The burden of global neurotrauma has been on the rise (1). Approximately 50 million traumatic brain injuries (TBIs) occur throughout the world every year (2), of which 80–90% are classified as mild TBI (mTBI) (3). MTBI is associated with neurocognitive dysfunction at the acute stage, and more than 20% of cases continue to report long-term neurocognitive complications years after the injury (4). With the rising prevalence of mTBI, cognitive problems followed by mTBI have attracted increasing attention (5-7). However, in the acute stage, mTBI patients with cognitive impairment lack brain abnormalities on conventional imaging modalities. Thus, the neurobiological mechanism of post-mTBI cognitive impairment is not fully understood.
In recent years, aberrant functional and structural networks have been detected in disease conditions including epilepsy (8), stroke (9), Parkinson’s disease (10), and Alzheimer’s disease (11). Moreover, the graph theory approach has emerged as a promising technique for characterizing functional and structural networks in a complex network at global and nodal levels (12). In the context of this approach, the human brain is modeled as a complex large-scale network that consists of substantial connecting nodes and edges. Meanwhile, a number of topological properties have been evaluated using the graph theory analysis. Some frequently used topological properties, such as global network properties (clustering coefficient and characteristic path length) and nodal properties [nodal degree centrality, nodal betweenness centrality and nodal efficiency (Ne)], have been reported to provide valuable insights into possible mechanisms underlying cognitive impairments in various neurological diseases.
To date, only a few studies have applied the graph theory approach to describe topological characteristics for functional connectivity (FC) and structural connectivity (SC) in mTBI. Patterns of FC and SC can be investigated using resting-state functional magnetic resonance imaging (rs-fMRI) and diffusion tensor imaging (DTI), respectively. Previous rs-fMRI and DTI findings revealed that mTBI patients had aberrant topological features that reflect disrupted modular organization, functional small world property changes, and diffuse axonal injury. These aberrances were related to depression scores or post-concussion symptom scale (PCSS) scores (12-15). However, many of these mTBI studies used either rs-fMRI for FC analysis or DTI for SC analysis or were conducted during the subacute and chronic stages of recovery. Although one DTI study demonstrated SC abnormalities using graph theoretical analysis in acute mTBI, the population was children not adults. More importantly, FC and SC are interdependent. Their combination could detect subtle brain changes more sensitively than any single imaging modality (8,16) and contribute to a better understanding of brain connectivity alterations (17). Previous literature has demonstrated abnormal FC-SC relationships in bipolar disorder (18), idiopathic generalized epilepsy (8), and diabetic kidney disease (19). Only a single study reported an aberrant relationship between FC and SC in acute mTBI, but it did not explore the correlation between the FC-SC relationship and neurocognitive performance (20). Therefore, integrating the information from structural and functional networks could help unveil the neurobiological mechanism of cognitive impairment following acute mTBI and remains to be studied.
We hypothesized that brain functional and structural large-scale network organization would differ significantly between mTBI patients during the acute stage of injury and healthy control (HC) participants and that these network alterations would be the partial mechanisms underlying neurocognitive impairments. Therefore, we identified altered large-scale functional and structural brain networks and internship patterns in acute mTBI patients compared with HC. We also investigated the associations between these network alterations and neurocognitive performance. We present the following article in accordance with the STROBE reporting checklist (available at https://qims.amegroups.com/article/view/10.21037/qims-22-450/rc).
