This study examined whether chronic neuropathic pain, modulated by a local anesthetic block, is associated with cortical magnetic field changes.
In a group of 20 patients with pain caused by unilateral traumatic peripheral nerve injury, a local block with lidocaine 1% was administered and the cortical effects were measured and compared with a control group. The global field power (GFP), describing distribution of cortical activation after median and ulnar nerve stimulation, was plotted and calculated. The effects on the affected hemisphere and the unaffected hemisphere (UH) before and after a block of the injured nerve were statistically evaluated.
Major differences based on the GFP curves, at a component between 50 ms - 90 ms (M70), were found in patients: in the affected hemisphere the M70 GFP peak values were statistically significantly larger in comparison with the UH, and the GFP curves differed morphologically. Interestingly, the mean UH responses were reduced in comparison with the control group, a finding suggesting that the UH is also part of the cortical changes. At M70, the GFP curves and values in the affected hemisphere were modulated by a local block of the median or the ulnar nerve. The most likely location of cortical adaptation is in the primary somatosensory cortex.
Cortical activation is enhanced in the affected hemisphere compared with the UH and is modulated by a local block. The UH in neuropathic pain changes as well. Evoked fields may offer an opportunity to monitor the effectiveness of treatments of neuropathic pain in humans.
What We Already Know about This Topic
Peripheral nerve injury leading to pain can cause neuroplasticity in the brain, although the extent and acute reversibility of these changes are relatively unexplored
What This Article Tells Us That Is New
Magnetoencephalography in 20 patients with unilateral peripheral nerve injury and pain compared to control demonstrated bilateral cortical changes which were acutely reversed by peripheral nerve block of the affected extremity
TRAUMATIC peripheral nerve injury (PNI) may produce a variety of symptoms including neuropathic pain, autonomic dysfunction, and disability.1–3Functionally, neuropathic pain may result from abnormal peripheral inputs and/or abnormal central processing.4–8The continuous volleys of ectopic afferent inputs produce central adaptive changes.9–16Neurophysiologic parameters that characterize these cortical changes range from peak latency differences to cortical map reorganization.17–20Anatomic changes caused by sprouting and growth into the deafferentiated area were found in animals after sensory loss of a forelimb.21,22In humans, electroencephalography studies showed functional changes in cortical evoked responses in amputees19,23–25after nerve injuries10,26,27and after stroke using magnetoencephalography.28After nerve injury in humans, cortical changes whereby recruitment from neighboring cortical areas occurred, also were reported.2,15,29–31
Nonetheless, central adaptations and sensitization in humans are difficult to demonstrate, and pain modulation at the cortical level is not well established.32–34
In this study, we hypothesized that the volley of impaired afferent information in the PNI group, as soon as it was interrupted by a local anesthetic block, would result in detectable cortical changes. Advances in magnetoencephalography, characterized by its accurate detection of fissural generators and undisturbed by reference activity, provides a better temporal resolution of the functional brain changes than functional magnetic resonance imaging (MRI). The aim of this study was to explore the cortical effects of local anesthesia at the site of the nerve injury and to test the reversibility of the functional cortical changes using magnetoencephalography. We compared the characteristics of the evoked cortical fields after electrical stimulation of the median and/or ulnar nerve in two groups: a group of healthy subjects and a group of patients with traumatic PNI in one upper extremity and the same patient group remeasured after local anesthesia in the pain-free condition.
Materials and Methods
The study was approved by the Medical Ethical Committee Alkmaar (NH04-196) and the VU Hospital Amsterdam. All healthy subjects and patients were adequately informed and gave their written consent. Twenty healthy subjects (13 males and 7 females, age range 27–48 yr, mean 34.1, SD ± 6.1 yr), all Caucasian and right-handed) were recruited from two hospital staffs. Twenty patients with a traumatic nerve injury and continuous pain were studied. Table 1presents demographic data of the PNI group. Although variation of the nerve injuries is observed, all were in pain.
