Abstract
Cardiorespiratory fitness was found to influence age-related changes of resting state brain network organization. However, the influence on dedifferentiated involvement of wider and more unspecialized brain regions during task completion is barely understood. We analyzed EEG data recorded during rest and different tasks (sensory, motor, cognitive) with dynamic mode decomposition, which accounts for topological characteristics as well as temporal dynamics of brain networks. As a main feature the dominant spatio-temporal EEG pattern was extracted in multiple frequency bands per participant. To deduce a pattern’s stability, we calculated its proportion of total variance among all activation patterns over time for each task. By comparing fit (N = 15) and less fit older adults (N = 16) characterized by their performance on a 6-min walking test, we found signs of a lower task specificity of the obtained network features for the less fit compared to the fit group. This was indicated by fewer significant differences between tasks in the theta and high beta frequency band in the less fit group. Repeated measures ANOVA revealed that a significantly lower proportion of total variance can be explained by the main pattern in high beta frequency range for the less fit compared to the fit group [F(1,29) = 12.572, p = .001, partial η2 = .300]. Our results indicate that the dedifferentiation in task-related brain activation is lower in fit compared to less fit older adults. Thus, our study supports the idea that cardiorespiratory fitness influences task-related brain network organization in different task domains.
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Introduction
Age-related changes in brain network activity are characterized by dedifferentiated and compensatory involvement of wider and more unspecialized brain regions during task completion which relates to a decline of sensory, motor and cognitive skills (Baltes and Lindenberger 1997; Park et al. 2004; Sala-Llonch et al. 2015). Despite the general tendency towards a decline, brain activity and network interaction in older adults were shown to be highly dependent on the individual’s lifestyle (Smith and Thelen 2003). One influencing factor might be cardiorespiratory fitness, which has the potential to diminish the described age effects in resting state networks (Voss et al. 2016). Here, we aimed to detect characteristics of brain network activity representing rest- and task-related specificity of information processing in elderly with different cardiorespiratory fitness levels.
Dedifferentiation was detected in task-related fMRI studies investigating reduced neural specialization as well as compensatory involvement of task relevant brain areas in older adults, which is considered part of dedifferentiation in this work (Sala-Llonch et al. 2015). Furthermore, it was shown that regional hyperactivation in older compared to younger participants was related to changes in both fMRI- and EEG-derived task-related functional networks (Geerligs et al. 2012, 2014). These changes also showed up across different tasks leading to a less task-specific activation of task-related brain network processes (Dennis and Cabeza 2011). Moreover, age-related changes seem to be multidimensional and complex. Chen et al. (2017) and Nobukawa et al. (2019) found age-related reorganization in the dynamics of brain networks, indicated by either higher complexity or irregularity in brain network patterns (Nobukawa et al. 2019) or changes in variations of functional connectivity over time (Chen et al. 2017). These findings might relate to increased background activity or neural noise throughout task execution (Hong and Rebec 2012). Increases in neuronal noise have been suggested as contributing factors to cognitive deficits and have been linked to neurobiological mechanisms (such as a decline in the dopaminergic neuromodulation) associated with a decrease in the distinction of cortical representations due to dedifferentiated brain activation (Li et al. 2001; Sala-Llonch et al. 2015).
Douw et al. (2014) related a higher interconnected functional modular topology of MEG derived resting state brain networks to cardiorespiratory fitness in middle aged participants. The findings indicate that cardiorespiratory fitness has an influence on brain networks and might bear the potential to counteract age-related changes, i.e., dedifferentiation and compensatory mechanisms. Indeed, Stillman et al. (2019) reviewed effects of physical activity and fitness on fMRI derived resting state brain networks in older adults and reported opposing effects on age-related changes. In this context, several authors reported an increase of connectivity within resting state networks in older adults due to cardiorespiratory fitness, which suggests less dedifferentiated brain functioning (Prakash et al. 2011; Voss et al. 2010, 2016). However, less is known about the influence of cardiorespiratory fitness on task-related brain network processes and dedifferentiation across different tasks in older adults. The influence of cardiovascular fitness on the decrease in specificity of information processing in the sensory, motor, and cognitive areas, in which age-related decline is reported, seems to be particularly relevant for everyday life and is yet unclear. Especially the investigation of dynamic processes of central information processing could provide new insights into this impact.
EEG allows to study brain dynamics with high temporal resolution capture changes of the temporal characteristics of functional networks. Due to the high complexity of age-related reorganization of brain activity and its interaction with cardiorespiratory fitness, we chose a holistic approach which combines the representation of spatial and temporal brain activity patterns. Dynamic mode decomposition (DMD) is an algorithm that was developed in the field of fluid dynamics (Rowley et al. 2009; Schmid and Sesterhenn 2008). It was recently applied to various other fields, including neuroscientific data (Brunton et al. 2016; Casorso et al. 2019; Gölz et al. 2018; Kunert-Graf et al. 2019; Vieluf et al. 2018). DMD combines the properties of spatial and temporal decomposition methods enlarging classical functional connectivity (FC) approaches based on bivariate connectedness between voxels or electrodes, which is frequently done in literature (Sporns 2013).
Utilizing DMD, we therefore aimed to study the influence of cardiorespiratory fitness on task-related brain network activity by assessing coherent spatio-temporal patterns of EEG in rest as well as tasks representing the sensory, motor, and cognitive domains, respectively. Albeit exploratory, we expected electrophysiological signatures of dedifferentiation, i.e., less task specificity in different tasks in fit compared to less fit individuals. In addition, we hypothesized that fit older adults have lower levels of neural noise, which translates into a higher prominence of dominant brain network patterns.
Materials and methods
The data were collected during an intervention study, which was registered at the German Clinical Trials Register (DRKS00014921) and took place at Paderborn University. The study protocol was approved by the ethics committee of the University of Muenster. Written informed consent to participate in the study was obtained by each participant before the experiments. No compensation was offered.
