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The human motor cortex after incomplete spinal cord injury: an investigation using proton magnetic resonance spectroscopy
  1. B K Puria,
  2. H C Smithb,
  3. I J Coxa,
  4. J Sargentonia,
  5. G Savicc,
  6. D W Maskillb,
  7. H L Frankelc,
  8. P H Ellawayb,
  9. N J Daveyb
  1. aRobert Steiner MRI Unit, Imperial College School of Medicine, Hammersmith Hospital, London, UK, bDivision of Neuroscience and Psychological Medicine, Imperial College School of Medicine, Charing Cross Hospital, London, UK, cNational Spinal Injuries Centre, Stoke Mandeville Hospital, Aylesbury, Buckinghamshire, UK
  1. Dr NJ Davey, Department of Sensorimotor Systems, Division of Neuroscience and Psychological Medicine, Imperial College School of Medicine, Charing Cross Hospital, Fulham Palace Road, London W6 8RF. Telephone 0044 181 846 7284; fax 0044 181 846 7338; email n.davey{at}


OBJECTIVES (1) A biochemical investigation of the motor cortex in patients with incomplete spinal cord injury and normal control subjects using proton magnetic resonance spectroscopy (MRS). (2) To relate any altered biochemistry with the physiological changes in corticospinal function seen after spinal cord injury.

METHODS a group of six patients with incomplete spinal cord injury who showed good recovery of motor function were selected. The patients were compared with five healthy control subjects. Electromyographic (EMG) responses of thenar muscles to transcranial magnetic stimulation (TMS) of the motor cortex showed that inhibition of cortical output was weaker in the patients than the controls. Proton MRS data were collected from a plane at the level of the centrum semiovale. Two 4.5 cm3 voxels in the motor cortex and a third voxel in the ipsilateral occipital cortex were examined in the patients and control subjects.

RESULTS The mean level ofN-acetylaspartate (NAA), expressed relative to the creatine (Cr) peak (NAA/Cr), was significantly increased in the motor cortex of the patients compared with their ipsilateral occipital cortex or either cortical area in the controls. No differences between patients and controls were seen for any of the other metabolite peaks (choline (Cho), glutamate/glutamine (Glx) or the aspartate component of NAA (AspNAA)) relative to Cr. Choline relative to Cr (Cho/Cr) was higher in the motor cortex of the control subjects than in their ipsilateral occipital cortex. This difference was not present in the patients.

CONCLUSIONS Raised NAA/Cr in the motor cortex of the patients probably results from increased NAA rather than a decrease in the more stable Cr. The possible relevance of a raised NAA/Cr ratio is discussed, particularly with regard to the changed corticospinal physiology and the functional recovery seen in the patients.

  • spinal cord injury
  • magnetic resonance spectroscopy
  • N-acetylaspartate
  • transcranial magnetic stimulation

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Patients who have paresis may compensate for the impairment of motor function by increased use of muscles unaffected by the disease or trauma. This process can be accentuated by appropriate physiotherapy directed at learning new strategies. Physiotherapy also has a training effect on muscles in which a degree of function remains. The functional changes achieved are thought to take place as a result of altered connectivity or neurotransmission within the CNS.

The motor cortex is not static in its organisation and may exhibit plasticity. The representation of the body within the motor cortex may be modified after amputation in animals1 2 and humans.3 4 Levy et al 5described two tetraplegic patients who regained some power in proximal arm muscles whereas distal muscles showed no improvement. Using transcranial magnetic stimulation (TMS), the proximal muscles were found to have a larger scalp field for producing motor evoked potential responses than in non-paretic humans. Topka et al 6 found that the extent of the motor cortex from which TMS could evoke responses in muscles rostral to a complete spinal transection became enlarged.

