Methods  High-resolution volumetric T1-weighted images and magnetization transfer images were acquired from 30 patients (29 with first-episode schizophrenia and 1 with schizophreniform psychoses) and 30 control subjects. Images were processed using voxel-based morphometry, which allows whole-brain analysis.

Results  Compared with controls, the magnetization transfer ratio (an index of signal loss derived from magnetization transfer imaging) was reduced bilaterally in the medial prefrontal cortex (right greater than left), insula (left greater than right), and white matter incorporating the fasciculus uncinatus (left greater than right) in the patient group. Analysis of the T1-weighted images did not reveal significant volumetric differences between patients and controls.

Conclusions  Gray and white matter abnormalities are present in schizophrenia at illness onset. The magnetization transfer ratio is sensitive to these abnormalities, which cannot be explained by detectable atrophy in our patient group.

Recently, attention has focused on first-episode schizophrenia, in which detectable brain abnormalities are more likely to reflect the primary disease process, diminishing confounds such as medication exposure and chronicity. In their review, Shenton et al¹ concluded that abnormalities described in patients with first-episode schizophrenia were similar to those in chronic schizophrenia populations. Reduced gray matter volume,^11-12 increased ventricular volumes,^13-14 and temporolimbic abnormalities^15-16 are the most commonly reported abnormalities in first-episode schizophrenia. Hippocampus volume reduction has been considered one of the most consistent structural abnormalities in schizophrenia, and it may be present at illness onset.¹⁷ Perhaps because early structural changes may be subtle and patients with first-episode schizophrenia are more likely to have variable disease outcomes, some such studies have not found significant volumetric abnormalities for ventricles and temporal lobes,¹⁸ regional or total hemisphere volumes,¹⁹ and the hippocampus or parahippocampal gyrus.^20-21 Although high-resolution imaging continues to improve sensitivity with progressively decreasing slice thickness, the limitations of volumetric MRI include lack of neuropathological specificity and poor sensitivity to subtle neuropathological changes that may not culminate in atrophy. In schizophrenia neuroimaging, the enhanced sensitivity and neuropathological specificity of magnetization transfer imaging (MTI) offers considerable advantages.

First described by Wolff and Balaban,²² MTI is based on the interaction of protons bound to macromolecular structures and free protons in tissue water. In brain tissue, the major macromolecules in the bound proton pool are thought to be cell membrane proteins and phospholipids in gray matter and myelin in white matter. Bound protons are preferentially saturated using an off-resonance radiofrequency pulse. Chemical exchange or direct dipolar coupling transfers macromolecular saturation from bound to free protons, causing decreased longitudinal magnetization undetected by conventional MRI because bound protons have short relaxation times in biological tissues. The reduction in signal intensity depends on macromolecular density. The nature of the interaction sites has yet to be fully determined.²³ However, creatine-containing compounds seem to be involved in through-space dipolar interactions to a greater extent than glutamine/glutamate, N-acetylaspartate, and lactate, whereas chemical interaction may be more important for the latter.²⁴ The degree of signal loss, measured in percentage units, is the magnetization transfer ratio (MTR).

An MTR reduction correlates with myelin and axonal loss in postmortem tissue from the spinal cord²⁵ and brain²⁶ in multiple sclerosis, experimental allergic encephalitis,²⁷ toxic demyelination,²⁸ wallerian degeneration,²⁹ and experimental brain injury.³⁰ In vivo white matter MTR decreases occur in conditions with myelin or axonal loss, for example, multiple sclerosis,³¹ central pontine myelinolysis,³² cerebral ischemia,³³ systemic lupus,³⁴ human immunodeficiency virus infection,³⁵ and traumatic brain injury.³⁶ Gray matter abnormalities have been studied less extensively, but wallerian degeneration triggered by distant axonal damage and microscopic lesions are thought to explain cortical MTR reductions in multiple sclerosis.³⁷ The first study to use MTI in chronic schizophrenia³⁸ reported widespread cortical MTR reductions indicative of subtle structural abnormalities, which may reflect reported changes in dendritic density.³⁹

To the best of our knowledge, this study is the first application of MTI to the investigation of patients with first-episode schizophrenia, whom we compared with healthy volunteers using the MTR, an index of signal loss derived from MTIs. We also acquired high-resolution volumetric images to assess for atrophy. Voxel-based morphometric (VBM) analysis was used to study group differences using both types of imaging because VBM reduces observer bias and allows whole-brain analysis. Our hypothesis was that frontotemporal abnormalities would be detectable by the time patients first present to medical attention. Based on findings in chronic schizophrenia,³⁸ we further predicted that the MTR would be more sensitive to these abnormalities than conventional T1-weighted volumetric imaging.