Participants
Participants were recruited via local newspaper and social media advertisements as well as by personal contact with organizations providing leisure activities for seniors. Participants were included if they (1) were above 60 years old, (2) free of diagnosed neurological or mental diseases and (3) right-handed. Half of the participants participated in a golf training and half continued their normal activities prior to the recording. In the context of this study golf was considered as part of the daily activities. All included participants reported subjective memory complaints in daily life but had no diagnosed form of dementia or its preclinical manifestation mild cognitive impairment, and were therefore considered healthy. All participants scored below 13 on a neuropsychological test battery (see Alzheimer’s Disease Assessment Scale-Cognitive Subscale (ADAS-cog) Table 1). In sum, a total of 41 participants between 60 and 77 years of age participated in this study (age: 67 ± 4.16, gender: 22 ♀, 19 ♂; see Table 1). All participants had normal or corrected to normal vision.
Screening
In preceding appointments, participants’ cardiorespiratory fitness was assessed with a 6 min walking test (Enright 2003). Participants had to walk 6 min as far as possible with a fast and constant pace. The distance was assessed as marker of cardiorespiratory fitness as this test was shown to be a reliable and valid way to test physical endurance in older adults (Rikli and Jones 1998; Zhang et al. 2017). Prior to the EEG measurement and in relation to the domains of the main tasks, maximum voluntary contraction (MVC) as well as reaction time (RT) and tactile threshold (TT) were assessed. MVC measurements consisted of three 5 s lasting maximum precision grip trials with 60 s rest in between (Vieluf et al. 2013). RT was assessed with auditive stimuli, i.e., 60 spoken letters presented via speakers. As soon as a letter was presented, participants had to press a foot switch immediately with the right foot. The foot switch was positioned in a standardized position next to the right foot. Reaction time was measured in relation to stimulus onset (Voelcker-Rehage and Alberts 2007). The TT was detected on the non-dominant hand as a 2-point discrimination test. Participants were asked to distinguish between one-point and two-point stimulation. The distance between the stimulation points was successively increased by 1 mm starting at a minimum distance of 1 mm. TT was achieved when the participant could clearly distinguish 7 out of 10 stimulations presented (Finnell et al. 2004).
EEG experiments
All EEG measurements were recorded with an actiCap electrode cap and BrainAmp standard amplifiers (Brain Products, Munich, Germany). We recorded brain activity at 128 electrodes with a sampling rate of 500 Hz. Ground and reference electrodes were fixed at FPz and FCz, respectively. Impedances were kept below 15 kΩ.
At first, EEG was recorded four minutes in a rest condition in supine position with eyes closed. During the tasks, participants sat 80 cm in front of a screen (23′′, 1920 × 1080 pixels at 60 Hz, AOC, Taipei, Taiwan). Their right arm rested comfortably on an armrest grasping a force transducer with index finger and thumb in precision grip (1022-C3-20 kg, SOEMER, Lennestadt-Elspe, Germany). Participants placed their left index finger on a braille device (P11, Metec Ag, Stuttgart Germany). In addition, speakers were placed approximately 50 cm behind the participants as well as a footswitch (StealthSwitch SS1R4 Pro USB, StealthSwitch, Highwood, IL, United States) next to their right foot. The tasks consisted of a motor task (force control), a cognitive task (auditive 2 back), and a sensory task (sensory oddball task) lasting 90 s. Each task was presented 2 times.
Motor task
Participants had to apply force to a force transducer with their index finger and thumb in precision grip to match a visually presented target (Voelcker-Rehage et al. 2006). The visual target was a line that moved from the right to the left on the screen for 90 s and changed level every 3 s in randomized order between heights that represents 10%, 20% and 30% of their individual MVC (see Fig. 1). Mean force level was set to 20% of participants MVC throughout the experiment. Participants were given online feedback on a screen 80 cm in front of them. Target line was displayed in blue whereas a red curser represented the applied force (see Fig. 1d).
Cognitive task
Participants were asked to listen to a sequence of letters presented via two speakers behind them and press the foot switch with the right foot, if a letter appeared again two letters later (2-back; see Fig. 1c). The sequences consisted of 60 letters in predefined randomized selections with 20% matching rate (Bopp and Verhaeghen 2018; Gajewski and Falkenstein 2014).
Sensory task
The braille device presented two stimuli (see Fig. 1a and 1b) to the participants with a randomized inter stimulus interval of 0.8–1.2 s (mean 1 s) and a duration of 0.5 s each. In this passive oddball design no response was required from the participants. Pattern (a) was set to 80% occurrence and pattern (b) to 20% (Reuter et al. 2012, 2013, 2014).
Data analysis
Data analysis was performed with BrainVision Analyzer 2.1.2 (Brain Products, Munich, Germany), MATLAB 2018b (Mathworks, Natick, MA, United States), EEGLAB 14.1.2 (Brunner et al. 2013), as well as Brainstorm 3.4 (Tadel et al. 2011) software packages. EEG data were cut from task onset to offset. Next, data were filtered with a zero-phase shift 4th order Butterworth filter from 1 to 30 Hz and an additional notch filter at 50 Hz implemented in Brain Vision Analyzer 2.1.2 was applied. After down sampling to 200 Hz, data were inspected for bad channels as well as electrode bridges using Alschuler’s et al. (2014) algorithm, which is based on the electrical distance of neighboring electrodes. To avoid false positives, coherence between adjacent channels was additionally checked for each pair of channels, where a value of 1 indicates complete coherence and a value of 0 indicates complete incoherence. Bad channels or channel pairs identified by Alschuler’s et al. (2014) algorithm and with a coherence above 0.97 were rejected. Participants whose rejection rate was above 15% or exhibited a bridged reference were excluded from further analysis. Seven participants had to be excluded here. From the remaining participants, we excluded on average 4% of the electrodes per participant. Then, data was re-referenced to common average and segmented into non-overlapping segments of 150 data points (0.75 s). Before performing an ICA on the re-concatenated data in EEGlab (AMICA, Palmer et al. 2011) for artifact rejection, segments containing non stereotypical artifacts identified by visual inspection were excluded. ICA components reflecting unambiguous artifacts such as eye blinks, heartbeat or muscle activity were marked as bad (mean rejection rate: 19 ± 5%) and excluded. After reconstruction of the signals all rejected channels were interpolated using spherical spline interpolation (Perrin et al. 1989) and checked again visually for segments containing artifacts.