This study is a prospective study. The study was conducted in accordance with the Declaration of Helsinki (as revised in 2013). The study was approved by the Institutional Review Board of Nanjing Medical University. Written informed consent was obtained from all participants before their participation in the study protocol. The sample size calculation was determined by the freely downloadable software named “PS: Power and Sample Size Calculation” (by William D. Dupont and Walton D. Plummer, Jr). Between April 2019 and January 2020, mTBI patients were recruited from the emergency department of Nanjing First Hospital, and HC participants were recruited from the local community. The inclusion criteria for the mTBI patients were as follows (21): (I) Glasgow Coma Scale (GCS) score ranging from 13 to 15 on presentation to the emergency department and (II) a closed head injury within 14 days with either loss of consciousness (LOC) of shorter than 30 min or posttraumatic amnesia (PTA) of shorter than 24 h. LOC is a disruption of consciousness (22). PTA has been said to terminate with the return of continuous memory for ongoing events (23). The exclusion criteria for all participants (mTBI patients and HC patients) were as follows (21): (I) a history of brain injury; (II) a history of neurological disease and long-standing psychiatric condition; (III) MRI contraindications; and (IV) coexisting alcohol and drug abuse. Furthermore, all participants underwent the neuropsychological assessment via the Beijing version of the Montreal Cognitive Assessment (MoCA) within 24 h after MRI, one of the tools suggested to assess cognitive impairment following mTBI (24). MoCA changes could be not only statistically significant but also clinically relevant from a clinical perspective, even if this screening tool is simple. It appears to be sufficiently stable and sensitive for detecting the early presence of cognitive impairment after mTBI and assess changes over time (24). The MoCA scores contained seven subscales, including the visual-executive index score (MoCA-VEIS), naming index score (MoCA-NIS), attention index score (MoCA-AtIS), language index score (MoCA-LIS), abstraction index score (MoCA-AbIS), memory index score (MoCA-MIS) and orientation index score (MoCA-OIS).
A 3.0 T magnetic resonance imaging scanner (Ingenia, Philips Medical Systems, Netherlands) equipped with a 12-channel head coil was used. Parallel imaging was employed. MRI were performed by two radiographers (5-year experienced and 7-year experienced, respectively) following the same scanning parameters. For each participant, rs-fMRI data, DTI data, and high-resolution T1-weighted anatomic imaging data were acquired. Rs-fMRI data were obtained using a gradient echo-planar imaging sequence [axial: repetition time (TR) =2,000 ms; echo time (TE) =30 ms; slices =36; thickness =4 mm; gap =0 mm; field of view (FOV) =240 mm × 240 mm; acquisition matrix = 64×64; flip angle (FA) =90°, and total volume =230]. The fMRI sequence took 8 min and 8 s. High-resolution T1-weighted anatomic imaging data were acquired with a three-dimensional turbo fast echo (3D-TFE) T1WI sequence [sagittal: TR =8.1 ms; TE =3.7 ms; FA =8°; FOV = 256 mm × 256 mm; acquisition matrix =256×256; thickness =1 mm; gap =0 mm; and total =172 slices]. The fluid-attenuated inversion recovery (FLAIR) employed TR =7,000 ms; TE =120 ms; slices =18; thickness =6 mm; gap =1.3 mm; FA =110°; and voxel size =0.65 mm × 0.95 mm × 6 mm. Susceptibility-weighted imaging (SWI) was obtained with a 3D gradient echo (GRE) sequence: TR =22 ms; TE =34 ms; FA =20°; acquisition matrix =276×319; thickness =1 mm; and FOV = 220 mm × 220 mm. DTI employed the following parameters: TR =3,000 ms; TE =1,000 ms; slices =55; thickness =2.5 mm; gap =0; FA =90°; acquisition matrix =120×177; and FOV =240 mm × 240 mm; 32 volumes with diffusion gradients along 32 nonlinear directions [b=1,000 s/mm2] and 1 volume without diffusion weighting [b=0 s/mm2]. The DTI sequence took 11 min and 9 s. All participants were instructed to stay awake and keep their head still. Foam padding was used to reduce head motion (8,21). No participants reported falling asleep during the scanning when asked right after the scanning (8,21).
The rs-fMRI data were preprocessed using Graph Theoretical Network Analysis (GRETNA) software (http//www.nitrc.org/projects/gretna) implemented in MATLAB (version R2013b) (25). Standard preprocessing methods were used (8,19,20). First, the first ten volumes were discarded due to the instability of the initial magnetic field. Second, slice time correction was performed to correct the remaining functional images, and head motion was corrected. No group differences were observed with respect to head motion (P>0.05). Then, functional images were spatially coregistered with their high-resolution T1-weighted anatomic images with a voxel size of 3×3×3 mm3 (25). Next, rs-fMRI time series were bandpass filtered (0.01–0.08 Hz) to improve the signal-to-noise ratio (8) and images were detrended for making strong instrumental stability. In this study, to avoid artificial local spatial correlations, no spatial smoothing was applied (26). To remove spurious sources of variance, the Friston 24 parameter obtained via head motion correction and signals from cerebrospinal fluid and white matter were regressed. Global brain signals were not regressed in order to result in fewer negative values of brain connectivity (25).
