Imaging for Peripheral Nerve Disorders

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CHAPTER 235 Imaging for Peripheral Nerve Disorders

The development of most subspecialties in neurosurgery has been closely associated with developments in imaging—radiography, pneumoencephalography, and angiography, all of which have played a large role in guiding spine and brain surgical planning for many decades. This was before the advent of cross-sectional imaging with computed tomography (CT) and magnetic resonance imaging (MRI) greatly improved the accuracy and simplicity of making an image diagnosis in the 1970s and 1980s.

Peripheral nerve surgery, however, has developed in almost complete isolation from imaging, both because radiography, angiography, CT, and standard MRI have not proved widely useful or reliable for the diagnosis of nerve impingement or injury, and because electrodiagnostic studies have provided an effective alternative in many situations. Nonetheless, peripheral nerve surgery is one subspecialty where clinical physical examination and exploratory surgery to define the pathology have continued to play a dominant role.

The discovery of a series of magnetic resonance (MR) pulse sequence strategies for tissue-specific imaging of nerves in 1991 and 1992 has opened a new diagnostic world in which a wide variety of pathologies involving nerves can now be visualized directly.15 These techniques are grouped under the term MR neurography to emphasize the fact that it represents tissue-specific imaging of peripheral nerves in which the image signal arises from the nerve tissue itself and specialized imaging strategies are required.

Before these developments in 1992, it had generally been assumed that peripheral nerves simply could not be imaged reliably.6 The strategy of using diffusion-based MRI sequences to help produce linear neural images was first discussed by Filler and colleagues in 19917 and emerged as a workable technique through discoveries by Filler, Howe, and Richards (in London and Seattle) during late 1991 and early 1992,2,4,5 both for peripheral nerve and for CNS neural tractography (diffusion tensor imaging).

The resulting neurograms then served as a model for discovering additional nondiffusion tractographic methods for peripheral nerves. By 1993, there were several major publications in these fields.810 In the subsequent 14 years, more than 150 academic publications have reported on various aspects of this new imaging modality for peripheral nerves, including several large-scale formal outcome assessment trials.1113 Nonetheless, most textbooks of radiology or neuroradiology do not devote any pages at all to nerve imaging.14

In a number of settings, MR neurography has proved to be more efficacious than electrodiagnostic studies for identifying nerve compression that will improve with surgical treatment. This is true both in diagnoses that are typically evaluated by electrodiagnostic studies, such as carpal tunnel syndrome,12,13 and in diagnoses in which such studies have proved difficult to rely on, such as thoracic outlet syndrome (TOS), piriformis syndrome, and related sciatic nerve entrapment and pudendal nerve entrapment syndromes.11,1517

Utility for MR neurography has now been established for the evaluation of entrapment syndromes,11,1821 nerve injury/evaluation of repair,22 and nerve tumor assessment,2325 as well as in the setting of neuritis and a variety of neuropathies.26 It has also proved effective for evaluating nerve disorders affecting young pediatric patients, such as obstetric brachial plexus palsy.27

Technical Aspects

The basis for tissue-specific MRI of nerve derives from the existence of a variety of unique types of tissue water in nerves. Clinical use of MR neurography is based on the application of new findings about nerve image characteristics. It is also based on a specific strategy of using imaging to evaluate nerves.

The two major types of neurographic techniques that have been described are diffusion neurography and T2-based neurography. Diffusion neurography was the first reported.1,2,5 This method has extremely high selectivity for nerves and should be very sensitive to a variety of types of pathology. However, the technical demands necessary to perform diffusion neurography have delayed its clinical application until quite recently.2830 In addition, diffusion images tend to degrade in detail at locations of severe pathology.

T2-based neurography, however, can be applied on a reliable basis with many existing top-quality clinical scanners, with minor modifications. Even when the technical equipment requirements can be met, however, there may be limitations on the provision of MR neurography because of a lack of expertise in prescribing, postprocessing, interpreting, and acting on the MR data. Once the technical limitations are resolved, however, T2 neurography has the advantage of improvement in quality of detail as the severity of the nerve abnormality increases—the opposite of diffusion neurography.

Diffusion-Based Tractographic Techniques

Neural tissue is among several tissues in the body that demonstrate the property of linearly correlated water diffusion. Instead of diffusing freely in any direction (isotropic diffusion), the water molecules in neural tissue are restricted in their diffusion such that they tend to move linearly along the main longitudinal axis of the neural tissue (anisotropic diffusion). The detailed biophysical basis of this restricted diffusion is still not fully understood because water molecules should move freely through cell membranes.