In order to extract spatio-temporal coherent patterns within the EEG we decomposed the preprocessed data segments with the exact DMD algorithm described in Brunton et al. (2016) after Tu et al. (2014). Specifically, we constructed the two data matrices \(X \in {\mathbb{R}}^{{n \times \left( {m - 1} \right)}}\) and \(X^{{\prime }} \in {\mathbb{R}}^{{n \times \left( {m - 1} \right)}}\), where \(X\) is the original data matrix and \(X^{{\prime }}\) is the data matrix shifted by one time point containing \(m - 1\) datapoints of \(n\) electrodes. Moreover, the relationship between these two matrices can be expressed with a linear operator \(A\) describing the underlying dynamical process such that
The DMD of \(X\) is then obtained via eigen-decomposition of \(A\). In other words by analyzing the relationship between \(X\) and \(X^{{\prime }}\) in a given time window (see Brunton et al. 2016 for details of the algorithm) it is possible to approximate the linked spatial and temporal characteristics. Therefore, we can obtain an approximation \(\hat{X}\) of the observed measurement \(X\) by defining a dynamical model
The matrix \(\varPhi\) contains the dynamic modes, i.e., eigenvectors of \(A\) (see Theorem 1 in Tu et al. 2014) and \(\varOmega = \frac{\log \left( \varLambda \right)}{\Delta t}\) reveals the dynamics of the system, where the diagonal matrix \(\varLambda\) contains the DMD eigenvalues, i.e., eigenvalues of \(A\), on its diagonal. The variable \(t\) denotes time whereby \(\Delta t = 0.005\;{\text{s}}\). The constant \(z\) can be obtained from the initial conditions \(x_{1} = \varPhi z.\) Moreover, it is possible to obtain the oscillation frequencies in cycles per second (Hz) from \(\varOmega\):
We conjecture that the dimension of the underlying system is larger than the one obtainable from the original data matrix \(X\). Thus to avoid an underestimation, we propose to increase the dimension of the data matrix via the delay embedding method applied by Tu et al. (2014) and described in Brunton et al. (2016) as well as in Cohen (2018). In order to estimate the optimal values of the stacking factor h and the window size w we applied an error analysis on participant data of five randomly selected participants as described in Brunton et al. (2016). Based on these results we decided to choose a stacking depth of h = 5 and w = 150 data points.
To obtain the influence of each electrode in the DMD mode, the absolute DMD values associated with the θ (4 to < 7 Hz), α (7 to < 12 Hz), low β (12 to < 16 Hz) and high β (16 to < 30 Hz) frequencies were determined obtaining DMD mode magnitudes. Each DMD mode reflects a spatially coherent structure associated with a certain dynamic behavior, i.e., growth or decay and oscillation, where magnitude indicates the element’s (electrode) involvement in the mode. Next, we calculated a singular value decomposition (SVD) over all frequency specific modes over all time windows per participant to reduce the dimension of all time windows to its main features. Besides we calculated the proportion of variance among all activation patterns over time for each SVD mode:
where \(s_{j}\) are the singular values obtained via SVD and \(s_{i}\) denotes the \(i\)-th singular value corresponding to the \(i\)-th SVD mode. Since the first SVD mode explained most of the variance of the activation patterns in all subjects (M = 81.7% ± 1.1%) we extracted only the first mode to obtain the dominant feature of all DMD modes (DMD main mode) in all analyzed time windows. Moreover, we calculated the proportion of variance among all activation patterns explained by the obtained DMD main mode. The higher the proportion the more variation among all activation patterns during task completion is captured by this dominant mode which is considered representative for stability or prominence of this pattern.
As DMD is closely related to source separation, we used sLoreta to visualize the obtained spatial DMD maps in source space to demonstrate its relation. We created a three layer Boundary Element (BEM) forward model using the brainstorm toolbox based on a template of the McConnell Brain Imaging Center (MNI/ICBM152) and fitted the electrodes using recorded individual electrode positions per subject (Fonov et al. 2009; Gramfort et al. 2010; Pascual-Marqui 2002; Tadel et al. 2011).
Statistical analysis
All statistical analyses were conducted using SPSS 24 for Windows (IBM, Armonk, NY, United States), Matlab 2018b (Mathworks, Natick, MA, United States) with the additional Brainstorm package (Tadel et al. 2011) as well as R with RStudio (version 1.1.456) and the additional cramer-package (Baringhaus and Franz, 2004). To test differences between fit and less fit participants we divided them based on their performance in the 6-min walking test with a median split for men and women separately to account for gender differences (Bohannon 2007) in two groups. In order to characterize brain network activity and test for task specificity of the obtained DMD maps we compared the task- and rest-specific DMD mode maps pairwise with a permutation t-test for dependent measurements. The permutation approach was chosen as a non-parametric alternative and offers the advantage of calculating the exact test statistic. For this we chose a Monte Carlo approach with 10,000 randomizations, i.e., all possible values of the test statistics have been determined with a 10,000-fold random reordering of the data, the distribution of the t-test statistics under the null hypothesis (Maris 2012; Maris and Oostenveld 2007). By choosing this nonparametric statistic, we intended to account for the high dimensionality of the EEG data causing possible inaccuracies in test assumption requirements. By using an exact test statistics we intended a reduction of type I and type II errors (Maris and Oostenveld 2007). All p values were corrected with false discovery rate to account for type I errors (Benjamini and Hochberg 1995). For a statistical evaluation of the group differences, we exploratively compared the multivariate distribution of obtained t-values in each frequency band with Cramér tests between the groups. This nonparametric two sample test works on Euclidean interpoint distances to test the equality of the underlying distributions (Baringhaus and Franz, 2004).
