One of the greatest merits of magnetic resonance (MR) methodology is the capabilities for noninvasively studying both physiology and pathology in vivo. Numerous MR imaging (MRI) approaches have been developed with various imaging contrasts, which can be tightly relevant to organ functions and diseases.Recent MRI technology developments have resulted in several important functional MRI (fMRI) methods based on the blood oxygenation level dependent (BOLD) contrast [1][2][3][4][5] and/or cerebral blood flow (CBF). The CBF-based fMRI relies on the spin-tagging techniques [6][7][8]. These fMRI methods are becoming most important neuroimaging modalities for mapping brain activation and studying brain cognitive functions. In general, BOLD-based fMRI has better sensitivity for mapping brain activation. In contrast, CBF-based fMRI is less sensitive but more specific for mapping perfusion and its changes induced by brain stimulation. In some brain mapping applications, both BOLD-and CBF-based fMRI maps can be obtained in the same measurements [9]. There are two new exciting and promising MRI applications for brain research: 1) the resting-state functional connectivity mapping based on low frequency (<0.1 Hz) BOLD signal fluctuation [10], and 2) brain fiber tracking based on the diffusion tensor imaging (DTI) [11]. These new developed and improved MRI methods are playing an essential role for investigating and understanding basic brain structure, functions and mental disorders. In contrast with MRI approaches, in vivo MR spectroscopy (MRS) is capable of determining metabolite concentrations, metabolic rates and neurochemistry in living organs. These capabilities can be further enhanced at high magnetic fields (t 3 Tesla) due to significant gain in MR sensitivity and improvement in spectral resolution [12-14]. There are a variety of in vivo MRS approaches including in vivo 1 H, 31 P, 13 C and 17 O MRS. These MRS approaches are capable for measuring several important cerebral metabolic rates of oxygen utilization (CMRO 2 ), glucose consumption (CMR glc ) and ATP synthesis and utilization (CMR ATP ). These metabolic rates are tightly coupled to brain activity and brain pathology. Specifically, in vivo 1 H MRS is useful to measure brain glucose concentration and its change, ultimately, to determine CMR glc [15]. This method had been used to determine the CMR glc increase in the human visual cortex in response to visual stimulation [16]. The new developed in vivo 17 O MRS imaging approach at high/ultrahigh field adds another powerful neuroimaging modality for directly and noninvasively obtaining 3D CMRO 2 image within few minutes of inhalation of 17 O-labeled oxygen gas [17-21].Recently, this 17 O imaging approach has been successfully applied to mapping CMRO 2 changes in the cat brain during brain stimulation. Finally, the in vivo 31 P MRS approach combined with the magnetization transfer has been demonstrated to be extremely useful for directly measuring the ATP metabolism and their metabolic rates in both animal and human brai...