In MRI, a radiofrequency pulse is used to synchronize the spin of protons in water molecules, and a return signal from the tissue then results. The signal decays as synchronization is lost. Tissue contrast arises on T1- and T2-weighted images because the spinning protons in water molecules interact with surrounding tissues and with each other and these interactions cause small changes in the spin rate so that the spins desynchronize. Loss of synchrony makes the signal decay, and such loss takes place at various rates in different tissues.

In diffusion-based imaging, tissue contrast also arises because it is possible to use the relative degree of diffusional isotropy and anisotropy in a given tissue to affect the rate of signal decay in that tissue. MRI can be sensitized to anisotropy by applying magnetic field gradients during the pulse sequence of the image acquisition process. When diffusion carries a proton to a new position in the gradient, it experiences a slightly different local magnetic field strength, and thus its spin rate changes, which results in desynchronization of the spins. When water diffuses equally in all directions in a tissue, the rate of this cause of signal decay is not affected by how the gradient is oriented.

In anisotropic diffusion, however, there is a large impact on the decay rate if the gradient is directed strictly perpendicular or strictly parallel to the direction of the nerve. When the gradient is parallel, the nerve protons move rapidly to new positions in the gradient and their signal decays more rapidly than in an isotropic tissue. When the direction of the gradient is strictly perpendicular, the protons stay in the same field strength region of the gradient as they diffuse along the longitudinal axis of the nerve, and they show little or no signal decay relative to surrounding isotropic tissues.

In a peripheral nerve, anisotropic water makes up just a small fraction of the total water in the nerve, and therefore the effect is seen only when both fat and isotropic water signals are suppressed—one of the discoveries made by Filler, Howe, and colleagues in 1992.1 When they found a means of selectively suppressing the signal of isotropic water, the result was a pure nerve image in which all other tissues disappeared and only the image of the nerve was left.

For both peripheral nervous and CNS tissue, Filler and colleagues4,9 also pointed out that it was possible to check each voxel (three-dimensional pixel) in an image volume by using three, six, or more gradient directions to determine both the magnitude and the direction in three-dimensional space of the anisotropy and then use this information to depict actual curving neural tracts rather than simply displaying two-dimensional differences in contrast in cross sections.

Until this time, the relative amount of anisotropic diffusion had been used to assign contrast to a given image pixel in a cross section or to assign colors to regions of neural tissue that respond to a given gradient direction. In tractography, however, each voxel is represented by an arrow that is a vector in three-dimensional space—representing a tensor.

When the arrows are followed from voxel to voxel, the result is a linear tract image that moves through the three-dimensional volume of the tissue along the course of the neural tissue. A variety of three-dimensional computer graphic techniques are now used to assemble tractographic images from these linear anisotropy traces—the basis of tractographic diffusion tensor and vector imaging.

T2-Based Neurography

Once the diffusion method was understood, it was possible to show that structures with long decay times (imaged at a relatively long echo time) in fat-suppressed spin echo images were, in fact, nerves. Previously, nerves had been misinterpreted as exhibiting short decay times on T2-weighted imaging31 because they are a mixture of different tissues, including protein-laden axoplasmic water, myelin, fatty interfascicular epineurium, and connective tissue. Older methods allowed the image signal from these various component tissues to mix. In a variety of different imaging techniques, the result of mixing the image signals was a featureless gray image of the nerve, which left it difficult to distinguish clearly in an image and caused confusion about the fundamental imaging characteristics of nerves.

The Physiologic Basis of T2 Neurography

Several pieces of evidence suggest that the low-protein endoneurial fluid is what is seen most prominently in T2 neurography images. Endoneurial fluid is a low-protein liquid that lies within the privileged space of the endoneurium, confined by the perineurial blood-nerve barrier, and bathes the axons.32,33 It has a bulk proximal-to-distal flow along the nerve34 that may be disrupted by nerve compression and edema.

Although endoneurial fluid is responsible for only a fraction of the protons that can be imaged in a nerve, it is one of the most distinctive types of tissue water in nerves from the point of view of MRI. By applying a chemical shift–selective (CHESS) pulse, it is possible to not only suppress fat around nerves but also suppress much of the fat signal from within nerves. A similar effect can be produced with inversion recovery–type sequences that achieve fat suppression. Then, by selection of an appropriate echo time (around 90 msec), a T2 weighting can be achieved that results in suppression of muscle signal, thereby leaving most of the signal from endoneurial fluid intact. Any one of several methods can also be used to suppress bright fluid signals from flowing blood. For all MR neurography studies, echo times should be greater than 40 msec (usually 70 to 100 msec) to ensure that no magic angle effects could occur.35

When all three measures are taken—fat suppression, T2 weighting, and blood suppression—conditions are created to allow the generation of selective nerve images in virtually any location in the body. However, these pulse sequence manipulations by themselves are not sufficient to reliably obtain useful images.

