labelled vertex and an unlabelled vertex will be placed in the queue first if these vertices are significantly connected Voronoi neighbours. Then, the unlabelled vertex will be placed in the clique in which one of its Voronoi neighbours has the highest coherence with this vertex compared to others in the queue. For example, at S3 in Fig. 6, the vertex g is assigned to f since their connection value is 0.71 while the connection value with h is 0.69. The final cliques are shown in S12.
The community cliquebased (CCB) method detects the dense spatially connected cliques in a coherence network. It first calculates the degree of connections between nodes and community cliques, which is quantified by modularity. Then, the node will be placed in the clique which has the strongest nodecommunity connection. For example, at T8 in Fig. 4, vertex g has a stronger connection with clique {d,h,l} than with clique {a,b,e,f}. At T21, vertex g still has a stronger connection with clique {d,h,l} than with clique {a,b,e,f,i,j}. The final cliques are shown in T26.
Results
In this section, we will first describe the experimental setup, before applying the CCB method to twelve participants for an example application. To compare the three methods when applied to real EEG coherence networks, we selected four of these sixteen participants (two young and two old) to demonstrate any differences.
Experimental setup
Brain responses were recorded during an auditory oddball detection experiment, in which older and younger participants were instructed to count target tones and ignore standard tones. After the experiment, each participant had to report the number of perceived target tones. In our data, brain responses to L target tones were analyzed in L segments of 1 second, sampled at 256Hz. A procedure from Neurospec was adopted to compute the coherence (www.neurospec.org). A detailed description of the procedure is given in ten Caat et al. (2008).
In the present study we do not consider ongoing EEG but the eventrelated potential (ERP) which is an EEG recording of the brain response to a sensory stimulus. To calculate the coherence for an ERP with L repetitive stimuli, the EEG data can be separated into L segments. A significance threshold for the estimated coherence is then given by Halliday et al. (1995):
where p is a probability value associated with a confidence level α, such that p=1−α.
Throughout this section, we use p=0.01, and L=13 segments. In addition, we set the interFU coherence threshold to the same value as the significance threshold θ.
Comparison of methods applied to real EEG coherence networks
Besides comparing the three methods when applied to the synthetic EEG network in the “Method” section, we also compared the three methods when applied to real EEG coherence networks as obtained from two younger and two older participants in the experiment described in “Experimental setup” subsection. The results are shown in Fig. 8, and we make the following observations.

For the young participants, it can be observed that there is no big difference between FU maps obtained from these three methods. In the [1, 3]Hz frequency band, FU maps are very similar for both young participants in terms of, for example, the number of FUs and their location. Similarly, for the [4, 7]Hz frequency band, there are no big differences between the methods either.

