Following upper limb peripheral nerve transection and surgical repair, some patients regain good sensorimotor function while others do not. Understanding peripheral and central mechanisms that contribute to recovery may facilitate the development of new therapeutic interventions. Plasticity following peripheral nerve transection has been demonstrated throughout the neuroaxis in animal models of nerve injury. However, the brain changes that occur following peripheral nerve transection and surgical repair in humans have not been examined. Furthermore, the extent to which peripheral nerve regeneration influences functional and structural brain changes has not been characterized. Therefore, we asked whether functional changes are accompanied by grey and/or white matter structural changes and whether these changes relate to sensory recovery? To address these key issues we (i) assessed peripheral nerve regeneration; (ii) measured functional magnetic resonance imaging brain activation (blood oxygen level dependent signal; BOLD) in response to a vibrotactile stimulus; (iii) examined grey and white matter structural brain plasticity; and (iv) correlated sensory recovery measures with grey matter changes in peripheral nerve transection and surgical repair patients. Compared to each patient’s healthy contralesional nerve, transected nerves have impaired nerve conduction 1.5 years after transection and repair, conducting with decreased amplitude and increased latency. Compared to healthy controls, peripheral nerve transection and surgical repair patients had altered blood oxygen level dependent signal activity in the contralesional primary and secondary somatosensory cortices, and in a set of brain areas known as the ‘task positive network’. In addition, grey matter reductions were identified in several brain areas, including the contralesional primary and secondary somatosensory cortices, in the same areas where blood oxygen level dependent signal reductions were identified. Furthermore, grey matter thinning in the post-central gyrus was negatively correlated with measures of sensory recovery (mechanical and vibration detection) demonstrating a clear link between function and structure. Finally, we identified reduced white matter fractional anisotropy in the right insula in a region that also demonstrated reduced grey matter. These results provide insight into brain plasticity and structure-function-behavioural relationships following nerve injury and have important therapeutic implications.
Keywords: cortical thickness; fMRI; diffusion tensor imaging; plasticity; peripheral nerve injury
Abbreviations: BA=Brodmann area; BOLD=blood oxygen level dependent; fMRI=functional magnetic resonance imaging;
PNIr=peripheral nerve transection and surgical repair; S1=primary somatosensory cortex; S2=secondary somatosensory cortex
Table of Contents
Following upper limb peripheral nerve transection and surgical repair (PNIr), 25% of patients have not returned to work 1.5 years after surgery (Jaquet et al., 2001). In addition, 57% of patients with nerve injuries are between 16–35 years of age (McAllister et al., 1996); thus, a long life of disability and economic difficulties may accompany upper limb nerve transection. Understanding the central and peripheral ramifications of peripheral nerve injury may facilitate the development of new therapeutic strategies and intervention programs.
It is not known how the brain responds to PNIr in humans. However, animal studies have established that plasticity within the somatosensory cortex begins immediately following peripheral nerve transection, and that 1 year after complete nerve transection and surgical repair, cortical maps contain patchy, non- continuous representations of the transected and adjacent nerves (Wall et al., 1986). The mechanisms that facilitate functional plasticity are thought to include the immediate unmasking of pre-existing projections from adjacent cortical and subcortical levels, and long term sprouting of axons at multiple levels of the neuroaxis, including the primary somatosensory cortex (S1) (Florence and Kaas, 1995; Hickmott and Steen, 2005).
Human brain imaging studies have corroborated the findings from animal models with the identification of altered functional MRI activation maps due to spinal cord injury, amputation, toe- to-thumb transfer, and in patients with carpel tunnel syndrome (Lotze et al., 2001; Manduch et al., 2002; Jurkiewicz et al., 2006; Napadow et al., 2006). Furthermore, structural MRI studies have recently visualized grey and white matter changes following traumatic injuries and in diverse pathological conditions, including limb amputation and chronic pain (Apkarian et al., 2004; Draganski et al., 2006; Davis et al., 2008; Geha et al., 2008; May, 2008). Grey matter changes are thought to be related to changes in cell size, atrophy and/or loss of neurons or glia, whereas white matter changes are impacted by axonal degenera- tion and loss of myelin (Beaulieu, 2002; May, 2008).
