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The value of quantitative diffusion tensor imaging indices of spinal cord disorders



Different lesions affecting the spinal cord can lead to myelopathy. Diffusion tensor imaging (DTI) is widely used to predict the degree of spinal cord microstructure affection and to assess axonal integrity and diffusion directionality. We hypothesized that not all DTI parameters have the same affection with different spinal cord pathologies. The purpose of this study is to assess the value of the quantitative diffusion tensor imaging indices in different spinal cord lesions.


There is highly statistically significant difference of the fractional anisotropy (FA), relative anisotropy (RA), volume ratio (VR) and secondary eigenvector values (E2 and E3) between various studied cord lesions and control levels. There is no statistically significant difference of the apparent diffusion coefficient (ADC) and the primary eigenvector value (E1) (ANOVA test). The ROC curve analysis showed the higher sensitivity and accuracy were ‘88% and 62.5%, respectively,’ with FA cutoff value about 0.380.


The resulted quantitative DTI indices ‘fractional anisotropy, relative anisotropy, volume ratio and secondary eigenvalues’ work as a numerical in vivo marker of overall tissue injury in different pathologies affecting the spinal cord.


Myelopathy defines any neurologic deficit linked to the spinal cord, which usually arises secondary to compression of the spinal cord by osteophyte or herniated disc material, metastatic extradural mass or trauma. Many primary neoplastic tumors and infectious, inflammatory, neurodegenerative, and idiopathic disorders may lead to myelopathy [1].

Magnetic resonance imaging (MRI) is currently the most important modality for imaging of the central nervous system. It offers excellent anatomical information as regards the spinal cord macrostructure [2, 3]. MRI has an important role in diagnosing the intramedullary tumors and visualizing its extent and texture [4]. Conventional MRI provides qualitative information rather than quantitative data [4, 5].

The diffusion tensor imaging (DTI) is an advanced noninvasive magnetic resonance imaging technique that allows visualization of the white matter tracts. It allows quantitative evaluation of tissue microstructure integrity by probing the diffusion of water molecules [6,7,8].

The diffusion tensor imaging (DTI) has quantitative indices, including the apparent diffusion coefficient (ADC) refers to the overall diffusivity of the tissue irrespective of directional dependence, and the fractional anisotropy (FA) measures the fraction of the ‘magnitude’ of total diffusion that can be assigned to anisotropic diffusion within one particular voxel. It reflects the directional dependence of the diffusion process and is expressed as a relative number ranging from 0 to 1 that increases in relation to the anisotropic diffusion within the tissue being evaluated [6, 9].

Volume ratio (VR) is indicative of the ellipsoid volume in comparison with a sphere with radius equal to the mean diffusivity of the water protons. Consequently, a high VR is indicative of isotropic diffusion [10].

For simplification and practical purposes, the neuron can be expressed as a long ellipsoid, and its vectors are defined as eigenvectors (E1, E2, and E3). The longest vector (E1) along the long axis of the axonal cylinder signifies the longitudinal diffusion in the white matter, while E2 and E3 are minor eigenvectors signifying the transverse diffusion within the white matter of the spinal cord. A high E1 and lesser E2 and E3 values mean highly anisotropic diffusion in the neurons with intact walls [11].

This study hypothesized the specific DTI quantitative parameters to allow in vivo discrimination between various spinal cord lesions with the assessment of the axonal integrity and diffusion directionality.


An observational cross-sectional study was done from January 2020 to January 2021. Patients were having various neurological deficits related to the spinal cord and were subjected to detailed clinical history. Their medical reports were revised. All patients underwent conventional spine MRI study as a first investigation tool, and then, diffusion tensor imaging sequence was run for patients with positive conventional MRI findings abnormality affecting the cord.

Inclusion criteria involving patients with abnormal spinal cord findings in conventional MRI.

Exclusion criteria Patients with contraindication for MRI, e.g., an implanted magnetized device, pacemaker and claustrophobia, cerebral palsy and spine radiation and patients with vertebral fixation by screws damaging diffusion sequence by the metal artifacts.