Optimizing Performance of the Magnetic Resonance Imaging Main Magnet

One source of variation in quality among MRI scanners that has a very large impact on image quality in neurography is the homogeneity of the main magnetic field of the imager. MRI scanners are designed to provide a precise level of magnetic field strength over a useful volume. At a minimum, this volume will be large enough to cover the entire brain when the head is positioned at the exact center of the magnet. However an imager that can do only that will be relatively ineffective in producing a brachial plexus image, which requires a larger field of view and will be off center in the magnet. Good versatile nerve imaging therefore requires an MRI scanner with good magnetic field homogeneity off center in the magnet and over a relatively large volume.

Another aspect of this design factor concerns fat suppression via a CHESS pulse, which is used for the most selective T2 neurography. CHESS pulses work well only when the main magnetic field is very accurate and very uniform—this is accomplished by a process called shimming. All MRI scanners come with an ability to shim the magnet to improve field performance. In some imagers, shimming is done as a weekly or daily maintenance function, which is generally adequate for routine brain, spine, and general imaging work. Top-performing MRI scanners for nerve imaging are actually shimmed at the beginning of each imaging sequence on the volume of interest with the patient in position. Nerve imaging is one of very few applications when per-patient local shimming is important, and some expensive top-of-the-line academic MRI scanners do not offer the necessary shimming capability and thus produce very poor-quality neurography images.

Phased-Array Coils

Signal-to-noise performance can be greatly enhanced with the use of a specialized class of radiofrequency antennas as the receiver coil for collecting the image data called “phased-array coils.”36 The basic idea behind phased array is to use more than one antenna to collect the weak signal. Two phased-array receiver coils can be placed at two different positions within the imager. Each will collect data that contain both signal and noise, but a considerable part of the noise derives from physical aspects of the scanner, so the noise spectrum looks slightly different in different locations of the scanner. The actual data signal from the tissue, however, is effectively the same anywhere in the scanner. By comparing the information from the two antennas it is possible to discard data when it differs between the two antennas because it is likely to be noise but to keep data when it is identical in the two antennas. This strategy results in greatly enhanced signal-to-noise performance.

Phased-array coil technology may allow four or even more receivers to be run simultaneously to achieve even greater signal-to-noise enhancement. The most important issues for the referring physician to be aware of are that phased-array capability is critical for high-resolution imaging and that performance varies among phased-array coils from different manufacturers. Consequently, a specialized image center with the optimal equipment for neurographic imaging may do a much better job than a center that does not specialize in this very demanding type of imaging.

Image Plane Orientation

For most types of routine MRI, the original scan can be collected in three standard planes—axial, coronal, and sagittal—and then printed on film and read. However, MR neurography is considerably more demanding to acquire and is essentially wedded to an electronic reading format. The initial scanning must be done with attention to the main orientation of the nerves of greatest interest so that a set of nerve-perpendicular and a set of nerve-parallel images can be obtained. The nerve-perpendicular plane is identified by obtaining an initial image in the coronal plane and then orienting a specialized oblique image plane to be perpendicular to the principal longitudinal direction of the nerve or plexus of interest. A nerve-parallel image plane can also be prescribed during the image study, depending on the individual patient and the nerve to be imaged.

Areas of nerve irritation can be confirmed by comparing the appearance of serial nerve cross sections in the nerve-perpendicular views with those seen in the nerve-parallel views. In nerve-perpendicular images, the fascicle pattern can generally be observed, and this adds further confidence to a finding of focal nerve hyperintensity noticed in the nerve-parallel views. It will demonstrate expansion of the fascicle compartment at the expense of the interfascicular compartment at areas of focal hyperintensity (Fig. 235-1). The nerve-parallel images provide a linear overview.

Nerve Image Reconstruction, Three-Dimensional Reconstruction, and Partial Volume Averaging

In general, effective interpretation of nerve-parallel images depends on the ability of the MR neurography imaging pulse sequence to make the nerve brighter than surrounding tissues. However, partial volume effects at the edges of nerves can lead to the artifactual appearance of variation in image intensity within a nerve image. Even when image plane orientation is attended to during image collection, the raw image may capture only pieces of nerves in individual image planes.