A powerful approach to delineate mechanisms of pathology and plasticity is to combine functional and structural grey and white matter imaging techniques. We previously reported that patients with complete upper limb PNIr retained profound somatosensory deficits that persist 41.5 years following surgery (Taylor et al., 2008a). Based on these findings, we reasoned these patients would exhibit functional and structural brain changes in key somatosensory brain areas. Therefore, in this study, we hypothesized that PNIr patients would have: (i) reduced blood oxygen level dependent (BOLD) responses to vibratory stimulation of the transected nerve territory, in the region of S1 that represents the injured upper limb and in the secondary somatosensory cortex (S2); (ii) a corresponding reduction in cortical thickness in these regions of the contralesional S1 and S2; (iii) a correlation between changes in cortical thickness and psychophysical measures of somatosensory function (vibration and touch detection thresh- olds); and (iv) reduced fractional anisotropy (a measure of white matter integrity) in white matter feeding into/out of these somatosensory cortical areas.
We recruited 27 patients with complete transection of the median and/or ulnar nerve followed by surgical repair from plastic surgeons affiliated with the University of Toronto Hand Program between June 2006 and May 2008. From this larger cohort, 14 pain-free patients (three females, 11 males; 34 10 years) with complete transection of the right median and/or ulnar nerve were included in the study [to avoid confounds related to the presence of pain and laterality patients with pain (n=6) and left sided lesions (n=7) were excluded from this analysis]. All patients underwent microsurgical nerve repair at least 1.5 years prior to study enrolment (recovery time varied from 1.5 to 8 years). In addition, we recruited 14 age- and sex-matched healthy controls (3 females, 11 males; 34 10 years). All subjects gave informed written consent to procedures approved by the University Health Network Research Ethics Board. All subjects were right handed (determined using the Edinburgh handedness inventory: Oldfield, 1971) and had no history of neurological injury or chronic pain (either before or after nerve transection). See Table 1 for demographic details.
All subjects participated in an imaging session that included: (i) functional magnetic resonance imaging (fMRI) in response to vibrotactile stimuli applied to the right index finger (within the median nerve territory); (ii) a high-resolution anatomical scan of the whole brain, acquired for image registration and for the analysis of cortical grey matter; and (iii) two diffusion tensor imaging scans for the assessment of white matter integrity. Prior to imaging, subjects were instructed in the basic design of the experiment and reminded to remain as still as possible throughout the duration of the scan.
Subjects were free to withdraw from the study at any time. In addition, a sensory and motor assessment was performed for all subjects (Taylor et al., 2008a). As touch and vibration detection thresholds were correlated with cortical thickness a description of these methods is included below (other psychophysical measures will be reported elsewhere).
Vibration detection thresholds were determined using a hand held Bio-Thesiometer (Bio-Medical Instrument Company, USA). The device has a 12-mm probe that was placed on the distal phalanx of the right index finger (D2). Thresholds were determined using the method of limits: the amplitude (voltage) was gradually increased until the subject indicated that they perceived the stimulus. Vibration thresholds were acquired three times and an average value was calculated. During vibration threshold testing, subjects were instructed to close their eyes and rest the back of their hand on a supportive cushion.
Mechanical detection thresholds were determined using a standardized set of von Frey filaments (OptiHair2 Marstock Nervtest, Germany) containing 12 logarithmically spaced calibrated filaments that delivered forces from 0.25–512 mN. The contact surface diameter of all 12 filaments was ~0.4mm. Trials were conducted with the subject’s eyes closed and hands resting on a soft cushion. Probes were applied in an ascending series and subjects were required to make a response every time they felt a probe touch the right D2 fingertip. This process was repeated three times. The force for the filament that was detected in at least two of three trials was reported as that subject’s mechanical detection threshold.
