Distribution of brain sodium long and short relaxation times and concentrations: a multi-echo ultra-high field 23Na MRI study

Sodium (23Na) MRI proffers the possibility of novel information for neurological research but also particular challenges. Uncertainty can arise in in vivo 23Na estimates from signal losses given the rapidity of T2* decay due to biexponential relaxation with both short (T2*short) and long (T2*long) components. We build on previous work by characterising the decay curve directly via multi-echo imaging at 7 T in 13 controls with the requisite number, distribution and range to assess the distribution of both in vivo T2*short and T2*long and in variation between grey and white matter, and subregions. By modelling the relationship between signal and reference concentration and applying it to in vivo 23Na-MRI signal, 23Na concentrations and apparent transverse relaxation times of different brain regions were measured for the first time. Relaxation components and concentrations differed substantially between regions of differing tissue composition, suggesting sensitivity of multi-echo 23Na-MRI toward features of tissue composition. As such, these results raise the prospect of multi-echo 23Na-MRI as an adjunct source of information on biochemical mechanisms in both physiological and pathophysiological states.

In the physiological state, the maintenance of the transmembrane sodium ( 23 Na) concentration gradient (10-15 mM intracellular sodium concentration and ~140 mM extracellular sodium concentration) is a precondition for several critical cellular functions. These include the transport of ions, neurotransmitters and nutrients; regulation of osmotic and electrostatic forces on cells and macromolecules; as well as the transmission of action potentials [1][2][3] . In the diseased state, multiple pathological pathways can lead to aberrations of these functions. Such alterations can lead to changes in intra-and extracellular concentrations due to a reduced ability to maintain resting conditions and due to conformational changes in cells themselves as well as the cellular environment in which they are embedded. Thus, 23 Na-MRI is a potential source of more direct and quantitative biochemical information than is generally possible with conventional proton ( 1 H) MRI 4 . As such, there is substantial interest in 23 Na-MRI regarding a range of neurological conditions despite the additional complications of acquiring 23 Na-MRI signal, including stroke 5 , epilepsy 6 , tumors 7 and neurodegenerative diseases [8][9][10][11][12] .
The quadrupolar 23 Na nucleus (spin = 3/2) is subject to the influence of fluctuations in neighbouring electric fields due to net positive and non-uniform distribution of charge 3,[13][14][15] . In the presence of a magnetic field, 23 Na nuclei exhibit four discrete energy states, with three possible (single quantum, SQ) transitions (−1/2, +1/2 "central transition"; −3/2, −1/2 and 1/2, 3/2 "satellite transitions"). In highly motile environments such as plasma or cerebrospinal fluid (CSF), the correlation time (τ C ) is much shorter than the Larmor period (ω 0 −1 ) (ω 0 • τ C ≪ 1), leading to monoexponential longitudinal (T 1 ) and transverse (T 2 ) relaxation. This is in contrast to tissue environments such as within cells and the interstitial spaces between cells where diffusion is restricted by interactions of the 23 Na cation with macromolecular anions. Such interactions modulate decay behaviour in a measurable way: the satellite transitions are subject to additional fast relaxation processes so that both T 1 and T 2 reflect  Figure 2 provides an overview of the workflow applied to data, including the extraction of decay time components (T 2 * short and T 2 * long ), concentrations (Na SF , Na LF ), total sodium concentration (TSC) and extracellular fraction (EcF). See Table 1 for mean estimates of each parameter for each tissue type and region.

Results
Goodness of fit indicated high performance of the biexponential decay model across the 10 ROIs including complete GM and WM segmentations and eight sub-cortical ROIs (mean r 2 = 0.97 ± 0.01(s.d.)). The mean proportion of the signal fraction (f) associated with the short T 2 * component to total signal estimated by the biexponential model is 57.7% ± 0.07 (s.d.). There was also variation among ROIs (Fig. 3) with the overall highest value obtained for the centrum semiovale (70% ± 0.04 (s.d.)). The caudate nucleus (52% ± 0.06 (s.d.)) and pons (52% ± 0.1 (s.d.)) jointly provide the lowest estimates among subcortical regions, while the lowest mean estimate across all ROIs was for the entire GM segmentation (46% ± 0.03(s.d.)).