The full image of the nerve can then be reconstructed in several ways. The first is oblique or multiplanar reformatting. This step is very helpful in interpreting most MR neurography studies. By shifting the effective image plane a few degrees and changing the effective slice thickness it is typically possible to reassemble significant lengths of nerve or plexus. Without this step it is far more challenging for the reader of the image to comment on local variations in nerve image intensity or distortions in the course of the nerve. Some reformatting is mandatory for nearly all MR neurography studies.

In the brachial plexus, multiplanar reformatting is usually sufficient to generate a series of images that can reliably confirm the existence of a focal change in nerve image intensity. This is aided by positioning the patient in the scanner in a manner that tends to straighten the plexus. When a change in fascicle pattern shows increased intensity in the nerve-perpendicular views that matches a change seen in nerve-parallel views (Fig. 235-1), there can be a very high level of confidence about the clinical reality of nerve edema at the location that appears abnormal in the image.

Yet another category of three-dimensional postprocessing is the use of curved reformatting. This step is often capable of producing an image of an extended length of nerve or nerve plexus. The process of curved reformatting can generate a trace of the course of the nerve (Fig. 235-2). This nerve trace is also very useful for interpreting the image because it documents any unusual deviations in the course of a nerve or plexus. However, this method does add some subjectivity to the image analysis process and should not be read without comparison to more objective comparison images such as the original image planes or multiplanar reconstructions.

Conspicuity and Maximum Intensity Projection Images

Maximum intensity projections (MIPs) essentially stack up the image slices and have the effect of reassembling the nerves (Fig. 235-3). These MIP images can help in appreciation of the overall course of the nerve and variations in course, caliber, and intensity because they may vary along the length of a nerve.

The greatest amount of additional diagnostic information in these analyses occurs in brachial plexus cases.37 Because of the significant incremental amount of clinical information provided by three-dimensional analysis and the susceptibility of most studies to this, these are essential aspects of the diagnostic interpretation process in this group.

Classes of Image Findings

Image findings in MR neurography studies include the presence of regions of nerve hyperintensity or nerve swelling, which result from edema at the fascicular level (see Figs. 235-1 and 235-3). Distortions in the normal course of the nerve, abnormal contours, and alterations in nerve caliber are also readily seen—any of which can be classed by the degree or severity of the abnormality. These findings can indicate entrapment or adhesions, as well as posttraumatic effects.

In trauma, assessment of nerve continuity or the location of severed nerve endings, or both, is feasible, although edema at a site of injury limits the utility of MR neurography in acute injury settings. With the elapse of time after injury or repair, the development of traumatic neuromas may be readily appreciated.

In patients with hereditary neuropathies, disordered distribution of interfascicular lipid can be detected. The various classes of nerve image findings are most reliable for the larger named nerves greater than 3 mm in diameter, although there is no technical limit on the size of a nerve that can be imaged (Fig. 235-4).

image

FIGURE 235-4 Detailed imaging of small nerve branches. The dorsal ramus of a lumbar nerve demonstrates the degree of detail that can be achieved under optimal conditions.

(From Filler AG, Maravilla KR, Tsuruda JS. MR neurography and muscle MR imaging for image diagnosis of disorders affecting the peripheral nerves and musculature. Neurol Clin. 2004;22:643.)

Imaging in the Setting of Nerve Entrapment and Pain

Image Findings in Brachial Plexus Studies

Thoracic Outlet Syndromes

TOSs have been problematic diagnostically because of the difficulty of obtaining surgically useful localization of brachial plexus compression sites. Indeed, limitations in the quality of diagnostic techniques have led to ongoing disagreement about the very existence of this class of nerve entrapment syndromes.

In part, these problems arise because of the difficulty of placement of diagnostic electrodes for electrophysiologic studies in this region. In addition, because many cases of TOS are due to nerve compression by the scalene muscle, the situation often arises that patients have pain elicited by motions such as arm raising but do not have sufficient motor symptoms to produce abnormal findings on electromyography (EMG). Finally, the diagnosis of TOS is greatly complicated because the term describes a variety of diverse underlying pathologies that have in common only the fact that they affect some part of the brachial plexus.

MR neurography has shown promising capability for discriminating among several different types of TOS lesions and in many cases can depict well-delineated and readily treatable specific pathologies.38,39 Such pathologies include distortions of the course of the proximal elements at the scalene triangle (Fig. 235-5A to D), fibrous band entrapments affecting the C8 and T1 spinal nerves and the lower trunk of the brachial plexus (Fig. 235-5F), gross distortions of the midplexus region (Fig. 235-5G and H), irritation at the level of the first rib (Fig. 235-6), and distal plexus irritation.