We further analyzed the variance of all DMD modes explained by the DMD main mode with repeated measurement analysis of variance (ANOVA) with the between factor group (2; fit, less fit) and the within factor task (4; rest, motor, cognitive, sensory) for each frequency band (θ, α, low β, high β). Shapiro–Wilk and Box tests showed no violation of normal distribution and homogeneity of error variances (all p > .05). There was homogeneity of the error variances, as assessed by Levene’s test except for the variables in the theta and alpha band during n-back and sensory tasks. We nevertheless report those values, as ANOVA was shown to be a robust test statistics in groups with almost the same size larger than 10 (Box 1954; Schmider et al. 2010). Significant interactions and main effects were followed by Bonferroni corrected pairwise comparisons. Independent t-tests and Mann–Whitney U tests, in case of violation of normal distribution, were used to check for differences in characteristics between the groups. The level of significance was set a priori to α = 0.05 for all tests.
Results
The personal characteristics of the final sub-sample are shown in Table 1. Mann–Whitney U tests and independent t-tests showed no significant differences between the groups of fit and less fit participants for personal characteristics or screening variables, except for the walked distance in the six minute walking test (fit: M = 765 m, SD = 127 m; less fit: M = 549 m, SD = 100 m, t(29) = − 5.25, p < .001).
DMD mode maps
Figure 2 illustrates the DMD topographical maps with an estimated source localization. Note that the source localization is only presented for visualization purposes here. Each DMD mode reflects a pattern of correlation in space at certain frequencies (Kutz et al. 2016). Low values indicate low contribution to the mode whereas high values indicate high contribution to that mode. Noticeable DMD main mode maps at rest showed frequency specific characteristics. The θ activity was dominant over frontal-central areas and showed highest values in the motor task. Dominant α activity over occipital regions during rest was suppressed and shifted to temporo-parietal areas. The low β activation showed the highest values at rest above the central areas and became more extensive in temporal direction during tasks. While the high β-band showed a similar central activation during rest, the activity in this frequency band changed towards a dominant activation over frontal with a shift towards centro-temporal areas that seemed to be most pronounced during the motor task (see Fig. 2).
Figure 3a–d illustrates the comparisons between the tasks for the fit and less fit groups separately in the analyzed frequency bands (θ, α, low β and high β) as topographic t-maps. For simplicity and clarity of presentation only minimum and maximum t- and corresponding p-values as well as their electrode position are presented in Tables 2 and 3. Means and standard deviations per electrode are available in the supplementary material (Online Resource 1).
For both groups and frequency bands, DMD main mode maps differed between each task and rest with the strongest differences in the θ-band and in the high β-band. Both groups θ-band main mode during task was characterized by higher activity over parieto-occipital areas and lower activity over fronto-temporal areas compared to rest. In contrast, in the high β-band, the differences between task execution and rest are marked by lower activation over (parieto-) central and higher activation over frontal and occipital areas in both groups.
Comparing the t-distributions with Cramér tests between the two groups revealed significant differences for all frequency bands (all p < .001). Studying the t-maps in group comparison, finer spatial differences can be observed. The differences between task and rest seem to be similar between the groups in the θ-band and in the high β-band. However, the differences between tasks and rest might be stronger in α- and low β-bands in the fit compared to the less fit group. This is especially observed in the α-band with lower parieto-occipital/frontal and higher temporal-central activation during motor task compared to the rest condition. Similar trends could be observed in the low β-band with higher parieto-occipital and lower central activation in the cognitive task compared to (see Fig. 3; Table 2).
There were likewise fewer pronounced differences between the task conditions with the highest expression between the motor task and the two other tasks in both groups. The differences, however, seemed to predominate in the fit group, especially in the θ-band and in the high β-band in the motor task compared to the sensory and cognitive tasks. In the fit group the θ-band is characterized by reduced activation of parieto-occipital and higher activation of temporo-parietal areas in the n-back task as well as higher temporo-frontal and a reduced activation of central and parietal areas of the sensory compared to the motor task. High β-band differences were present in form of activation over central areas and sporadically decreased over frontal or occipital areas of the cognitive and sensory tasks compared to the motor task. There were likewise only small differences in both groups in task comparisons in the low β-band. Comparison of cognitive and sensory task revealed almost no differences in both groups (see Table 3).
Explained variance
Results of DMD main mode explained variance are illustrated in Fig. 3e–h. Repeated measures ANOVA revealed a significant effect of task in the θ-band [F(3, 87) = 26.704, p < .001, partial η2 = .479] but none for group [F(1, 29) = 3.174, p = .085, partial η2 = .099]. Post hoc tests revealed significant differences between the motor and the n-back task independent of group (p = .023).
Moreover, there was a significant main effect of task in the α-band [F(3, 87) = 4647, p = .005, partial η2 = .138] but no significant effect of group [F(1, 29) = 2.79, p = .106, partial η2 = .088]. All tasks differed significantly from rest (sensory: p < .001; motor: p < .001; cognitive: p = .002). Sensory and motor differed significantly (p = .008) as well as motor and n-back (p < .001).
In the low β-band there was a significant effect of task [F(3, 87) = 31.399, p < .001, partial η2 = .520], but neither an effect of group [F(1, 29) = 1.034, p = .318, partial η2 = .030] nor an interaction between task and group [F(3, 87) = 1.204, p = .313, partial η2 = .040] were significant. The sensory task and motor task explained variance showed significantly lower values compared to rest (p < .001). Motor task was characterized by significantly lower values compared to the sensory task (p < .001) and cognitive task (p = .001) as well as higher values of the cognitive compared to the sensory task (p = .020).
Repeated measures ANOVA revealed a significant main effect of task [F(3, 87) = 41.855, p < .001, partial η2 = .600] and group [F(1, 29) = 12.572, p = .001, partial η2 = .300] in the high β-band. There was no significant interaction of task and group [F(3, 87) = 2.004, p = .119, partial η2 = .070]. Bonferroni-corrected post hoc tests demonstrated significantly higher values in rest compared to all tasks (all p < .001).