The group consisted of 5 male and 15 female right-handed patients; age was between 22 and 69 yr (mean 48.3 and SD ± 14.7 yr). In all patients, neuropathic pain had been present between 1–25 yr (mean 5.4 SD ± 6.5 yr). In 13 of 20 patients, traumatic nerve injury was assessed during microsurgical repair, secondary neurolysis after a carpal tunnel syndrome (N = 2), after surgery for de Quervain syndrome and neuroma forming (N = 3) or after a metacarpal fracture (N = 2). Neuroanatomic damage varied from full nerve transection to digital nerve injury. In five patients after major nerve injury (A-1, A-3, A-4, A-6, A-11) partial paralysis or paresis was found; patient A3 also suffered from spasms. Mechanical allodynia was present in all patients, with change in severity prompted by the level of activity. Other sensory symptoms included hyperalgesia, hypoesthesia, and paraesthesia. All patients complained of a cold hand, particularly during severe pain. Trophic changes included hyperhidrosis. The diagnosis of complex regional pain syndrome is based on signs and symptoms.35,36At the time of the measurements in 5 of 20 patients, this syndrome was diagnosed. Patient A-7, who only had a radial branch injury after surgery for de Quervain syndrome, suffered from pain for 22 yr. Considerable edema, dystonia, and loss of function were intermittent symptoms. The verbal rating score before the measurements ranged from 4 to 9 (mean 7.0, SD ± 1.0); after the local block each patient had to be pain free. At the time of admission to the pain clinic, analgesics (nonopioids and opioids) and antiepileptic agents all had been used without good results. Patients randomly used different medications such as paracetamol and nonsteroidal antiinflammatory drugs and opioids such as tramadol or morphine. Three to 7 days before the measurements, patients were free of pain medication. No neurologic diseases were present and no medication was used that might bias cortical results (i.e. , antiepileptic agents).
In the subject group, the four possible stimulation sites of both hands received a number, the left median nerve a “1” and the left ulnar a “2,” for the right side “3” and “4” respectively. Stimulation order of the median or ulnar nerve was performed in a randomized way (i.e. , 4, 2, 1, 3 for subject HC-04) with a bipolar electrode at the wrist and the cathode placed proximally.37For patients, to avoid inducing additional pain, we stimulated the nerves parallel to the injured nerves, e.g. , after median/radial nerve injury the ulnar evoked responses were studied. Stimulation of the nerve parallel to the injured painful nerve is supported by experiments in squirrel monkeys and in human subjects where dominance of the adjacent intact nerve emerged cortically.38–40Subjects and patients were measured in the supine position under identical conditions, for a duration of approximately 45 min with the head well positioned in the helmet. Foam rubber and the position of the bed close to the helmet stabilized the head in the helmet without much space left to move, which might alter the position. A resting period between stimulation sessions of 5–10 min was ensured. An electrical nerve stimulator (Grass, model S48, Pegasus Scientific Inc., Rockville, MD) and photoelectric stimulus isolation unit (Grass, model SIU7) was used. The stimulation current was pulsed at a repetition rate of 2 Hz with a pulse duration of 0.2 ms. In 10 of 20 patients, median nerve stimulation and ulnar nerve stimulation were performed. Patients were measured three times: first, on the unaffected side, and then on the affected side before and after the administration of a local anesthetic block (2 ml lidocaine 1%) subcutaneously at the painful site (affected hemisphere [AH] block). Full pain alleviation was achieved in 16 of 20 patients after 15 min. In four patients, a fourth measurement was performed because full pain alleviation required a second block. A distinction was made between the AH and UH; the AH and UH correspond to the contralateral side of affected and unaffected extremity, respectively. Stimulus intensity threshold reached a 1.5-fold motor twitching level.41Five hundred stimuli were recorded from each nerve; after 100 stimuli the position of the head to the helmet was electronically reassessed for accuracy. The peristimulus interval was 50–100 ms pretrigger and 400 ms posttrigger. During measurements, subjects and patients were asked to ignore the stimuli and refrain from blinking as much as possible, to keep eyes open, and fixate on a point on the ceiling. Stimulations were tolerable for both groups during all measurements. Two patients were unable to maintain their position and were left out of the study.
