Assessment of Internal Auditory Canal Tumors: A Comparison of Contrast-Enhanced T1-Weighted and Steady-State T2-Weighted Gradient-Echo MR Imaging

Petra Schmalbrock; Donald W. Chakeres; James W. Monroe; Ashok Saraswat; Beth A. Miles; D. Bradley Welling

Abstract

BACKGROUND AND PURPOSE: Although contrast-enhanced T1-weighted MR imaging is the standard of reference for diagnosing tumor in the cerebellopontine angle, high-resolution T2-weighted imaging may show more details of the seventh and eighth cranial nerve branches, resulting in more accurate tumor volume measurements. The purpose of this study was to compare two MR sequences for their ability to delineate internal auditory canal tumors.

METHODS: Twenty-seven ears in 21 patients with 16 confirmed schwannomas were studied with the 3D T2-weighted prototype segment-interleaved motion-compensated acquisition in steady state (SIMCAST) and the T1-weighted contrast-enhanced spoiled gradient-echo (SPGR) techniques. Twenty-eight axial sections were acquired using parameters of 17/3.3 (TR/TE), a 40° flip angle, a 20 × 15-cm or 22 × 16-cm field of view (FOV), a 512 × 256 matrix, and a 0.4- or 1.2-mm section thickness for the SIMCAST technique, and 30/4.2, a 30° flip angle, a 20 × 20-cm FOV, a 512 × 288 matrix, and a 1.5-mm section thickness for the SPGR technique. Tumor appearance and depiction of surrounding anatomy, including the cranial nerves, were evaluated. Tumor volumes were measured by manual tracing.

RESULTS: Both sequences clearly identified tumors that ranged in size from 0.06 to 3.0 cm³. Measurements on both sequences agreed, on average, within 14%. The information from both sequences was complementary. SIMCAST usually delineated the CSF spaces better, whereas SPGR more clearly showed the tumor/brain boundary.

CONCLUSION: SIMCAST and SPGR are suitable for tumor detection and volume measurements. SPGR has somewhat better contrast, but SIMCAST excels at depicting the surrounding anatomy and tumor involvement of the seventh and eighth cranial nerves.

Because lesions in the inner ear and cerebellopontine angle (CPA) are readily detected with contrast-enhanced T1-weighted MR imaging, this is the preferred method for screening patients with suspected CPA tumors (1–3). However, a more detailed characterization of the lesions, beyond mere detection, would be of significant clinical interest. For example, for patients with small tumors, knowledge of the involvement of individual nerve branches may better aid surgical procedures aimed at hearing preservation. Furthermore, it is common clinical practice not to treat older patients surgically but rather to monitor their tumor growth. The monitoring and characterizing of tumors are also of interest for follow-up studies in patients who have had surgery or who have been treated with stereotactic radiosurgery.

Although contrast-enhanced T1-weighted MR imaging is the standard of reference for tumor detection, the relatively large section thickness (1.5 to 3 mm) and the low signal of nonenhancing structures (nerves, fluid) limit its capability for detailed tumor characterization and for allowing accurate measurements of tumor volume, especially in very small tumors. Thus, an assessment of very high-resolution T2-weighted MR imaging, which results in high fluid signal and high fluid/tumor and fluid/nerve contrast, as well as a comparison of T2-weighted with standard contrast-enhanced T1-weighted imaging is of interest. Finally, T2-weighted imaging without the need for expensive contrast agents (4–10) has been discussed as a lower cost MR imaging alternative to the cheaper but less sensitive auditory brain stem response (ABR) testing (11, 12). While large lesions have been clearly depicted with fast spin-echo (FSE) (7, 8) and constructive interference in steady state (CISS) (9, 10) imaging, some small lesions (<5 mm) were missed in previous work (8). Therefore, it is desirable to further increase spatial resolution; in particular, slice resolution with T2-weighted MR imaging.