Discussion
Utilizing the multivariate analysis method dynamic mode decomposition (DMD), we aimed to find characteristics of task specific brain network patterns and their differences in fit compared to less fit elderly. We analyzed EEG data recorded during sensory, motor, and cognitive tasks in comparison to rest. DMD revealed frequency-dependent spatio-temporal scalp patterns that appear at rest and three different tasks. In fit older adults, these patterns showed trends of higher task specificity pointing to less dedifferentiated brain activity. Furthermore, we found this pattern’s proportion of total variance explained higher in fit participants which might indicate less neural noise during task execution. The results jointly support the idea that physical fitness reduces the impact of dedifferentiation.
We identified main features of frequency specific brain network dynamics expressed in task-specific EEG patterns. As DMD can be conceptualized as a combination of well-known spectral analysis methods like the Fourier Transform with the Fast Fourier Transform algorithm (FFT) and spatial decomposition with principle component analysis (PCA) our results are comparable to well-known EEG-power characteristics modified throughout the tasks reflecting markers of frequency specific network interaction and modulation dominant throughout the tasks. However, in addition DMD links the assessed spatial and temporal properties providing a low-dimensional representation of the underlying time-variable complex system.
In examining the DMD derived EEG patterns we aimed to study selectivity of neural responses, or dedifferentiation, across rest and three different tasks. The dominant fronto-central θ activation found here has been discussed as being sensitive to cognitive involvement and was dominant in the task conditions compared to rest (Jensen and Mazaheri 2010; Onton et al. 2005; Siegel et al. 2012). Occipital α activity being suppressed in the task conditions in this study has been discussed as a marker for the suppression of the visual network during visual attention. In general, the activity of α could play a role in so-called gating by inhibition processes, i.e., the selective activation of task-relevant and suppression of task-irrelevant areas and networks (Jensen and Mazaheri 2010). Moreover, high β was discussed as a marker of large-scale coupling and sensorimotor information integration showing wider distribution in the tasks compared to the rest condition (Siegel et al. 2012). Overall, the expression of these patterns was different in rest and the three tasks and can be regarded as reflection of task-specific network activation processes linked to aforementioned processes. Indeed, comparing these patterns across tasks both groups showed differences between rest and all tasks in all frequency bands, most dominant in θ- and high β-bands. The role of these two frequency bands could indicate the importance of cognitive control and large-scale coupling in maintaining functioning in older age pointing to compensatory activity as it was found by Vlahou et al. (2014) and Knyazev et al. (2015).
In line with the influence of cardiorespiratory fitness on resting state networks we hypothesized to find task specificity of these task-related brain network patterns less pronounced in less fit participants compared to fit participants. By comparing information processing between a motor, cognitive, and sensory task, we were able to study the influence of cardiorespiratory fitness on the reduction of neuronal specialization between tasks. These task domains should correspond to the domains in which age-related decline is reported and thus provide a high relevance for everyday life. In fact, the differences between the tasks seem to be more pronounced in the fit group compared to the less fit group. In other words, task-related neural responses of fit compared to less fit participants showed higher differentiation across task. This finding thus might indicate opposing effects of cardiorespiratory fitness on age-related reduction of neuronal dedifferentiation found in literature in motor, cognitive as well as visual tasks (Carp et al. 2011; Park et al. 2004; Rajah and D’Esposito 2005) and is in line with findings showing these effects on resting state networks (Voss et al. 2016). However, there were no clear significant differences between the sensory and the cognitive task in both groups. The undetectable difference indicates a similar degree of dedifferentiation that is independent of the cardiorespiratory fitness level. On the other side it has been shown that both tasks are highly dependent on the cognitive resources of working memory, this may have masked task-specific differences between the two tasks (Dehghan Nayyeri et al. 2019). It is also noteworthy that the clearest differences between the tasks were again found in the theta and high beta range. This could again show the influence of cognitive control processes and large-scale coupling in maintaining function in older adults and could also indicate that these processes are influenced by cardiorespiratory fitness.
Based on recent reports on age-related changes in the dynamics of reorganization processes linking increased levels of neural noise and dedifferentiation, we characterized each DMD main mode in terms of the proportion of the total variance of all activation patterns explained by the dominant pattern. By analyzing this as stability or prominence of the main DMD mode throughout task execution, we intended to take into account the changes in the dynamics of age-related reorganization reported in the literature (Chen et al. 2017; Li et al. 2001; Nobukawa et al. 2019). Furthermore, we aimed to investigate differences in this dynamic between subjects with different levels of cardiorespiratory fitness. Expecting lower levels of neural noise in the fit group, we found lower values in high β main mode explained variance in the less fit group independent of the task. Carefully interpreted, this could lead to a more targeted, task-specific information processing throughout task execution. With this finding, the present study can contribute to previous literature describing effects of cardiorespiratory fitness on age-related cognitive changes and brain network dynamics. To the best of our knowledge, no study has yet investigated the influence of cardiorespiratory fitness on dynamic brain network processes in older adults in the context of dedifferentiation. The comparison of brain networks during a variety of tasks and analyzing the similarities and differences allows to gain insights into functional organizations of task relevant activities. Our results point to less neural noise throughout task execution in the fit group and extend the existing knowledge about the influence of cardiorespiratory fitness on dynamic processes and age-related changes in these processes.
On a methodological level, decomposing EEG spatial temporal dynamics with DMD is dependent on delay embedding, i.e., stacking factor, as well as number of electrodes and chosen window size. We picked the parameters according to an error analyses over several participants to choose the optimal parameters. Moreover, delay embedding was used by other authors before (Brunton et al. 2016; Cohen 2017). As we measured high density EEG, we decided to check for bridging artifacts. Therefore, we used an algorithm proposed by Alschuler et al. (2014) which identifies bridges based on the electrical distance distribution of the signals. However, Alschuler et al. (2014) note that this algorithm might be too conservative. We therefore decided to double check this step and calculated the coherence between neighboring channels.
In order to achieve a high level of comparability between tasks and groups of participants, we decided to reduce dimensionality of the variables with SVD and chose the most important characteristic, i.e., the first principle component. We decided not to study further components since we describe a coarse phenomenon such as dedifferentiation.