The DTI data were preprocessed using PANDA software (27). PANDA is a MATLAB toolbox for pipeline processing of diffusion MRI images based on the Diffusion Toolkit (http//www.trackvis.org/dtk/) and the FSL tool. First, DICOM files were converted into NIfTI format and the raw images were cropped. Second, the eddy current distortions and head motions were corrected by aligning all 32 noncolinear diffusion-weighted images with the b0 image using an affine transformation. Then, the fractional anisotropy (FA) of each voxel was calculated, and the affine transformation was used to coregister the FA image with the corresponding T1 image in the native space. After that, deterministic white matter tractography based on the fiber assignment by continuous tracking (FACT) algorithm was used in the reconstruction of fibers for each individual DTI dataset (18,28). Continuous fiber tracking was terminated when FA <0.15 or the minimum turning angle >45°.
Our final analysis was restricted to the participants whose data quality was reliable within a tolerable range (13). Visual inspection at each step was employed to guarantee the quality of the preprocessed rs-fMRI and DTI data (13). After that, a subset of participants’ data was removed from the study for the following reasons (13): (I) the functional images did not fall within the prescribed FOV, (II) intensity variation artifacts of low spatial frequency, (III) substantial susceptibility artifacts in inferior frontal and inferior temporal regions, (IV) motion correction failure due to a large amount of abrupt motion (translation >2.0 mm or rotation parameters in any direction >2.0°), and (V) lack of complete imaging frames.
Functional and structural network construction
A total of 116 non-overlapping anatomical regions were defined as the nodes of the functional and structural networks (90 nodes in the non-cerebellar brain: 45 nodes in each hemisphere and 26 nodes in the cerebellum). The 116 brain nodes initially parcellated in MNI space based on the automated anatomical labeling (AAL) atlas were inversely warped back to participants’ native space (18). In native diffusion space, these 116 nodes were used as masks to guide the counting of white matter streamlines. If there were at least two streamline counts and the length of passing fibers was longer than 10 mm, any two nodes were considered structurally connected through an edge (18). For each edge, we computed the mean FA values of all fibers as its weights (18). Thus, a 116×116 SC matrix for each participant was constructed with the mean FA values between every paired node. To obtain the FC network, the mean fMRI time series were extracted from all voxels for each of the aforementioned 116 nodes. Then, a 116×116 FC matrix for each participant was determined by computing Pearson’s correlation coefficients between the processed time series of every paired node (Figure 1).
Graph theory analysis
The graph theoretical properties of large-scale functional and structural networks were calculated using the GRETNA toolbox (29). Network topologic properties included small-world parameters: clustering coefficient (Cp), which quantifies the extent of local interconnectivity or cliquishness of a network, reflecting the global efficiency of a network; characteristic path length (Lp), which measures the extent of overall communication efficiency of a network, reflecting the regional efficiency of a network; normalized clustering coefficient (γ) (γ = Cp/Cprand, where Cp is the real clustering coefficients and Cprand is the same calculated from a matched random network) (30), normalized characteristic path length (λ) (λ = Lp/Lprand, where Lp is the real characteristic path length and Lprand is the same calculated from a matched random network) (30), the number of random networks selected in the calculation of the small word attribute is 100. The most parameter is the small worldness (σ, σ = γ/λ), a small-world network has similar path length but higher clustering than a random network, that means λ>1, λ≈1; network efficiency parameters: global efficiency (Eg) and local efficiency (Eloc) (Eglob and Eloc are the measures of network efficiency in transmitting information at the local and global levels, respectively) (30); and nodal parameters: Ne, nodal local efficiency (Nloc), nodal clustering coefficient (NCp), degree centrality (Dc), and betweenness centrality (Bc). When brain graphs were constructed, each graph of the participants was thresholded to create an equal number of nodes and edges across them. We operated network parameters over a range of threshold values to guarantee high correlation coefficients of the remaining connections. The sparsity threshold, which denotes the ratio between the number of actual edges and to all the possible edges in the matrix was applied to create the binary network (23). In the study, a sparsity threshold ranging from 0.05 to 0.5 with an interval of 0.01 was chosen to remove the possible false edges. Furthermore, the area under the curve (AUC) over the full range of defined sparsity thresholds was calculated for each network topological metric. The AUC provides a summarized scale for the topologic characterization of brain networks and is sensitive to topologic alterations in brain disorders (31).