Responses to TMS have longer latencies7 and durations8 after spinal cord injury. These changes could reflect reduced conduction velocity in corticospinal tract axons or redirection of transmission to smaller corticospinal neurons with slower axons. Weakness of voluntary muscle contraction in incomplete spinal injury correlates with delayed or absent responses to TMS.9 Studies made after incomplete spinal cord injury in humans have disclosed abnormalities in the EMG responses to TMS of the motor cortex. The pattern of recruitment of motor neurons with increasing stimulus intensity10 and facilitation of the corticospinal pathway with increasing voluntary effort11are altered. In addition, the suppression of voluntary contraction (SVC) in the absence of a preceding compound motor evoked potential (cMEP),12 has a longer latency in patients with incomplete spinal cord injury who have shown a degree of functional recovery.13 14 We have reasoned that this longer latency reflects a “down regulation” of inhibitory connections activated by TMS within the motor cortex as a result of axonal sprouting or changes in synaptic efficacy.15

An additional method of detecting alterations in cortical function that may underly recovery of function after spinal cord injury, is magnetic resonance spectroscopy (MRS). This is a non-invasive technique that allows brain chemistry to be measured by the in vivo study of specific metabolites such as compounds containing choline (Cho), creatine and phosphocreatine (Cr),N-acetylaspartate (NAA), the aspartate component of NAA (AspNAA), and glutamate and glutamine (Glx). A range of spectral changes have been found in neurological disease.16 For example, NAA is thought to be localised in neurons and neuronal processes in the mature brain, and is relatively decreased in several different types of cerebral pathology (for example, Huntington’s disease17); such decreases are interpreted as reflecting neuronal dysfunction. During the first year of life, compared with levels at birth, NAA levels double, even though the number of neurons remains constant; this is thought to reflect neuronal maturation, including dendritic sprouting and increases in the number of axons and synaptic connections.18 There is only one neurological disease, Canavan’s disease, in which relative levels of NAA are known to increase.19 20

Using current localisation techniques, MRS spectra can be obtained from regions of 1–10 cm3 within the timescale of a clinical examination. It is therefore feasible to define spectral changes specific to the motor cortex. For example, significant differences in NAA/Cr and NAA/Cho in the motor cortex between controls and patients with motor neuron disease/amyotrophic lateral sclerosis have been reported.21 To our knowledge there have been no previous cerebral proton MRS studies of spinal injury in humans.

The aim of this study was to use MRS to look for biochemical changes in the motor cortex accompanying functional recovery after spinal cord injury. We compare the results of the MRS with the changes in corticospinal physiology known to occur after incomplete spinal cord injury. The work has been presented at the Society for Neuroscience.22



Permission for this study was obtained from the research ethics committee of the Royal Postgraduate Medical School of Hammersmith Hospital (REC 93/4047), the Aylesbury Vale local research ethics committee, and Charing Cross and Westminster Medical School. All subjects provided informed written consent in accordance with the declaration of Helsinki.

Six male patients with incomplete spinal cord sections were referred by consultants at the National Spinal Injuries Centre, Stoke Mandeville Hospital, for inclusion in the study; their clinical details are summarised in table 1. Five male control subjects with no history of neurological disease also took part in the study. The patients with spinal injury did not differ significantly in age (mean 47.8 (SD 11.7) years) from the control subjects (42.0 (SD 6.6) years). The study was performed on the dominant hand/cortical hemisphere unless motor function was lateralised, in which case the weaker side was assessed. The dominant hand was taken to be the one used for handwriting. One patient and one control subject had their left hand function assessed (see table 1).

Table 1

 Clinical details of the patients with incomplete spinal cord injury


Electrophysiological studies were performed on all subjects within three months of MRS. Surface EMGs were recorded from thenar muscles using self adhesive electrodes (Arbo Neonatal Pink). EMG signals were filtered (−3 dB below 100 Hz and above 2 kHz) and amplified (×1000) before being sampled (4 kHz) by a computer for analysis (Cambridge Electronic Design 1401 with SIGAVG software). Subjects were instructed to make a weak isometric contraction (5%-10% of maximum voluntary contraction (MVC)), in the thenar muscles throughout the recording. The MVC in thenar muscles was assessed using a force transducer. The patients had a mean (SEM) MVC of 51 (10) N and the controls 90 (11) N indicating a reduced, but nevertheless substantial, level of motor function in the patients. A physician assessed motor and sensory function in each patient according to the international standards for neurological and functional classification of spinal cord injury.23 All the patients had “motor incomplete” spinal cord injuries (American Spinal Injuries Association23— grade D). The examination, which was performed on the day of the electrophysiological recording, indicated that a good degree of functional recovery had taken place since the injury occurred. Neurological assessment scores are presented in table1.