Patients participated in bilateral sensory and motor nerve conduction studies at the Toronto Western Hospital electromyography (EMG) clinic. For motor nerve conduction, the stimulating electrode was placed at the wrist and elbow (separately) and the recording electrode was placed over the abductor pollicis brevis, for median nerve assessment, or the abductor digiti minimi for ulnar nerve assessment. For sensory nerve testing the recording electrode was placed at the wrist and the stimulating electrode was placed at digits D2, D3 and D5. A senior, experienced neurologist from the Toronto Western Hospital EMG Clinic (Dr Peter Ashby) reviewed all clinical assessments to deter- mine which nerves demonstrated normal/abnormal responses. As amplitude and latency measures are known to vary substantially between subjects (due to factors such as the density of innervation, the depth of the nerve and the thickness of an individual subject’s skin) (Kimura, 2001) each patient’s untransected nerve served as their own control for comparison with values from the transected side. In those patients with detectable nerve conduction responses, paired t-tests were performed to assess the difference in latency or amplitude measures between each patient’s transected and contralesional untransected nerves.
Brain imaging data were acquired using a 3T GE MRI system fitted with an eight-channel phased array head coil. Subjects were placed supine on the MRI table and each subjects’ head was padded to reduce movement. Whole-brain fMRI data was acquired using echo planar imaging (28 axial slices, field of view (FOV) = 20 x 20 cm, 64 x 64 matrix, 3.125 x 3.125 x 4mm voxels, echo time (TE) = 30 ms, repetition time (TR) = 2000 ms). The scan time was 5 min and 8 s (154 frames). During scanning, a non-painful, 12 Hz vibrotactile stimulus was applied to the distal phalanx of the right D2 using balloon diaphragms driven by compressed air (Device man- ufactured by Dr Christo Pantev; www.biomag.uni-muenster.de). Stimuli were delivered in blocks of 10s interleaved with 20s of rest, for a total of 10 blocks of stimulation and 10 blocks of rest. The first 8 s (4 TRs) of data acquired from each run were discarded to allow for fMRI signal equilibration. Subjects were instructed to keep their eyes closed throughout scanning and focus on the stimuli. A whole brain three dimensional (3D) high-resolution anatomical scan (124 sagittal slices, 24 x 24 cm FOV, 256 x 256 matrix, 1.5 x 0.94 x 0.94 mm voxels) was acquired with a T1-weighted 3D spoiled gradient echo sequence (one signal average, flip angle = 20 , TE 5 ms). In addition, two diffusion tensor imaging scans (38 axial slices, FOV 24 x 24 cm, 128 x 128 matrix, 1.875 x 1.875 x 3 mm voxels) were acquired along 23 directions with a b-value of 1000smm–2. Each run also contained two volumes with no diffusion weighting.
Data were analysed using Brainvoyager QX v1.8 (Brain Innovaton, Maastricht, Netherlands). Pre-processing included: 3D motion correction, slice scan-time correction, linear trend removal, high-pass filtering (five cycles per run), and spatial smoothing with a 6mm full width at half maximum (FWHM) Gaussian kernel. fMRI data sets were interpolated to 3 x 3 x 3 mm voxels, registered to the high-resolution ana- tomical image, and normalized to standard Talairach space (Talairach and Tournoux, 1988). Voxels are reported as 1 x 1 x 1 mm. Data were analysed using the general linear model; the model was obtained by convolving the boxcar function of the time course of tactile stimulation with the standard haemodynamic response function. To identify between group differences in activation patterns a fixed effects analysis was performed with the contrasts: (i) healthy controls: stimulation 4 rest; (ii) PNIr: stimulation 4 rest; and (iii) healthy controls 4 PNIr. Activation maps were thresholded at a corrected value of P50.05 (derived from an uncorrected P50.0001 and 120mm3 contiguous voxels as previously reported: Taylor and Davis, 2009); this was also validated by running a Monte Carlo Simulation with AlphaSim application implemented in the Analysis of Functional Neuroimage (AFNI) software. This analysis included only the 11 patients that sustained transection of the right median nerve (n=9) or the right median and ulnar nerve (n = 2) (i.e. the three patients with a pure right ulnar nerve transection were not included in this analysis).