A 151-channel whole-head magnetoencephalography system (VSM-CTF, Port Coquitlam, British Columbia, Canada) was used and measurements were performed in a three-layer magnetically shielded room (Vacuum Schmeltze GmbH, Hanau, Germany). The x, y, and z coordinate system, common to each individual magnetoencephalography and MRI, was based on three anatomic landmarks and fixed to nasion, left and right preauricular points. Using the positions of these fiducials, a head-centered coordinate frame was defined. The (+) axis was directed to the nose, the (+) y-axis to the left ear and the (+) axis to the vertex. Magnetoencephalographic signals were sampled at 1,250 Hz, triggered by the synchronization pulse of the electric stimulator. Online, filters were set at direct current for high pass and at 400 Hz (fourth order Butterworth filter - IMST GmbH, Kamp-Lintfort, Germany) for antialiasing low pass. Offline, the magnetoencephalographic data were screened for artifacts, averaged, and direct current-corrected using the pretrigger interval to determine the recording offset. Furthermore, ± averages were calculated to obtain noise level estimates. The raw data were visually inspected after data acquisition. Trials showing clear artifacts caused by eye blinks or by muscle activity, e.g. , due to swallowing, were removed from the dataset. MRI registration was performed with a 1.5-T 3-day MRI (Siemens Sonata, Erlangen, Germany).
Data Management and Statistical Analysis
This study was designed as an explorative study for the parameters that describe the cortical evoked differences between healthy subjects and PNI patients. Because no previous experimental and quantitative results as to the magnitude of the expected effects were available, a formal calculation of a prespecified power was not possible. Absence of an a priori power analysis indicates that negative statistical results have to be interpreted with caution because an existing difference may not be detected. Based on the low availability of PNI patients with continuing pain, groups of 20 subjects and patients were selected. Experimental design consisted in all cases of simple two-group comparisons. Statistical tests used were the independent groups Student t test (or its nonparametric equivalent the Mann–Whitney U test where appropriate) for between-groups comparisons, and the paired Student t test (or its nonparametric equivalent the Wilcoxon signed rank test where appropriate) for within-groups comparisons. A P value less than 0.05 was considered as a statistically significant rejection of the null-hypothesis specified with two-tailed alternative hypotheses. Effect sizes and P values are reported wherever relevant magnitudes of effects existed. Whereby:
The effect size (ES)42,43is a numeric way of expressing the strength or magnitude of a reported relationship, be it causal or not. An ES near 0.0 means that, on average, the experimental group and control group performed the same; a negative ES, on average, means that the control group performed better. A positive ES means that the experimental group performed better than the control group. The more effective the intervention the higher the positive ES value. Statistical analysis was performed using SigmaStat 3.5v software (Systat Software, Inc. Point Richmond, CA). Control for multiple testing was deemed unnecessary because in this explorative study no common hypothesis or theory covering two or more individual statistical tests was present. Control for the familywise error rate is important only when a conclusion based on several statistical tests is falsified, if at most one of the underlying tests is negative.44Given the clinical significance of our results and the likelihood of an increase of type II errors, control for the family wise error rate, i.e ., a Bonferroni correction, was not performed.45,46Only contralateral hemispherical activity was analyzed in this study for comparison of the subject and patient groups. A Compressed Waveform Profile (CWP), the butterfly-like display of the superimposed evoked responses of all sensors of all subjects and patients, was made. Of each subject and patient, the global field power (GFP) curves and peak values after nerve stimulation of each hand were plotted and calculated to identify power differences and changes after the blocks. The GFP (in femtoTesla2) was computed for each individual as the sum of squares over all channels, divided by the number of channels (N = 151). For magnetoencephalography, the GFP is a measure of the variability of the magnetic field energy distribution and reflects neuronal activity.47–49Together with the CWPs, peak stages and peak latencies were identified. Three stages were defined: an early (less than 50 ms), middle (50 ms-90 ms), and a late stage (90 ms-400 ms). Peaks in the poststimulus 400-ms time window, with clear dipolar somatosensory-evoked field activity, were selected as the cortical areas of interest for analysis. A peak was identified by visual inspection and defined by an amplification factor (= poststimulus amplitude/the prestimulus root mean square value as an indication of noise) >3. Peaks in each of these stages are presented as, i.e. , M20 for the peak around 20 ms, etc . Three-dimensional cortical maps were made for all subjects (left hemisphere and right hemisphere) and patients (UH, AH, and AH block) at different latencies. VSM - CTF software50was used to model the single equivalent current dipole (ECD) sources and Advanced Neuro Technology software (ANT A/S, Enschede, The Netherlands) for graphic display. The conventional single moving dipole analysis51was used for magnetoencephalographic data evaluation and based on individual MRIs.