The TMS was delivered using a MagStim 200 stimulator connected to a 9 cm round coil placed tangentially on the head centred over the vertex. The coil was positioned A side up so as preferentially to activate the muscles of the right hand or B side up to activate left hand muscles.24 The stimulus strength was increased in steps of 5% maximum stimulator output until just above threshold for evoking either SVC (fig 1B) or a cMEP response (fig 1A). Up to 30 responses were rectified and averaged at each stimulus strength. The latency of cMEPs and SVC were measured in each subject.

Figure 1

Averaged rectified EMG responses to TMS in a control subject (42 years old) recorded from the thenar muscles of the right hand during a weak voluntary contraction. (A) Average of 10 responses to TMS delivered at 35% of maximum stimulator output. A compound motor evoked potential (cMEP) is evident. (B) Average of 20 responses to TMS delivered at 22% of maximum stimulator output. A period of suppression of voluntary contraction (SVC) is evident. The horizontal dashed lines mark the mean level of voluntary EMG and the vertical dashed lines mark the start point of each response. Note the differences in scaling between the two records.


All the patients had spinal cord injury resulting from physical trauma 193 to 717 days before the day of MRS. Care was taken to ensure that subjects for MRS study had no cardiac pacemaker or ferromagnetic implant, and did not have claustrophobia.

Cerebral MR data were obtained using a Picker prototype spectroscopy system (Picker International, Cleveland, Ohio, USA) based on a whole body magnet (Oxford Magnet Technology, Oxford, UK) operating at 1.5 T. An enveloping birdcage radiofrequency coil was used, tuned to protons (1H, 64 MHz). Multislice T1 weighted transverse images (SE 300/22) were obtained to visualise the location of the anatomy within the magnet coordinate system. Localised shimming was performed on a 20 mm transverse plane centred at the centrum semiovale.

Chemical shift imaging spectral acquisition consisted of a 1331–180° spin echo: a 1331 composite pulse for water suppression with a 90° excitation at the N-acetylaspartate (NAA) resonance (intrapulse spacing 2.1 ms), and a slice selective 180° and phase encoding in the two in plane directions.25 The sequence acquisition parameters were repetition time 1500 ms; delay before data acquisition 130 ms; 16×32 phase encoding steps giving 512 averages; and total data collection time 13 minutes. The spatial resolution was 20 mm×15 mm×15 mm, giving a nominal voxel size of 4.5 cm3. In addition, a non-selective inversion pulse preceded each data acquisition, inversion time 150 ms, to reduce the fat signal from surface voxels and consequent “bleeding” into neighbouring voxels. The relative peak areas were influenced by some MR factors, including the non-uniform excitation profile of the 1331 pulse and T2 relaxation during the delay before data acquisition. The data have not been manipulated to account for these factors.

The dataset was processed with an exponential filter of 120 ms (2.7 Hz) in the time domain and cosine filtering in each spatial direction. The individual spectra were manually phased. A knowledge based algorithm26 was used both for removal of the water peak residuum and for baseline flattening.