Cortical thickness analysis was performed using Freesurfer (http:// surfer.nmr.mgh.harvard.edu); methods have been outlined in detail elsewhere (Dale et al., 1999; Fischl et al., 1999a, b; Fischl and Dale 2000). Briefly, high-resolution T1-weighted anatomical data sets were registered to the Talairach atlas (Talairach and Tournoux, 1988). This was followed by intensity normalization, skull stripping and separation of the hemispheres. Subsequently, the white/grey matter (called the white surface) and grey/CSF (called the pial surface) boundaries were identified and segmented. The distance between the white and pial surfaces was then calculated at every point in each hemisphere of the brain. To identify group differences between the 14 patients and 14 age/sex-matched controls, a general linear model analysis was performed at every point on the brain. As individual’s cortical topography is inherently heterogeneous, a 5mm FWHM spatial smoothing kernel was applied prior to statistical analysis. Data are displayed at a corrected P50.05 (derived from an uncorrected P50.0075 and 102 contiguous vertices); this was calculated by running a Monte Carlo simulation with AlphaSim. A vertex represents a point on a two dimensional sheet, and, in this study, the distance between two vertices is 0.80mm2.
As patients exhibited significant deficits in somatosensory function within the transected nerve territory, we hypothesized that measures of somatosensory function (vibration and touch detection) would correlate with cortical thickness in the contralesional post-central gyrus (primary and secondary somatosensory cortices). Therefore, we performed correlation analyses in the patient group between: (i) cortical thickness and vibration detection threshold; and (ii) cortical thickness and touch detection thresholds. One patient did not complete psychophysical assessment; therefore, this analysis included 13 PNIr patients. In addition, to determine if there was a relationship between cortical thickness and recovery time a correlation analysis was also performed between these two measures. These correlation analyses were restricted to the contralesional post-central gyrus by including a mask (taken from Freesurfer’s built in atlas) in the general linear model. A Monte Carlo simulation was performed that was restricted to the number of vertices within contralesional post-central gyrus; images are displayed with a corrected P50.05 (derived from an uncorrected P50.0075 and 68 contiguous vertices).
Diffusion tensor image processing was performed with DTiStudio (www.MriStudio.org) and FSLv.4.0 (www.fmrib.ox.ac.uk/fsl/). Images were first realigned with the Automatic Image Registration tool implemented in DTiStudio, using the first B0 image in the first series acquired as the template. This process corrects for subject motion and eddy-current distortion. All images were then inspected visually to assess image quality and the alignment of the separate diffusion tensor imaging runs. If an artefact was detected, the slice was removed prior to calculating the average of the two separate diffusion tensor imaging runs. Individual FA maps were calculated using the DTIFIT tool implemented in FSL. Voxel-wise statistical analysis was performed to identify group differences in the mean fractional anisotropy using Tract Based Spatial Statistics; for a full description of these methods see Smith et al. (2006). Briefly, images were non-linearly registered to a target image (MNI152), the mean image was then created from all datasets and this image was subsequently thinned to represent all tracts that were common to all subjects. Each subject’s highest fractional anisotropy values were then projected onto the skeleton by searching in white matter perpendicular to each point on the white matter skeleton. A whole-brain voxel-wise statistical analysis was then performed between groups (14PNIr and 14 healthy controls) and images were whole brain corrected at P50.05. In addition, a region of interest analysis was performed in white matter tracts adjacent to the contralateral S1, thalamus and bilateral anterior and posterior insula. These regions were chosen as they have previously been implicated in aspects of somatosensation and because they correspond with regions that were identified in the fMRI and cortical thickness analysis (CTA) group analyses. Regions of interest were drawn on the white matter skeleton as follows: (i) The contralateral S1 region of interest originated medially at the junction between the white matter skeleton of the corona-radiata and the skeleton section feeding into the post- central gyrus; terminating at the end of the tract within a given slice.