The purpose of this study was to compare the prototype SIMCAST sequence with routine contrast-enhanced T1-weighted 3D spoiled gradient-echo (SPGR) imaging for the evaluation of tumors of the internal auditory canal (IAC). The SIMCAST sequence is based on similar principles as the CISS sequence (7, 13) but uses fractional echoes and averaging of four or more interleaved acquisitions with different RF phases (rather than the maximum intensity projection of two acquisitions used with CISS) to minimize susceptibility artifacts and to produce maximal signal for moving fluid. Previous studies have shown that the SIMCAST sequence, particularly when used with high-speed gradients, has the highest resolution capability among the T2-weighted sequences for inner ear imaging (14). SIMCAST and contrast-enhanced T1-weighted imaging were compared for their ability to allow accurate measurements of tumor volume, for their characterization of tumor signal, and for their depiction of the spatial relationship between tumors and nerves in the IAC.

Methods

We examined 21 patients with contrast-enhanced T1- and T2-weighted high-resolution gradient-echo MR imaging. Six patients had bilateral tumors; thus, a total of 27 ears were evaluated. All 27 tumors were studied before any treatment was administered. The clinical history of the patients is given in Table 1. In accordance with common clinical practice, MR imaging was used in the follow-up of the 10 patients who were over the age of 65 years. One younger patient with a small tumor (case 18) was also followed up. Of the 10 patients under the age of 65 years, two had unilateral tumors that were surgically removed and confirmed as schwannomas. The remaining eight patients had bilateral tumors, consistent with neurofibromatosis type 2. These eight patients underwent unilateral surgery, and the surgically removed tumors were confirmed as schwannomas. Six patients had surgery after the MR imaging study reported here and two had unilateral surgery before the first MR imaging evaluation. Data on these postsurgical ears were excluded from the image analysis. Thus, 16 of 27 tumors were schwannomas (eight confirmed by postsurgical evaluation plus an additional eight that were assumed to be schwannomas, since the other ear had a surgically confirmed schwannoma).

View this table:

TABLE 1:

Patient data and tumor sizes

Axial images were acquired with a 1.5-T MR system using the standard quadrature head coil. Images with T2-weighted appearance were acquired with the segment-interleaved motion-compensated acquisition in steady state (SIMCAST) sequence, which is a prototype 3D gradient-echo pulse sequence (14). Gradient moments were compensated over TR for all axes. Short fractional echoes were acquired to minimize dephasing due to flow motion and susceptibility effects. Susceptibility artifacts were also avoided by averaging four acquisitions with different RF phase stepping (13, 14). To avoid potential problems with gross patient motion, the four data sets with different RF phases were acquired in an interleaved fashion. The first 11 SIMCAST examinations were acquired with parameters of 17/3.5 (TR/TE), a flip angle of 40°, a 22 × 16-cm field of view (FOV), a 512 × 256 matrix, and 32 1.2-mm-thick sections. In the 10 more recently acquired studies, high-speed gradient coils were used, with smaller FOVs, of 20 × 15 cm, and thinner sections, of 0.8 mm (interpolated to 0.4 mm). In all cases, the SIMCAST images were acquired before the injection of contrast material.

Contrast-enhanced T1-weighted images were obtained after the injection of 10 mL of contrast agent with a 3D spoiled gradient-echo sequence (15) using parameters of 30/4.2/1 (TR/TE/excitation), a flip angle of 30°, a 20 × 20-cm FOV, a 512 × 288 matrix, and 64 1.5-mm-thick sections. Both sequences had similar scan times of 7 minutes.

Magnified views of the inner ears of patients with acoustic lesions obtained with both the contrast-enhanced T1-weighted and the SIMCAST sequences were analyzed in detail. Images were assessed for tumor extent, tumor heterogeneity, and depiction of other inner ear structures (cochlea, vestibule, and semicircular canals). A relative grading scheme was used to assess the tumor contrast. For the T1-weighted images, the grade levels were 0 (darkest) = hypointense relative to CSF, 1 = isointense with CSF, 2 = isointense with brain, and 3 (brightest) = hyperintense relative to brain. For the SIMCAST images, the grading scheme was 0 (darkest) = hypointense relative to brain, 1 = isointense with brain, 2 = isointense with CSF, and 3 (brightest) = hyperintense relative to CSF (Table 2).

View this table:

TABLE 2:

Grading of image contrast

For tumor volume measurements, the images were transferred to an off-line workstation (GE, Advantage Windows workstation). On each image section, tumors were manually traced by a neuroradiologist using the workstation software, and volumes were computed. In all cases, the SIMCAST images were traced first so as to avoid biasing toward the standard of reference (the T1-weighted images).