The region of the motor cortex for analysis was selected to be comparable in both the MRS and the electrophysiological studies. Two voxels from the motor cortex of the selected hemisphere (for example, fig 2; voxels marked B) were selected for MRS analysis. These voxels lay in the hand area of the motor strip directly inferior to the perimeter of the magnetic stimulating coil, as sited in the electrophysiological study. In these two voxels the tangent of induced current would have flowed anteromedially; this is the lowest threshold orientation for evoking both cMEPs and SVC.12 One voxel in the ipsilateral occipital cortex was also selected as an internal control (for example, fig 2; voxel marked A). Each data set was inspected and a spectrum was selected from a voxel as posterior as possible, excluding those voxels heavily contaminated with signal from subcutaneous lipid, a result of “signal bleed”. In practice, when dealing with an irregular structure such as the brain, it was difficult to position the voxel (20 mm×15 mm×15 mm) so that it was completely uncontaminated by lipid, CSF, or bone. These factors meant that it was not possible to position voxels so that they contained purely cortical grey matter where we speculated that neuronal reorganisation may have occurred. It is clear from the slice presented in figure 2 that the selected voxels contain a combination of cortical white and grey matter and that there is possibly some contamination from CSF. In every subject the voxels best fitting the above criteria were chosen.

Figure 2

T2 weighted transverse MRI through the head of a patient with incomplete spinal cord injury (table 1, patient 1). The voxels selected for proton MRS analyses were typically 8J for the occipital cortex (marked A) and 7/8F for the motor cortex (marked B). Magnetic stimulation was applied to the cranium with the perimeter of the circular coil lying over the coordinates of voxels 7/8F.


Ratios of Cho, AspNAA, Glx, and NAA peaks relative to the Cr peak were measured using the NMR1® spectral processing program (New Methods Research Inc, E Syracuse, NY, USA) on a SUN SPARCstation 10 (Sun Microsystems Inc, Mountain View, CA, USA). For each subject the spectral information from the two selected voxels in the motor cortex was averaged to produce a single set of cerebral parameters.

Pooled spectral data for each metabolite were compared between cortical sites within each group of subjects and between groups of subjects using one way analysis of variance (ANOVA) with a Bonferoni correction. Differences in metabolite ratios to Cr within each group of subjects were assessed by Student’s paired t test. Pearson product moment correlation was carried out in the patient group to see if the NAA/Cr ratio was correlated with neurological score, duration of injury, or MVC in the thenar muscle.


Figure 3 shows the latencies of cMEPs and SVC measured in the patient and control groups. The latency (mean (SEM) of cMEPs was longer (Student’s t test, p<0.05) in the patient group (25.5 (0.8) ms) than in the control subjects (21.8 (0.5) ms). The mean latency of SVC, in the absence of a preceding cMEP, was longer (p<0.01) in the patient group (50.8 (2.8) ms) than in control subjects (33.3 (1.2) ms). The latency difference between cMEPs and SVC was longer (p<0.01) in the patients (25.3 (2.3) ms) than in the controls (11.5 (1.1) ms). These values are consistent with previously reported results.13-15

Figure 3

Average latencies of cMEPs and SVC in the control group (open bars) and the patient group (filled bars). The right hand bars show the latency difference between cMEPs and SVC (SVC-cMEP) in each group. All three times are significantly longer (p< 0.05) in the patient group. Error bars indicate SEM

Figure 4 shows proton MR spectra from the ipsilateral occipital cortex (fig 4A) and motor cortex (fig 4B) of a patient with spinal injury. It is evident that the NAA peak has a larger area, relative to Cr, in the spectrum from the motor cortex than in the spectrum from the occipital cortex. Figure 4C shows an example of the analysis technique, showing that the NMR1 software has produced an accurately modelled spectrum of the data presented in figure 4 A. The modelled specrum is presented (fig 4C(top)) together with the experimental plot (fig 4C (middle) and the difference plot (fig 4C (bottom)).

Figure 4

Example MRS spectra taken from voxels in the occipital cortex (A) and motor cortex (B) in a patient (table 1, patient 2). The ratio NAA/Cr is higher in the motor cortex than in the occipital cortex. The modelled spectrum for the occipital cortex is presented (C (top)) together with experimental spectrum (same as in A) (C (middle)) and the difference plot (C (bottom). Note different scaling in C.

Table 2 presents the raw metabolite peak ratios relative to the Cr peak for each subject.