METHODS

Thirty patients (19 were men and 3 were left-handed) with a mean age of 27.3 years (range, 18-47 years) were examined. The catchment area included deprived inner city and affluent suburban areas of London. Patients were recruited as soon as possible after first presenting to mental health services with schizophreniform psychosis (DSM-IV). Diagnostic criteria were reviewed by 2 experienced clinicians (E.M.J.) 1 year after recruitment to establish a diagnosis of schizophrenia. One patient was lost to follow-up before this diagnostic review. Antipsychotic medications included olanzapine, risperidone, sulpiride, haloperidol, and zuclopenthixol (19 patients used atypical agents, 6 used typical agents, and 5 were unmedicated). Symptom severity was assessed using the Scale for the Assessment of Negative Symptoms, the Scale for the Assessment of Positive Symptoms,⁴⁰ and the Comprehensive Psychopathological Rating Scale.⁴¹ We also determined handedness⁴² and parental social class⁴³ and estimated premorbid IQ using the National Adult Reading Test.⁴⁴ Table 1 summarizes demographic and clinical indices.

View this table: [in this window] [in a new window] Table 1. Demographic and Clinical Data for 60 Study Participants

Thirty healthy volunteers (18 were men and 2 were left-handed) with a mean age of 28.9 years (range, 21-49 years) were recruited to match the patient group for age, sex, handedness, and estimated premorbid IQ. Controls with a history of neurological or systemic illness, head injury, substance abuse, or alcohol intake greater than 240 g/wk were excluded. Controls with a personal or family history of psychiatric illness were also excluded. Permission to conduct the study was obtained from all relevant research ethics committees. Written informed consent was obtained from all participants. A neuroradiologist reviewed the brain MRIs. No gross abnormalities were reported.

MAGNETIC RESONANCE IMAGING

Participants underwent MRI using a 1.5-tesla scanner (Signa; GE Medical Systems, Waukesha, Wis) with a standard quadrature head coil. Total scanning time (including sequences not reported herein) was 60 minutes. A preliminary sagittal localizing scan was acquired. High-resolution coronal volumetric images were acquired using a 3-dimensional T1-weighted spoiled gradient recalled echo (SPGR) sequence generating 124 contiguous, 1.5-mm coronal slices (echo time, 4.2 milliseconds; repetition time, 15 milliseconds; field of view, 24 cm²; 256 x 192 matrix; and flip angle, 20°). The 1.0 x 1.2 x 1.5-mm acquisition parameters were determined by scan time constraints and were automatically reconstructed by the scanner to a 1.0 x 1.0 x 1.5-mm voxel size. Axial MTIs were acquired using a dual spin-echo–based MTI sequence (echo time, 30/80 milliseconds; repetition time, 1720 milliseconds; 28 contiguous 5-mm axial slices; 256 x 128 pixel image matrix; and field of view, 24 cm²) with and without a saturation pulse (16 milliseconds, 23.2-µT Hamming appodised 3 lobe sinc pulse applied 1 kHz from water resonance). The 1 x 2 x 5-mm MTI acquisition parameters were determined by scan time constraints. The scanner automatically reconstructed images to a 1 x 1 x 5-mm voxel size. The MTI sequence described in detail by Barker et al⁴⁵ generates proton-density and T2-weighted images along with MT-weighted images. These images are all inherently registered to each other and to the calculated MTR image created from proton-density and MT-weighted images. The MTR is an index of signal loss in percentage units, calculated on a pixel-by-pixel basis from the following formula:

MTR = [(M_o - M_s)/M_o] x 100,

where M_s and M_o are mean signal intensities with and without the saturation pulse, respectively. The MTR is not calculated in voxels if values in source images are below the mean background noise level. We used the 30-millisecond echo for MTR calculation because the resulting map has a higher signal-to-noise ratio than that from the 80-millisecond echo. Typical MTR values are 30% to 50% for white matter, 20% to 40% for gray matter, and approaching 0% for cerebrospinal fluid. For our sequence, MTR values were approximately 40% for white matter, 35% for subcortical gray matter, 32% for cortical gray matter, and 2% for cerebrospinal fluid.