Results

All 27 lesions were clearly depicted with both sequences. Using the contrast-enhanced T1-weighted study as the standard of reference, the sensitivity of the SIMCAST sequence was 100% (27/27). Remarkably, small tumors with volumes as low as 0.05 cm³ were clearly depicted. In all 21 patients, the cochlea, vestibule, and semicircular canals were clearly delineated bilaterally on the SIMCAST images, whereas these structures were seen poorly on the T1-weighted images. The complete course of the seventh and eighth nerves in the CPA and IAC was seen on the SIMCAST sequences in normal ears. Lesions were seen in the IAC (27/27 lesions) protruding into the CSF spaces of the CPA (12/27) and eroding the IAC (9/27).

In 18 of the 27 affected ears, portions of the vestibulocochlear or facial nerve branches could be seen on axial SIMCAST images (Figs 1 and 2). In these cases, the axial images were reformatted into sagittal, coronal, and oblique planes or along a curved plane that followed the shape of the nerves. Individual vestibulocochlear nerve branches are best depicted on sagittal or oblique sagittal reformatted sections through the IAC (14), whereas curved reformatted images often allowed visualization of the entire course of the nerves from the brain stem to the fundus of the IAC. Since the contrast-to-noise ratio between CSF and nerves is low on T1-weighted sequences, nerve depiction was usually poor on T1-weighted images. Nerves were never seen inside the tumor mass.

fig 1.

Case 19: Slightly oblique axial reformatted images of a small mass.

A, SIMCAST image acquired in 5:05 minutes with parameters of 12.3/2.3, 40° flip angle, 22 × 16-cm FOV, 512 × 256 matrix, 32-kHz receiver bandwidth, four RF phase stepping loops (14), and 32 0.8-mm-thick sections interpolated to 0.4 mm.

B, Contrast-enhanced study acquired in 4:07 minutes with parameters of 40/4.2/1, 30° flip angle, identical FOV and matrix size, 15.6-kHz receiver bandwidth, and 32 1.6-mm-thick sections interpolated to 0.8 mm.

Both images (A and B) depict the superior portion of the IAC. On the SIMCAST image (A), a continuous dark line extending from the brain stem to the fundus of the IAC is seen in the anterior portion of the IAC, presumably the facial nerve (solid arrows). Only a portion of the facial nerve is seen on the T1-weighted image (B). With SIMCAST, the tumor mass (open arrow) is clearly seen in the posterior portion of the IAC, displacing the facial nerve anteriorly and leading to a tortuous course around the tumor. Tumor volumes of 0.082 cm³ and 0.078 cm³ were measured on the SIMCAST and T1-weighted images, respectively. The tumor size is 6 mm along the IAC with both sequences, but may appear slightly wider across the IAC on the T1-weighted image than on the SIMCAST image, possibly due to partial volume effects or to tumor involvement of the nerve, leading to signal enhancement. Note that small vessels (dashed arrows) have low signal on the SIMCAST image and high signal on the T1-weighted images, due to the presence of contrast agent in the vessels. With the SIMCAST sequence, using zero-order motion-compensated gradients over TR, no signal loss is observed with slow motion, such as is present in CSF or in the IAC (v < 0.6 cm/s; phantom study by Schmalbrock P, presented at the International Society for Magnetic Resonance in Medicine, 1998). Higher-order motion components are present for faster vascular flow and result in dephasing and signal decrease, accounting for the low vascular signal.

For the 27 SIMCAST images, the contrast was rated 0 (hypointense relative to brain, Table 2) in seven cases and 1 (isointense with brain) in 20 cases. That means lesions were always clearly differentiated from the surrounding high-signal CSF, but for most lesions extending toward the brain stem, the tumor/brain boundary was not distinguishable merely by the tissue signal contrast. However, in most cases, the tumor margin could be determined on the basis of the shapes of the anatomic structures or by using intervening vessels as landmarks separating the tumor from the brain (Fig 3). For the 27 contrast-enhanced T1-weighted sequences, the contrast was rated 3 (hyperintense relative to brain) in 25 cases and 2 (isointense with brain) in two cases. Thus, tumor/brain distinction was better on contrast-enhanced T1-weighted images. However, owing to the low CSF signal on T1-weighted images, fluid/bone boundaries were poorly defined, and thus the extent of tumor from the fluid spaces into the bony regions was not as clearly distinguishable.

fig 2.