In the subject and patient group and between the two groups, no significant threshold differences were found between the left and right hand for all stimulated nerves and for all conditions (P > 0.05 and ES values). For somatosensory-evoked field peak stages,the incidences and latencies of the peaks in the early, middle, and late stages for subjects and patients were assessed. The number of peaks demonstrated high consistency for both groups. Between the subject and patient groups, at M20, M30, and M70, no consistent significant latency differences were found that indicated facilitation of nerve transmission for patients (see Supplemental Digital Content 1, http://links.lww.com/ALN/A748, listing the number of peaks and peak latencies for both groups).
Characteristics of the CWP
The CWP morphologies of all subjects and patients, after median and ulnar nerve stimulation, demonstrated large interindividual variation but fewer intraindividual hemispherical differences. The CWPs of two patients are presented in figure 1, each from the median and ulnar group, and displayed different profiles. In patient A-10 (fig. 1A–C), the CWPs after median nerve stimulation of both hands before and after the anesthetic block of the affected hand are presented. After ulnar stimulation in patient A-1 (fig. 1D–F) a similar configuration was observed.
The effect of the anesthetic block on the amplitude (reduction) once the patient was pain free, is observed in the middle stage in both patients (fig. 1C and fig. 1F).
For the subject and patient groups, GFP plots were made of the 400-ms poststimulus time window. Results are depicted in figure 2. For subjects, LH Med denotes the mean left hemispherical GFP response after stimulation of the right median nerve, RH med the right hemispherical GFP response after left median nerve stimulation, etc . Figure 2Apresents the mean GFP overlay curves of the subject group after nerve stimulation. The top two curves (black and red) for the median nerve are morphologically slightly different; the same applies for the ulnar nerve (blue and green). The distribution (curves) of the power for both nerves in the entire time window is highly congruous with three distinct peaks in the first 90 ms: at M20, M30, and M70.
The morphology of the median and ulnar GFP curves (fig. 2BC, and) differed from the subject group. In the median group, the M20 and M30 peaks are part of a broad complex. In the middle stage the power in the AH is larger than in the UH, after the block the power decreases. In the ulnar group, small M20 and M30 peaks are present. At M70, AH power is larger than in the UH but after the block no difference is recognized. Strikingly in the first 90 ms poststimulus, for both the median and ulnar group,the GFP peaks in the AHs are higher, particularly between 50 ms - 90 ms compared with the UH. For subjects versus patients, for both patient groups the GFP peaks at M20 are hardly distinguishable but are lower compared with that of subjects. In the patient groups all the median and ulnar, M30, and M70 GFP peaks, especially in the UH, were lower compared with those of the subjects.
Patients: GFP after the Local Block (AH Block)
The GFP curves of the responses on the AH, AH block, and UH of patient A-10 after median nerve stimulation are depicted in figure 3A. In the middle stage, around the M70 peak, clear differences are visible. After a local block with 1–2 ml lidocaine 1%, magnetoencephalography was repeated in the pain-free state. As shown, there is a considerable reduction in GFP peak value (blue) of the AH block at 68.8 ms. The individual GFP profiles in patient A-1 (fig. 3B) after ulnar stimulation differ, and power changes are observed between 30–130 ms. After the block, a considerable GFP reduction for both peaks is observed. Most consistent finding after the block for the patient group were GFP changes during the middle stage.
GFP Values at M20, M30, and M70
Based on the GFP curves of each individual subject and patient, the peak values (fT2) were assessed. GFP data were statistically compared in and between the subject and patient groups (median and ulnar). At M20 in both groups, no statistical differences were found. In addition, no statistical differences comparing the LH and right hemisphere were found between the GFP values (in fT2) at M30 and M70 in the subject group (table 2). The ES data, the LH as dominant hemisphere taken as control in the equation, indicate that there is hardly any difference between the right hemisphere and LH. However, no complete homology of GFP values in healthy subjects for both nerves were found.
In the middle stage, the patient groups demonstrated a significant change. At M70, after median and ulnar nerve stimulation the AH values were significantly larger compared with the UH and AH block values for both nerves (table 3). After the block in the pain-free state, no statistical difference of GFP values between the UH and the AH block was found for both nerves (P > 0.05). Effect size data support these findings and accentuate the effectiveness of the block.
Subjects versus Patients.
Statistical analysis of the individual GFP data between both groups and for both hemispheres demonstrated no significant differences at M20. Table 4presents the M30 and M70 GFP values, statistical differences, and ES data for both groups.