MR imaging technique

Images were obtained using closed 1.5-Tesla Siemens MRI system (MAGNETOM, Sempra) with 18-channel spine phase array coil. Patients were scanned in the supine position with head first. Patients were asked to reduce movement during the scan.

MRI sequences The following sequence done in the study: sagittal T1WI with (TR/TE: 494/9.2ms, acquisition matrix 320 × 224, field of view = 330 × 100 mm2, number of slices 12, slice thickness 4mm, slice gap 20 percent), sagittal T2WI with (TR/TE: 3250/130ms, acquisition matrix 384 × 269, field of view = 330 × 100 mm2, number of slices 12, slice thickness 4mm, slice gap 20 percent), axial T2-TSE (TR/TE: 6930/121ms) and sagittal DTI (TR/TE: 5800/105ms) using a single-shot echo-planar imaging sequence, with 20 diffusion with (b=1000 s/mm2) with additional measurement without diffusion gradient (b=0 s/mm2), repetition time (TR)/echo time (TE) = 5800/105 ms, acquisition matrix 128 × 128, field of view (FOV) = 250x 100 mm2, number of slices=36, slice thickness 2mm, slice gap = 0, flip angle = 0, acquisition time (TA) = 09 minute 36 seconds. Post-contrast T1-TSE with a dose of 0.1mmol/kg of gadolinium that was injected automatically at a rate of 2 ml/s. Contrast was given for patient showing mass like cord lesions, infection or demyelinating disorders.

Imaging processing and analysis

Diffusion tensor data were post-processed and analyzed on the Syngo MR E11 station (Siemens Healthcare) using the Neuro 3D toolbox by drawing similar region area of interest (ROI) size at area of lesion, areas above and below (controls 1 and 2, respectively); qualitative images including grayscale and color-coded FA, ADC, trace images and 3D tractogram images were constructed (Figs. 1, 2, 3).

Fig. 1
figure 1

A 31-year-old male patient, fall from height ‘palm tree’ presented with paraplegia and incontinence. Sagittal T2-weighted (A) and T1-weighted (B) images show compression fracture of L1 vertebral body with posterior retropulsion and posterior paraspinal soft tissue injury including flava, interspinous and supraspinatus ligaments. Large amount of cord edema with high T2 signal intensity and no appreciated T1 signal abnormality. Sagittal trace (C), ADC (D) and grayscale FA (E) images show high trace signal intensity with corresponding low ADC value and low FA signal intensities within the compressed part of the spinal cord. 3D MR fiber tractography images (F, G) show partial fiber disruption on the posterior aspect of the contused spinal cord

Fig. 2
figure 2

A 22-year-old male patient presented with low back pain of two-month duration, with progressive left foot drop. Sagittal and axial T2-weighted (A, C), sagittal T1-weighted image precontrast (B), sagittal, coronal axial, and post-contrast T1-weighted images (DF). The terminal part of the spinal cord and conus medullaris region show expansile solid appearing space occupying mass lesion. The lesion shows bright T2 signal intensity with isointense signal intensity in T1WI. It shows irregular peripheral post-contrast enhancement. Diagnosis: Myxopapillary ependymoma. Sagittal trace (G), ADC (H), grayscale FA (J), color-coded FA (K) and 3D MR tractography (L, M) images. Trace image shows areas of mixed restricted and facilitated diffusion within the space occupying mass lesion. High ADC value and low FA values. The tractograms show widely separated fiber tracts with frank fiber disruption

Fig. 3
figure 3

A 45-years old female patient presented with progressive quadriparesis of 30 days duration. Sagittal T2-weighted (A) and sagittal T1-weighted (B), axial T2-weighted (C), sagittal and axial T1-weighted imges postcontrast (D & E) images show ill-defined patchy high T2 signal intensity of the spinal cord opposite at C5 & C6 vertebral body levels. Postcontrast study show irregular patchy peripheral enhancement at the lesion…Diagnosis: Transverse myelitis. Sagittal Trace (F), ADC (G), gray scale FA (H) & 3D MR tractography (I) image show high trace signal with bright ADC and low FA central signal intensity. The tractogram shows expansion of the spinal cord with mixed color intensities

