Quantitative magnetic resonance spectroscopy (MRS) amends differential diagnostics of neurological pathology. However, due to technical challenges, it has rarely been applied to the spinal cord and has mainly been restricted to the very upper part of the cervical spine. In this work, an improved acquisition protocol is proposed that takes technical problems as strong magnetic field inhomogeneities, pulsatile flow of the cerebrospinal fluid (CSF), and small voxel size into account. For that purpose, inner-volume saturated point-resolved spectroscopy sequence (PRESS) localization, ECG triggering, and localized higher-order shimming and F 0 determination, based on highresolution cardiac-triggered static magnetic field B 0 mapping, are combined. For inner-volume saturation a highly selective Magnetic resonance spectroscopy (MRS) noninvasively provides information on the biochemistry of neuronal tissue which is complementary to conventional MRI investigations. Concentration changes of metabolites such as Nacetyl-aspartate (NAA), choline containing compounds (Cho), creatine (Cre), or myo-inositol (mI) indicate decreased neuronal density or neuronal dysfunction, such as decreased neurotransmitter excretion, distorted membrane synthesis, malfunction of the energy metabolism, or demyelination, respectively. Specific patterns of metabolic changes observable by MRS point toward certain disorders of the central nervous system such as multiple sclerosis, low-and high-grade tumors, amyotrophic lateral sclerosis, or spino-cerebellar ataxia. Hence, MRS aids in the differential diagnosis of space-occupying lesions and various metabolic diseases. Therefore, investigation of human brain pathology by quantitative MRS has gained increased acceptance by clinicians (1).However, due to technical challenges, quantitative spinal cord MRS has rarely been used and was mainly restricted to the brain stem and the upper part of the cervical spine down to the C2-C3 level (2-6). Preliminary studies indicate that metabolite concentrations are sufficiently high to be observed by MRS in the entire spinal cord, but spectral quality was insufficient for quantification in the middle and lower cervical and even more in the thoracic and lumbar spinal cord (7-9). Susceptibility differences between vertebral bodies, intervertebral discs, and the surrounding tissue lead to strong magnetic field inhomogeneities (2). The pulsatile flow of the cerebrospinal fluid (CSF) induced by cardiac and respiratory motion causes phase fluctuations, water suppression failure, and movement of the spinal cord. F 0 misdetermination leads to dislocation of the spectroscopy voxel and, therefore, to lipid contamination arising from epidural, muscular, and subcutaneous fat, and bony marrow. The chemical shift displacement artifact, caused by bandwidth limitations of slice-selective excitation and refocusing pulses, limits the signal-to-noise ratio (SNR) due to imprecise localization and anomalous J-modulation (10) and induces ghosting artifacts (11) due to the inclusion of CSF ...