IMAGE PROCESSING

Data were processed on a computer workstation (Sun Ultra; Sun Microsystems Inc, Santa Clara, Calif) using SPM99 statistical parametric mapping software (Wellcome Department of Cognitive Neurology, London) and working in an analysis environment (MATLAB; The MathWorks Inc, Natick, Mass), unless otherwise stated.

SPOILED GRADIENT RECALLED ECHO

Images were reoriented into axial slices aligned parallel to the anteroposterior commissural axis. The origin was set to the anterior commissure. Images were spatially normalized to the standard T1 template in SPM99, following a method that optimizes segmentation accuracy for VBM described by Good et al.⁴⁶ Affine registration (12 nonlinear iterations, medium nonlinear regularization, resliced to 2 x 2 x 2-mm voxels) produced isotropic voxels of higher signal-to-noise ratio than the original images. The images were flipped to neurological space and then segmented using image intensity nonuniformity correction. A mixture model cluster analysis identifies voxel intensities matching tissue types (gray matter, white matter, and cerebrospinal fluid) combined with a priori knowledge of the spatial distribution of these tissues derived from probability maps.⁴⁷ Gray and white matter segments were extracted to remove nonbrain voxels and then underwent nonlinear normalization to the gray-and-white image template in SPM99 using 7 x 8 x 7 basis functions, 12 nonlinear iterations, and medium nonlinear regularization. The resulting images were segmented, producing gray matter, white matter, and cerebrospinal fluid tissue maps in Montreal Neurological Institute (MNI) space having excluded nonbrain voxels. Optimized methods, as described by Good et al,⁴⁶ were used to incorporate information from the deformation fields using a modulation step to preserve within-voxel volumes that may have been altered during nonlinear normalization. Voxel values in segmented images were multiplied by Jacobian determinants, derived from spatial normalization, to provide intensity correction for the induced regional volumetric changes. Analysis of modulated data tests for regional differences in absolute tissue volume. Unmodulated data analysis is a complementary test for regional differences in tissue concentration per unit volume based on differences in image intensity.^46-48

MAGNETIZATION TRANSFER RATIO

Axial images were acquired parallel to the anteroposterior commissural axis. Spatial normalization involved registration of the T2-weighted images, which are implicitly registered (from acquisition) to the MTR images, into standard space. This inherent coregistration of an MTR image and a T2-weighted image allows us to apply registration parameters determined from T2-weighted images (whose contrast matches the MNI template) to MTR images (for which no template is available). The registration used a modified algorithm for 3-dimensional alignment of positron emission tomographic images, relying on anatomic information to align 2 images by calculating the least squares difference of the 2 images on a voxel-by-voxel basis and iteratively moving the images relative to one another to minimize this cost function.^49-50 The T2-weighted images were registered to the MNI T2-weighted average brain in SPM99 using affine 12-parameter, 3-dimensional linear transformations through a 2-stage process. For each participant, a transformation was first found between the T2-weighted image and the MNI T2-weighted average brain, retaining all tissue within the image (brain parenchyma, skull, scalp muscle and fat, and other extracranial tissue). Although reasonably robust, the registration is potentially susceptible to motion artifacts of brain relative to surrounding tissue. To overcome this, the inverse of the transformation found was applied to a version of the MNI T2-weighted average brain from which the skull had been removed. This transformed the skull-stripped MNI template to the native image space of the particular participant, allowing it to be used as a mask to remove nonbrain tissue from the individual participant's T2-weighted image. Each skull-stripped T2-weighted image thus created was then registered to the skull-stripped T2-weighted MNI atlas, transforming it into MNI space. As mask and T2-weighted images have now been skull stripped, this second registration is much more robust. This final transformation was then applied to the participant's MTR image, mapping it into MNI space. Nonbrain features were removed by masking with the skull-stripped T2-weighted MNI average brain. Thus, MTR images were normalized to MNI space but were not subjected to warping or segmentation. Resolution of voxel size of 1 x 1 x 5 mm was maintained for MTR images because, unlike SPGR data, resampling 1 x 1 x 5-mm MTR images to a 2 x 2 x 2-mm isotropic voxel size would have produced only a small increase in signal-to-noise ratio. To determine whether MTR changes were in gray or white matter, we overlaid MTR decreases in patients onto thresholded a priori gray and white matter probability maps provided with SPM99 using the "write filtered" function. A threshold of 16384 (50% of 32768, the intensity representing a probability of 1 in the images) on the white matter map was chosen to identify areas having a greater than 50% probability of being in white matter rather than gray matter.³⁸