Statistical analysis

Data were analyzed using Statistical Program for Social Science (SPSS) version 24*. A p value > 0.05 was considered statistically significant. Repeated-measure ANOVA test was used to analyze the continuous data and expressed as mean ± SD. The diagnostic performance of the DTI quantitative parameters at spinal cord lesion versus conventional MRI T2WI-detected signal abnormality was analyzed by ROC curve for calculating cutoff value, sensitivity, specificity, positive, negative values and accuracy.


Demographic date The study included 31 patients (13 female and 18 male patients) with mean age of 38.23 ± 19 years with age range from 15 to 88 years. Twelve patients had spinal cord traumatic lesions, 7 patients with neoplastic spine lesions and 12 patients with demyelinating and infectious cord lesions. Patients were divided into two groups (traumatic and non-traumatic non-degenerative group). The results were compared between all lesion levels and control levels of both groups.

Quantitative results between the normal control levels and the cord lesion level in both groups are given in Tables 1 and 2:

  • There was a statistically significant difference between the mean FA value of the traumatic and non-traumatic cord lesion levels and control levels with mean ±  SD values about (0.420 ± 0.111 and 0.471 ± 0.115), (ANOVA test p = 0.001 and 0.007, respectively).

  • There was no statistically significant difference between mean ADC value of the traumatic and non-traumatic cord lesion levels and control levels with mean ± SD value about (1.176 ± 0.245 and 1.161 ± 0.121) (ANOVA test p = 0.318 and 0.220, respectively).

  • There was a statistically significant difference between mean RA value for the traumatic and non-traumatic lesions levels and control levels showed highly significant RA value with mean ± SD of (0.375 ± 0.108 and 0.434 ± 0.127) (ANOVA test p = 0.001 and 0.012, respectively).

  • There was a statistically significant difference in the mean VR value between the traumatic and non-traumatic cord lesions and control levels and showed mean ± SD of (0.800 ± 0.086 and 0.740 ± 0.116) (ANOVA test p = 0.001 and 0.034, respectively).

  • There was no statistically significant difference between the mean E1 value of the traumatic and non-traumatic cord lesion levels and control levels with mean ± SD (1.721 ± 0.288 and 1.826 ± 0.255) (ANOVA test p = 0.444 and 0.449, respectively).

  • The minor eigenvector values showed statistically significant values with mean ± SD of E2 were (1.048 ± 0.283 and 0.972 ± 0.105) (ANOVA test p = 0.035 and 0.006, respectively). The other minor eigenvector values showed statistically significant values with mean ± SD of E3 were (0.778 ± 0.213 and 0.700 ± 0.165 SD) (ANOVA test p = 0.016 and 0.047, respectively).

  • When comparing the results between the two study groups of pathology by ANOVA test, the results showed no statistically significant difference in the measured quantitative parameters for FA, ADC, RA with p value = 0.150, 0.978 and 0.167, respectively. Also, there was no statistical difference between the measured VR, E1, E2 and E3 with p value = 0.213, 0.416, 0.596 and 0.582, respectively.

  • The ROC curve analysis (Fig. 4 and Table 3) showed the FA cutoff value of 0.380 between all lesions and control levels with sensitivity of 88%, specificity of 37%, negative predictive value about 76%, positive predictive value about 58% and accuracy of 62.5%. The RA cutoff value was 0.370, which had sensitivity of 77%, specificity of 46%, negative predictive value about 67%, positive predictive value of 59% and accuracy of 61.5%. The VR cutoff value of 0.640 between all lesions and control levels with sensitivity of 77%, specificity of 52%, negative predictive value of 69%, positive predictive value of 62% and accuracy of 64.5%.