T 2 * short and T 2 * long differences between white and grey matter. Table 2a provides results for the whole model (ANOVA, corrected at P < 0.008) and main effects of Tissue Type (GM, WM) for each parameter. Effects of Age and Sex were not found to be significant for any parameter. Significant effects were observed for whole model for T 2 * long (P < 0.0001) and T 2 * short (P = 0.005) as well significant effects of tissue type for T 2 * long (P < 0.0001) and T 2 * short (P = 0.001).
Results of post-hoc Steel-Dwass tests are detailed in Table 3 and represented in Fig. 4. Significantly higher (z = −3.03, P < 0.003) values of T 2 * short were observed in GM (4.99 ms ± 0. 41 T 2 * short and T 2 * long differences between sub-cortical regions. ANOVAs revealed significant (P < 0.0001) effects for both the whole model and the effect of Region (Table 2b) on both T 2 * short and T 2 * long . Overall, in terms of the post-hoc analysis ( Table 3, Fig. 4b), we observed substantial variation for each parameter between subcortical regions. The shortest mean decay time components were observed in the pons for both T 2 * short (2.43 ms ± 0.58(s.d.)) and T 2 * long (31.52 ms ± 11.45(s.d.)), with the longest observed in the centrum semiovale (T 2 * short : 4.37 ms ± 0.43(s.d.); T 2 * long : 54.74 ms ± 14.98(s.d.)). The centrum semiovale also evidenced a wide distribution of T 2 * long estimates between subjects.
Concentration differences between white and grey matter. The whole model and the main effect of tissue type were significant (P < 0.0001) for Na LF  Concentration differences between sub-cortical regions. Both NaSF and NaLF, as well as TSC and EcF, demonstrated significant (P < 0.0001) effects for both the whole model and the effect of Region. A significant effect of Sex was also observed for TSC (P = 0.006). As above, concentrations and derived metrics showed a variety of variations between regions. The thalamus demonstrated the highest mean estimates of Na SF (24.28 mM ± 1.66(s.d.)) and TSC (40.30 mM ± 2.33(s.d.)), with the lowest estimates observed in the pons (Na SF : 13.19 mM ± 3.68(s.d.); TSC: 25.18 mM ± 3.17(s.d.)). The caudate (Na LF : 17.80 mM ± 2.95(s.d.); EcF: 0.13 ± 0.02(s.d.)) and centrum semiovale (Na LF : 8.46 mM ± 1.68(s.d.); EcF: 0.06 ± 0.01 (s.d.)), provided the highest and lowest estimates, respectively, for both Na LF and EcF. Inter-subject variability was especially present for EcF and Na LF in the corpus callosum.

Discussion
Data from a multi-echo 23 Na radial sequence acquired at ultra-high field (UHF) were analysed using a biexponential relaxation model to derive T 2 * short and T 2 * long relaxation times. In addition, 23 Na concentrations apparent at short and long TEs were quantified. As such, to our knowledge, we provide the first 23 Na-MRI data to address regional variation in T 2 * short at UHF, and to quantify the apparent 23 Na concentrations corresponding to short and long signal fractions associated with the respective components of T2* relaxation. Given the interest in 23 Na-MRI particularly for neurological research, quantification of these parameters and characterisation of their variation is necessary as an adjunct to even standard UTE 23 Na-MRI protocols.
The overall contribution of short and long T 2 * components to the measured sodium signal is considered to be ~60% to 40% 2 , respectively, consistent with our mean estimate of 57.7% ± 0.07% (s.d.) for the signal fraction associated with the short T 2 * component (f) across all considered ROIs. In the biexponential relaxation model applied here contributions of different T 2 * components were not fixed. The model revealed that while f was comparable to the general estimate in some regions (eg the entire WM), it varied in others (eg. the lowest signal contributions over the entire GM) (Fig. 3). Additionally, variation was observed across sub-cortical ROIs which are themselves likely to include diverse proportions of grey and white matter. Examples include regions that mainly contain white matter tracts but also grey matter nuclei (eg. Pons), as well as the inverse (eg. thalamus). Deviation from the theoretical ratio of 60:40 may reflect the contribution of additional compartments, for example an increased contribution of highly motile ions pool in CSF where signal decay is monoexponential (eg T 2 * ~ 47 ms) 27 . Higher estimates of f may reflect reduced contributions of this type, for example in the centrum semiovale which provided the highest signal fraction associated with the short T 2 * component observed here.