SMOOTHING

Taking account of voxel size and the size of structures within which abnormalities were predicted, images were smoothed to 15 mm (MTR) and 12 mm (SPGR) using a full-width–half-maximum Gaussian filter to improve the signal-to-noise ratio, allow for intersubject anatomical variability, and render the data more normally distributed by the central limit theorem. The probability distributions used in SPM99 for voxel and cluster analysis are approximations, which are valid within certain limits, especially with respect to smoothness and number of images. Low smoothing (full-width–half-maximum <3 times voxel size) with low df can cause aberrant voxel-level results. Consequently, smoothing of 3 times voxel size is recommended.^51-52 Accordingly, we selected 15-mm full-width–half-maximum smoothing for MTR (3 times voxel size). This relatively high degree of smoothing also helped overcome problems due to the multislice nature of the MTR, which reduced the accuracy of data reconstruction in the slice direction during normalization. For SPGR data, we selected 12-mm full-width–half-maximum smoothing, the spatial scale at which the analysis is most sensitive to differences in regional gray matter. This spatial scale also allows comparison with previous SPM99 voxel-based studies in chronic schizophrenia.^53-55 Each voxel in the smoothed data represents a locally weighted average intensity from a region of surrounding voxels defined by the size of the smoothing kernel.

STATISTICAL ANALYSIS

Group comparisons for MTR (whole brain) and SPGR (both gray matter and white matter maps) between patients with first-episode schizophrenia and controls were performed based on the general linear model and the theory of Gaussian random fields⁵⁶ using 2-sample t tests to compare populations with 1 scan per participant. Thresholds for MTR and SPGR data were set at 40% of mean image intensity to minimize low signal-to-noise voxels. Only voxels exceeding this intensity threshold (40% of mean image intensity) were included in the analyses. As calculation of mean intensity includes all the (very-low-intensity) pixels outside the head, the cutoff value of 40% of this value should not exclude any pixels that are fully brain tissue. This procedure excluded noise areas outside the brain or in the ventricles. Proportional scaling was used to normalize image intensity in SPGR gray and white matter maps. Using 2 contrasts, the analysis detected whether each voxel had a greater or lesser probability of change, that is, a reduction or increase in the parameter of interest in patients with first-episode schizophrenia compared with controls. The resulting set of voxel values for each contrast constitutes a statistical parametric map of the t statistic.

This study was a structural VBM analysis, and, consequently, we selected a study threshold of t>3.24 (P<.001, uncorrected). Statistical parametric mapping was originally designed to analyze functional data, and correction for multiple comparisons can be considered overly conservative when applied to structural data.⁵⁷ We validated our analysis parameters by dividing the control subjects into 2 subgroups matched for age, handedness, and sex. At the threshold of t>3.24 (P<.001, uncorrected), there were no voxel-level differences in the MTR or SPGR (gray and white matter) between the 2 subgroups of controls, suggesting that this threshold minimizes false positives.

We also report cluster-level statistics for the MTR. Data histograms in a large single-slice region of interest (ROI) incorporating gray and white matter resembled a Gaussian distribution. This satisfies suggested criteria for using cluster size to assess significance in SPM99, considered appropriate only if data are normally distributed.⁴⁷ This was not the case for SPGR segmented gray and white matter data. Consequently, we used only voxel-level thresholds for SPGR analysis.