Table 2

 Ratios of metabolite peaks relative to Cr in each of the six patients and five control subjects

When these ratios were subjected to statistical analyses using a one way ANOVA with Bonferoni correction, we found that the mean NAA/Cr ratio was 50% higher (p<0.05) in the motor cortex of the spinal injury group than in their ipsilateral occipital cortex. Moreover, the mean NAA/Cr ratio was 37% higher (p<0.05) in the motor cortex of the spinal injury group than in the motor cortex of control subjects and 46% higher (p<0.05) than in the occipital cortex of control subjects. No other metabolite levels, relative to Cr, differed between these regions in the patient group with spinal injury or between patient with spinal injury group and the control group. The mean ratios of each metabolite peak, relative to Cr, are plotted in figure5.

Figure 5

Ratios of each metabolite, relative to Cr, present in voxels from occipital cortex (A) and motor cortex (B). Open bars represent data from control subjects and filled bars data from patients. NAA/Cr is significantly (ANOVA with Bonferoni correction p< 0.05) higher in the motor cortex of the patients than the ipsilateral occipital cortex or either cortical area in the controls. Error bars indicate SEM.

In the control group the Cho/Cr ratio was 52% higher in the motor cortex compared with their ipsilateral occipital cortex (Student’s paired t test; p<0.05). No other relative metabolite levels differed between these regions (fig 5).

There was no correlation (Pearson product moment correlation; p>0.05), in this group of patients, between the NAA/Cr ratio and either duration of injury, neurological score, or MVC in thenar muscles.


This study has found two significant MRS changes. Firstly, in patients recovering from incomplete spinal cord injury, there was a raised NAA/Cr ratio in the hand area of the motor cortex compared with both the ipsilateral occipital cortex and the motor cortex of the control group. Secondly, in the control group, there was a higher Cho/Cr ratio in the motor cortex compared with the ipsilateral occipital cortex.


The increased latency of cMEP responses and SVC could result, in part, from slowing of conduction at the site of the lesion in the patients with spinal cord injury.7 However, as previously reported,13-15 the time interval between SVC and cMEP responses in the patients with spinal cord injury was also increased. Therefore, the latency of SVC must have increased by a greater amount than the latency of the cMEP response. We have suggested15that this greater increase in latency of SVC could be due to a down regulation of the early portion of the inhibition, probably in the cortex,12 to a level that makes it undetectable. The early portion of the SVC or “silent period” is also reduced in Parkinson’s disease27 and schizophrenic patients treated with antidopaminergic neuroleptic medication.28 A natural mechanism inherent in the processes of functional recovery could have led to the same phenomenon being present in the patients with spinal cord injury. It is likely that such a process would involve axonal sprouting or changes in efficacy at the synaptic level.


The increased NAA/Cr ratio in the motor cortex of patients after incomplete spinal cord injury raises important questions. Can this be interpreted as an increase in absolute level of NAA? Firstly, Cr is often used as an internal marker29 and that its cortical levels are unchanged in brain conditions such as epilepsy.30 As no other metabolite ratios to Cr have altered in our study, an absolute increase in NAA level remains the most likely possibility.

Assuming that absolute NAA levels are raised in the motor cortex, can this be interpreted as a neuronal adaptation to spinal cord injury, reflecting, for example, cortical dendritic sprouting? Certainly NAA levels double during the first year of life compared with levels at birth, even though the number of neurons remains constant.18 This change is thought to reflect neuronal maturation, including dendritic sprouting and increases in synaptic connections. It is clearly consistent with the idea that patients with spinal cord injury undergo similar cortical changes as they recover useful function. NAA levels are also markedly raised in the childhood disorder Canavan’s disease.19 20 In the mature brain NAA is relatively decreased in many different types of cerebral pathology. Our finding of an increase of NAA/Cr in the adult brain is novel.