T 2 * relaxation refers to the dephasing of collections of nuclei due to reciprocal interactions of their local magnetic fields (T 2 ) in addition to magnetic field inhomogeneities (T 2 ') 30 . Attempts to characterize in vivo 23 Na relaxation times in human brain tissue have been made for several decades 22,24 . Such applications show variation in terms of applied methods, following developments in sequence design and the availability of higher field strengths. These factors are especially important for 23 Na, given not only the relative rapidity of biexponential relaxation but also due to its lower concentration and intrinsic sensitivity compared to 1 H. This leads to a relatively lower SNR in 23 Na-MRI, which can be partly compensated for by higher fields 3,31 . Consequently, among studies that attempt to quantify either long or short components of T 2 * relaxation in brain tissues (for an overview see Table 4), progressively higher fields have been employed. At 4 T, values of T 2 * long were observed to vary little between cortical GM and WM ROIs, though with some evidence of variation in subcortical regions (thalamus) and higher values in some white matter structures like the corpus callosum (CC) 25 . In line with theoretical expectations, and as observed in animal experiments 32 , longer relaxation times are observed at the higher field strengths in the current data (Table 1) and more generally at 7 T (Table 4). At 7 T, despite the lack of variation in T 2 * long values between general GM and WM ROIs, variation among other sub-regions comparable to the relative levels of T 2 * long seen in the current work was observed (thalamus > CC > cerebellar WM > putamen) 26 . Due to insufficient data points to characterize the initial portion of the decay curve, given that the smallest TEs are > 3 ms, these studies did not attempt to quantify T 2 * short . Thus the possibility of an unknown bias in measurement, relative to studies that model both T 2 * components remains. In a 7 T study in healthy controls of both T 2 * short and T 2 * long in white matter, estimates in excellent agreement with the current data were observed by Nagel et al. 18 . More recent data 27 in five subjects provide similarly concordant data for GM, though some disagreement for relative T 2 * short relaxation times between tissues should be noted. Recently, Blunck et al. 28 validated a multi-echo sequence with a large numbers of TEs, estimating decay components in 4 subjects, and observe T 2 * short relaxation times that are within the range of those seen here, as well as less variation between GM and WM for T 2 * long . The principal T 2 * short (ms) T 2 * long (ms) Na SF (mM) Na LF (mM) TSC (mM) EcF   The approach adopted was to use logarithmic spacing for the first echoes and equal spacing for later echoes. Logarithmic spacing on the early echoes provides good sensitivity to a range of T 2 * short values. The current data suggest that GM and WM give rise to significantly different time constants of decay, and do so differentially for short and long T 2 * components. These considerations, in addition to the variation among subregions and between T 2 * components for given regions, raise the possibility of the influence of tissue composition on observed relaxation (discussed below). By modelling the relationship between signal (M0) and known reference concentrations, we obtained -from estimates of M0 SF and M0 LF derived from in vivo data -quantitative values for the apparent 23 Na (Na SF , Na LF ) concentrations relating to short (f) and long (1-f) signal fractions (Fig. 2). Na SF was observed to be comparable between GM (21.16 mM ± 0.87(s.d.)) and WM (22.28 mM ± 0.97(s.d.)). These values are higher than the reference intracellular sodium concentration (10-15 mM) commonly cited in the literature 1-3 , possibly reflecting contributions from extracellular spaces. Various attempts have been made to weight measures of concentration toward the restricted sodium pool. For example, subtraction of only two SQ sodium images as a means of suppressing contributions from the long T 2 * component obtains a concentration of 25.9 ± 1.2 mM for bound sodium in the 'healthy' GM of patients with brain tumours 33 . This estimate is not dissimilar to our estimates of GM though most similar to the Na LF concentration we observe in WM (Table 1). Recent studies -utilizing IR at 3T 4,34 and TQF at UHF 10,35 -find little difference in concentration estimates weighted toward the restricted pool between GM and WM in their healthy control comparison samples. This is consistent with the similarity between our estimates of Na SF from whole tissue type segmentation maps for GM (21.16 mM ± 0.87(s.d.) and WM (22.28 mM ± 0.97(s.d.)) (Fig. 4a). Similarly, attempts to measure volume fractions associated with bound sodium (WM > GM) 10,35 , are complementary with the current work's estimate of sodium extracellular fraction (GM > WM) derived from Na LF . Indeed, the sodium EcF estimates observed here (0.06-0.18) fall well within the expected overall volume fraction of the extracellular space in healthy adult brains (0.2) derived from a variety of methods 36 . Furthermore, they specifically correspond to previous estimates of greater 23 Na extracellular volume fractions in grey versus white matter using 23 Na-MRI 4,34 .