In the z direction the region of interest extended from z=49 to 57; white matter tracts supplying the hand region. (ii) The contralateral thalamus region of interest was restricted to white matter tracks surrounding the posterior and medial thalamic nuclei (nuclei involved in somatosensory function), extending from z = –1 to 4. (iii) Insular regions of interest were drawn bilaterally within white matter adjacent to the anterior and posterior insula based on criteria previously published by our lab (Taylor et al., 2008b). The region of interest extended from z = 2 to 8. Fractional anisotropy values were extracted from each of these regions of interest and a multivariate analysis of variance (MANOVA) was performed using the Statistical Package for the Social Sciences v13.0 (SPSS Inc, Chicago), which included fractional anisotropy values for all six regions of interest.
Table 1 provides demographic details for study participants. All 14 patients sustained a complete transection of the right median and/or ulnar nerve followed by microsurgical repair at least 1.5 years prior to study enrolment. The time from surgery to testing ranged from 1.5 to 8 years with a mean (SD) of 4.8 3 years. Patients and controls did not (34 10 years both groups; t = 0.04; P = 0.97).
Vibration thresholds were calculated from all three measurements since one-way repeated measures analysis of variance (ANOVA) indicated no significant differences between the three trials [F (25, 1)=0.227, P=0.64]. Vibration and mechanical detection thresh- olds were significantly impaired in PNIr patients compared to healthy controls (vibration: t = 4.77, P50.001, Fig. 3A; mechanical: t=3.10, P=0.005, Fig. 3D).
Amplitude and latency measures obtained from each patient’s contralesional nerves were classified as normal by an experienced neurologist at the Toronto Western Hospital EMG Clinic. Nine of the 14 patients completed nerve conduction testing. Table 2 displays the average increase/decrease latency and amplitude data for sensory nerve conduction from the wrist to the abductor pollicis brevis (median) or abductor digiti minimi (ulnar) muscles and for sensory conduction from the wrist to D2 (median) and D5 (ulnar) compared to each patients uninjured contralesional nerve. Out of nine, seven patients had transections that included the median nerve. Of these seven, one patient had no detectable response during motor testing and another patient had no detectable response during sensory testing.
decreased by 41% (t = –5.9; P = 0.010). Sensory testing of the ulnar nerve demonstrated a 27% increase in latency (t = 4.3; P = 0.049) but no significant increase in amplitude (t = 3.5; P = 0.072).
Functional MRI maps were calculated from the 11 PNIr patients with right median nerve transections (patients with ulnar nerve transections were excluded from this analysis) and 11 age- and sex-matched healthy controls. From Fig. 1A, it is clear that PNIr patients have significantly less activation, compared to healthy controls, in a region of S1 corresponding to Brodmann area 2 (BA2) (Talairach and Tournoux, 1988) and S2 (see Table 3 for details). The average event-related responses from these regions of interest highlight the attenuated BOLD response within the patients’ left BA2 and left S2 (Fig. 1B and C, respec- tively). Curiously, vibrotactile stimulation in the patients activated a more superior part of the post-central gyrus (probably BA1/3) (Talairach and Tournoux, 1988) (Fig. 1A and Table 3). An event- related average (Fig. 1D) demonstrates that healthy controls had minimal activation in this region. Furthermore, patients had significantly more activation in brain regions collectively known as the task positive network (asterisks in Fig. 1). See Table 3 for the full list of task positive brain areas activated. This network includes lateral prefrontal, lateral parietal, premotor and inferior temporal cortices (Table 3): brain areas that are activated during the performance of an attention demanding task and suppressed or inactive during rest or tasks that are not cognitively or attentionally challenging (Fox et al., 2005; DeLuca et al., 2006; Seminowicz and Davis 2007).