RESULTS

SPGR GROUP DIFFERENCES

Neither modulated (optimized) nor unmodulated (standard) SPGR T1-weighted gray matter and white matter maps revealed any significant differences between patients and controls for voxel-level statistics at a threshold of t = 3.24 (P<.001, uncorrected). Thus, regional atrophy was not detected because we did not demonstrate any significant regional differences in absolute tissue volume or tissue concentration per unit of volume of gray or white matter in patients with first-episode schizophrenia compared with matched controls.

MTR GROUP DIFFERENCES

At the study statistical threshold of t>3.24 (P<.001, uncorrected), the MTR was reduced bilaterally in patients with first-episode schizophrenia compared with controls in the insula and adjacent white matter incorporating the fasciculus uncinatus, the right anteromedial frontal lobe extending into the anterior cingulate bilaterally, the right inferior and superior temporal gyrus, the left precuneus, and the left cerebellum (Figure 1, Figure 2, and Figure 3 and Table 2). Using the segmented white matter map, we ascertained that the MTR decreases were predominantly cortical, extending into white matter adjacent to the insula, encompassing the fasciculus uncinatus. To exclude the possibility that these were chance findings (type I error), a further analysis was undertaken correcting for multiple comparisons using Gaussian random fields (t>4.61; P<.05, corrected). Reductions in the MTR in the right medial prefrontal cortex, left insular cortex, and left fasciculus uncinatus survived this correction (Table 2). No MTR increases were observed in patients compared with controls at a threshold of t>3.24 (P<.001, uncorrected).

View larger version (42K): [in this window] [in a new window] Figure 1. Glass brain image of magnetization transfer ratio reductions in patients with first-episode schizophrenia vs controls. Arrowheads indicate peak voxel. SPM indicates statistical parametric map. Height threshold: t = 3.24; P = .001.

View larger version (77K): [in this window] [in a new window] Figure 2. Magnetization transfer ratio reductions in patients with first-episode schizophrenia vs controls (peak voxel in the left insula) demonstrating bilateral reductions in the insula and subcortical white matter rendered onto a T1-weighted image (threshold t = 3.97).

View larger version (77K): [in this window] [in a new window] Figure 3. Magnetization transfer ratio reductions in patients with first-episode schizophrenia vs controls (peak voxel in the right prefrontal cortex) demonstrating bilateral (right greater than left) reductions rendered onto a T1-weighted image (threshold t = 3.97).

View this table: [in this window] [in a new window] Table 2. SPM Statistics of Relative Regional MTR Decreases in 30 Patients* With First-Episode Schizophrenia vs 30 Controls

We conducted a post hoc validation study to confirm the SPM99 findings using ROI methods in native-space MTR images. Rectangular ROIs (37.9 mm²) were placed in the medial prefrontal cortex and insula using a standardized protocol in a sample of 8 male, right-handed patients with first-episode schizophrenia and age-, handedness-, and sex-matched controls using DispImage⁵⁹ software. Axial proton-density slices were used to identify the lowest slice in which the head of the caudate was visible. Bilateral ROIs were placed in the medial prefrontal cortex, adjacent to the interhemispheric fissure, midway between the frontal pole and the anterior margin of the head of the caudate. Similarly, bilateral ROIs were also placed in the long gyrus of the insula in the adjacent slice. Proton-density images were coregistered to MTR images during acquisition, as previously described. The ROIs were automatically transferred to the coregistered MTR image using DispImage. Care was taken to avoid partial volume effects. The ROIs were placed masked to participant identity. Decreased MTRs were found using Mann-Whitney tests in the right prefrontal cortex and insula (bilaterally) that are consistent with the SPM99 analysis (Table 3).