Most in vivo studies of brain 23  Specifically, in the majority of studies that report healthy control values in GM, TSC is observed to exhibit higher values compared to WM, including across field strengths and different acquisitions 8,10,12,37-40 . Niesporek et al. 41 , employing a partial volume correction method adapted from PET accounting for both point spread function spreading and resolution issues in 23 Na-MRI, suggest corrected TSC values for GM (48 mM ± 1 (s.d.)) and WM (43 mM ± 3(s.d.)) notably similar to our estimates. Where available, regional TSC estimates in healthy controls are concordant with the current results in terms of finding higher values in the thalamus and caudate compared to putamen and pallidum as well as much lower values in the cerebellum 11 , and specifically its white matter 37 . The correspondence of our observed TSC values (the sum of Na SF and Na LF ) and those in the literature are encouraging, suggesting that the current methods appropriately characterize the overall 23 Na signal with respect to the rest of the literature. This lends further credence to the signal fractions and concentrations associated with the short and long T 2 * components as observed here. Crucially, the current methods achieve this without a high SNR penalty and permit quantification.  Relaxation is influenced by factors constraining molecular motion as well as the structure and content (tissue density) of the molecular environment experienced by nuclei 30 . For example, one factor of tissue density is water/ fluid content which can be explored via invasive electrophysiological measures of impedance 42 , in vivo MRI estimates of proton density 43 and post-mortem wet-to-dry mass ratios 44 . Higher water/fluid content is observed in GM tissues versus WM, and particularly in the caudate among sub-cortical regions explored here. This may be reflected here by lower signal fractions associated with the short T 2 * component observed in GM and the caudate in the current data (Fig. 3), and inversely higher values of Na LF and the related metric EcF (Table 1, Fig. 4). Conversely, the white matter ROI in the centrum semiovale provides the highest short signal fraction (f) and the lowest estimates of Na LF and EcF.

F-Values
The extent and an-/isotropy of the mobility of nuclei also impacts relaxation, with the structure and cellular make-up and the constituents of intracellular and extracellular environments all potentially playing a role. The fluid environment in the interstitium between brain cells differs from the environment of CSF in the ventricles due to the presence of the negatively-charged long-chain molecules of the extracellular matrix 36,45 . The extracellular matrix regulates the ionic environment necessary for cellular functions such as synaptic transmission and action potentials, interacts with diffusion through extracellular spaces via viscous drag and the interaction with positive charged ion species such as 23 Na, and varies in composition and density across brain structures 3,36,45 . The properties of the extracellular space and matrix are in turn influenced by cellular populations of neurons and glia, in terms of the distribution of different subtypes and the manner in which they constrain the structure of their environment via the formation of sheets, extension of processes and size alterations influencing the volume of intra-/extracellular spaces 36 .
Estimates from histology, DNA extraction and immunocytochemistry suggest that the human brain contains ~100 billion neurons and an equivalent number of non-neuronal cells including glia (oligodendrocytes > astrocytes > microglia) 46 and a small proportion of endothelial cells, leading to an approximate overall glia-to-neuron ratio (GNR) of 1:1 47 . At the same time, GNRs vary widely between brain regions with extremes including the cerebellum (0.23) due to its small, densely packed neurons, while reaching 11.35 in other regions of the brain including brainstem, diencephalon and striatum (i.e. many of the subregions considered here) 47 Table 3. Significant differences between regions. Differences (z) are provided for each significant comparison (P < 0.008), with the corresponding P value provided in italics, and non-significant comparisons indicated by a dash (-). Diagonal elements with asterisks represent borders between the results of different tests, for example in the top row the bottom triangle represents results between regions for T 2 * short , while the upper triangle represents results between regions for T 2 * long . Th, thalamus; Pu, putamen; Pa, pallidum; Ca, caudate; Cc, corpus callosum; Cb, cerebellar WM, Cs, centrum semiovale; Po, pons.
are thought not to reflect differences in glia density, which varies much less between structures, but rather with increasing neuronal density that is itself due to decreasing neuronal cell size (including soma and dendritic and axonal arborisations) 47,49 . 500-fold variation in average neuronal cell masses are observed across structures and   48 . The above evidence suggests that while the WM represents a restrictive environment determined mainly by the anisotropy 51 of axons and small-bodied 46 myelin-supporting oligodendrocytes, the GM represents a wider variety of cellular environments especially given the range of neuronal sizes. This is a possible explanation for the variation in relaxation times, associated signal fractions and derived metrics observed here. Similarly, these factors may contribute to the variation between regions (Fig. 4) to the extent that they reflect proportions of white and grey matter. It is notable that T 2 * short and T 2 * long, as well as Na LF tend to be lowest in axon/myelin-rich structures. This is most evident across metrics in the pallidum and pons, but also to some extent in centrum semiovale, cerebellar white matter and the corpus callosum. It should be recognized that variability across metrics among these regions suggests additional factors at work as well.
