Magnetic resonance imaging apparatus in which a rotating field is generated and detected

In a magnetic resonance imaging apparatus an RF rotating field is generated by applying RF energy to two mutually perpendicular coil systems, a 1/4.lambda. lead being provided between the connection points of the systems. In that case the drive points and the detection signal output points are not the same, so that in the case of a change-over from transmission to reception, the connection between the transmitter and the receiver must be switched over. In the magnetic resonance imaging apparatus in accordance with the invention, a phase difference of 180.degree. is created between two junctions by means of 1/4.lambda. leads so that an intermediate junction will actually not carry a voltage. This point (for transmission and reception, two different points) is connected to ground by means of a PIN diode. A simplification enables connection of the transmitter as well as the receiver to the transmitter/receiver coil system via a single coaxial cable.

The invention relates to a magnetic resonance imaging apparatus, comprising 
a device for generating and detecting RF electromagnetic fields, which 
device comprises a transmitter/receiver with two coils and electrical 
connection means for generating RF magnetic fields. 
A magnetic resonance imaging apparatus of this kind is known from European 
Patent Application No. 0,114,405. Therein, two separate coil systems are 
used for the transmission and reception of RF signals. In order to avoid 
mutual influencing between an RF transmitter coil and an RF detection 
coil, use must be made of an uncoupling circuit whereby, for example the 
circuit which includes the transmitter coil is adjusted to a substantially 
higher own frequency during activation of the transmitter coil. On the 
other hand, the transmitter coil can be short-circuited by a low-ohmic 
short-circuit circuit during detection by the receiver coil, so that the 
RF signals to be received are no longer disturbed. The book Nuclear 
Magnetic Resonance Imaging, published by Saunder's Company, Philadelphia, 
1983, describes that the transmitter coil and the receiver coil can be 
combined so as to form a receiver/transmitter coil. Obviously, the 
described problems are thus avoided. When two mutually perpendicular coil 
systems are used, a rotating field can be generated. The supply terminals 
of these coil systems must then be connected via a 1/4.lambda. lead in 
order to ensure that the signals are applied to each coil in the correct 
phase. However, the supply terminals for activation and reception of such 
coil systems are not the same, so that two supply terminals are required. 
When one terminal is connected to the transmitter, the other terminal must 
be uncoupled from the receiver. Similarly, when the receiver is connected 
to the second supply terminal, the transmitter will be uncoupled from the 
first supply terminal. The foregoing means that fast switching over is 
required. This is difficult notably when the assembly is included in a 
magnetic resonance imaging apparatus. Thus, standard switches cannot be 
used for this purpose. 
It is the object of the invention to provide a magnetic resonance imaging 
apparatus in which RF rotating fields can be generated as well as detected 
by means of the same coil system, without requiring mechanical switching 
contacts for coupling and uncoupling supply terminals to and from the 
transmitter or receiver. 
To achieve this, a magnetic resonance imaging apparatus in accordance with 
the invention is characterized in that in order to generate an RF rotating 
field, the magnetic fields generated by the coils extend perpendicularly 
to one another, a first supply terminal of a coil being connected, via a 
1/4.lambda. lead, to a second supply terminal whereto the other coil is 
connected, the first and the second supply terminal being connected, via 
phase-shifting connection means, to a first and a second junction, 
respectively, which are connected to the transmitter/receiver via 
connection means, the first junction being uncoupled from the second 
junction by means of electrical means during the transmission by the 
transmitter and the reception by the receiver.

