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A fast version of the arterial spin tagging technique for the detection of cerebral perfusion is presented. Based on adiabatic spin inversion in combination with snapshot FLASH imaging, our technique allows the recording of perfusion changes with a temporal resolution of about 3 s. Differences of cerebral perfusion dependent on the choice of anesthesia were observed in rat brain. Furthermore, with this arterial spin tagging method we demonstrated perfusion increases in the somatosensory cortex of anaesthetized rats during forepaw stimulation. Comparison of the activated areas in the T2 -weighted BOLD images and the perfusion-weighted images showed good spatial correspondence, but the sensitivity to the functional activation was more than ten times higher in the perfusion technique.

F98 gliomas, E367 neuroblastomas, and RN6 Schwannomas in rat brain were studied non-invasively in vivo by localized proton MR spectroscopy (MRS). The spectra obtained from homotopic brain contralateral to the tumors were qualitatively indistinguishable from those of normal rat brain in vivo and showed resonance lines assigned to N-acetylaspartate, glutamate, total creatine (creatine and phosphocreatine), choline, glucose, and myo-inositol. The tumor spectra displayed marked differences compared to those obtained from contralateral brain. There were increases in choline, myo-inositol and lipids, which are presumably associated with increased membrane turnover. The presence of lactate indicated anaerobic glycolysis. Other differences included the absence of signals from NAA resulting from the destruction or displacement of neuronal tissue by the tumor. There was also a loss of total creatine. Although the spectra of all three tumor types were distinct from contralateral brain, there were no obvious differences between the different tumor types.

Localized proton NMR spectroscopy in vivo allows focal studies of cerebral metabolites in both man and laboratory animals from image-defined regions as small as 1 mL or 64 microL, respectively. Although brain tumours lead to remarkable spectral alterations relative to normal brain, a number of problems may compromise the interpretation of the results. Potential complications arise from the chosen experimental conditions (method, TE, size and location of volume of interest), from regional metabolic heterogeneity in and around tumours, from differences between human tumours and animal models, and from discrepancies between in vivo and in vitro findings. Strategies and pitfalls are illustrated with use of selected examples from primary brain tumours, a rat tumour model and perchloric acid extracts of resected specimens.

Recent progress in image-controlled, localized proton MR spectroscopy offers a non-invasive means of gaining unique insights into brain metabolism in man. Combined studies with MR imaging can be performed within about 1 h. Results obtained in healthy subjects provide the basis for reliable identification and quantification of metabolite concentrations in the CNS and allow determination of their regional variability and age dependence. Clinical applications include infarcts, tumors, and neurodegenerative diseases, and also metabolic disturbances resulting from diseases of the internal organs, such as diabetes mellitus or liver cirrhosis.

Subsecond fast low-angle shot (FLASH) magnetic resonance imaging (MRI) allows single shot studies of the human heart within measuring times of about 100-300 ms depending on the data matrix. In contrast to conventional FLASH MRI subsecond applications acquire data during the approach to steady state. A detailed analysis of the saturation behavior of the signal is given for the ideal case of a rectangular slice profile. In a second step, realistic slice profiles assuming Gaussian-shaped excitation pulses were taken into account by means of a numerical solution of the Bloch equations. It turns out that the signal strength and the resulting image intensity is considerably higher than may be expected from steady-state considerations. Correspondingly optimized flip angles depend on the number of phase-encoding steps. Assuming long T1 relaxation times as, for example, encountered in muscle and brain tissue and repetition times of 5 ms or less, optimum flip angles are 12 degrees-16 degrees. The use of even higher flip angles (greater than or equal to 20 degrees) causes heavily distorted slice profiles and a dynamic increase of the effective slice thickness. Flip angles of the order of the Ernst angle (6 degrees) correspond to steady-state conditions and lead to considerable signal losses. The theoretical results are confirmed by subsecond FLASH MRI studies of the human heart using a 2.0 T whole-body system (Siemens Magnetom).