MR neurography is also helpful when it demonstrates a completely normal course and caliber of all nerve elements under suspicion. In the presence of normal findings, it is possible to take a firm stance against surgical treatment of any hand, arm, or shoulder problems that may have tentatively been attributed to TOS.

Brachial Plexus Neuritis

In addition to surgically treatable entrapment, MR neurography is also helpful in identifying patients with complaints attributable to nerve inflammation.40 Such patients often have painless hand atrophy with no associated sensory abnormality. This has sometimes been termed Gilliatt-Sumner hand syndrome. Brachial plexus elements appear bright and swollen but demonstrate no distinct evidence of impingement.

Lumbar Foraminal Pathology

The normal course of the lumbar spinal nerves is a smooth straight line (Fig. 235-7A). In patients with nondiagnostic MRI and myelographic findings, MR neurography can demonstrate distortions of the course of the exiting nerve in the distal foramen (Fig. 235-8A; also see Fig. 235-7B).

image

FIGURE 235-8 A, Extraforaminal impingement of a descending L5 spinal nerve by a lateral marginal osteophyte (lmo) distal to the foramen. drg, dorsal root ganglion. B, Nerve imaging in the setting of reflex sympathetic dystrophy (RSD). Sciatic nerve hyperintensity is associated with adhesion to a site of pelvic fracture in a patient with new-onset RSD. The RSD symptoms resolved after nerve release surgery. C, Severe focal compression of the sciatic nerve at the sciatic notch (arrows). The nerve is flattened, hyperintense, and expanded to more than twice its normal diameter. This is a postoperative result that occurred when only one of the two bipartite elements of the piriformis muscle was released in a patient with a split nerve and split muscle. Differential retraction of the cut piriformis segment relative to the intact segment caused a severe mechanical impingement syndrome. D, Distal pudendal nerve neurographic anatomy. The pudendal nerve in the Alcock canal (AC) runs along the medial aspect of the obturator internus muscle (OI) medial to the ischial tuberosity (IT). The rectal branch of the nerve (RB) is well seen in most imaging cases (Re, rectum).

(B, From Filler AG, Maravilla KR, Tsuruda JS. MR neurography and muscle MR imaging for image diagnosis of disorders affecting the peripheral nerves and musculature. Neurol Clin. 2004;22:643; D, from Filler AG: Diagnosis and management of pudendal nerve entrapment syndromes: impact of MR neurography and open MR-guided injections. Neurosurg Q. 2008;18:1.)

Even when myelography is capable of demonstrating that a nerve root is cut off, an MR neurogram can provide considerable additional information. The full length of the foraminal impingement requiring treatment can easily be appreciated on a neurographic image. In addition, the ability of MR neurography to demonstrate hyperintensity in the lumbar root adjacent to the impingement helps confirm the clinical significance of the impingement (Fig. 235-8A). MR neurography is also particularly helpful for imaging foraminal spinal disease in the presence of scoliosis because the three-dimensional aspects of the imaging tend to resolve some of the ambiguities arising from the spatial complexity that may otherwise make diagnosis very challenging.

Magnetic Resonance Neurography in the Pelvis

The use of MR neurography has had a significant impact on diagnosis in the pelvis.11,15,16,41,42 Although sciatic pathologies have been an important part of the advance, the ability of MR neurography to track other nerve elements in the pelvis such as the ilioinguinal nerve, pudendal nerve, and lateral femoral cutaneous nerve has gone a long way to resolving what had been a troublesome black box. Imaging of the complete course of the L4 spinal nerve as it progresses into the femoral nerve has made it possible to search for abnormalities along the intra-abdominal and intrapelvic course that previously were almost impossible to diagnose.

A single imaging study can demonstrate the full course of the L5 and S1 spinal nerves and their descendants in the lumbosacral plexus and proximal sciatic nerve (Fig. 235-9). It is very reliable for demonstrating the presence of a split nerve/split muscle configuration in the setting of a possible piriformis syndrome. Focal sciatic impingements at the ischial margin (see Fig. 235-8C), at the tendon of the obturator internus, at the distal ischial tunnel on the lateral aspect of the ischial tuberosity, and at various locations in the thigh are readily distinguished.

Reliable identification of anatomic variants of the sciatic nerve now plays a critical role in improving the safety of surgery for the release of pelvic sciatic nerve entrapment. Isolated section of a single piriformis segment in patients with a split nerve passing through a split muscle can cause severe nerve compromise from some types of piriformis surgery if this condition is not detected in advance (Fig. 235-9).

