Magnetic resonance apparatus comprising a superconducting shielding magnet

Abstract: In a magnetic resonance apparatus comprising a superconducting magnet system (1) for generating a steady magnetic field there is also included a superconducting shielding coil system (22) in order to compensate for magnetic field variations induced in the magnet by external magnetic flux variations. The shielding coil system (22) comprises coil sections (24) of different diameter.

Description: The invention relates to a magnetic resonance apparatus, comprising a superconducting steady field magnet coil system for generating a magnetic field in a measurement space within the magnet and also comprising a superconducting shielding coil system which is arranged so as to be coaxial with the steady field magnet coil system, the shielding coil system comprising coil sections of different diameter. A magnetic resonance apparatus of this kind is disclosed in EP-A-0 167 243. In the known apparatus, the length of shielding coil system exceeds the length of the steady field magnet system. This results in a comparatively long coil system. Superconducting MR magnets are customarily used in the so-called persistent mode where the magnet is short-circuited in itself and, if the magnet coil circuit is suitably superconducting, current and field will remain very stable over a prolonged period of time. When a magnet thus short-circuited is exposed to a varying, externally generated magnetic field, for example originating from a moving magnetized object or resulting from a varying electric current, the total magnetic flux enclosed by the magnet will remain constant. When the external field causes a magnetic flux in the magnet, the current in the magnet will change so that the variation of the flux within the magnet will be equal but opposed to the external magnetic flux. Within the magnet a current variation causes a field variation whose extent is co-determined by a coil constant of the magnet. This field variation is generally opposed to the external field variation. It is to be noted that US-A-4,974,113 discloses a coil system which aims to reduce the effect of external field variations on the measurement field homogeneity, but also this solution leads to a comparatively long coil system. It is an object of the invention to provide a magnetic resonance apparatus of the kind set forth in which the coil system can be relatively short. To achieve this, the magnetic resonance apparatus according to the invention is characterized in that the shielding coil system comprises three series-connected coaxially mounted coil pairs, an inner pair and an outer pair, viewed in the axial direction, and a central pair situated between the inner pair and the outer pair, the central pair having a diameter that exceeds the diameter of the inner end the outer pair, the steady field magnetic coil system comprising two halves that are mirror-symmetrically arranged about the central plane perpendicular to the axis of the coil system, and each coil pair of the shielding coil system being mirror-symmetrically arranged about the central plane. A shielding factor which is strongly dependent on the geometry of the coil can be assigned to a magnet coil system. A superconducting MR magnet may consist of, for example six coaxial coil sections of the same diameter which have a geometry such that the field is uniform up to the 12 th order and have a shielding factor of approximately 0.75, which value is dependent on, for example the width of the coil sections. This means that with the magnet the effect of an external field variation is reduced by induction to approximately one quarter of that outside the magnet. The aforementioned class of magnets with active stray field compensation constitute a special case. The superconducting circuit then consists of coil sections having two different diameters, the coils of the greatest diameter having an opposed polarity. One requirement to be satisfied so as to achieve suitable own stray field suppression consists in that the magnetic dipole moment must be substantially zero. The shielding factor, being proportional thereto, thus also becomes substantially zero. An actively shielded superconducting magnet, therefore, has no significant compensating effect as regards external field variations. In order to reduce any reciprocal induction between coils of a magnet coil system in accordance with the invention, the shielding coil system comprises three pairs of coil sections with two different diameters. Optimum shielding can thus be combined with, for example due to the configuration of the winding, a high degree of field homogeneity for the shielded magnet system. The shielding coil system is notably coaxial and mirror-symmetrical with respect to an axial central plane and comprises coil sections of mutually the same polarity with diameters adapted to coil sections of the magnet coil system. Thus, shielding coil systems can be realised which can be mounted in a common Dewar vessel, preferably on supports for coil sections of the steady magnet coil system, their length in any case not being substantially greater than that of the main magnet. Using, for example an axially most inwards situated shielding coil pair, the shielding and the field homogeneity can be optimized. From a constructional point of view, actively shielded magnet systems make the use of shielding coil sections of mutually different diameter comparatively simple by adaptation of diameters to inner or outer diameters of the two coil systems thereof. In a preferred embodiment superconducting switches are included in the shielding coil circuit in order to prevent high current intensities in shielding coils, for example due to quenching or upon activation of the magnet etc. Some preferred embodiments in accordance with the invention will be described in detail hereinafter with reference to the drawing. Therein: Fig. 1 diagrammatically shows a magnetic resonance apparatus in accordance with the invention, and Fig. 2 shows an embodiment of a coil system for such an apparatus. A magnetic resonance apparatus as shown in Fig. 1 comprises a steady field magnet with an electromagnetic coil system 1 which comprises, for example from four to eight coils 2 for generating a strong, steady, uniform magnetic field in a measurement space 3 within the coil system. For various feasible coil systems reference is made to Nuclear Magnetic Resonance "NMR" Imaging W.B. Saunders Company, pages 121-123. For the use as a magnetic resonance tomography apparatus, i.e. an apparatus for the slice-wise imaging of an object, to be described hereinafter use is made of gradient coils 4. In magnetic resonance spectrometry apparatus, i.e. apparatus for the detection of various spin types of elements or molecules in an object, the gradient coils can be dispensed with. Furthermore, RF coils 5 are arranged comparatively closely around the measurement space, which RF coils serve as transmitter coils for an RF electromagnetic field and as a detection coil for spin resonance signals thus generated. It is alternatively possible to use separate coils for these two functions. Spin resonance signals stimulated by the RF electromagnetic field in an object to be measured are picked up via a signal amplifier 6 and applied, via a phase-sensitive amplifier 8, to a central arithmetic and control device 10. Also shown are a modulator 12 for an RF supply source 14, a supply source 16 for the main field magnet coils, a supply source 17 for the gradient coils, an RF oscillator 18, and a monitor 20 for image display. The oscillator 18 controls the modulator 12 for the RF fields as well as the phase-sensitive amplifier 8 which processes the measurement signals. In accordance with the invention, a shielding coil system 22 with a control device 25 is arranged concentrically around or in the steady field magnet coil system. In a preferred embodiment, the shielding coil system, in this case adapted to a steady field magnet system with active own shielding, comprises three pairs of coil sections 24, an inner pair 241 and an outer pair 243, viewed in the axial direction, of which are mounted on a coil former for a first magnet coil system 26 of the main magnet 1, a central pair 242 being arranged on a coil former for a second magnet coil system 28 of the main magnet 1. The shielding and the field homogeneity can be optimized notably by way of the axial length and the winding configuration of the coil pair 241. It has already been stated that many coil configurations are feasible which satisfy the requirements imposed. A simple solution consists in simple solenoid coils having a finite length with a uniform number of turns per unit of length. Calculations demonstrate that as a function of the length-to-diameter ratio of the solenoid the shielding factor 1 of this type of coil is achieved for a length-to-diameter ratio of 1.75. When the coil is longer, an external field variation is overcompensated, whilst a shorter coil offers inadequate compensation for an external field. A length-to-diameter ratio of 0.875 is unpractical for a practical MR magnet. In the embodiment described with reference to Fig. 2 a substantially shorter coil system having the shielding factor 1 is obtained by utilizing two coaxial coils of different diameter, which coils together constitute a closed superconducting circuit. It is desirable to design the shielding coil system so that a high field homogeneity is achieved within the coil. Such a high homogeneity is desirable because, in the event of poor homogeneity the shielding factor outside the isocentre will not be equal to that in the isocentre; this difference may not become excessively large. Furthermore, if a nett inductive coupling exists between the superconducting magnet and the superconducting shielding coil, field drift of the magnet, caused by its residual resistance, will induce a current in the shielding coil which is liable to become much greater than the current variations induced due to external interference fields; the field of this drift-induced current may not have an adverse effect on the homogeneity of the magnet system. When reciprocal induction occurs between a shielding coil and the magnet coil, the variation in the coil current induced due to the inductive coupling must also be taken into account in the calculation of the shielding coil configuration. In order to prevent large currents in the secondary system in the case of quenching of a primary coil, it is desirable that the reciprocal induction is then approximately zero. Because the current intensity through current windings of the shielding coil system is comparatively low, it is usually possible to utilize superconductors having a comparatively low I c , for example single current conductors composed of a superconducting core wire and a non-superconducting sheath.