Case 11.

A and B, Reformatted axial (A) and coronal (B) SIMCAST images acquired in 5:05 minutes with parameters of 12.3/2.3, 40° flip angle, 22 × 16-cm FOV, 512 × 256 matrix, 32-kHz receiver bandwidth, four RF phase stepping loops (14), and 32 0.8-mm-thick axial sections interpolated to 0.4 mm. A was magnified by a factor of three from the original data and reformatted along an axially oriented curved surface from the brain stem to the superior portion of the IAC containing the facial nerve (fn). Only a portion of the superior vestibular nerve (svn) is seen in this view. B was magnified sixfold and reformatted along a coronally oriented curved surface following the facial nerve in the anterior portion of the IAC. Other labeled structures include the pons (pons), the pontomedullary junction (pmj), and the superior aspect of the porus acousticus (spa). The curved views permit continuous depiction of the facial nerve from the brain stem to the fundus of the IAC. On the curved axial image (A) the facial nerve is pushed anteriorly by the tumor (open arrow). On the curved coronal image (B), the nerve courses superiorly to the tumor. There is remodeling of the IAC. In this patient, surgery preserved hearing.

fig 3.

Case 10: IAC mass (right side) with a tumor volume of 0.6 cm³.

A–D, On SIMCAST images (A and C), acquired in 5:05 minutes with parameters of 12.3/2.3, 40° flip angle, 22 × 16-cm FOV, 512 × 256 matrix, 32-kHz receiver bandwidth, four RF phase stepping loops (14), and 32 0.8-mm-thick sections interpolated to 0.4 mm, the tumor is isointense with brain tissue; nevertheless its boundary may be estimated by using vascular structures (arrows) as reference points. On contrast-enhanced images (B and D), acquired in 5:20 minutes with parameters of 30/4.2/1, 30° flip angle, 20 × 20-cm FOV, 512 × 288 matrix, 15.6-kHz receiver bandwidth, and 60 1.5-mm-thick sections, the hyperintense tumor is easily distinguishable from the adjacent flocculus (fl) and cerebral peduncle.

In a significant fraction of cases, IAC tumor signal was inhomogeneous. Signal heterogeneity was observed with both sequences in nine of the 27 cases, with the T1-weighted sequence alone in two cases, and with the SIMCAST sequence alone in two cases. This indicates that some of the tumors were probably necrotic, hemorrhagic, or partially cystic. On SIMCAST images, cystic tumor regions had higher signal intensity than brain, helping to distinguish the brain tumor margin; however, these tumor regions were more difficult to separate from CSF. Tumors that were partially cystic or necrotic did not enhance homogeneously. This led to difficulty in identifying margins between tumor and CSF with confidence on the contrast-enhanced images, and such tumor portions were defined better on the SIMCAST studies.

The results of the tumor volume measurements are listed in Table 1. We observed 10 tumors with volumes less than 0.15 cm³ (ie, less than 5 mm long), seven tumors of 0.15 to 0.35 cm³ (less than 7 mm long), five tumors of 0.35 to 1.0 cm³ (less than 10 mm long), and five larger tumors. Thus, our study contained a significant number of fairly small tumors. It is notable that tumor volumes were consistent between studies (ie, in agreement within 15% or less) in the majority of cases (17/27). Specifically, when the tumors were surrounded by CSF or bone interfaces, the measurements were accurate. Discrepancies in tumor volumes of more than 15% were observed only in 10 cases. Two of these patients (cases 4 and 9) had heterogeneous tumors, and variations in tumor volume measurements may be anticipated, since each technique presented difficulties in evaluating different portions of the tumors. In a third patient (case 10), a large CPA component was not accurately evaluated with the SIMCAST sequence. Large discrepancies in tumor volume were also observed in seven small tumors, with volumes less than 0.15 cm³. However, these percentage differences amounted to small differences in actual volume (0.01 to 0.03 cm³), corresponding to only a few image voxels. Finally, measurements were repeated in five ears by another investigator, and were in agreement to within 10%, except in one ear, in which the tumor margin was not clearly delineated (case 10).

Discussion

The goal of our study was to assess the capabilities of a new prototype T2-weighted MR imaging method, the SIMCAST sequence, and to compare it with standard contrast-enhanced T1-weighted imaging. Specifically, we measured tumor volumes, evaluated tumor signal characteristics, and studied the tumor involvement of the individual nerve branches.