These data support the morphology of the GFP curves in figure 2where in the patient groups, the M30 and M70 peaks were lower compared with those of subjects. For both patient groups, significantly lower GFP values of the UH at M30 and M70, in comparison to that of subjects, is demonstrated. In conclusion, significant power changes in the patient groups were found at M70 before and after the block. In contrast, between subjects and patients at M30 and M70, significant statistical power differences occur.
Three-dimensional Topography of Somatosensory-evoked Fields
Three-dimensional cortical maps were made for all subjects and patients at all major peak latencies (see Supplemental Digital Content 2, http://links.lww.com/ALN/A749, and Supplemental Digital Content and 3, http://links.lww.com/ALN/A750, presenting Median and Ulnar brain maps, respectively for two patients). In the Subject group and patient groups, the first (M20/M30) polarity reversal for both nerves was highly consistently found (more than 90–95%). The second polarity reversal in the subject group was present between M90 - M180 (more than 90%). In the patient group for all three stages and for both nerves, the second reversal differed and ranged from no to even three reversals (from M50 to M180). In the middle stage, reversals occurred several times. In the late stage (M90, M150, and M180), no second reversal between 20–80% for both nerves was present, which indicates wide variation.
At M20 and M30, for the median and ulnar nerve, after mirroring the dipoles to the same hemisphere, only the ulnar nerve ECD at M20 demonstrated a significantly different x-value interhemispherically. In the LH, the ulnar ECD was positioned more posterior (P = 0.013). The M70 ECDs in the subject groups with a low residual error (less than 6%) for both nerves present in 12–14 of 20were located in the contralateral primary somatosensory cortex. For patients, statistical analysis of M20 and M30 dipole parameters did not show any significant difference. At M70, only those ECDs with a low residual error (less than 6%) for all stages (before and after block) were studied.
Figure 4 Apresents four measurements of patient A-8 after median nerve stimulation. Patient A-8 is an example of the 4 of 20 patients (see Materials) in whom a second anesthetic block was needed. The red curve depicts the GFP curve of the patient in pain. After the first block, pain was hardly present but the injured hand felt painfully cold (green curve). The GFP peaks at M30 and M70 after the first block are relatively the highest. After the second block (black curve), the AH M30 GFP peak value decreases and is comparable to the UH M30 peak (UH = 16198.2 fT2, AH second block = 15525.7 fT2). In the full pain-free state, the UH (blue curve) and AH-second block (black) peaks at M30 and M70 are morphologically nearly identical. In the late stage (more than 90 ms), changes are relatively low.
Figures 4B and Cpresent a one-dimensional image of the MRI of patient A-8 with all four dipoles projected over both hemispheres at M30 and M70, respectively. The UH dipole at M30 and M70 is depicted in blue, and the AH dipoles in red. The dipole depicting the first block is green and yellow after the second block. Both at M30 and M70, the UH dipole is located more anterior, lateral, and inferior compared to all AH stages. The spatial data of the M30 and M70 dipoles in the AHs indicate that the dipoles hardly changed their positions (table 5). Combining the dipole localizations in figure 4Cwith the two other three-dimensional spatial images (coronal, sagittal) indicates that M70 activity is localized in the primary somatosensory cortex (see Supplemental Digital Content 4, http://links.lww.com/ALN/A751, presenting a 3-dimensional overview of the M70 dipole characteristics of patient A-8). After selection, in 6 of 10 patients (median nerve) and 5 of 10 (ulnar nerve) with a low residual error (less than 6%), the dipoles were compared with those of subjects, also located in the primary somatosensory cortex. In 9 of 20 patients M70 dipoles were not included because modeling with a single moving dipole was not possible or for reasons related to residual error (more than 6%). Combining subjects and patient data at M70, no significant statistical differences were found.