Moreover, we used the 6-min walking test to asses cardiorespiratory fitness instead of VO2max measurements. This test is highly influenced by motivational aspects. However, there is a strong relation between the 6-min walking test and VO2max and it is used as a common standard for indirect measurement of cardiorespiratory performance (Zhang et al. 2017) and the practicability as well as the motivation of the participants was very high for the selected test. Although all participants can be seen as rather fit in comparison to norm values reported in literature (Bohannon 2007) we found differences between fit and less fit in line with dedifferentiation. When measurements took place, participants had either learned golf within the last 22 weeks or continued with their normal daily activities. The golf training could have obviously influenced the results. In this study we were more interested in the long-term effects associated with cardiorespiratory fitness, reflected by the 6-min walking test, than in short-term effects caused by golf training. Moreover, Voss et al. (2016) pointed out that the influence of cardiorespiratory fitness and short-term physical activity on brain networks are independent phenomena. Of course, longitudinal recordings and a more objective measurement of cardiorespiratory fitness and daily activity would extend presented findings. As this study was part of a bigger intervention study, sample size was fixed a priori. The primary outcome of this study was the ADAS-Cog based on the randomized controlled trial of Lautenschlager et al. (2008). The standardized mean difference for ADAS-Cog was -1.22. The drop-out rate was set to 20%. It was estimated that a sample size of 46 participants (23 in each group) would provide 95% power for detecting a significant group difference. A healthy young control group would be beneficial in order to categorize our findings.
Conclusion
In applying DMD to continuous EEG recordings during rest and three different tasks, we considered both topological properties and the temporal dynamics of task-related brain networks. Thus, we identified electrophysiological signatures of age-related brain reorganization processes in fit and less fit older adults. Fit participants showed higher task specificity, i.e., more differentiated brain activation patterns, as well as higher prominence of these patterns, indicating less neural noise throughout task execution. Our findings support the idea that physical fitness manifests in task-related brain network activation patterns that are in line with reduced dedifferentiation in older adults.
Data availability
Data and material are available from the corresponding author, SV, upon reasonable request.
References
Alschuler DM, Tenke CE, Bruder GE, Kayser J (2014) Identifying electrode bridging from electrical distance distributions: a survey of publicly-available EEG data using a new method. Clin Neurophysiol 125:484–490. https://doi.org/10.1016/j.clinph.2013.08.024
Baltes P, Lindenberger U (1997) Emergence of a powerful connection between sensory and cognitive functions across the adult life span: a new window to the study of cognitive aging? Psychol Aging 12:12–21. https://doi.org/10.1037//0882-7974.12.1.12
Baringhaus L, Franz C (2004) On a new multivariate two-sample test. J Multivar Anal 88(1):190–206. https://doi.org/10.1016/S0047-259X(03)00079-4
Benjamini Y, Hochberg Y (1995) Controlling the false discovery rate: a practical and powerful approach to multiple testing. J R Stat Soc Series B Stat Methodol 57:289–300. https://doi.org/10.1111/j.2517-6161.1995.tb02031.x
Bohannon RW (2007) Six-minute walk test: a meta-analysis of data from apparently healthy elders. Top Geriatr Rehabil 23:155–160. https://doi.org/10.1097/01.TGR.0000270184.98402.ef
Bopp KL, Verhaeghen P (2018) Aging and n-back performance: a meta-analysis. J Gerontol B Psychol 25:2252. https://doi.org/10.1093/geronb/gby024
Box GEP (1954) Some theorems on quadratic forms applied in the study of analysis of variance problems, II. Effects of inequality of variance and of correlation between errors in the two-way classification. Ann Math Stat 25:484–498. https://doi.org/10.1214/aoms/1177728717
Brunner C, Delorme A, Makeig S (2013) Eeglab: an open source matlab toolbox for electrophysiological research. Biomed Tech (Berl). https://doi.org/10.1515/bmt-2013-4182
Brunton BW, Johnson LA, Ojemann JG, Kutz JN (2016) Extracting spatial–temporal coherent patterns in large-scale neural recordings using dynamic mode decomposition. J Neurosci Methods 258:1–15. https://doi.org/10.1016/j.jneumeth.2015.10.010
Carp J, Park J, Hebrank A, Park DC, Polk TA (2011) Age-related neural dedifferentiation in the motor system. PLoS ONE 6:e29411. https://doi.org/10.1371/journal.pone.0029411
Casorso J, Kong X, Chi W, van de Ville D, Yeo BT, Liégeois R (2019) Dynamic mode decomposition of resting-state and task fMRI. NeuroImage 194:42–54. https://doi.org/10.1016/j.neuroimage.2019.03.019
Chen Y, Wang W, Zhao X, Sha M, Liu YN, Zhang X, Ma J, Ni H, Ming D (2017) Age-related decline in the variation of dynamic functional connectivity: a resting state analysis. Front Aging Neurosci 9:203. https://doi.org/10.3389/fnagi.2017.00203
Cohen MX (2017) Comparison of linear spatial filters for identifying oscillatory activity in multichannel data. J Neurosci Methods 278:1–12. https://doi.org/10.1016/j.jneumeth.2016.12.016
Cohen MX (2018) Using spatiotemporal source separation to identify prominent features in multichannel data without sinusoidal filters. Eur J Neurosci 48:2454–2465. https://doi.org/10.1111/ejn.13727