The analysis of FC-SC coupling was described in previous studies (8,18,19,32,33). We calculated Pearson’s correlation coefficients between the functional and structural network matrix, which is considered the network coupling strength, for each participant (Figure 1). The analysis was performed at the group and individual levels (32). At the group level, the mean FC and mean SC matrix were computed as the average of the FC and SC matrices of all participants within each group. The nonzero network edges of the SC matrix were extracted, rescaled to Gaussian distribution, and correlated with their functional counterparts to develop one FC-SC correlation coefficient for each group. Negative connections were discarded because the number was small. At the individual level, a single FC-SC “coupling” value was calculated as the correlation between the strength of the non-zero SC edges and corresponding FC within each participant.
Statistical analysis of demographic and neuropsychological data was performed using SPSS software 20.0 (SPSS, Chicago, IL, United States). Differences in demographic information and neuropsychological measures between the mTBI group and the HC group were analyzed using independent two-sample t-tests for normal distribution (age, education level, and MoCA score) and Mann-Whitney U tests for non-normal distribution (MoCA-VEIS, MoCA-NIS, MoCA-AtIS, MoCA-AbIS, MoCA-OIS, MoCA-MIS, and MoCA-LIS). A Chi-square test was applied for group differences in sex.
Group differences in FC and SC global and nodal properties (AUC values for network topologic parameters) were examined by a two-sample t-test (age, sex, and education level as covariates) with Bonferroni corrections for multiple comparisons in MATLAB. Group differences in FC-SC correlation coefficients at the group level were compared using Fisher’s z test. FC-SC coupling between two groups at the individual level was compared using general linear models controlling for age, sex, and education level with Bonferroni corrections for multiple comparisons. Data for group differences are presented as the means, standard deviations, P values and Cohen’s d statistic for effect sizes.
After significant intergroup differences were identified in the network measures,
Spearman’s rank correlations were computed between these measures and the neuropsychological test scores in the total group of patients with acute mTBI using MATLAB (34). The potential confounding factors including age, sex, and education level, motion and time post-injury were set as nuisance covariates in the analysis. Correction for multiple comparisons was performed using Bonferroni corrections. P<0.05 was considered statistically significant.
Demographic and neuropsychological data
During the study period, 221 patients who presented to our emergency department were diagnosed with acute mTBI. Among them, 109 (49.3%) patients with acute mTBI were contacted and 79 (72.5%) of 109 were willing to participate in our study. Among the 79 patients with acute mTBI, 8 (10.1%) were excluded. Among the total 62 HC, 5 (8%) were excluded. The number and the reason were showed in Figure 2. Thus, the data from the remaining 71 patients within an average of 3.29 days (range, 0–10 days) after head injury and 57 HC were finally analyzed. Table 1 lists the basic comparison of demographic characteristics of 71 acute mTBI patients versus 57 HC. Both groups did not show any significant difference in age (P=0.13, d=−0.272), sex (P=0.05), or years of education (P=0.14, d=−0.270). The mTBI group had lower MoCA, MoCA-VEIS and MoCA-AbIS scores than the HC group (P<0.001, d=−0.864; P=0.002, d=−0.747; P=0.001, d=−0.824). There were no significant differences between groups with respect to MoCA-NIS, MoCA-AtIS, MoCA-MIS, MoCA-LIS and MoCA-OIS (P=0.44, d=0.105; P=0.16, d=−0.401; P=0.47, d=−0.110; P=0.73, d=−0.076; P=0.09, d=−0.421). All participants showed no abnormalities on CT or MRI (FLAIR and SWI).
