Magnetic resonance apparatus having an improved rf coil.

The invention relates to a magnetic resonance apparatus having a magnet system for generating a stationary magnetic field, a gradient magnet system for generating magnetic gradient fields, and an RF coil system which is connected to an RF source, the RF coil system comprising a coil with conductors serving as antenna wires, means being provided for an individually controllable drive of antenna wires or subgroups of antenna wires, a power amplifier being incorporated for each one of the individually drivable antenna wires or antenna wire groups of the coil, said power amplifiers being connected to an RF power source comprising a single RF generator.

Such a magnetic resonance apparatus is known from EP-A-0 156 979. In an apparatus of this kind, many different objects are examined. Therefore, it is desirable to have the possibility to adapt the impedance of the RF coil to the object to be measured. The known apparatus does not have this possibility.

It is an object of the invention to improve the known apparatus so that it is possible to adapt the impedance of the RF coil to individual needs. For that purpose, the magnetic resonance apparatus according to the invention is characterized in that the power amplifiers are connected to the antenna wires via contacts that can slide along the antenna wires so as to adapt the impedance of the RF coil to an object to be measured.

In a preferred embodiment, the power amplifier comprises a MOSFET transistor which is connected, via an input network comprising an inductance and a capacitance, to the RF power source.

In a further preferred embodiment, the RF coil comprises a number of antenna wires present on a cylinder surface about a central axis which are connected to ring conductors on each side via a capacitance. The ring conductors are preferably constructed as flanges adapted to the cylinder.

In behalf of circularly polarized rf fields, a circuit is incorporated in a further preferred embodiment for adjusting a phase shift, for example, given by the number of antenna wires, between successive antenna wires of, for example, a bird cage coil as described in EP 213665 of a transversal electromagnetic (TEM) coil as described in US 4,712,067.

A few preferred embodiments according to the invention will be described in greater detail hereinafter with reference to the accompanying drawing, in which <ul id="ul0001" list-style="none"><li>Fig. 1 shows a magnetic resonance apparatus comprising an rf transmitter coil according to the invention,</li><li>Fig. 2 shows an embodiment of such an rf coil,</li><li>Fig. 3 shows a circuit diagram for driving such a coil for generating a circularly polarized rf pulse, and</li><li>Fig. 4 shows an example of an amplitude and phase correcting network therefore.</li></ul>

A magnetic resonance apparatus as shown in Fig. 1 comprises a magnet system 2 for generating a homogeneous stationary magnetic field H, a magnet system 4 for generating magnetic gradient fields, supply sources 6 and 8, for the magnet system 2 and the magnet system 4, respectively. A radio frequency magnet coil 10 serves to generate a radio frequency magnetic alternating field and for that purpose is connected to a radio frequency source 12. For the detection of nuclear spin resonance signals generated by the radio frequency transmitter field in an object to be examined the rf coil 10 may also be used which for that purpose is connected to a signal amplifier 14. Another coil, for example, a surface coil, may also be used for detection. The signal amplifier 14 is connected to a phase-sensitive rectifier 16 which is connected to a central control device 18. The central control device 18 further controls a modulator 20 for the radio frequency source 12, the supply source 8 for the gradient coils and a monitor 22 for display. A high-frequency oscillator 24 controls both the modulator 20 and the phase-sensitive rectifier 16 processing the measured signals. A cooling device 26 with cooling ducts 27 serves for the cooling, if any, of the magnet coils 2 for the main field. Such a cooling device can serve water cooling for resistance coils or liquid nitrogen and/or helium cooling for high field strength, superconductive magnet coils. The transmitter coil 10 placed within the magnet systems 2 and 4 encloses a measuring space 28 which in an apparatus for medical diagnostic measurements is wide enough to comprise a patient lying on a patient table 29. So a homogeneous magnetic field H, cross-sections of the object-selecting gradient fields and a spatial homogeneous radio frequency alternating field can be produced in the measuring space 28.

An rf coil according to the invention as shown in Fig. 2, in this case in the form of a transversal electromagnetic coil as described in US 4,712,067, comprises current conductors 30 which are connected to electric ring conductors 34 <u style="single">via</u> capacitors 32. The ring conductors in this case have the form of flanges forming part of a cylindrical housing 35 having a cylinder surface 36 for screening the rf field to be generated by the coil from interference fields. In the embodiment shown the cylinder 35 also forms a mass electrode for the antenna wires and may also serve as a heat dissipating element. Antenna wire parts 38 are connected, <u style="single">via</u> a power amplifier 40 which comprises, for example, a MOS-FET transistor, to an amplitude and phase-controlling network 42 <u style="single">via</u> preferably coaxial connection cables 44. Uncoupling capacitor 46 for uncoupling purposes are incorporated in the antenna wire parts 38. In this manner each of the antenna wires can be energized individually by means of the control network 42; however, several antenna wires may also receive an equal supply. The supply for various antenna wires may also differ in phase only. The control network is supplied <u style="single">via</u> a connection cable 48 from an rf transmitter 49 corresponding to the rf source 12 in Fig. 1.

Fig. 3 shows in greater detail a part of a coil as shown in Fig. 2. An antenna wire 30 with a capacitor 32, flanges 34 and a cylinder surface part 36 of the coil are shown. <u style="single">Via</u> a sliding contact a power MOS-FET 52 is connected to a part 38 of the antenna wire. The antenna wire part 38 is coupled, on the one hand <u style="single">via</u> a capacitor 32, to the antenna wire 30 and on the other hand, <u style="single">via</u> an uncoupling capacitor 46, to the flange 34.

A supply source from which a fixed voltage of, for example, 50 V can be applied to the antenna wire is incorporated for a fixed supply for the antenna wire. The MOS-FET transistor 52 is connected, <u style="single">via</u> an input network 56 which comprises a coil 58 and a capacitor 60, to the amplitude and phase correcting network 42 <u style="single">via</u> a supply line 44. A quiescent current can be applied to the transistor 52 <u style="single">via</u> a resistor 62.

Fig. 4 shows an example of an amplitude and phase correcting network 42. This is connected to amplifiers 40 as shown in Fig. 2 <u style="single">via</u> the coaxial cables 44 and may be fed from the rf transmitter 49 <u style="single">via</u> the coaxial cable 48.

The network itself comprises N sections 70 each having an L-C circuit 72 built up from an inductance 74 and two capacities 76. The number of sections equals the number of antenna wires or groups of antenna wires to be controlled individually and in practical cases is, for example, 6 to 12. For generating a circularly polarized rf field the amplitude to be applied to each of the coil wires is equal but for each of the wires mutually shifted in phase so that the amplitude wave hence rotates with the desired frequency over the antenna wires of the coil.