Abstract

To develop quantitative susceptibility mapping (QSM) of bone using an ultrashort echo time (UTE) gradient echo (GRE) sequence for signal acquisition and a bone-specific effective transverse relaxation rate ( R2*) to model water-fat MR signals for field mapping. Three-dimensional radial UTE data (echo times ≥ 40 μs) was acquired on a 3 Tesla scanner and fitted with a bone-specific signal model to map the chemical species and susceptibility field. Experiments were performed ex vivo on a porcine hoof and in vivo on healthy human subjects (n = 7). For water-fat separation, a bone-specific model assigning R2* decay mostly to water was compared with the standard models that assigned the same decay for both fat and water. In the ex vivo experiment, bone QSM was correlated with CT. Compared with standard models, the bone-specific R2* method significantly reduced errors in the fat fraction within the cortical bone in all tested data sets, leading to reduced artifacts in QSM. Good correlation was found between bone CT and QSM values in the porcine hoof (R2 = 0.77). Bone QSM was successfully generated in all subjects. The QSM of bone is feasible using UTE with a conventional echo time GRE acquisition and a bone-specific R2* signal model. Magn Reson Med 79:121-128, 2018. © 2017 International Society for Magnetic Resonance in Medicine.

Highlights

  • Magnetic susceptibility is a fundamental tissue property that can be observed in MRI [1]

  • Quantitative susceptibility mapping of the bone has been challenging because it requires complete measurements of phase everywhere within the region of interest (ROI), and cortical bone typically has very low signal at conventional echo times in gradient echo (GRE) imaging

  • It should be noted that the good correspondence between diamagnetic regions in Quantitative susceptibility mapping (QSM) and regions of high HU values in CT images is supported by a strong linear correlation

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Summary

Introduction

Magnetic susceptibility is a fundamental tissue property that can be observed in MRI [1]. Bound bone water has an ultrashort apparent transverse relaxation time (TÃ2 $300 ms [27]), resulting in no meaningful phase for QSM reconstruction on conventional MRI. Because of these limitations, previous work in musculoskeletal applications of QSM was either focused on cartilage, or used piece-wise estimations of bone susceptibility [2,28,29,30,31,32,33,34]. An additional problem arises from intermingling of fat and water protons in the bone marrow, necessitating the application of water–fat separation techniques for field mapping

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