View this table: [in this window] [in a new window] Table 3. Post hoc Region of Interest Analysis of MTRs in the Prefrontal Cortex and Insula in a Sample of 8 Male, Right-handed Patients With First-Episode Schizophrenia and 8 Matched Control Subjects Using Native-Space MTR Images*

COMMENT

The anteromedial prefrontal cortex in schizophrenia has received little attention, although results of animal studies⁶⁰ suggest that it may be relevant. Voxel-based studies in chronic schizophrenia have demonstrated anteromedial prefrontal cortex gray matter reductions in some^{55, 61-62} but not all⁵⁴ of a small number of studies. Region of interest studies have been complicated by methodological differences, with few studies evaluating frontal lobe subregions. In a study⁶³ of patients with chronic schizophrenia and neocortex segmented into 48 topographic regions, the greatest volumetric reductions were in medial and orbitoprefrontal cortices, anterior cingulate gyrus, paracingulate gyrus, and insula. Anterior prefrontal cortex has been associated with monitoring of self-generated information and selection of appropriate executive processes, playing a central role in mediating dorsolateral and ventrolateral prefrontal cortical interaction.⁶⁴ Impairment in anteromedial prefrontal regions may contribute to some of the cognitive deficits in schizophrenia.

The anterior cingulate may be relevant to several psychiatric disorders having connections with the hippocampus, orbitofrontal cortex, and amygdala. In schizophrenia, abnormalities in the anterior cingulate include increased glutamatergic axons,⁶⁵ axospinous synapses,⁶⁶ decreased inhibitory interneurons,⁶⁷ and projection neuron loss in deeper laminae.⁶⁸ Anterior cingulate volume reductions have been reported in first-episode¹⁶ and chronic^{61, 63} schizophrenia. Functional imaging data suggest that anterior cingulate cortex may be essential for the internal monitoring necessary to engage top-down attentional processes in adapting to a changing environment.^69-70 Disruption of cingulate-striate circuits has been associated with apathy and a lack of drive,⁷¹ characteristic negative symptoms of schizophrenia.

Recent studies have found decreased insular volume in first-episode¹⁶ and chronic^{54, 61} schizophrenia. Functional imaging studies^72-73 have reported reduced cerebral blood flow in insular cortex during verbal fluency and recognition memory tasks. The insula may also have a pivotal role in cognitive and emotional processes, permitting the internal representation of external events,^74-75 and in the differentiation of internally and externally generated sensory stimuli.⁷⁶ Impairment of these processes may mediate some perceptual disturbances in schizophrenia.

Abnormalities in the fasciculus uncinatus replicate findings from a recent study⁶¹ of patients with schizophrenia and predominantly negative symptoms. The fasciculus uncinatus is a bundle of association fibers connecting orbitofrontal, superofrontal, and middle frontal gyri with anterior temporal lobe cortex, and it may play an important role in schizophrenia. It contains the lateral cholinergic pathway originating in the nucleus basalis of Meynert and innervates frontal, parietal, and temporal neocortex.⁷⁷ Cortical cholinergic pathways are important mediators in processing information essential for cognition.⁷⁸ Fasciculus uncinatus abnormalities may explain the reduced postsynaptic prefrontal muscarinic receptor binding recently reported in schizophrenia.⁷⁹ Right frontotemporal disconnection after injury to the right ventral frontal lobe and underlying fasciculus uncinatus leads to impaired awareness of self over time, which is integral to the formulation and implementation of future goals.⁸⁰

White matter abnormalities may be relevant in schizophrenia. Schizophrenialike symptoms occur in metachromatic leukodystrophy,⁸¹ and recent diffusion imaging studies have reported reduced anisotropy in prefrontal white matter^82-83 and corpus callosum,⁸⁴ suggesting myelin or axonal abnormalities. Differential expression of myelination-related genes in dorsolateral prefrontal cortex,⁸⁵ apoptosis, and necrosis of oligodendroglial cells and damaged myelin sheaths in prefrontal cortex and caudate nucleus have been reported in schizophrenia.⁸⁶ Myelination of frontotemporal connections continues into early adulthood.⁸⁷ Delayed or abnormal frontotemporal myelination in schizophrenia could explain the onset of symptoms in early adulthood.