Cortical thickness analysis in all 14 patients and 14 age/ sex-matched healthy controls revealed several loci of significant cortical thinning in the PNIr group (Fig. 2 and Table 4). Specifically, patients had a 13%–22% reduction in cortical thick- ness in the left (contralesional) S1, S2, pregenual anterior cingulate gyrus, ventrolateral prefrontal cortex and right anterior insula, anterior/posterior mid cingulate gyrus and paracentral lobule. Interestingly, the locations of grey matter thinning within the post-central gyrus coincide with the regions of reduced BOLD following vibrotactile stimulation (Table 4). Since we had prior knowledge of the patients’ sensory deficits and recovery time (i.e. time since microsurgical repair), we next asked whether the patients’ cortical thickness in the post-central gyrus correlated with their sensory mechanical and vibration detection thresholds, or with their recovery time. These analyses revealed a negative correlation between cortical thickness and vibration detection thresholds in a region encompassing BA1/2 and S2 (P50.001, r=0.80 and 0.91, for BA1/2 and S2, respectively; Fig. 3 and Table 5). In addition, mechanical detection thresholds were also negatively correlated with cortical thickness in a slightly more superior BA2 region and the same S2 region (P50.001, r = 0.83 and 0.85, for BA2 and S2, respectively; Fig. 3 and Table 5). However, we did not identify a significant relationship between recovery time and cortical thickness. Therefore, in the post-central gyrus cortical thinning was associated with more severe sensory deficits. However, we did not identify a significant relationship between recovery time and cortical thickness. Again, there was a correspondence between the cortical thinning in areas negatively correlated with vibratory stimuli and the regions showing group fMRI and CTA abnormalities.
To assess white matter integrity we utilized a region of interest approach to examine white matter group differences based on a priori hypotheses. Regions of interest were restricted to white matter tracts surrounding and feeding into the contralesional S1 and thalamus. In addition, we also drew regions of interest in white matter adjacent to left and right, anterior and posterior insula. The insula was chosen as it is implicated in somatosensory processing and because we identified reduced grey matter in the right anterior insular with CTA. This region of interest approach revealed that patients had significantly reduced white matter fractional anisotropy values (MANOVA including all six regions of interest) adjacent to the right anterior [F (1, 26) = 4.39, P = 0.046; Fig. 4A] and posterior insula [F (1, 26) = 5.55, P = 0.026; Fig. 4B], but there were no group differences in the white matter adjacent to the left insula (left anterior insula: P = 0.51; left posterior insula: P=0.26), thalamus (P=0.46) or S1 (P=0.46).
Here, we have demonstrated for the first time that there is functional plasticity and both grey and white matter structural abnormalities in several cortical areas following upper limb peripheral nerve transection and surgical repair. This plasticity may arise from incomplete peripheral nerve regeneration (peripheral cell death and/or incomplete re-myelination), as nerve conduction measures in these patients demonstrated severe abnormalities. In addition, our data demonstrate that decreased vibrotactile-evoked fMRI responses in the post-central gyrus correspond with grey matter thinning in the patient group. These results suggest that reduced BOLD responses may be facilitated by a reduction in cortical grey matter and/or a decrease in the afferent input to the post-central gyrus. In addition, cortical thickness within these same parts of the post-central gyrus negatively correlated with behavioral measures of somatosensory function. That is, increased somatosensory deficits were correlated with thinner cortex; both of which may be related to afferent input. Taken together, our data suggest that incomplete peripheral nerve regeneration contributes to somatosensory impairments, cortical grey matter atrophy and reduced fMRI activation (see Fig. 5 for a summary of these findings).
It is well known that cortical plasticity following peripheral nerve transection and surgical repair can occur throughout the CNS in non-human primates (Kaas, 1991). This plasticity is thought to be due to the unmasking of previously silent synapses or axonal sprouting into deafferented territory (Wall et al., 1986; Florence and Kaas, 1995). In the primate model, 1 year following nerve transection and surgical repair, the denervated cortex is characterized by incomplete and disorderly representations of the regenerated and adjacent (intact) nerves. This patchy representation is attributed to incomplete peripheral regeneration resulting in a partial recovery of the denervated cortical space (Kaas, 1991). To assess the extent of peripheral regeneration in our patient population we performed sensory and motor nerve conduction studies across the transected area. Our nerve conduction results demonstrate that PNIr patients have significantly decreased amplitude and increased latency in both sensory and motor nerves compared to their own untransected side. Decreased amplitude combined with increased latency is indicative of peripheral fibre loss (i.e. cell death) and/or abnormal or incomplete re-myelination following transection (Kimura, 1984). In addition, it is well established that between 20% and 50% of dorsal root ganglion neurons die following nerve transection (Liss et al., 1996). Thus, afferent cell death and incomplete regeneration can result in decreased afferent input to the cortex, which may account for ongoing sensory deficits and decreased BOLD response in BA2 and S2. Furthermore, this diminished afferent input could also account for the cortical thinning we observed in the same regions of the cortex. Sensory deprivation has been shown to cause trans- neuronal degeneration in several regions of the CNS, including the dorsal horn following sciatic nerve section (Knyihar-Csillik et al., 1989), and may involve second- and third-order neurons (Powell and Erulkar, 1962). Transneuronal degeneration is characterized by cell shrinkage and is thought to be related to decreased, or non-existent, afferent input (Knyihar-Csillik et al., 1989). Thus, cortical grey matter loss (or atrophy) could also be directly related to decreased afferent input.