Dehghan Nayyeri M, Burgmer M, Pfleiderer B (2019) Impact of pressure as a tactile stimulus on working memory in healthy participants. PLoS ONE 14:e0213070–e0213070. https://doi.org/10.1371/journal.pone.0213070
Dennis NA, Cabeza R (2011) Age-related dedifferentiation of learning systems: an fMRI study of implicit and explicit learning. Neurobiol Aging 32:2318.e17–2318.e30. https://doi.org/10.1016/j.neurobiolaging.2010.04.004
Douw L, Nieboer D, van Dijk BW, Stam CJ, Twisk JWR (2014) A healthy brain in a healthy body: brain network correlates of physical and mental fitness. PLoS ONE 9:e88202. https://doi.org/10.1371/journal.pone.0088202
Enright PL (2003) The six-minute walk test. Respir Care 48:783–785
Finnell JT, Knopp R, Johnson P, Holland PC, Schubert W (2004) A calibrated paper clip is a reliable measure of two-point discrimination. Acad Emerg Med 11:710–714. https://doi.org/10.1197/j.aem.2003.11.022
Fonov VS, Evans AC, McKinstry RC, Almli CR, Collins DL (2009) Unbiased nonlinear average age-appropriate brain templates from birth to adulthood. NeuroImage 47:S102. https://doi.org/10.1016/S1053-8119(09)70884-5
Gajewski PD, Falkenstein M (2014) Age-related effects on ERP and oscillatory EEG-dynamics in a 2-back task. J Psychophysiol 28:162–177. https://doi.org/10.1027/0269-8803/a000123
Geerligs L, Saliasi E, Maurits NM, Lorist MM (2012) Compensation through increased functional connectivity: neural correlates of inhibition in old and young. J Cognit Neurosci 24:2057–2069. https://doi.org/10.1162/jocn_a_00270
Geerligs L, Maurits NM, Renken RJ, Lorist MM (2014) Reduced specificity of functional connectivity in the aging brain during task performance. Hum Brain Mapp 35:319–330. https://doi.org/10.1002/hbm.22175
Gölz C, Voelcker-Rehage C, Mora K, Reuter E-M, Godde B, Dellnitz M, Reinsberger C, Vieluf S (2018) Improved neural control of movements manifests in expertise-related differences in force output and brain network dynamics. Front Physiol 9:1540. https://doi.org/10.3389/fphys.2018.01540
Gramfort A, Papadopoulo T, Olivi E, Clerc M (2010) OpenMEEG: opensource software for quasistatic bioelectromagnetics. Biomed Eng Online 9:45. https://doi.org/10.1186/1475-925X-9-45
Hong S, Rebec G (2012) A new perspective on behavioral inconsistency and neural noise in aging: compensatory speeding of neural communication. Front Aging Neurosci 4:27. https://doi.org/10.3389/fnagi.2012.00027
Jensen O, Mazaheri A (2010) Shaping functional architecture by oscillatory alpha activity: gating by inhibition. Front Hum Neurosci 4:186. https://doi.org/10.3389/fnhum.2010.00186
Knyazev GG, Volf NV, Belousova LV (2015) Age-related differences in electroencephalogram connectivity and network topology. Neurobiol Aging 36:1849–1859. https://doi.org/10.1016/j.neurobiolaging.2015.02.007
Kunert-Graf JM, Eschenburg KM, Galas DJ, Kutz JN, Rane SD, Brunton BW (2019) Extracting reproducible time-resolved resting state networks using dynamic mode decomposition. Front Comput Neurosci 13:75. https://doi.org/10.3389/fncom.2019.00075
Kutz JN, Brunton SL, Brunton BW, Proctor JL (2016) Dynamic mode decomposition: data-driven modelling of complex systems. SIAM, Philadelphia
Lautenschlager NT, Cox KL, Flicker L, Foster JK, van Bockxmeer FM, Xiao J, Greenop KR, Almeida OP (2008) Effect of physical activity on cognitive function in older adults at risk for Alzheimer disease: a randomized trial. JAMA 300:1027–1037. https://doi.org/10.1001/jama.300.9.1027
Li S-C, Lindenberger U, Sikström S (2001) Aging cognition: from neuromodulation to representation. Trends Cogn Sci 5:479–486. https://doi.org/10.1016/S1364-6613(00)01769-1
Maris E (2012) Statistical testing in electrophysiological studies. Psychophysiol 49:549–565. https://doi.org/10.1111/j.1469-8986.2011.01320.x
Maris E, Oostenveld R (2007) Nonparametric statistical testing of EEG- and MEG-data. J Neurosci Methods 164:177–190. https://doi.org/10.1016/j.jneumeth.2007.03.024
Nobukawa S, Kikuchi M, Takahashi T (2019) Changes in functional connectivity dynamics with aging: a dynamical phase synchronization approach. NeuroImage 188:357–368. https://doi.org/10.1016/j.neuroimage.2018.12.008
Onton J, Delorme A, Makeig S (2005) Frontal midline EEG dynamics during working memory. NeuroImage 27:341–356. https://doi.org/10.1016/j.neuroimage.2005.04.014
Palmer J, Kreutz-Delgado K, Makeig S (2011) AMICA: an adaptive mixture of independent component analyzers with shared components. https://sccn.ucsd.edu/~jason/amica_a.pdf. Accessed 3 December 2019
Park DC, Polk TA, Park R, Minear M, Savage A, Smith MR (2004) Aging reduces neural specialization in ventral visual cortex. Proc Natl Acad Sci USA 101:13091–13095. https://doi.org/10.1073/pnas.0405148101
Pascual-Marqui RD (2002) Standardized low-resolution brain electromagnetic tomography (sLORETA): technical details. Method Find Exp Clin 24(Suppl D):5–12
Perrin F, Pernier J, Bertrand O, Echallier JF (1989) Spherical splines for scalp potential and current density mapping. Electroencephalogr Clin Neurophysiol 72:184–187. https://doi.org/10.1016/0013-4694(89)90180-6
Prakash RS, Voss MW, Erickson KI, Lewis JM, Chaddock L, Malkowski E, Alves H, Kim J, Szabo A, White SM, Wójcicki TR, Klamm EL, McAuley E, Kramer AF (2011) Cardiorespiratory fitness and attentional control in the aging brain. Front Hum Neurosci 4:229. https://doi.org/10.3389/fnhum.2010.00229
Rajah MN, D’Esposito M (2005) Region-specific changes in prefrontal function with age: a review of PET and fMRI studies on working and episodic memory. Brain 128:1964–1983. https://doi.org/10.1093/brain/awh608