We did not demonstrate atrophy. Our volumetric findings are contrary to those of some studies demonstrating decreases in medial temporal lobe structures, particularly the hippocampus,^{17, 88-89} superior temporal gyrus,⁹⁰ insula,¹⁶ and prefrontal cortex⁵⁴ in first-episode schizophrenia. This may reflect the heterogeneity of first-episode schizophrenia populations, which include patients with variable disease outcomes. However, there is considerable variance in image intensity in small medial temporal lobe structures, and some subcortical gray matter structures have image intensities similar to white matter, increasing risk of tissue misclassification during segmentation in these regions. Partial volume effects may have contributed, as the model assumes that all voxels contain only 1 tissue type, and those containing more than 1 may be modeled incorrectly. Accordingly, ROI methods may be more sensitive in such subcortical structures. These methodological problems, however, are unlikely to account for our findings for several reasons. First, the normalization and segmentation procedures used in SPM99 have been considered robust and accurate for volumetric T1-weighted images.⁴⁷ Second, gray matter losses have been reported in cortical and subcortical gray matter in patients with chronic schizophrenia and other conditions using similar analysis methods.^{38, 55, 91-93} Third, we excluded nonbrain voxels and used a modulation step that allows comparison of absolute amounts of gray matter. Finally, despite normal findings in volumetric imaging, MTR abnormalities were detected in regions where volumetric deficits have been reported in chronic and first-episode studies.

The discrepancy between circumscribed MTR abnormalities in first-episode schizophrenia reported herein and the more widespread abnormalities previously reported in chronic schizophrenia by Foong et al³⁸ deserve comment. There are 2 possible explanations. The first assumes that any brain abnormalities in schizophrenia are static and that widespread cortical abnormalities occur only in those with severe, chronic disease. If this model is correct, a much larger sample of patients with first-episode schizophrenia than is reported herein would be required to ensure that sufficient numbers of patients destined to have severe chronic illness were included. The alternative is that brain abnormalities are progressive, at least in some patients, and that cortical abnormalities spread as disease becomes chronic. Support for this explanation accrues from the longitudinal study of Thompson et al⁹⁴ reporting progressive gray matter loss extending from parietal regions to include temporal, dorsolateral prefrontal, and frontal eyefield cortices in a small sample with childhood-onset schizophrenia. Longitudinal studies are ongoing to determine whether the abnormalities we reported are progressive and the relationship to illness course and treatment response.

Several limitations of this study should be mentioned. There are potential limitations in the use of VBM that have been discussed in detail elsewhere.^46-48,95 Data on MTRs could be prone to partial volume effects due to the 5-mm slices. However, we did not segment or warp the MTR data, which minimizes the risk of tissue misclassification. In addition, our post hoc native-space MTR ROI analysis was consistent with the SPM99 analysis. We reported cluster and voxel analyses for MTR data. Histograms of our data samples incorporating gray and white matter on a given slice resembled a Gaussian distribution, as previously demonstrated in chronic schizophrenia in reporting cluster analysis.³⁸ The use of cluster size to assess significance in SPM is appropriate only if the data are normally distributed.⁴⁷ It is possible that the MTR signal may not be normally distributed locally. A permutation analysis may be more reliable for cluster analysis in future studies. Most patients were receiving neuroleptic agents, and it could be argued that our findings may be different in a drug-naive population. However, there is little evidence from neuropathological studies, conducted mainly in animals, to suggest that neuroleptic medication causes or exacerbates brain abnormalities in schizophrenia,⁷ and most of our patients were receiving atypical neuroleptic agents for short periods, making this even less likely. Nonetheless, the effects of neuroleptic medication use on MTRs have not been studied and could be a potential confound. We repeated our analysis excluding the 5 unmedicated patients. Decreases in MTRs were found in the same regions. We did not analyze unmedicated patients separately because the sample size would have insufficient df to produce meaningful results. Our sample was relatively small, and it may not be possible to generalize our findings to other first-episode schizophrenia populations.

From the Department of Neuroinflammation, Institute of Neurology, Queen Square, University College London (Drs Bagary, Symms, Barker, and Ron), and Division of Neuroscience and Psychological Medicine, Imperial College Faculty of Medicine, Charing Cross Campus (Mr Mutsatsa and Dr Joyce), London, England.

REFERENCES