Identification of the presence or absence of pudendal nerve irritation in the Alcock canal along the medial aspect of the obturator internus muscle or at the rectal branch of the pudendal nerve proximal to its entrance to the Alcock canal (see Fig. 235-8D) has also been quite useful clinically.16

Distal Entrapments

Distal entrapments, including less common problems such as posterior interosseous nerve entrapment of the distal radial nerve and common issues such as peroneal nerve entrapment at or above the fibular head, tarsal tunnel syndrome, cubital tunnel syndrome, and carpal tunnel syndrome, benefit from MR neurography when physical examination or electrodiagnostic studies show that locations other than the most routine sites may be involved. For instance, median nerve entrapment in the distal part of the forearm can lead to failure of treatment if only the flexor retinaculum is addressed. Ulnar entrapment in Guyon’s canal and proximal peroneal nerve entrapment along the tendon of the biceps femoris just distal to the sciatic bifurcation are other specialized issues that can best be investigated by imaging. Electrodiagnostics can be misleading if they are done under the assumption that abnormalities in certain regions (e.g., the median nerve in the distal end of the forearm) will always be at the flexor retinaculum—particularly if uncomfortable and time-consuming inching studies are not done.

Identification of distal entrapment of cranial nerves, including the inferior alveolar nerve in the jaw (Fig. 235-10) and the glossopharyngeal nerve as it descends in the upper part of the neck, is also very effective with neurographic imaging.

image

FIGURE 235-10 Injury-associated nerve hyperintensity on imaging. Brightness and swelling are noted on T2 neurography at a site of nerve trauma (*) resulting from an oral surgery procedure. The lingual and inferior alveolar components of the mandibular nerve (M) are well seen.

(From Filler AG, Maravilla KR, Tsuruda JS. MR neurography and muscle MR imaging for image diagnosis of disorders affecting the peripheral nerves and musculature. Neurol Clin. 2004;22:643.)

Nerve Adhesions

An interesting aspect of image-based diagnosis of focal neuropathies is that it has been capable of further elucidating the role of adhesive entrapment and in some cases distinguishing it from compressive entrapment. MR neurography has been particularly helpful in demonstrating the degree to which nerves move across some joints. In Figure 229-5, two images of the median nerve at the carpal tunnel reveal very different positions of the nerve within the tunnel. However, both images are from the same individual and were obtained at the same location in the wrist—they differ only in that one is in a position of flexion and one in extension of the wrist. Imaging of a series of patients with clinically and electrodiagnostically confirmed EMG revealed that although most had compressive lesions, some demonstrated only nerve adhesion with loss of normal mobility of the nerve on flexion and extension of the wrist.

From the points of view of electrodiagnosis and surgical treatment, there is little difference between adhesive and compressive carpal tunnel syndrome. They produce similar clinical and diagnostic pictures and respond to the same surgical treatment. However, from the point of view of imaging it is important to appreciate that patients may have moderate to severe carpal tunnel symptoms with no evident nerve compression if adhesion is present.

Clinically, this demonstration is of potentially greater importance because in many cases it is possible to demonstrate with imaging that a nerve is not gliding normally across a joint. Restriction of movement of a nerve can cause repeated trauma to the nerve, as well as symptoms of pain exacerbated by extremes of motion or by assuming particular postures or limb positions. When this finding has been documented preoperatively, it becomes possible to plan on taking special measures to reduce the risk for recurrent scar formation postoperatively.43

Nerve Trauma

Management of severe nerve trauma has traditionally been complicated by the difficulty of distinguishing between situations in which a nerve will recover with the passage of time and those in which a nerve graft or other sort of surgical treatment would be appropriate. The problem arises because recovery after axonotmesis may require several months but there are few reliable means of distinguishing this situation from neurotmesis, in which no recovery can be expected without surgical intervention. MR neurography can be fairly efficient in establishing the existence of significant nerve injury,44 as well as in demonstrating continuity in a nerve (Fig. 235-12). At present, there still exists a limitation in that hemorrhage immediately after trauma may obscure some details of the nerve image in the first few days after an injury. In the future it is likely that enhancements in MR neurographic pulse sequences will help resolve this problem.

There is still no completely reliable means of confirming true nerve root avulsion by imaging.45 An MR neurographic study includes an effective MR myelogram (Fig. 235-12A) and can therefore demonstrate any meningoceles that may be associated with nerve root avulsions. The procedure is less invasive than CT myelography and provides information of similar quality.