Considering concordance of our results and the available relevant literature, in addition to recent insights into tissue composition, this raises the prospect of multi-echo 23 Na-MRI's sensitivity to microstructural properties of imaged tissues. Future work, including additional measures of microstructure, such as via the measurement of the diffusion properties of 1 H or 23 Na itself 14,15,18,52 , could confirm and expand the current results, and speak to limitations of the current approach. For example, despite the measures taken to avoid partial volume effects, as is the case for all 23 Na-MRI there is a remaining possibility of an unknown bias due to the influence of higher concentrations of 23 Na in extracellular and cerebrospinal fluid, and the possibility of differences between tissue types in terms of this bias. Further gains in spatial resolution could further ameliorate this issue 3 , as well as the application of partial volume correction methods originally applied in positron emission tomography and recently adapted to 23 Na-MRI 27,41 . Given the duration of the scan required to characterise the decay curve, there is the possibility of artefacts arising from subject motion. Measures such as the use of foam supports to support subjects' heads and constrain movement were employed; however optimisation of the sequence to shorten overall acquisition times should be pursued. In any case, this will be required for clinically feasible scan times.
In summary, we provide evidence that in the physiological state multi-echo 23 Na-MRI depicts variation in T 2 * relaxation between major distinctions in tissue structure -GM and WM -as well as between diverse brain regions of differing composition and structure. This includes variations in decay times, including the T 2 * short component. Additionally, quantification of 23 Na concentrations apparent at short and long TEs was evaluated via a quantitative multi-echo approach for the first time. This provides a foundation for the examination of the alteration of these properties in pathophysiological populations, as a means of shedding light on both disease processes and the mechanisms underlying normal ionic homeostatic mechanisms as imaged by 23 Na-MRI.  Table 4. Examples of literature estimates for short and long component of T 2 * derived using biexponential models, and CSF transverse relaxation rates using monoexponential models. Note that data is attributed to structures as described in the papers concerned, and the details of ROIs likely differ between reports. Brain parenchyma refers to estimates derived from (an) ROI(s) where no specific anatomic attribution was made. Values reproduced from Bartha

Methods
Subjects. 14 healthy subjects with no history of neurological or psychiatric illness provided informed consent and were enrolled in the protocol, as approved by the local Ethics Committee (Comité de Protection des Personnes sud Méditerranée 1). All methods were performed in accordance with the relevant guidelines and regulations. Due to excessive movement in one subject, the final sample consisted of n = 13 subjects (5 female) (mean age: 23.9 ± 3.6 (s.d.) years, range: 20-32).

MRI acquisition.
Data were acquired on a whole-body 7 T Magnetom MR system (Siemens, Erlangen, Germany). 23 Na-MRI was acquired using a dual-tuned 23  Pre-processing. Sodium images were reconstructed offline in Matlab (Mathworks, Natick, MA) using a Kaiser-Bessel gridding method 29 leading to a full 3D data set for each individual, at each echo time (See Fig. 1 for an example). 23 Na images from all TEs were realigned to the shortest TE (0.3 ms) for each individual. 3D 23 Na images from the shortest TE were then realigned to high resolution 3D-MP2RAGE images obtained from the same individual and the resulting spatial transform was applied to the remaining 23 Na images (SPM12; Wellcome Institute, London, UK). Subsequent analyses using ROIs (see below) were applied to these coregistered 23 Na-MRI images in the native 3D-MP2RAGE space. Figure 2 provides an overview of the workflow applied to data.