Both contrast-enhanced T1-weighted imaging and the SIMCAST method clearly depicted all tumors, and tumor volume measurements were obtained for a wide range of sizes, from 0.05 to 3.1 cm³. In addition, the SIMCAST sequence provided excellent visualization of the inner ear anatomy. All individual branches of the cranial nerves in the IAC and CPA were routinely seen with SIMCAST, whereas these structures generally were not depicted on T1-weighted images. Even though both methods could identify the presence of tumor, availability of contrast-enhanced T1- and T2-weighted images allowed a more thorough assessment of the disease. Comparison of the signal characteristics of heterogeneous tumors on T1- and T2-weighted images may allow assessment of the nature of the abnormality (cystic, necrotic, hemorrhagic), and tumor boundaries may be more accurately determined, as both methods may fail to clearly delineate tumor margins. Thus, acquisition of complementary information may be particularly useful in follow-up examinations.

Our study gives some initial indication of the advantages of SIMCAST imaging with very high spatial resolution.

Tumor Detection and Screening

T2-weighted imaging for screening patients with suspected CPA tumors has been discussed by several authors (4–10) as an alternative to T1-weighted imaging, with its additional cost for contrast material, or the less reliable ABR testing (11, 12). It is not clear whether other abnormalities that cause hearing loss, such as inflammatory (Ramsey-Hunt syndrome, syphilis, viral otitis, middle ear sepsis), metastatic, or other idiopathic entities, are reliably detected on noncontrast examinations. However, it is clear that only T2-weighted studies with very high resolution are capable of showing them, as low-resolution studies are known to have missed tumors (8). This may be due, at least in part, to partial volume averaging. For example, one may assume a worst-case scenario in which a very small tumor is located partially in two adjacent sections, which leads to reduced tumor contrast; such a tumor may easily be missed. It is therefore important to increase the section resolution. One may expect to detect all tumors if the section thickness is comparable or less than the thickness of the cranial nerve branches. Consequently, SIMCAST imaging, using high-speed gradients with the capacity for nearly isotropic voxels, may be a favorable method for tumor screening.

Accuracy of Tumor Volume Measurements

Our data indicate that accuracy of tumor volume measurements is limited mainly by the inability to delineate tumor margins. In our study, in-plane resolution was 0.4 × 0.8 mm (interpolated to 0.4 × 0.4 mm), and the section thickness was 1.2 in older studies or 0.8 mm (interpolated to 0.4 mm) for the most recent SIMCAST studies and 1.5 mm for contrast-enhanced T1-weighted images. Thus, partial volume effects are expected to be most significant in the section direction in which the resolution is two to four times lower. In our study, even the 10 smallest tumors (<0.15 cm³) were clearly seen on four to five sections on the older studies and in 10 to 15 sections on the recent SIMCAST studies, whereas they were seen in only two to three sections on the T1-weighted images with lower section resolution. Thus, problems with partial volume averaging in the section direction were insignificant. Limited in-plane resolution may lead to errors in tracing tumor boundaries. Since volume measurements from SIMCAST and contrast-enhanced images agreed within 15%, and because repeated measurements by two investigators agreed within 10%, one may assume that errors due to manual tracing and partial volume effects were approximately 10% to 15%. So even though our study did not include test/retest evaluation, one may conclude that tumor growth can be estimated with 15% to 20% accuracy, provided that tumor boundaries are clearly delineated.

Depiction of Nerve Involvement

Finally, high-resolution T2-weighted SIMCAST imaging is advantageous because it permits evaluation of tumor involvement of individual nerves (Figs 1 and 2). Previous studies of healthy subjects have shown that the SIMCAST technique can depict the nerve branches accurately even in narrow IACs (14). Very high-resolution SIMCAST images also give a better picture of nerve placement and can be used to measure nerve diameters. In our study, vestibulocochlear nerves or nerve segments were seen in 17 of 27 affected ears. Four of these patients underwent unilateral surgery, and some degree of hearing preservation was achieved in three cases (Table 1). Note that patients in whom nerves were depicted had consistently better hearing. The average hearing threshold was 41 dB when nerves were seen and 77 dB when nerves could not be identified (Table 1). This suggests that high-resolution SIMCAST images may be good predictors of surgical outcome.

