Anomalous diffusion model has been introduced and shown to be beneficial in clinical applications, compared with conventional diffusion models. However, the anisotropy of anomalous diffusion was neglected and its clinical feasibility remains uncertain. In this study, the use of anisotropy of anomalous diffusion is investigated for differentiating low- and high-grade cerebral gliomas. Based on the results, it is shown that the anisotropy of anomalous diffusion offers advantages compared to that of conventional diffusion models, indicating its potential to facilitate future studies of neuropathological changes in clinical populations.
A total of 22 patients with pathologically-verified gliomas were enrolled in this prospective study. According to the World Health Organization (WHO) criteria10, these patients were divided into two groups: low-grade (n = 6; 1 females; mean age, 40.5±10.0 years; 4 WHO grade II astrocytic tumors and 2 WHO grade II oligoastrocytic tumors) and high-grade (n = 16; 6 females; mean age, 43.9±12.0 years; 1 WHO grade III astrocytic tumor, 11 WHO grade IV astrocytic tumors, and 4 WHO grade III oligoastrocytic tumors).
The MRI acquisition was performed on a 3.0T MRI scanner (Discovery MR750, GE Healthcare, Milwaukee, Wisconsin) equipped with an 8-channel head coil. The acquisition parameters were: TR/TE = 3800 ms/110 ms; accelerating factor = 2; field-of-view = 24 cm × 24 cm; matrix size = 128 × 128; slice thickness = 5 mm; and number of excitations = 2. The diffusion gradient separation time (Δ) was varied at 27.5, 40.0, and 55.5 ms consecutively. For each Δ value, the diffusion gradient amplitude (G0) was varied at 15.67, 19.68, 24.73, 31.06, 39.01, and 49.00 mT/m. The gradient duration (δ) was kept constant at 20.4 ms. Therefore, a total of 18 non-zero b-values were applied in one direction, ranging from 151 to 3482 s/mm2. The diffusion gradients were successively applied along the x-, y-, and z-axes.
After correction for eddy current distortions and head motions using FSL tools11, the diffusion MRI images were analyzed using the fractional motion (FM) model, which is thought appropriate to describe the anomalous diffusion in biological tissue12. The Noah exponent α and the Hurst exponent H were calculated, both of which characterize the FM model13,14. In addition, apparent diffusion coefficient (ADC) maps were also obtained using the images acquired at b-values of 0 and 950 s/mm2. To quantify anisotropy, an index similar to FA, termed generalized FA (gFA), was introduced as the sample standard deviation dividing the root mean square:
$$gFA(V)=\sqrt{\frac{N}{N-1}\frac{\sum^N_{i=1}(V_i-\bar{V})^2}{\sum^N_{i=1}V_i^2}}$$
where N is the number of sampling directions, Vi is the parameter in the i-th direction, and $$$\bar{V}$$$ is the directionally averaged parameter. The gFA maps were calculated for ADC, α, and H.
Two experienced radiologists manually placed region of interests (ROI) on solid tumor and normal-appearing white matter (NAWM) regions on the b0 images, with reference to contrast-enhanced T1-weighted images and T2-weighted images. The NAWM ROI was drawn in contralateral normal-appearing centrum semiovale to the tumor ROI, with the same size. The mean values of the gFA for ADC, α, and H were calculated over the selected ROIs and compared between low- and high-grade gliomas using the Mann-Whitney U test. Receiver operating characteristic (ROC) curves were generated to assess the sensitivity and specificity of different parameters in differentiating low- and high-grade gliomas.
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