Using SPM12, 1 H images were segmented into probability maps of GM, WM and CSF to create masks to be applied to sodium images. A conservative probability threshold of 0.9 for tissue type segmentation was applied to GM and WM prior to the creation of masks. FSL (version 6.0, FMRIB, Oxford, UK) was used to define 8 regional sub-cortical ROIs using 1 H images, thresholded GM and WM maps and 23 Na images of the earliest (high SNR) TE (0.3 ms). Sodium images and thresholded tissue probability maps were projected onto 1 H images to aid expert (S.G.) manual definition of ROIs for each individual. In addition to thresholding of tissue probability maps attempts to limit partial volume effects included the avoidance of tissue boundaries and evident areas of heightened signal due to the proximity of CSF spaces such as the ventricles during manual ROI definition (Fig. 2). In total, 10 ROIs were applied for each individual to derive mean 23 Na signal (MARSBAR toolbox, SPM12) for each ROI for each echo time. ROIs correspond to the entire (thresholded) GM and WM segmentations, in addition to eight sub-cortical manual bilateral ROIs: thalamus, pallidum, putamen, caudate nucleus, corpus callosum, centrum semiovale, cerebellar white matter and pons. Biexponential model. Considering the design of the sodium sequence providing a maximum reduction of T1 weighting (TR = 120 ms, around four times longer than the T1 values 7 ), determination of signal fractions and the time constants of short and long T2* components of signal decay in 23 Na images can be modelled by a bi-exponential fitting procedure. For each ROI, we analysed the mean signal intensity across each of the 24 TEs and apply a biexponential model to the obtained curve (Fig. 2a) using the equation: where A is an amplitude scaling term, f is the signal fraction associated with the short T 2 * component and Ric refers to a Rician noise-related scaling parameter as described in Gudbjartsson et al. 53 . The best-fit parameters were obtained from nonlinear least-squares (lsqnonlin) fitting. Model performance was measured by goodness of fit (r 2 ). From the model we estimated a signal fraction for short (f) and long (1-f) T 2 * components, as well as estimating the time constants (T2* short and T2* long ). We calculated magnetization (M0) corresponding to the signal fraction estimated by the model in terms of the intercepts of the signal fraction components of the model, obtaining M0 SF = A·f and M0 LF = A·(1-f).
Quantification: Na SF & Na LF . As these signal fraction parameters are expressed in arbitrary units, we attempted to obtain quantitative values to access the same measurement scale across subject in order to explore variations in tissue types and regions, and permit literature comparisons. For each reference tube for each individual, we obtained the value of M0 and the time of transverse relaxation (T 2 *) for a given tube across the 24 TEs, through monoexponential fitting via MATLAB (R2012a, MathWorks) (Fig. 2b). We then model a linear relationship between obtained M0 and known concentrations across all tubes (Fig. 2c), which can be applied to parameters estimated from the biexponential model of in vivo data (M0 SF and M0 LF , Fig. 2a). As such, the apparent concentrations equivalent to a given level of magnetization was obtained, yielding quantitative estimates (Na SF and Na LF ) for each brain ROI. Note that given that we have dynamic information in the form of the curve of signal intensity across TEs, we can hypothesize that at the longest TEs, the major signal contributors will be the slowest relaxing/most motile pools. Accordingly, the magnetization estimated from the intercept of the signal fraction associated with the long T 2 * component may be considered a good approximation of the sodium concentration of extracellular spaces. 'Extracellular fraction' (EcF) was obtained by the division of Na LF by the commonly used value of 140 mM for extracellular Na concentration 7,15,54 . We also calculated the parameter total sodium concentration (TSC) as the sum of Na SF and Na LF .
Statistical analyses. Six dependant variables of interest were investigated via analysis in JMP v.9 (SAS Institute Inc., Cary, NC). These included T 2 * short and T 2 * long (ms) derived from the biexponential fitting procedure, the quantitative estimates Na SF and Na LF, (mM), as well as TSC (mM) and EcF. An ANOVA was applied separately to the six dependant variables to investigate the factor of interest Tissue Type (2 levels: GM, WM), in addition to factors for Sex and Age. Additionally, an ANOVA was applied to the sub-cortical regional data, with the factor of interest Region (8 levels) as well as Sex and Age. Differences between the levels of factors of interest that were found to be significant were further investigated via non-parametric Steel-Dwass (p < 0.05, adjusted for multiple comparisons between levels) in a pairwise fashion. Based on the possibility of dependence between measures, Bonferroni correction was also applied across tests based on 6 dependant variables yielding a corrected α-level of P = 0.05/6 = 0.008.
Data Availability. Generated datasets are available on reasonable request from the corresponding author.