Conclusion

Our study demonstrates that high-resolution T2-weighted SIMCAST imaging can detect small lesions in the inner ear with a high degree of accuracy. Although 3D FSE imaging may produce similar results, our previous study showed that SIMCAST provides a better signal-to-noise ratio per unit of scan time (14). This may make SIMCAST imaging a suitable candidate for low-cost tumor screening; however, the addition of contrast-enhanced T1-weighted imaging provides complementary information and is therefore beneficial, especially in the follow-up of patients with known lesions or in presurgical evaluation. Monitoring of tumor growth is important, since the biological behavior of these tumors is unpredictable. Many are found in elderly patients with other medical problems. If they are stable, it may be best to observe them, for without an accurate means of following up these tumors, it is not possible to decide on the best management strategy. Our study offers some initial indication that high-resolution SIMCAST imaging and contrast-enhanced 3D-SPGR can be used for accurate monitoring of tumor growth; however, a more extensive study with a larger number of follow-up studies is needed.

Footnotes

↵1 Supported in part by research grant 5-R29-DC-01646 from the National Institute for Deafness and Other Communication Disorders, National Institutes of Health.
2 Address reprint requests to Petra Schmalbrock, PhD, Department of Radiology, The Ohio State University, MRI Facility, 1630 Upham Dr, Columbus, OH 43210.

References

↵
Weissman J. Hearing loss. Radiology 1996;199:593-611
PubMed
Chakeres DW, Oehler M, Schmalbrock P, Slone W. Temporal bone imaging. In: Som PM, Curtain HD, eds. Head and Neck Imaging St Louis: Mosby; 1996;1319-1350
Stone JA, Chakeres DW, Schmalbrock P. High resolution imaging of the auditory pathway. MR Clin North Am 1998;6:195-217
↵
Lee JN, King BD, Parker DL, Buswell HR. High resolution 3D imaging of the inner ear with a modified fast spin-echo pulse sequence. J Magn Reson Imaging 1996;6:223-225
PubMed
Casselman JW, Kuhweide R, Deimling M, Ampe W, Dehaene I, Meeus L. Constructive interference in steady-state-3DFT MR imaging of the inner ear and cerebellopontine angle. AJNR Am J Neuroradiol 1993;14:47-57
Abstract/FREE Full Text
Jackler RK. Cost-effective screening for acoustic neuroma with unenhanced MRI: a clinician's perspective. AJNR Am J Neuroradiol 1996;17:1226-1228
PubMed
↵
Allen RW, Harnsberger HR, Shelton C, et al. Low-cost high resolution fast spin-echo of acoustic schwannoma: an alternative to enhanced conventional spin-echo MRI? AJNR Am J Neuroradiol 1996;17:1205-1210
Abstract
↵
Fukui M, Weissman JL, Curtin HD, Kanal E. T2-weighted MR characteristics of internal auditory masses. AJNR Am J Neuroradiol 1996;17:1211-1218
Abstract
↵
Casselman JW, Kuhweide R, Dehaene I, Ampe W, Devlies F. Magnetic resonance examination of the inner ear and cerebellopontine angle in patients with vertigo and/or abnormal findings at vestibular. Acta Otolaryngol Suppl (Stockh) 1994;513:15-27
Stuckey SL, Harris AJ, Mannolini SM. Detection of acoustic schwannoma: use of constructive interference in the steady state three-dimensional MR. AJNR Am J Neuroradiol 1996;17:1219-1225
Abstract
↵
Carrier DA, Arriaga MA. Cost-effective evaluation of asymmetric sensorineural hearing loss with focused magnetic resonance imaging. Otolaryngol Head Neck Surg 1997;116:567-574
CrossRef PubMed
Welling D, Glasscock M, Woods C, Jackson C. Acoustic neuroma: a cost-effective approach. Head Neck Surg 1990;103:364-370
↵
Zur Y, Wood ML, Neuringer LJ. Motion-insensitive, steady-state free precession imaging. Magn Reson Med 1990;16:444-459
PubMed
↵
Kurucay S, Schmalbrock P, Chakeres DW, Keller PJ. A segment interleaved motion compensated acquisition in the steady state technique for high resolution imaging of the inner ear. J Magn Reson Imaging 1997;7:1060-1068
PubMed
↵
Vlaardingerbroek MT, DeBoer JA. Magnetic Resonance Imaging. Berlin: Springer 1996;167-214
Schmalbrock P, Monroe JW, Can high resolution steady state MRI depict cochlea fluid motion? Presented at: Sixth Scientific Meeting of the International Society for Magnetic Resonance in Medicine; April, 1998; Sydney, Australia.