Table 1 Repeated-measures ANOVA test comparing the difference in the calculated mean of different DTI metrics within the same group of pathology and between different pathology along the study cohort
Table 2 Repeated-measures ANOVA test comparing the difference in the calculated mean of different DTI metrics within the same group of pathology and between different pathology groups along the study cohort
Fig. 4
figure 4

ROC curve for DTI parameters at lesion versus conventional MRI T2WI detected myelopathy

Table 3 Diagnostic performance of DTI indices at lesion level versus T2WI detected myelopathy, analyzed as area under the curve (95% CI)


Diffusion tensor imaging and diffusion tensor tractography have been used successfully to assess the demyelinating or inflammatory disease burden [12, 13]. DTI can be used to assess the integrity of fiber tract and to guide the management of the spinal cord tumors [14, 15]. Also, DTI and DTT can be used to assess the functional state and prognosis of traumatic spinal cord lesions [9].

In this study, we found a statistical significant difference between the mean FA, RA, VR, E2 and E3 values between the lesion level and both control levels. We found also no statistical significant difference between the mean of ADC and E1 at these levels.

Our result for traumatic cord lesions, the FA and RA showed statistically significant reduction with no statistically significant raised ADC or E1 values. In agree with our result and on studying traumatic spine lesions by Alizadeh, they attributed that the decrease in FA may indicate degeneration of the fiber architecture, specifically the myelin will permit diffusion perpendicular to the neuronal axis, thus lowering the degree of FA. Although not statistically significant, the increase in MD may be attributed to an increase in cord edema [16].

Also, Facon previously found in their cohort no significant change in ADC values with a statistically significant difference for FA in patients with spinal cord injury and compression [17]. Werring and Beaulieu explained these findings in degenerated sciatic frog nerve and in human brain, a loss of anisotropy was noted, but average diffusivity may remain unchanged owing to an accumulation of cellular debris from a breakdown of the longitudinal axonal structure, while glial proliferation may hinder water movement in a parallel direction [18, 19]. In vitro study was carried out on spinal cord specimens of Indian calf (Bos primigenius indicus). The specimens consisted of the spinal cord surrounded by the vertebral column and paraspinal muscles. In the compression injury sites, FA, RA and VR were significantly altered, and more importantly, there was a progressive decrease in the values as the severity of compression increased. On the contrary, the ADC and E1 values again did not show significant changes at the sites of pathology [20].

This agreed with our findings in each group of pathology studied separately, as Shanmuganathan findings with the FA and RA showing statistical significant differences in spinal cord injury with the greatest reduction were found at the site of spinal cord injury. Also they found significantly increased VR in the hemorrhagic injury site compared to those in control subjects, denoting an increased isotropic behavior at these sites. A high VR means isotropic diffusion. An increase in VR at the site of injury is consistent with corresponding decreases seen in FA and RA when compared with control subjects. The RA followed FA trends and E1 mirror ADC value [10].

Loss of myelin integrity, which is typically secondary to demyelinating lesions, can be assessed with DTI. Demyelinating lesions demonstrate reduced FA values owing to a loss of anisotropy, as well as increased RD values secondary to an increase in water movement in the short axis, which occurs because the normal myelin barrier is damaged. On the contrary, after successful treatment, a decrease in RD and an increase in FA values occur with remyelination, indicating a positive response to treatment [21].

by Kang’s result, which was previously described, was in agreement with our results. They observed significant increase in minor eigenvalues E2 and E3, signifying the increase in transverse diffusion and loss of anisotropism. The preservation of E1, or longitudinal diffusion, reflects the maintenance of axonal integrity [22]. Klawiter described a linear trend for increased λ with increased demyelination and axonal loss within MS spinal cords [23]. In their study on neuromyelitis optica patient, Qian showed the reduced FA and increased increase in λ (diffusivity perpendicular to the axonal fibers) in their cohort. This suggests that the most relevant pathological mechanism occurring in the spinal tracts of these patients was probably demyelination [24], while Naismith in their study showed highly increased radial diffusivity, which has been associated with severe demyelination and axonal loss, correlating with the development of persistent T1 hypointensities or “black holes” in gadolinium enhancing brain lesions [25].

