F.M. Kirby Research Center for Functional Brain Imaging, Kennedy Krieger Institute, Baltimore, MD 21205, USA.
Neuroimage. 2012 Aug 1;62(1):314-30. doi: 10.1016/j.neuroimage.2012.04.042. Epub 2012 Apr 28.
High-resolution magnetic resonance phase- or frequency-shift images acquired at high field show contrast related to magnetic susceptibility differences between tissues. Such contrast varies with the orientation of the organ in the field, but the development of quantitative susceptibility mapping (QSM) has made it possible to reproducibly image the intrinsic tissue susceptibility contrast. However, recent studies indicate that magnetic susceptibility is anisotropic in brain white matter and, as such, needs to be described by a symmetric second-rank tensor( ̅χ). To fully determine the elements of this tensor, it would be necessary to acquire frequency data at six or more orientations. Assuming cylindrical symmetry of the susceptibility tensor in myelinated white matter fibers, we propose a simplified method to reconstruct the susceptibility tensor in terms of a mean magnetic susceptibility, MMS=(χ(//)+2 χ(⊥))/3 and a magnetic susceptibility anisotropy, MSA=χ(//)-χ(⊥), where χ(//) and χ(⊥) are susceptibility parallel and perpendicular to the white matter fiber direction, respectively. Computer simulations show that with a practical head rotation angle of around 20°-30°, four head orientations suffice to reproducibly reconstruct the tensor with good accuracy. We tested this approach on whole brain 1 × 1 × 1 mm(3) frequency data acquired from five healthy subjects at 7 T. The frequency information from phase images collected at four head orientations was combined with the fiber direction information extracted from diffusion tensor imaging (DTI) to map the white matter susceptibility tensor. The MMS and MSA were quantified for regions in several large white matter fiber structures, including the corona radiata, posterior thalamic radiation and corpus callosum. MMS ranged from -0.037 to -0.053 ppm (referenced to CSF being about zero). MSA values could be quantified without the need for a reference and ranged between 0.004 and 0.029 ppm, in line with the expectation that the susceptibility perpendicular to the fiber is more diamagnetic than the one parallel to it.
高磁场下采集的高分辨率磁共振相位或频率移位图像显示与组织间磁化率差异相关的对比。这种对比随器官在磁场中的方向而变化,但定量磁化率映射(QSM)的发展使得能够重现组织固有磁化率对比。然而,最近的研究表明,脑白质中的磁化率具有各向异性,因此需要用对称二阶张量( ̅χ)来描述。为了完全确定该张量的元素,有必要在六个或更多方向上采集频率数据。假设髓鞘白质纤维中磁化率张量具有圆柱对称性,我们提出了一种简化方法,用平均磁化率 MMS=(χ(//)+2 χ(⊥))/3 和磁化率各向异性 MSA=χ(//)-χ(⊥)来表示磁化率张量,其中 χ(//)和 χ(⊥)分别表示平行于和垂直于白质纤维方向的磁化率。计算机模拟表明,在实际头部旋转角度约为 20°-30°的情况下,四个头部方向足以准确地重现张量。我们在 7 T 下对五名健康受试者的全脑 1×1×1mm(3)频率数据进行了该方法的测试。在四个头部方向采集的相位图像的频率信息与从扩散张量成像(DTI)中提取的纤维方向信息相结合,以绘制白质磁化率张量。在几个大的白质纤维结构中,包括放射冠、丘脑后辐射和胼胝体,定量了 MMS 和 MSA。MMS 范围从-0.037 到-0.053ppm(以 CSF 为参考约为零)。MSA 值可以在不需要参考的情况下进行量化,范围在 0.004 到 0.029ppm 之间,这与纤维垂直方向的磁化率比平行方向的磁化率更抗磁性的预期一致。