Nerve Tumors

MR neurography permits a directed examination for nerve tumors that has greater sensitivity than other MR methods because of its reliability in showing that a given mass is actually inside a nerve or in direct continuity with it. In any body region the nerves can readily be evaluated for tumors, the symptoms of which are often mistaken for sciatica because of routine spinal pathology. In some cases, the level of detail also allows distinguishing among types of tumors, such as the reported capability of distinguishing perineurioma from schwannoma,46 as well as for identifying very small tumors that just slightly expand the caliber of a nerve.

In addition to the potential for diagnosing a nerve tumor, MR neurography can be extremely helpful in surgical planning for the treatment of these lesions.47 In the setting of a brachial plexus lesion it is possible to definitively distinguish which elements of the plexus are involved in the lesion (Fig. 235-13). It is also often possible to identify the relationship of the main nerve trunk to the mass of the tumor and thus plan the safest possible surgical approach.

Imaging may play a role in the initial diagnosis of neurofibromatosis and is also helpful in tracking and analysis of advanced stages of the disease (Fig. 235-14). Other types of tumor-associated neuropathy can frequently be evaluated quite productively by neurography as well.48

Magnetic Resonance Findings in Systemic Neuropathies

MR neurography can help make or confirm the diagnosis of neuropathy on a noninvasive basis. The two important types of nerve abnormality that have now been observed may be classified as intrafascicular pathology and interfascicular pathology.

In the setting of Charcot-Marie-Tooth hereditary familial neuropathy, the normal fascicle pattern is altered by an increase in the relative amount of fatty interfascicular epineurium and a relative decrease in the cross-sectional area of the fascicles themselves. Externally, on direct examination this would be manifested as a relative hypertrophy or increase in nerve caliber whereas in fact the fascicles themselves actually demonstrate relative atrophy.

An entirely different image effect is seen in chronic inflammatory demyelinating polyradiculoneuropathy. Affected patients have gross dilation of the fascicles themselves (Fig. 235-15). This alteration reflects an apparent increase in low-protein water inside the fascicles. It is somewhat similar to the pattern seen in wallerian degeneration. Although some onion bulb formations are seen in sural nerve biopsy specimens from these patients, there are perivascular mononuclear cells and notable edema in the endoneurial fluid compartment.49

Diagnosis of Pathologies Affecting Muscle

A variety of types of muscle pathology can be assessed by imaging.5052 MRI can contribute to diagnosis by providing precise information about the location and distribution of involved muscle tissues, as well as by providing qualitative information about several types of abnormalities. Abnormal muscle may demonstrate hypertrophy, atrophy, excess fluid—findings causing brightness on T2 imaging—or fatty replacement causing brightness on T1 imaging. The pattern of muscle involvement in these abnormalities, as well as the distribution of these findings within individual muscles and muscle groups, can provide valuable diagnostic information.

Imaging of Denervated Muscle

In a variety of situations, MRI can be a useful adjunct to electrodiagnostic studies for the evaluation of muscle denervation. Denervated muscle becomes hyperintense when imaged with a standard T2-based MR neurography protocol. When this phenomenon is present, it greatly simplifies the task of identifying individual muscles involved in a selective focal or distal injury (Fig. 235-16).

The development of signal alterations in muscle after denervation was first reported by Shabas and associates53 and by Polak and colleagues.54 It is now known that abnormal muscle appearance may be detected as early as 4 days after an axonotmetic or neurotmetic injury. The signal abnormalities become progressively more intense as months pass and reach a maximum about 4 months from the date of injury. In the 1- to 2-year range, the quality of the abnormality changes but it will continue to persist unless the nerve regrows or is restored through grafting.

The initial change is increased intensity on T2-weighted imaging. This has been observed by using an “inversion recovery” pulse sequence called STIR (short tau inversion recovery), as well as other T2-weighted, fat-suppressed sequences used for neurography. Animal work has shown how the appearance of increased signal occurs.55 There is no increase in water content of the muscle; however, the use of radiolabeled tracer compounds allowed the authors to establish that extracellular fluid volume was expanded at the expense of intracellular fluid. This shift was apparently associated with atrophy of the muscle cells.

A larger detailed human study by Fleckenstein and coworkers established that the onset of imaging changes is variable from patient to patient and that there is variability in the effect even among muscles in the distribution of a single damaged nerve.51 In the 1- to 2-year range, the quality of the abnormality changes as the muscles undergo substitution with fat. This additional change may correlate with the development of nonreceptivity to regrowing nerve fibers, which is known to take place at a similar interval after denervation; however, this concept has not yet been firmly established. Fleckenstein and associates also point out that muscle edema from trauma, as well as several other confounding sources of image abnormalities, must be kept in mind when considering this type of data.