Claims: A magnetic resonance apparatus, comprising a superconducting steady field magnet coil system (1) for generating a magnetic field in a measurement space within the magnet and also comprising a superconducting shielding coil system (22) which is arranged so as to be coaxial with the steady field magnetic coil system, the shielding coil system comprising coil sections (241,242,243) of different diameter, characterized in that the shielding coil system (22) comprises three series-connected coaxially mounted coil pairs, an inner pair (241) and an outer pair (243), viewed in the axial direction, and a central pair (242) situated between the inner pair and the outer pair, the central pair having a diameter that exceeds the diameter of the inner and of the outer pair, the steady field magnetic coil system (1) comprising two halves that are mirror-symmetrically arranged about the central plane perpendicular to the axis of the coil system, and each coil pair of the shielding coil system (22) being mirror-symmetrically arranged about the central plane. A magnetic resonance apparatus as claimed in Claim 1, characterized in that the shielding coil system (22) comprises a superconducting solenoid. A magnetic resonance apparatus as claimed in Claim 1 or 2, characterized in that the shielding coil system (22) is composed of coil pair sections (242,243;242) mounted on formers for magnet coils (26;28) of the steady field magnet. A magnetic resonance apparatus as claimed in any one of the preceding Claims, characterized in that coil sections (241,242,243) of the shielding coil system (22) are wound using a single superconducting wire provided with a non-superconducting sheath. A magnetic resonance apparatus as claimed in any one of the preceding Claims, characterized in that a superconducting switch is included in the superconducting magnet coil circuit of the shielding coil system (22). A magnetic resonance apparatus as claimed in Claim 1, characterized in that the shielding coil system comprises (22) a bush of a superconducting material.

Inventors: OVERWEG JOHANNES ADRIANUS, PEEREN GERARDUS NERIUS, OVERWEG, JOHANNES ADRIANUS, PEEREN, GERARDUS NERIUS
Applicants: KONINKL PHILIPS ELECTRONICS NV, KONINKLIJKE PHILIPS ELECTRONICS N.V.
Application year: 1991
Main classification: G01R33
IPC codes: A61B5, H01F7, G01R33