For the older participants, however, there are large differences between FU maps for the different methods. In the [4, 7]Hz frequency band, the three methods result in a similar number of FUs. In the [1, 3]Hz frequency band for participant 3 both MCB and IWB methods detect two large FUs located anteriorly and posteriorly: FUs^{MCB}1, 5 and FUs^{IWB}1, 3. In the CCB method, however, these FUs are split into small FUs due to a weak intercommunity connection. For example, FU^{MCB}5 splits into FUs^{CCB}6 and 7, while FU^{MCB}1 splits into FUs^{CCB}1 and 2. From these splits, we can see that FUs^{CCB}6 and 7 have higher average coherence than FU^{MCB}5, and the interFU coherence between FUs^{CCB}6 and 7 is also lower than their average coherence. This is also true for FU^{MCB}1 and FUs^{CCB}1, 2. From a global point of view, FU^{CCB}7 has the highest average coherence, followed by 1 and 2, and there are higher interFU coherences among these FUs. For participant 4, the MCB method detects two large FUs located anteriorly and posteriorly, with significant interFU coherence between them. The IWB method has a similar result, except for the frontocentral connection. The CCB method, in contrast, finds a total of seven FUs with size above five. Compared to the CCB method, FU 1 obtained by the MCB and IWB methods is split into four FUs 1, 2, 3, 4 in the CCB method due to the weak intercommunity connections with each other. FU^{CCB}1 in the CCB method has the highest average coherence among these four FUs. From a global point of view, the two FUs^{CCB} having the strongest connection are 1 and 7, which are located at the frontal and parietaloccipital areas of the brain, respectively. In the [4, 7]Hz frequency band, the MCB and IWB methods produce similar results, except in the frontocentral area of the brain. The main difference between methods is that FU^{MCB}1 splits into FUs^{CCB}1 and 2 in the CCB method due to weak intercommunity connections. In addition, the average coherence of FU^{CCB}1 and 2 is higher than FU^{MCB}1. FU^{MCB}6 is an extension of FU^{CCB}7, but it can be seen that their average coherence differs.
In this example, the FU maps obtained from older participants generally have larger FUs and the coherence withinand between FUs is also high compared to the young participants. This could be interpreted as the older participants having higher local and global synchronization. All the methods are trying to find cliques and for the young participants brain areas are apparently less synchronized, which results in lower coherence. In this case we end up with small(er) FUs. This also explains why the FU maps obtained from the three methods are similar for the younger participants. For the older participants, there is apparently high synchronization between brain areas. In this case, more electrodes make up larger cliques. The MCB and IWB methods then detect larger FUs. Consequently, the detected FUs are less suited for analyzing local synchronization. In this case, however, the CCB method still considers the community properties: if an electrode can be put into several FUs, it will be added to the FU with which it has a strong connection rather than to the largest FU as in the other methods.
FU^{CCB} maps
In this subsection, we apply (only) the CCB method to the data of six younger and six older participants in the experiment described in the “Experimental setup” subsection.
Figure 9a and b show FU^{CCB} maps of the younger and older adults, respectively. In general, the color of circles and edges is lighter for older participants than for younger participants over the three frequency bands. This probably corresponds to earlier findings using a hypothesisdriven method (Maurits et al. 2006), indicating the older adults have higher local and global synchronization compared to the younger adults and that aging is associated with increased EEG coherence during a relatively easy cognitive task. The midline regions are usually less synchronized as reflected in the FUs of these regions being small and the color of circles and edges connecting with other FUs having darker colors. Throughout the three frequency bands, FUs with high average coherence (light circle color) are usually found in anterior and posterior regions, and these FUs usually have high interFU coherence which is also in accordance with previous observations in the literature (ten Caat et al. 2008), particularly for the older participants.
For the younger participants, the interFU coherence decreased with increasing frequency except for participant 1 (Fig. 9a). The left and righttemporal part of the brain are usually less synchronized compared to the older participants, for example, participants 1 and 3 have no lefttemporal FUs while these FUs in the rest of young participants have a low average withinFU coherence. Participant 1 seems to be an exception in more ways, having the least synchronization among all FU maps for frequencies between 13 Hz and having only 4 FUs with a size above 5 and no lateral FUs for this frequency band.
For the older adults, the interFU coherence also decreased with increasing frequency, especially for the FUs located at the anterior and posterior regions, which can be derived from the color of the edge connecting these FUs fading (Fig. 9b). For example, it is very obvious for old participant 5: the interFU coherence between FU^{CCB}7 and 1 for frequencies between 13 Hz is very high; the interFU coherence between FU^{CCB}6 and 1 for frequencies between 47 Hz is low, and the interFU coherence between FU^{CCB}6 and 1 for frequencies between 812 Hz is the lowest. There is also a variety in these findings among old adults, for example, the size of FUs for old participant 1 is usually smaller compared to other old participants and the color of the circle or edges is darker compared to the rest, as well. Another example is old participant 2 for frequencies between 47 Hz for which FUs 3, 6 and 7 left and righttemporally are small and not connected with other FUs, which means these regions are less synchronized and also are less synchronized with other regions.
Conclusions and future work
Visualization is an important aspect in the analysis of EEG coherence, especially for multichannel EEG coherence networks. Since conventional methods either suffer from reduced spatial information or visual clutter, they have inherent limitations when applied to EEG coherence networks. We developed a visualization approach based on the functional unit (FU) concept that attempts to preserve spatial relationships between functional brain regions and allows analysis of functional connectivity within and between regions.
A new community clique based (CCB) method was proposed that first partitions an EEG coherence network into dense groups of spatially connected electrodes recording pairwise significantly coherent signals. The resulting communities (groups of electrodes) were visualized in an FU map, which makes it possible to investigate the relationship between functional brain connectivity and underlying brain structure. The novelty of this method is that it is helpful to analyze the local and global connectivity without any a priori hypotheses. Community cliques found by the CCB method can be used for further analysis, e.g., the analysis of ERP components across FUs and synchronization between FUs.
As topics for future work we first mention the influence of the order in which nodes are traversed in the CCB procedure, which needs to be further analyzed. Second, differences between FU maps were assessed only visually in our study. However, there is still the need to develop methods for comparing FU maps quantitatively, and to discriminate not only between single subjects, but also between different groups, e.g., old and young participants. Our method is a visually aided preprocessing method that can be used before analysis questions about data are well defined. Although our method is specific to EEG coherence networks, we believe that it can be easily adapted to other network visualizations which need to capture the whole structure of networks and that do not only depend on the analysis of single nodes or specified connections between pairs of nodes.
Abbreviations
 CCB:

Community clique based
 EEG:

Electroencephalography
 ERP:

Eventrelated potential
 FU:

Functional unit
 (I)WB:

(Improved) watershed based
 MCB:

Maximal clique based
 ROI:

Regions Of interest
References
Achard, S (2006) A resilient, lowfrequency, smallworld human brain functional network with highly connected association cortical hubs. J Neurosci 26(1):63–72. https://doi.org/10.1523/jneurosci.387405.2006.
Ahmadlou, M, Adeli H (2011) Functional community analysis of brain: A new approach for EEGbased investigation of the brain pathology. NeuroImage 58(2):401–408. https://doi.org/10.1016/j.neuroimage.2011.04.070.
Alper, B, Bach B, Henry Riche N, Isenberg T, Fekete JD (2013) Weighted graph comparison techniques for brain connectivity analysis In: Proceedings of the SIGCHI Conference on Human Factors in Computing Systems  CHI, 483–492.. ACM Press, Paris. https://doi.org/10.1145/2470654.2470724.
Blondel, VD, Guillaume JL, Lambiotte R, Lefebvre E (2008) Fast unfolding of communities in large networks. J Stat Mech Theory Exp 2008(10):10008. https://doi.org/10.1088/17425468/2008/10/p10008.
Bron, C, Kerbosch J (1973) Algorithm 457: finding all cliques of an undirected graph. Commun ACM 16(9):575–577. https://doi.org/10.1145/362342.362367.
Christodoulou, EG, Sakkalis V, Tsiaras V, Tollis IG (2011) BrainNetVis: An openaccess tool to effectively quantify and visualize brain networks. Comput Intell Neurosci 2011:1–12. https://doi.org/10.1155/2011/747290.
Danon, L, DíazGuilera A, Duch J, Arenas A (2005) Comparing community structure identification. J Stat Mech Theory Exp 2005(09):09008–09008. https://doi.org/10.1088/17425468/2005/09/p09008.
Dosenbach, NUF, Nardos B, Cohen AL, Fair DA, Power JD, Church JA, Nelson SM, Wig GS, Vogel AC, LessovSchlaggar CN, Barnes KA, Dubis JW, Feczko E, Coalson RS, Pruett JR, Barch DM, Petersen SE, Schlaggar BL (2010) Prediction of individual brain maturity using fMRI. Science 329(5997):1358–1361. https://doi.org/10.1126/science.1194144.
Fruchterman, TMJ, Reingold EM (1991) Graph drawing by forcedirected placement. Softw Pract Experience 21(11):1129–1164. https://doi.org/10.1002/spe.4380211102.
Fujiwara, T, Chou JK, McCullough AM, Ranganath C, Ma KL (2017) A visual analytics system for brain functional connectivity comparison across individuals, groups, and time points In: 2017 IEEE Pacific Visualization Symposium (PacificVis).. IEEE. https://doi.org/10.1109/pacificvis.2017.8031601.
Gerhard, S, Daducci A, Lemkaddem A, Meuli R, Thiran JP, Hagmann P (2011) The connectome viewer toolkit: An open source framework to manage, analyze, and visualize connectomes. Front Neuroinformatics 5. https://doi.org/10.3389/fninf.2011.00003.
Ghoniem, M, Fekete JD, Castagliola P (2005) On the readability of graphs using nodelink and matrixbased representations: A controlled experiment and statistical analysis. Inf Vis 4(2):114–135. https://doi.org/10.1057/palgrave.ivs.9500092.
Gladwin, TE, Lindsen JP, de Jong R (2006) Prestimulus EEG effects related to response speed, task switching and upcoming response hand. Biol Psychol 72(1):15–34. https://doi.org/10.1016/j.biopsycho.2005.05.005.
Halliday, DM, Rosenberg JR, Amjad AM, Breeze P, Conway BA, Farmer SF (1995) A framework for the analysis of mixed time series/point process data—theory and application to the study of physiological tremor, single motor unit discharges and electromyograms. Prog Biophys Mol Biol 64(2):237–278. https://doi.org/10.1016/s00796107(96)000090.