The insula is thought to play a role in integrating multimodal information important for sensorimotor, emotional, allostatic/ homeostatic and cognitive functions (Devinsky et al., 1995; Critchley, 2004; Craig, 2008) and has been designated a limbic sensory cortex (Craig, 2008). Several studies have reported insular activation in response to tactile stimulation (Gelnar et al., 1998;
Downar et al., 2002) and anatomical tracing studies in primates have demonstrated that the insula is reciprocally connected to frontal, parietal and temporal lobes (Augustine, 1996). In our patients, the right anterior insula was the only cortical area that demonstrated significant cortical thinning in conjunction with reduced fractional anisotropy values in the adjacent white matter, suggesting that the cortical thinning within this region is associated with a loss of fibres projecting to or from this structure. The right anterior insula has been implicated in interoception as it is situated to integrate homeostatic input from the body with motivational, emotional and social conditions (Craig, 2008). Furthermore, Critchley et al. (2004) reported a correlation between interoceptive abilities and the grey matter volume of the right anterior insula. Given our finding that the patients have decreased grey matter in the right anterior insula, it would be of interest to assess interoceptive capabilities following peripheral nerve injury in a future study.
Taken together, we have demonstrated for the first time that functional and structural alterations are present in the human cerebral cortex 1.5 years after a complete transection of an upper limb peripheral nerve that was microsurgically repaired. In addition, nerve conduction measures indicate incomplete peripheral regeneration in these patients. Furthermore, we show that cortical thickness is related to psychophysical measures of recovery, in that thinner cortex within BA2 and S2 was associated with poorer somatosensory function. These data suggest that the reestablishment of normal functional activation maps is directly associated with the successful regeneration of peripheral afferents.
Keri S. Taylor,1,2 Dimitri J. Anastakis2,3,4 and Karen D. Davis1,2,3
1 Division of Brain, Imaging and Behaviour – Systems Neuroscience, Toronto Western Research Institute, University Health Network, Toronto, Canada M5T258
2 Institute of Medical Science, University of Toronto, Canada
3 Department of Surgery, University of Toronto, Canada
4 Clinical Studies Resource Centre, Toronto Western Research Institute, University Health Network, Toronto, Canada M5T2S8
Correspondence to: Karen D. Davis, Ph.D.,
Division of Brain, Imaging and Behaviour – Systems Neuroscience, Toronto Western Research Institute,
Toronto Western Hospital,
University Health Network,
Room MP14-306, 399 Bathurst Street,
Toronto, Ontario,
Canada M5T 2S8
E-mail: kdavis@uhnres.utoronto.ca
The authors thank Mr. Geoff Pope, Dr. Adrian Crawley, Mr. Eugene Hlasny and Mr. Keith Ta for expert technical assistance. The authors would like to thank Dr. Peter Ashby and Mr. Freddy Paiz from the Toronto Western Hospital EMG Clinic for conduct- ing the nerve conduction tests and for providing expert assess- ment of the findings. The authors also thank Drs Dvali, Binhammer, Fialkov and Antonyshyn for collaborating with this project. Dr. Davis is a Canada Research Chair in Brain and Behaviour (CIHR MOP 53304).
The Physicians’ Services Incorporated and a joint seed grant from the University of Toronto Centre for the Study of Pain/ AstraZeneca.
Supplementary material is available at Brain online.
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