Klawiter described that, where λ|| and λ may be distended in a similar quantity, anisotropy may continue comparatively unchanged and so less informative. This is in distinction to other conditions where a differential increase in λ or decrease in λ|| may result in reduced anisotropy [23]. As Song found in their animal studies, we have reported that demyelination causes an increase in λ without changing λ|| [26]. Wang reported in their DTI animal study, which is in combination with biochemical validation, suggesting that increased λ with no change in λ|| represents an early sign of non-cystic white matter injury with reduced myelination before severe damage in structural integrity and necrosis [27].

When comparing the quantitative DTI indices between the two study groups of pathology, the results showed no statistically significant difference in the measured quantitative parameters for all indices. In agreeing with El Maati who found that the ADC and FA means of the tumor group were not significantly different from those of the non-tumor subjects (p = 0.539) [28]. In their study, Facon and Hassan showed decrease in FA value with variable ADC according to the type of extra-medullary tumor compressing the spinal cord [17, 29]. In agreeing with Facon, the FA measurements proved to have high sensitivity and specificity in the detection of spinal cord pathology in patients with extra-medullary spinal canal tumors [17].

In our findings, we support that the value of RA follows the trend of FA value and inverse to VR, while E1 mirrors ADC. The main contributing mechanism for FA reduction is the raised transverse diffusivity along the minor eigenvectors, which indicates the relative anisotropy and lowers the anisotropism. The preservation of E1, or longitudinal diffusion, reflects the maintenance of axonal integrity.


This study showed that the value of the newly additional sequence with its various measurable values ADC, FA, VR, RA and eigenvector values helps in depicting and supporting microstructure disorganization of various spinal cord lesions. We recommend DTI, whenever there is a focal abnormal signal in the cord, particularly when it shows post-contrast mass like enhancement. This study demonstrates the sensitivity of diffusivity along the minor axes (E2, E3 or λ) for the degree of demyelination, and injury of the spinal cord in contrast to (E1 or λ||) did not show significant correlation supporting the loss of anisotropism with reduced FA and RA values. More follow-up of the same disease categorization of spinal cord lesions with these numerical DTI values was to provide applicable measures for disease prognosis.

Availability of data and materials

The data that support the findings of this study are available and not for public view.



Diffusion tensor imaging


Non-traumatic-non-degenerative disease


Fractional anisotropy


Apparent diffusion coefficient


Volume ratio


Relative anisotropy


Longest eigenvector value


Middle eigenvector value


Minor eigenvector value


Magnetic resonance imaging


Weighted image


Repetition time


Time to echo


Field of view


Acquisition time




Region of interest


Statistical Program for Social Science


Receiver operator characteristic curve


Analysis of variance


Standard deviation


Mean diffusivity


Radial diffusivity

λ :

Diffusion perpendicular to axonal fiber axis

λ :

Diffusion parallel to axonal fiber axis


Multiple sclerosis


Area under the curve


Confidence interval


Standard error




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Authors and Affiliations



AKH was the major contributor in writing the manuscript and providing structural advices. MZ helped in data analysis and interpretation of the study. MK helped in body research construction and guideline. All authors have read and approved the manuscript, ensure that this is the case. All authors read and approved the final manuscript.

Corresponding author

Correspondence to Mona Gouda Maghrabi.

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The study protocol was approved by the Research Ethics Board of faculty of medicine-Assiut University (IRB number 17200249), assuring respect of the confidentiality of the medical record, and informed written consent was obtained from every participant.

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All patients included in this research gave written informed consent to publish the data contained within this study.

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The authors declare that they have no competing interests.

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Omar, M.K.M., Abd Allah, A.EK.H., Maghrabi, M.G. et al. The value of quantitative diffusion tensor imaging indices of spinal cord disorders. Egypt J Radiol Nucl Med 52, 271 (2021).

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