Received April 1, 1998.
Accepted after revision March 22, 1999.

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High-Resolution T2-Weighted Imaging for Surveillance in Postoperative Vestibular Schwannoma: Equivalence with Contrast-Enhanced T1WI for Measurement and Surveillance of Residual Tumor

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Show more HEAD AND NECK

[1] ↵
Weissman J. Hearing loss. Radiology 1996;199:593-611
PubMed

[2] Chakeres DW, Oehler M, Schmalbrock P, Slone W. Temporal bone imaging. In: Som PM, Curtain HD, eds. Head and Neck Imaging St Louis: Mosby; 1996;1319-1350

[3] Stone JA, Chakeres DW, Schmalbrock P. High resolution imaging of the auditory pathway. MR Clin North Am 1998;6:195-217

[4] ↵
Lee JN, King BD, Parker DL, Buswell HR. High resolution 3D imaging of the inner ear with a modified fast spin-echo pulse sequence. J Magn Reson Imaging 1996;6:223-225
PubMed

[5] Casselman JW, Kuhweide R, Deimling M, Ampe W, Dehaene I, Meeus L. Constructive interference in steady-state-3DFT MR imaging of the inner ear and cerebellopontine angle. AJNR Am J Neuroradiol 1993;14:47-57
Abstract/FREE Full Text

[6] Jackler RK. Cost-effective screening for acoustic neuroma with unenhanced MRI: a clinician's perspective. AJNR Am J Neuroradiol 1996;17:1226-1228
PubMed

[7] ↵
Allen RW, Harnsberger HR, Shelton C, et al. Low-cost high resolution fast spin-echo of acoustic schwannoma: an alternative to enhanced conventional spin-echo MRI? AJNR Am J Neuroradiol 1996;17:1205-1210
Abstract

[8] ↵
Fukui M, Weissman JL, Curtin HD, Kanal E. T2-weighted MR characteristics of internal auditory masses. AJNR Am J Neuroradiol 1996;17:1211-1218
Abstract

[9] ↵
Casselman JW, Kuhweide R, Dehaene I, Ampe W, Devlies F. Magnetic resonance examination of the inner ear and cerebellopontine angle in patients with vertigo and/or abnormal findings at vestibular. Acta Otolaryngol Suppl (Stockh) 1994;513:15-27

[10] Stuckey SL, Harris AJ, Mannolini SM. Detection of acoustic schwannoma: use of constructive interference in the steady state three-dimensional MR. AJNR Am J Neuroradiol 1996;17:1219-1225
Abstract

[11] ↵
Carrier DA, Arriaga MA. Cost-effective evaluation of asymmetric sensorineural hearing loss with focused magnetic resonance imaging. Otolaryngol Head Neck Surg 1997;116:567-574
CrossRef PubMed

[12] Welling D, Glasscock M, Woods C, Jackson C. Acoustic neuroma: a cost-effective approach. Head Neck Surg 1990;103:364-370

[13] ↵
Zur Y, Wood ML, Neuringer LJ. Motion-insensitive, steady-state free precession imaging. Magn Reson Med 1990;16:444-459
PubMed

[14] ↵
Kurucay S, Schmalbrock P, Chakeres DW, Keller PJ. A segment interleaved motion compensated acquisition in the steady state technique for high resolution imaging of the inner ear. J Magn Reson Imaging 1997;7:1060-1068
PubMed

[15] ↵
Vlaardingerbroek MT, DeBoer JA. Magnetic Resonance Imaging. Berlin: Springer 1996;167-214

[16] Schmalbrock P, Monroe JW, Can high resolution steady state MRI depict cochlea fluid motion? Presented at: Sixth Scientific Meeting of the International Society for Magnetic Resonance in Medicine; April, 1998; Sydney, Australia.

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American Journal of Neuroradiology

Assessment of Internal Auditory Canal Tumors: A Comparison of Contrast-Enhanced T1-Weighted and Steady-State T2-Weighted Gradient-Echo MR Imaging

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