A magnetic resonance imaging apparatus as shown in FIG. 1 comprises a 
magnet system 2 for generating a steady, uniform magnetic field HO, a 
magnetic system 4 for generating magnetic gradient fields, and supply 
sources 6 and 8 for the magnet system 2 and the magnet system 4, 
respectively. A magnet coil 10 serves to generate an RF magnetic 
alternating field; to this end, it is connected to an RF source 12. For 
the detection of spin resonance signals generated in an object to be 
examined by the RF transmitter field there is provided a detection coil 
13. For reading out, the detection coil 13 is connected to a signal 
amplifier 14. The signal amplifier 14 is connected to a phase-sensitive 
rectifier 16 which is connected to a central control and processing device 
18. The central control and processing device 18 also controls a modulator 
20 for the RF source 12, the supply source 8 for the gradient coils, and a 
monitor 22 for display. An RF oscillator 24 controls the modulator 20 as 
well as the phase-sensitive rectifier 16 which processes the measurement 
signals. The transmitter coil 10, being arranged within the magnet systems 
2 and 4, encloses a measurement space 28 which is spacious enough so as to 
accommodate a patient in the case of an apparatus for medical diagnostic 
purposes. Thus, a uniform magnetic field HO, gradient fields for position 
selection of slices to be imaged, and a spatially uniform RF alternating 
field can be generated within the measurement space 28. The detection coil 
13 is to be arranged within the space 28. 
FIG. 2 is a perspective representation of the transmitter coil 10 and the 
detection coil 13 in their relative positions. For the sake of simplicity, 
the mutual orientation shown here will be defined as the perpendicular 
orientation, because the planes defined by the turns of the transmitter 
coil and the detection coil are substantially perpendicular in this 
position. The transmitter coil 10 comprises two windings Z1 and Z2 which 
are connected to the RF source 12. The detection coil 13 comprises two 
windings D1 and D2 which are connected to the signal amplifier 14. The 
connection means MZ and MD between the transmitter 12 and the detector 14 
are customarily formed by coaxial cables which are permanently available 
to the transmitter 12 and the transmitter coil 10 as well as to the 
detector 14 and the detection coil 13, so that the transmitter coil 10 can 
only transmit and the detection coil 13 can only detect. Using the coil 
configuration shown, RF rotating fields can also be generated and detected 
when the supply terminals C and D are connected via a 1/4.lambda. lead 
(coaxial cable) and switches are included in the lead MZ as well as in the 
lead MD. When the switch in the lead MD is open, an RF rotating field can 
be generated by the transmitter 12 with the aid of the four windings Z1, 
Z2, D1 and D2. When the switch in the lead MZ is subsequently opened and 
the switch in the lead MD is closed, RF rotating fields can be detected by 
means of the four windings Z1, Z2, D1 and D2 and the detector 14 which RF 
rotating fields are generated by spin resonance signals excited by the RF 
transmitter field. The switching over of the switches in the leads MZ and 
MD is experienced to be annoying, because the procedure must be carried 
out very quickly (ms!) and in the presence of magnetic fields (see FIG. 
1). 
FIG. 3 shows an embodiment in which the functions of the described switches 
are replaced partly by PIN diodes which are set to a blocking state or a 
conductive state by control voltages. The circuit shown in FIG. 3 also 
comprises phase-shifting connection means between the supply terminals C 
and D on the one side and the junctions E and F on the other side. Between 
the points C and E, D and F, and E and F there are arranged 1/4.lambda. 
leads, each of which produces a phase shift of 90.degree. (in an ideal 
situation). For completeness' sake it is to be noted that the 
characteristic impedance of the latter three 1/4.lambda. leads amounts to 
half the characteristic impedance of the 1/4.lambda. lead between the 
points C and D. The shielding jackets of the 1/4.lambda. leads and of the 
connection means MT and MD are grounded at the areas denoted by the 
reference A in the figure. 
When the transmitter 12 is active, the voltages generated at the points E 
and D will be opposed. The voltage at the point F will then amount to zero 
volts in the ideal case. The point F could be connected to ground A 
without disturbing the transmitter 12 or the transmitter or receiver coil 
10 or 13. Similarly, when the transmitter 12 is not active, the voltages 
occurring upon reception (resonance signals detected by the coils 10 and 
13) will produce opposed voltages at the points C and F. As a result, the 
point E will not carry a voltage in the ideal case. The ideal situation 
will be reached only if: 
(a) all leads have a length of exactly 1/4.lambda. 
(b) the 1/4.lambda. leads are loss-free 
(c) the coils 10 and 13 have exactly the characteristic impedance of the 
leads 
(d) the characteristic impedances of the 1/4.lambda. leads are exact. 
In practice, this cannot be achieved; therefore, the junction F is 
connected to ground A via diode DF when the transmitter 12 is active. To 
this end, the base of the transistor T2 receives a control voltage .theta. 
which connects the lead MD, via a resistor R2, to a d.c. supply source V+ 
so that the PIN diode DF is conductive and connects the junction F to 
ground A. The capacitances C12 and CE are provided in order to uncouple 
the transmitter 12 and the diode DE, respectively, from the d.c. voltage 
V+. During reception, the control signal on the transistor T2 amounts to 
zero volts, whilst the base of the transistor T1 receives a control 
voltage T, so that the lead MT is connected, via a resistor R1, to the 
supply source V+ and the PIN diode DE connects the junction E to ground A. 
The transmitter 12 is uncoupled from the supply source V+ by means of the 
capacitance C12. 
FIG. 4 shows a preferred connection of a transmitter 12/receiver 14 to a 
coil system 10/13 (not shown), the transmitter 12 and the receiver 14 
utilizing a single connection means MTD (for example, a coaxial cable 
which is shielded in the same way as shown in FIG. 3). In the connection 
shown in FIG. 4, the 1/4.lambda. lead between the junctions E and F can be 
dispensed with as will be described hereinafter. The 1/4.lambda. 
connections between the points E and C, F and D, and C and D as well as 
the coil configuration 10, 13 connected to the supply terminals C and D is 
the same. However, the end of the cable MTD is connected on the one side 
to ground A via two parallel series connections of two PIN diodes each. 
The rectifying sense of the diodes DE1 and DF1 is opposed, like that of 
the diodes DE2 and DF2, none of the series connections DE1, DE2 and DF1, 
DF2 being conductive. 
When the lead MTD is connected to a supply voltage V- via a resistor R, the 
diodes DE1 and DF2 will be conductive so that point F is connected to 
ground A. In this situation the transmitter 12 can be active. When 
subsequently a supply voltage V+ is applied to the resistor R, the PIN 
diodes DF1 and DE2 will be conductive. The junction E is then connected to 
ground A and the receiver 14 receives, via the cable MTD and the diode DF1 
(being conductive), the resonance signals detected by the coils 10 and 13. 
It is to be noted that the diodes DE1, DE2, DF1 and DF2 as well as the 
1/4.lambda. leads can be combined with the coils 10 and 13 so as to form 
one unit which can be connected to a coaxial cable (MTD) so that a 
transmitter/receiver coil system is obtained which can be simply exchanged 
.