The interpretation of the increase in NAA/Cr as associated with neuronal adaptation to injury relies on the assumption that this change is due to an increase in NAA present in neurons. NAA is thought to be located in neurons in the adult brain, although it has been identified as occurring in oligodendrocyte type 2 astrocyte progenitor cells in the developing brain. However, such NAA containing progenitor cells have only been characterised in vitro and cannot be isolated from the mature brain in significant numbers.31 The NAA peak could be multicomponent, comprising predominantlyN-acetylaspartate, but also includingN-acetylaspartate glutamate (NAAG).32 It was not possible to distinguish between the various components in this study. However as NAA and NAAG are both found in neurons and neuronal processes in the mature brain it follows that an increase in either could reflect neuronal adaptation. Another factor to be considered is that changes in the NAA signal could result from alterations in NMR relaxation properties,16 but there was insufficient examination time in this study to measure T1 and T2.

If the increased NAA/Cr ratios do reflect a genuine increase in NAA then one would expect to see a similar increase in the ratio of aspartyl resonances of NAA to Cr (AspNAA). However, the signal to noise ratio when measuring the AspNAA peak is substantially lower than when measuring the NAA peak. This could mean that noise levels in the spectrum are masking any changes in AspNAA levels in the patient motor cortex. Indeed, examination of the data (table 2 and fig 5) shows marked variation in AspNAA/Cr ratios within each group.

Another possibility is that, despite the use of an inversion pulse to suppress the lipid signal, the increase in the NAA peak in the patient motor cortex could be the result of macromolecule (lipid) contribution in addition to NAA itself. However, it is hard to reconcile why such an artefact should have occurred only in the patient motor cortex. It is beyond the scope of this small pilot study to resolve this potential problem. However, future work is planned to establish the time course of the putative changes in NAA levels and these points will be considered at that time.

There is evidence that significant recovery of NAA can occur after acute brain damage. For example reversible decreases in NAA were found in two patients with mitochondrial encephalopathy and four patients with demyelinating lesions.33 It was suggested that this reflected reversible impairment of mitrochondrial function.33 In mitochondrial encephalopathy the primary defect is mitochondrial, and in demyelinating lesions mitochondrial dysfunction is probably secondary to inflammation. There is no reason to suggest that mitochondrial dysfunction occurs in the cortex as a result of spinal cord injury. Moreover, if it were the case that the NAA level reflects the number of functioning mitochondria, then our finding of a raised relative NAA level would not be inconsistent with the hypothesis that dendritic sprouting had occurred.

The difference in Cho/Cr ratios between the motor cortex and the occipital cortex in the control group is consistent with a previous finding of spatial variation of choline levels.34 It is of interest to note that in the patients there was no significant regional variation in choline between the motor and occipital cortices.

If the increased NAA/Cr ratio can be interpreted as reflecting neuronal adaptation to injury, what is the time course of this adaptation and how does it depend on rehabilitation factors such as physiotherapy and occupational therapy? Our finding of no significant correlation between the increased NAA/Cr ratio and the time since injury or the neurological status does not support a progressive change. However, we have studied the patients several months after injury (table 1) and it is conceivable that any change may have occurred earlier and then stabilised; as seems to be the case with the electrophysiological changes seen in our ongoing longitudinal study. Clearly, further study is required on a larger group of patients to look at serial changes of NAA/Cr, especially in the more acute stages close to the time of injury. To this end, we intend to study more patients using newly acquired single voxel analyses techniques and absolute quatification of metabolite levels.

From a clinical point of view these findings are of importance. If it is confirmed that an increase in NAA/Cr accompanies recovery from spinal injury, then MRS could provide a non-invasive method for monitoring such patients. Moreover, if it were to turn out that NAA/Cr increases at an early stage after injury, a possibility consistent with our results, then this would further increase the value of MRS as a prognostic investigative technique in this group of patients.


This work was supported by grants from the Medical Research Council and the Wellcome Trust. We thank Graeme Bydder, Serena Counsell, Joe Hajnal, Anne McCreath, and Nadeem Saeed for their advice and support with this project. We, express our warmest appreciation to all the subjects for their involvement in this study.


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