Henry, N, Fekete JD (2006) MatrixExplorer: a dualrepresentation system to explore social networks. IEEE Trans Vis Comput Graph 12(5):677–684. https://doi.org/10.1109/tvcg.2006.160.
Holsheimer, J, Feenstra BWA (1977) Volume conduction and EEG measurements within the brain: A quantitative approach to the influence of electrical spread on the linear relationship of activity measured at different locations. Electroencephalogr Clin Neurophysiol 43(1):52–58. https://doi.org/10.1016/00134694(77)901948.
Honey, CJ, Kotter R, Breakspear M, Sporns O (2007) Network structure of cerebral cortex shapes functional connectivity on multiple time scales. Proc Natl Acad Sci 104(24):10240–10245. https://doi.org/10.1073/pnas.0701519104.
Ji, C, Maurits NM, Roerdink JBTM (2018) Visualization of Multichannel EEG Coherence Networks Based on Community Structure Analysis(Cherifi C, Cherifi H, Karsai M, Musolesi M, eds.). Springer, Cham. https://doi.org/10.1007/978331972150747.
Kamiński, M, Blinowska K, Szelenberger W (1997) Topographic analysis of coherence and propagation of EEG activity during sleep and wakefulness. Electroencephalogr Clin Neurophysiol 102(3):216–227. https://doi.org/10.1016/s00134694(96)957215.
Kirschner, A, Kam JWY, Handy TC, Ward LM (2012) Differential synchronization in default and taskspecific networks of the human brain. Front Hum Neurosci 6. https://doi.org/10.3389/fnhum.2012.00139.
Lachaux, JP, Rodriguez E, Martinerie J, Varela FJ (1999) Measuring phase synchrony in brain signals. Hum Brain Mapp 8(4):194–208. https://doi.org/10.1002/(SICI)10970193(1999)8:4%3C194::AIDHBM4%3E3.0.CO;2C.
Li, K, Guo L, Faraco C, Zhu D, Chen H, Yuan Y, Lv J, Deng F, Jiang X, Zhang T, et al (2012) Visual analytics of brain networks. NeuroImage 61(1):82–97. https://doi.org/10.1016/j.neuroimage.2012.02.075.
Luck, SJ (2005) An Introduction to the Eventrelated Potential Technique. An Introduction to the Eventrelated Potential Technique. MIT Press, The University of Michigan.
Ma, C, Kenyon RV, Forbes AG, BergerWolf T, Slater BJ, Llano DA (2015) Visualizing Dynamic Brain Networks Using an Animated DualRepresentation. In: Bertini E, Kennedy J, Puppo E (eds)Eurographics Conference on Visualization (EuroVis)  Short Papers.. The Eurographics Association. https://doi.org/10.2312/eurovisshort.20151128.
Maurits, NM, Scheeringa R, van der Hoeven JH, de Jong R (2006) EEG coherence obtained from an auditory oddball task increases with age. J Clin Neurophysiol 23(5):395–403. https://doi.org/10.1097/01.wnp.0000219410.97922.4e.
Munzner, T (2014) Visualization Analysis and Design. A K Peters/CRC Press, New York. https://doi.org/10.1201/b17511.
Nelson, SM, Cohen AL, Power JD, Wig GS, Miezin FM, Wheeler ME, Velanova K, Donaldson DI, Phillips JS, Schlaggar BL, Petersen SE (2010) A parcellation scheme for human left lateral parietal cortex. Neuron 67(1):156–170. https://doi.org/10.1016/j.neuron.2010.05.025.
Newman, MEJ (2004) Fast algorithm for detecting community structure in networks. Phys Rev E 69(6). https://doi.org/10.1103/physreve.69.066133.
Newman, MEJ (2006) Finding community structure in networks using the eigenvectors of matrices. Phys Rev E 74(3). https://doi.org/10.1103/physreve.74.036104.
Newman, MEJ, Girvan M (2004) Finding and evaluating community structure in networks. Phys Rev E 69(2). https://doi.org/10.1103/physreve.69.026113.
Nunez, PL, Srinivasan R, Westdorp AF, Wijesinghe RS, Tucker DM, Silberstein RB, Cadusch PJ (1997) EEG coherency: I: statistics, reference electrode, volume conduction, laplacians, cortical imaging, and interpretation at multiple scales. Electroencephalogr Clin Neurophysiol 103(5):499–515. https://doi.org/10.1016/S00134694(97)000667.