Cortical plasticity has been defined as the central nervous system's ability to adapt to environmental challenges or compensate for lesions.52,53Plasticity resulted in an enhancement of cortical activity after nerve injury or amputation in humans29–31,54or a shrinkage of the somatosensory hand representation in complex regional pain syndrome I.55Before the current study, stability and repeatability of the cortical evoked responses after median, ulnar, and posterior tibial nerve stimulation was assessed in subjects and PNI patients.56,57In this study, magnetic evoked responses in and between subjects and PNI patients were compared, before and after an anesthetic block. The GFP curves, presenting cortical activation in the subject and patient groups, differed morphologically and indicated: decreased cortical activity in the UH of both patient groups compared with the AH and AH block phase; and decreased cortical activity in patients in the AH, AH block but in particular in the UH compared with subjects. These findings are consistent with the interpretation that smaller or larger GFPs correspond to smaller or larger neural areas of activation. Therefore, our results suggest that in unilateral nerve injury of an upper extremity and continuous pain, both hemispheres are involved in cortical adaptations and hemispheric differences have to be compared with a healthy control group. The UH cannot simply serve as control to the AH. This is consistent with the observation that deafferentation in a body part elicits reorganizational changes in the sensorimotor cortex in both the contralateral and ipsilateral hemisphere.58Bilateral cortical reorganizational changes have been described after acute limb deafferentation52and in patients with nonpainful phantom limb phenomena after upper extremity amputation.25The mechanisms underlying these functional changes in both hemispheres were ascribed to changes in inhibitory transcallosal transmission.52In the patient groups, significant power changes occurred in the middle stage around M70 after the anesthetic block. In absence of the constant volley of impaired afferent information in patients with chronic neuropathic pain, central functional processes were reversible within 15 min even after years of chronic pain. At M70 after the anesthetic block and in the pain-free condition, the significant differences in GFP values between the UH and AH disappeared, a noteworthy finding. The high GFP response in patient A-8 after the first block (fig. 4A–green curve) is very interesting because it may reflect the cortical effects of sympathetic involvement in neuropathic pain.59
Because there were no significant stimulation threshold differences in both groups after standard electrical median and ulnar nerve stimulation at all stages of the measurements, threshold differences did not contribute to the cortical evoked magnetic responses. The CWP interindividual and intraindividual morphology differences of subjects and patients are supported by previous work.56,60–62CWP morphology and GFP curves indicated that the peak latencies and number of peaks of the subject and patient groups were highly consistent in the first 90 ms poststimulus period. Altered temporal processing of afferent information (facilitation) in this group of pain patients could not be demonstrated. Polarity reversals of the three-dimensional brain maps mainly reflect change in dipole orientation and are an indication of spatial somatosensory processing. The first and second polarity reversals, consistently seen in the three-dimensional maps in subjects and described earlier,63differed in the two groups. The significance of the finding is that in the patient group both reversals were less consistently observed and moreover at different latencies is yet unknown. It may, however, indicate altered cortical processing in the patients. These findings in patients are in agreement with experimental changes described in brain maps due to PNI in animals.9,30,64,65
Dipole parameters at M20 and M30 indicated that there were few differences between subjects and patients at these latencies. The difference between the two hemispheres at M20 for the ulnar nerve in subjects (the ulnar M20 in the LH more posterior) was not found in patients. This was in contrast with a small magnetoencephalographic study where in a group of three patients after median or ulnar transection enlarged dipole moments were found between the unaffected and affected side.66For all patients after median and ulnar nerve stimulation, the M70 dipoles with a low residual error (less than 6%) before and after the anesthetic block were located in the contralateral primary somatosensory cortex. The latency and position of these dipoles are in agreement with earlier studies on somatosensory processing in healthy subjects.67–70At M70, no bilateral hemispherical dipolar activity was found in the current study after unilateral electrical stimulation but occurred later (more than 90 ms poststimulus). This finding is in agreement with other magnetoencephalographic studies71,72and excludes involvement of the second somatosensory cortex.73,74Finally, cortical interhemispheric differences after electrical nerve stimulation were quite symmetrical in the two hemispheres, making the interhemispheric differences nondependent on age and sex.75,76
We conclude that in patients with neuropathic pain caused by nerve injury, major cortical changes measured by magnetoencephalography at M70 reside in the primary somatosensory cortex and may represent altered activation in the affected but also unaffected hemisphere after peripheral median and ulnar nerve stimulation. The functional cortical changes in neuropathic pain, after the modulatory effects of an anesthetic block, were found to be reversible. In these patients, an anesthetic block can valuable for the study of contralateral activation in neuropathic pain using magnetoencephalography. PNI with neuropathic pain in humans, studied with noninvasive diagnostic devices, may provide a pain model to study and monitor the effects of treatments.
Technical support was provided by Bob W. van Dijk, Ph.D., and Kees Stam, Ph.D., Professor and Head, Department of Clinical Neurophysiology and MEG Centre, VU Hospital, Amsterdam, The Netherlands. Clinical support provided by Monique A. Dekkers, M.Sc., Medical Centre Alkmaar, Alkmaar, The Netherlands.