|Characteristics||mTBI (n=71)||HC (n=57)||P value||Cohen’s d|
|Time since injury (day)||3.29±2.30||NA||NA||NA|
Data are presented as mean ± standard deviation. * denotes significant difference compared to HC, P<0.05. mTBI, mild traumatic brain injury; HC, healthy controls; GCS, Glasgow Coma Scale; MoCA, Montreal Cognitive Assessment; MoCA-VEIS, visual-executive index score; MoCA-NIS, naming index score; MoCA-AtIS, attention index score; MoCA-LIS, language index score; MoCA-AbIS, abstraction index score; MoCA-MIS, memory index score; MoCA-OIS, orientation index score; NA, not applicable.
Aberrant global FC and SC network
The mTBI group and HC group demonstrated an economical small word organization (γ>1 and λ=1) of FC networks constructed at all connection densities (0.05–0.5) following the AAL-116 parcellation scheme. Patients with acute mTBI showed significantly increased γ in the functional network (Figure 3A and Table 2). The mTBI group and HC group also demonstrated an economical small world organization (γ>1 and λ≈1) in SC networks constructed at all connection densities (0.05–0.5), following the AAL-116 parcellation scheme. Patients with acute mTBI showed significantly increased γ and σ in the structural network (Figure 3B and Table 2).
|Graph measures||mTBI (n=71)||HC (n=57)||P value||Cohen’s d|
Data are presented as mean ± standard deviation. The AUC across the full range of sparsity thresholds was calculated for graph measures of functional and structural network. * denotes significant difference compared to HC, Bonferroni-corrected P<0.05. mTBI, mild traumatic brain injury; HC, healthy controls; Cp, clustering coefficient; Lp, characteristic path length; Eg, global efficiency; Eloc, local efficiency; AUC, area under the curve.
Aberrant regional FC and SC network
Compared with the HC group, the mTBI group showed increased nodal properties (nodal degree, Ne, and Nloc) in the left inferior frontal gyrus, orbital part (ORBinf.L), right superior frontal gyrus, medial orbital (ORBsupmed.R), right parahippocampal gyrus (PHG.R), left Heschl gyrus (HES.L), right superior frontal gyrus, orbital part (ORBsup.R), IFGtriang.R, left amygdala_L (AMYG.L), ANG.R, TPOsup.R, left temporal pole: middle temporal gyrus (TPOmid.L), and TPOmid.R (Figure 4A and Table S1). The mTBI group also exhibited decreased nodal properties in the left fusiform gyrus (FFG.L), left supramarginal gyrus (SMG.L), right cerebellum, vermis, left superior frontal gyrus, dorsolateral (SFGdor.L), right superior frontal gyrus, dorsolateral (SFGdor.R), right lingual gyrus (LING.R), and right inferior occipital gyrus (IOG.R) (Figure 4A and Table S1).
Compared with the HC group, the mTBI group showed increased nodal properties (nodal degree, nodal betweenness, NCp and Ne) in the right temporal pole: superior temporal gyrus (TPOsup.R), right inferior frontal gyrus, opercular part (IFGoperc.R), right supplementary motor area (SMA.R), left angular gyrus (ANG.L), right angular gyrus (ANG.R), and bilateral cerebellum (Figure 4B and Table S2). The mTBI group also had decreased nodal properties in the left hippocampus (HIP.L), vermis, left caudate nucleus (CAU.L), right lenticular nucleus, putamen (PUT.R), right precentral gyrus (PreCG.R), left middle temporal gyrus (MTG.L), left inferior frontal gyrus, opercular part (IFGoperc.L), right inferior frontal gyrus, triangular part (IFGtriang.R), right rolandic operculum (ROL.R), SMA.R, left superior frontal gyrus, medial (SFGmed.L), right insula (INS.R), right superior occipital gyrus (SOG.R), left middle occipital gyrus (MOG.L), ANG.L, right temporal pole: middle temporal gyrus (TPOmid.R), right inferior temporal gyrus (ITG.R), and right cerebellum (Figure 4B and Table S2).
