MRI is a high-resolution nonionizing (safe) tomographic technique used extensively for medical diagnostics and other related applications. It offers outstanding soft-tissue contrast that makes it superior to all other medical imaging techniques. MRI is based on creating two distinct energy states for the quantum spin of hydrogen nuclei in water molecules using a very strong static magnetic field B0. Applying an RF magnetic field B1 of the spin Larmor frequency f0 (about 42 MHz for each B0-Tesla) results in perturbing the distribution of the hydrogen nuclei (protons) between the two energy states. Upon restoring the thermodynamic equilibrium of this distribution, the spins radiate a highly coherent electromagnetic field at their Larmor frequency f0 that is used for a 3D-image construction.

MRI scanners with moderate B0 (up to 3T) excite and receive the RF B1-field by using coil arrangements operating more or less magnetostatically. They feature a predominant magnetic field and a very weak electric field with a nearly standing-wave field distribution (negligible spatial phase variation) and can be fully characterized using lumped elements and electric circuit theory.
Better image resolution and higher tissue contrast are, however, achieved by increasing the strength of the static magnetic field B0. Scanners with B0 > 4T (f0 > 160MHz) are categorized as “High Field”. RF structures (or simply RF coils) for excitation and reception of the corresponding B1-field have geometrical dimensions comparable to the operating wavelength. Therefore, they excite a significant electric field and exhibit propagation effects. The magnetostatic approximation is no longer valid for characterizing, modeling and optimizing such RF coils; they must be analyzed electromagnetically.

One of the objectives in the design of high-field RF coils is how to maintain the homogeneity of a circularly polarized B1-field (the so-called B1+-field) within a certain region of interest and, at the same time, minimize the associated electric field there. Homogeneity of the B1+-field is necessary for a uniform illumination of the image. Illumination in MRI can be defined as the strength of the spin transition from the lower to the upper energy state, which is attributed to the effect of the B1+-field in the excitation phase, where the RF coil acts as a transmitter. Minimizing the electric field, on the other hand, is necessary for increasing the signal-to-noise ratio (SNR) of the received MR signal radiated by the precessing spins during their back transition from the upper to the lower energy state. Lossy tissues interact with the electric field associated with the MR signal, giving rise to noise. A similar interaction takes place during the excitation phase and is responsible for heat development in the tissues. The latter is usually characterized by the tissue specific absorption rate (SAR).

In addition to a detailed presentation of the fundamentals of MRI, the course puts special emphases on a number of technological challenges. These include improving the homogeneity of the B1+-field for a better image quality, minimizing the electric field losses responsible for high SAR in the transmit operation and low SNR in the receive one, and making use of the concept of a phased array for focusing the RF field. These objectives can be achieved by using multi-channel operation and novel antenna structures.