Reuter E-M, Voelcker-Rehage C, Vieluf S, Godde B (2012) Touch perception throughout working life: effects of age and expertise. Exp Brain Res 216:287–297. https://doi.org/10.1007/s00221-011-2931-5
Reuter E-M, Voelcker-Rehage C, Vieluf S, Winneke AH, Godde B (2013) A parietal-to-frontal shift in the P300 is associated with compensation of tactile discrimination deficits in late middle-aged adults. Psychophysiol 50:583–593. https://doi.org/10.1111/psyp.12037
Reuter E-M, Voelcker-Rehage C, Vieluf S, Winneke AH, Godde B (2014) Extensive occupational finger use delays age effects in tactile perception-an ERP study. Atten Percept Psychophys 76:1160–1175. https://doi.org/10.3758/s13414-014-0634-2
Rikli R, Jones J (1998) The reliability and validity of a 6-minute walk test as a measure of physical endurance in older adults. J Aging Phys Activ 6:363–375. https://doi.org/10.1123/japa.6.4.363
Rowley CW, Mezić I, Bagheri S, Schlatter P, Henningson DS (2009) Spectral analysis of nonlinear flows. J Fluid Mech 641:115–127. https://doi.org/10.1017/S0022112009992059
Sala-Llonch R, Bartrés-Faz D, Junqué C (2015) Reorganization of brain networks in aging: a review of functional connectivity studies. Front Psychol 6:663. https://doi.org/10.3389/fpsyg.2015.00663
Schmid P, Sesterhenn J (2008) Dynamic mode decomposition of numerical and experimental data. In: APS division of fluid dynamics meeting abstracts, MR.007
Schmider E, Ziegler M, Danay E, Beyer L, Buehner M (2010) Is it really robust? Reinvestigating the robustness of ANOVA against the normal distribution. Eur J Res Methods Behav Soc Sci 6:15–147. https://doi.org/10.1027/1614-2241/a000016
Siegel M, Donner TH, Engel AK (2012) Spectral fingerprints of large-scale neuronal interactions. Nat Rev Neurosci 13:121–134. https://doi.org/10.1038/nrn3137
Smith LB, Thelen E (2003) Development as a dynamic system. Trends Cogn Sci 7:343–348. https://doi.org/10.1016/S1364-6613(03)00156-6
Sporns O (2013) Structure and function of complex brain networks. Dialogues Clin Neurosci 15:247–262
Stillman CM, Donofry SD, Erickson KI (2019) Exercise, fitness and the aging brain: a review of functional connectivity in aging. Arch Sci Psychol. https://doi.org/10.31296/aop.v3i4.98
Tadel F, Baillet S, Mosher JC, Pantazis D, Leahy RM (2011) Brainstorm: a user-friendly application for MEG/EEG analysis. Comput Intell Neurosci 2011:879716. https://doi.org/10.1155/2011/879716
Tu J, Rowley C, Luchtenburg D, Brunton S, Kutz J (2014) On dynamic mode decomposition: theory and applications. JCD 1:391–421. https://doi.org/10.3934/jcd.2014.1.391
Vieluf S, Godde B, Reuter E-M, Voelcker-Rehage C (2013) Age-related differences in finger force control are characterized by reduced force production. Exp Brain Res 224:107–117. https://doi.org/10.1007/s00221-012-3292-4
Vieluf S, Mora K, Gölz C, Reuter E-M, Godde B, Dellnitz M, Reinsberger C, Voelcker-Rehage C (2018) Age- and expertise-related differences of sensorimotor network dynamics during force control. Neurosci 388:203–213. https://doi.org/10.1016/j.neuroscience.2018.07.025
Vlahou EL, Thurm F, Kolassa I-T, Schlee W (2014) Resting-state slow wave power, healthy aging and cognitive performance. Sci Rep 4:5101. https://doi.org/10.1038/srep05101
Voelcker-Rehage C, Alberts JL (2007) Effect of motor practice on dual-task performance in older adults. J Gerontol B Psychol Sci Soc Sci 62:P141–P148. https://doi.org/10.1093/geronb/62.3.P141
Voelcker-Rehage C, Stronge AJ, Alberts JL (2006) Age-related differences in working memory and force control under dual-task conditions. Neuropsychol Dev Cogn B Aging Neuropsychol Cogn 13:366–384. https://doi.org/10.1080/138255890969339
Voss MW, Prakash RS, Erickson KI, Basak C, Chaddock L, Kim JS, Alves H, Heo S, Szabo AN, White SM, Wójcicki TR, Mailey EL, Gothe N, Olson EA, McAuley E, Kramer AF (2010) Plasticity of brain networks in a randomized intervention trial of exercise training in older adults. Front Aging Neurosci 2:32. https://doi.org/10.3389/fnagi.2010.00032
Voss MW, Weng TB, Burzynska AZ, Wong CN, Cooke GE, Clark R, Fanning J, Awick E, Gothe NP, Olson EA, McAuley E, Kramer AF (2016) Fitness, but not physical activity, is related to functional integrity of brain networks associated with aging. NeuroImage 131:113–125. https://doi.org/10.1016/j.neuroimage.2015.10.044
Zhang Q, Lu H, Pan S, Lin Y, Zhou K, Wang L (2017) 6MWT performance and its correlations with VO2 and handgrip strength in home-dwelling mid-aged and older chinese. Int J Environ Res Public Health 14:473. https://doi.org/10.3390/ijerph14050473
Acknowledgements
We thank Franziska van den Bongard and Roman Gaidai for support during data collection.
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Open Access funding enabled and organized by Projekt DEAL. The study was supported within the framework of the equality concept of the Paderborn University through funding line 2.
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CG, JKS, FKH, CR and SV contributed to the study conception and design. CG and FKH set up the experiments. Data collection were performed by CG, JKS and FKH. CG and KM analyzed data. All authors interpreted results, drafted parts of the work, approved the final version of the manuscript, and agreed to be accountable for all aspects of the work.
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Goelz, C., Mora, K., Stroehlein, J.K. et al. Electrophysiological signatures of dedifferentiation differ between fit and less fit older adults. Cogn Neurodyn 15, 847–859 (2021). https://doi.org/10.1007/s11571-020-09656-9
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DOI: https://doi.org/10.1007/s11571-020-09656-9