Aberrant functional-structural coupling
At the group level, group-averaged FC was closely associated with group-averaged SC across all structurally defined connections within each group (mTBI: r=0.479, HC participants: r=0.451, P=0.08) (Figure 5A,5B). At the individual level, patients with acute mTBI had significantly higher FC-SC coupling than HC participants (0.218±0.039 vs. 0.203±0.033, P=0.02, d=0.415) (Figure 5C and Table 2). Thus, patients with acute mTBI showed a higher SC-FC correlation than HC participants.
Associations between FC, SC parameters, and FC-SC coupling and cognition
For the FC network, γ was negatively correlated with MoCA-OIS (rho =−0.274, P=0.01). Nodal degree and Ne of the ORBsupmed.R were negatively correlated with MoCA-OIS (rho =−0.274, P=0.02; rho =−0.259, P=0.02). Nloc of the LING.R was positively correlated with MoCA-NIS (rho =0.340, P=0.004). Nloc of the IFGtriang.R was negatively correlated with MoCA-OIS (rho =−0.317, P=0.007). Nloc of the SFGdor.R was associated with MoCA-MIS (rho =−0.311, P=0.008). No correlations were found between SC-FC coupling parameters and MoCA scores (Table S3).
For the SC network, patients with acute mTBI showed a significant positive correlation between γ and σ and MoCA score (rho =0.267, P=0.02; rho =0.268, P=0.02, respectively), a significant positive correlation between γ and σ and MoCA-AtIS (rho =0.358, P=0.002; rho =0.324, P=0.006, respectively), a significant positive correlation between nodal degree of the HIP.L and MoCA-AIS (rho =0.287, P=0.01), a significant positive correlation between the nodal betweenness of the OLF.L and MoCA-AtIS (rho =0.293, P=0.01), and a significant positive correlation between the Ne of the SFGmed.L and MoCA-AtIS (rho =0.387, P=0.001) (Table S4).
For the mTBI group, the functional and structural brain networks preserved small world characteristics. The γ and σ of the structural network and the γ of the functional network were significantly greater in patients with acute mTBI. An increase in γ was also reported in children with acute mTBI (12). These findings may reflect the compensatory response of the brain during the acute stage expecting that less impairment for those with larger network differences. The reason may be explained that brain regions are more connected at the local level across the entire network. Caeyenberghs et al. (35) found that adults with moderate to severe TBI showed increased γ during the 4-year follow-up, suggesting that the increase in γ would extend to persist longer following more severe TBI. In theory, the change in γ can result in the change in σ. In the present study, σ significantly increased in the structural network in acute mTBI. Similarly, Yuan et al. (12) found elevated σ at the acute stage. High levels of γ and σ in mTBI implied lower efficiency in global integration and a higher degree in regional segregation in their brain networks, reflecting a new balance between the competing demands for wiring cost and resilience to pathological conditions (12). However, this study failed to find changes in σ of the functional network, suggesting that structural connection alterations exert more effect on acute mTBI. Wang et al. (20) found no significant changes in σ in the acute stage possibly due to differences in sample size, AAL parcellation scheme without considering the importance of cerebellum, and sparsity threshold value. Further investigation with a larger number of participants and consistent parameters is needed to clarify whether changes in σ will be found in acute mTBI.
In addition to global functional and structural outcomes, aberrant nodal topology of FC and SC networks was found in patients with acute mTBI. Although the difference between functional and structural networks is small, our findings demonstrate evidence of functional and structural abnormalities mainly in the frontal, temporal, cerebellum, and subcortical areas, which are associated with mTBI. Reduced neural activity was also found in the frontal lobe, including the inferior frontal gyrus, middle frontal gyrus, and superior frontal gyrus, in mTBI (36). The temporal lobe, which is located at the midline, is vulnerable to brain injury. FC aberrances of the temporal lobe were found in the mTBI group in previous literature. At the acute stage, cerebral blood flow was reduced in the frontal lobe, occipital lobe, and parietal lobe (37). The frontal and subcortical gray regions also presented subtle lesions on SWI (38). To date, emerging evidence has demonstrated the involvement of cerebellum in mTBI (39). Patients with mTBI during the acute phase exhibited abnormal fractional anisotropy of the cerebellum region (39). Differences in frontal, temporal, cerebellum, and subcortical nodes may reflect reduced cortex integration, indicating the reduced role of the certain hubs in global network information processing with acute mTBI. The increased nodal centralities observed in the study indicate a possible compensatory mechanism for decreased connectivity.