Oostenveld, R, Praamstra P (2001) The five percent electrode system for highresolution EEG and ERP measurements. Clin Neurophysiol 112(4):713–719. https://doi.org/10.1016/s13882457(00)005277.
Rubinov, M, Sporns O (2010) Complex network measures of brain connectivity: Uses and interpretations. NeuroImage 52(3):1059–1069. https://doi.org/10.1016/j.neuroimage.2009.10.003.
Schaeffer, SE (2007) Graph clustering. Comput Sci Rev 1(1):27–64. https://doi.org/10.1016/j.cosrev.2007.05.001.
Sun, Y, Danila B, Josić K, Bassler KE (2009) Improved community structure detection using a modified finetuning strategy. EPL (Europhys Lett) 86(2):28004. https://doi.org/10.1209/02955075/86/28004.
ten Caat, M (2008) FuMapLab: multichannel EEG Matlab toolbox. http://www.cs.rug.nl/~roe/software/FuMapLab/FuMapLab02.tgz.
ten Caat, M, Maurits NM, Roerdink JBTM (2007a) Functional unit maps for datadriven visualization of highdensity EEG coherence. In: Museth K, Moeller T, Ynnerman A (eds)Proc. Eurographics/IEEE VGTC Symposium on Visualization (EuroVis), 259–266.. The Eurographics Association, Norrköping. https://doi.org/10.2312/VisSym/EuroVis07/259266. Stoneham: ButterworthHeinemann.
ten Caat, M, Maurits NM, Roerdink JBTM (2007b) Watershedbased visualization of highdensity EEG coherence. In: Banon GJF, Barrera J, de Mendoca BragaNeto U (eds)Proc. 8th International Symposium on Mathematical Morphology, Rio de Janeiro, 289–300.. Instituto Nacional de Pesquisas Espaciais (INPE), Sao Jose dos Campos. http://mtcm21b.sid.inpe.br/col/dpi.inpe.br/ismm@80/2007/10.26.11.43/doc/reference.bib.
ten Caat, M, Maurits NM, Roerdink JBTM (2008) Datadriven visualization and group analysis of multichannel EEG coherence with functional units. IEEE Trans Vis Comput Graph 14(4):756–771. https://doi.org/10.1109/tvcg.2008.21. Accessed 2017.
von Stein, A, Sarnthein J (2000) Different frequencies for different scales of cortical integration: from local gamma to long range alpha/theta synchronization. Int J Psychophysiol 38(3):301–313. https://doi.org/10.1016/s01678760(00)001720.
Xia, M, Wang J, He Y (2013) BrainNet viewer: A network visualization tool for human brain connectomics. PLoS ONE 8(7):68910. https://doi.org/10.1371/journal.pone.0068910.
Yi, JS, Elmqvist N, Lee S (2010) TimeMatrix: Analyzing temporal social networks using interactive matrixbased visualizations. Int J HumComput Interact 26(1112):1031–1051. https://doi.org/10.1080/10447318.2010.516722.
Acknowledgements
C. Ji acknowledges the China Scholarship Council (Grant number: 201406240159) for financial support.
Author information
Affiliations
Contributions
Conceptualisation: CJ, NMM, JBTMR. Data Curation: NMM, CJ. Formal analysis: CJ, NMM, JBTMR. Software: CJ. Supervision: NMM, JBTMR. Visualization: CJ. Original draft: CJ. Review and editing: CJ, NMM, JBTMR. All authors read and approved the final manuscript.
Corresponding author
Ethics declarations
Competing interests
The authors declare that they have no competing interests.
Publisher’s Note
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Rights and permissions
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.
About this article
Cite this article
Ji, C., Maurits, N. & Roerdink, J. Datadriven visualization of multichannel EEG coherence networks based on community structure analysis. Appl Netw Sci 3, 41 (2018). https://doi.org/10.1007/s411090180096x
Received:
Accepted:
Published:
Keywords
 Multichannel data
 Community structure
 Visualization
 Brain connectivity