Additional information about the clinical utility of muscle imaging was presented in a report on imaging of 32 patients by West and coauthors.56 They documented a similar range of alterations in image appearance in a case study format. These authors advocated the use of MRI to assess muscle denervation in patients who do not tolerate electrodiagnostic tests well, such as small children, in patients needing serial testing, and in patients in whom a complete view of the detailed pattern of innervation is required for surgical planning.

Myopathic and Neuropathic Effects on Muscle Image Patterns

In a number of myopathies and neuropathies, two aspects of muscle degeneration can be appreciated on imaging. There may be an increase in the T2 relaxation time of resting muscle because of effective edema in the muscle fibers.5759 In addition, characteristic patterns of fatty replacement or degenerative change have been described for several conditions. These changes can readily be appreciated on fat-suppressed T1-weighted images.6062 Changes in the T2 or T1 image parameters of muscle and the distribution of these changes have been reported for amyotrophic lateral sclerosis as well.63 Painful myopathies in diabetics can be evaluated with MRI to learn whether muscle infarction is playing a role as opposed to a more strictly neuropathic source of the pain.64

Suggested Readings

Aagaard BD, Maravilla KR, Kliot M. Magnetic resonance neurography: magnetic resonance imaging of peripheral nerves. Neuroimaging Clin N Am. 2001;11:viii.

Dailey AT, Tsuruda JS, Filler AG, et al. Magnetic resonance neurography of peripheral nerve degeneration and regeneration. Lancet. 1997;350:1221.

Filler; Filler AG. MR Neurography and diffusion tensor imaging: origins, history & clinical impact of the first 50,000 cases with an assessment of efficacy and utility in a prospective 5,000 patient study group. Neurosurgery. (in press).

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Filler AG, Howe FA, Hayes CE, et al. Magnetic resonance neurography. Lancet. 1993;341:659.

Filler AG, Kliot M, Howe FA, et al. Application of magnetic resonance neurography in the evaluation of patients with peripheral nerve pathology. J Neurosurg. 1996;85:299.

Filler AG, Maravilla KR, Tsuruda JS. MR neurography and muscle MR imaging for image diagnosis of disorders affecting the peripheral nerves and musculature. Neurol Clin. 2004;22:643.

Grant GA, Britz GW, Goodkin R, et al. The utility of magnetic resonance imaging in evaluating peripheral nerve disorders. Muscle Nerve. 2002;25:314.

Grant GA, Goodkin R, Maravilla KR, et al. MR neurography: diagnostic utility in the surgical treatment of peripheral nerve disorders. Neuroimaging Clin N Am. 2004;14:115.

Howe FA, Filler AG, Bell BA, et al. Magnetic resonance neurography. Magn Reson Med. 1992;28:328.

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Jarvik JG, Yuen E, Haynor DR, et al. MR nerve imaging in a prospective cohort of patients with suspected carpal tunnel syndrome. Neurology. 2002;58:1597.

Khalil C, Hancart C, Le Thuc V, et al. Diffusion tensor imaging and tractography of the median nerve in carpal tunnel syndrome: preliminary results. Eur Radiol. 2008;18:2283.

Kuntz C, Blake L, Britz G, et al. Magnetic resonance neurography of peripheral nerve lesions in the lower extremity. Neurosurgery. 1996;39:750.

Lewis AM, Layzer R, Engstrom JW, et al. Magnetic resonance neurography in extraspinal sciatica. Arch Neurol. 2006;63:1469.

Myers RR, Rydevik BL, Heckman HM, et al. Proximodistal gradient in endoneurial fluid pressure. Exp Neurol. 1988;102:368.

Raphael DT, McIntee D, Tsuruda JS, et al. Frontal slab composite magnetic resonance neurography of the brachial plexus: implications for infraclavicular block approaches. Anesthesiology. 2005;103:1218.

Singh T, Kliot M. Imaging of peripheral nerve tumors. Neurosurg Focus. 2007;22(6):E6.

Smith AB, Gupta N, Strober J, et al. Magnetic resonance neurography in children with birth-related brachial plexus injury. Pediatr Radiol. 2008;38:159.

West GA, Haynor DR, Goodkin R, et al. Magnetic resonance imaging signal changes in denervated muscles after peripheral nerve injury. Neurosurgery. 1994;35:1077.

Yoshikawa T, Hayashi N, Yamamoto S, et al. Brachial plexus injury: clinical manifestations, conventional imaging findings, and the latest imaging techniques. Radiographics. 2006;26(suppl 1):S133.

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