FC-SC coupling can be altered under physiological and pathological states (40-42). This study is the first to demonstrate FC-SC coupling in acute mTBI at the group and individual levels. As predicted, the FC-SC relationship was aberrant in patients with acute mTBI. Our study found increased FC-SC coupling compared with HC in agreement with previous studies that reported increased coupling in schizophrenia, epilepsy, anesthesia, and kidney transplantation (8,42-44). This phenomenon could be explained by the fact that patients with mTBI experience the most dramatic change in the acute phase because FC fluctuates in a complex pattern, reflecting a wealth of potential dynamics. As mentioned above, however, no correlation was found between FC-SC coupling and cognitive tests. Thus, the reliable relationship between FC–SC coupling and cognitive decline remains to be evaluated in future work.
Weak correlations were found between functional and structural network properties and neuropsychological test scores in patients with acute mTBI. Orientation, attention, naming, and memory were preferentially affected among patients with acute mTBI. In our study, the alterations of global and nodal FC properties were more likely to affect orientation function, and the alterations of global and nodal SC properties were found to be more correlated with attention. The correlated nodes were mainly distributed in the frontal lobe, followed by the temporal lobe. These findings are supported by previous studies that reported cognitive impairments in the mTBI population at the acute stage (36,45,46). The present findings also suggest a theoretical model in which the frontal lobe is an essential integrating node in brain networks to control high-order cognitive function. In humans, frontal lobe functions are conditional on the development of an intricate set of short- and long-range connections that guarantee direct access to most aspects of cognition and behavior or control over regions dedicated to cognitive information processing (47).
Several limitations of this study need to be addressed. First, the sample size was small; despite the clear findings, the replication of the study in a larger cohort is mandatory. Second, although this study aimed to examine cognitive impairment following mTBI at the acute stage, imaging data were only acquired once within 14 days following brain injury. No longitudinal data were available at additional time points for studying the progression of recovery. Thus, further prospective studies are warranted. Third, many brain areas have been verified to have complex fiber architecture including crossing fibers. DTI acquisition and deterministic tractography approaches are limited to distinguishing crossing fibers. In future studies, advanced tractography approaches based on neurite orientation dispersion and density imaging (NODDI) data may help to provide more accurate anatomical connectivity patterns of brain networks.
Our study revealed brain network damage with regard to functional and structural large-scale networks and SC-FC coupling strength in mTBI patients, compared with HC. These damages were related to cognitive impairment following acute mTBI. Our findings provide an implicative neural basis for the alterations of large-scale brain networks and valuable information to elucidate the neuropathological mechanisms of cognitive impairment after mTBI in the acute phase.
Funding: This work was funded by the Natural Science Foundation of China (Nos. 82102012 and 82102006).
Reporting Checklist: The authors have completed the STROBE reporting checklist. Available at https://qims.amegroups.com/article/view/10.21037/qims-22-450/rc
Conflicts of Interest: All authors have completed the ICMJE uniform disclosure form (available at https://qims.amegroups.com/article/view/10.21037/qims-22-450/coif). The authors have no conflicts of interest to declare.
Ethical Statement: The authors are accountable for all aspects of the work in ensuring that questions related to the accuracy or integrity of any part of the work are appropriately investigated and resolved. The study was conducted in accordance with the Declaration of Helsinki (as revised in 2013). The study was approved by the Institutional Review Board of Nanjing Medical University. Written informed consent was obtained from all participants before their participation in the study protocol.
Open Access Statement: This is an Open Access article distributed in accordance with the Creative Commons Attribution-NonCommercial-NoDerivs 4.0 International License (CC BY-NC-ND 4.0), which permits the non-commercial replication and distribution of the article with the strict proviso that no changes or edits are made and the original work is properly cited (including links to both the formal publication through the relevant DOI and the license). See: https://creativecommons.org/licenses/by-nc-nd/4.0/.
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