Magnetic field generating apparatus

Abstract: Magnetic field generating apparatus comprises a solenoid arranged to generate a steady magnetic field gradient along its axis. The arrangement is such that in use contours of constant field are formed within the solenoid. The contours extend generally radially outwardly from the axis of the solenoid and asymmetrically with respect to the centre plane of the solenoid orthogonal to its axis. Regions of substantially homogeneous magnetic field suitable for performing an NMR experiment exist about each contour, the regions having substantially constant thickness along the contours.

Description: The invention relates to magnetic field generating apparatus particularly for use in performing a nuclear magnetic resonance (NMR) experiment. NMR experiments rely on placing a sample to be examined in a controlled magnetic field, generally having a high homogeneity. MRI magnets have been designed to produce spherical zones of homogeneity by cancelling between axial coil arrays low error order terms, say Z2 and Z4, and as many higher order terms as permited by cost constraints. It is well known that an array of n axial coils will correct up to 2n axial even orders - ie. a four coil magnet corrects Z 2 , Z 4 , Z 6 (there are always considered an even number of coils symmetrically placed about the midplane of the magnet). The diameter of the homogeneous zone increases as higher orders are cancelled, but it becomes more costly to do this as more coils are needed. Now it happens, that the higher order terms contribute to the net field at a radial point more strongly as the radius of the homogeneous zone increases. Another way of looking at this is to say that as the considered field point is moved out in radius, closer to the inner radius of the coils, the local field contribution of the nearest coil dominates the situation, increasing the rate of field charge with radius. Therefore, it is usual to accept that MRI magnets, comprised of a few discrete coils are designed to produce useable homogeneity over, perhaps half of their bore diameter. It is too costly to correct a large number of high orders by discrete arrays. As the maximum diameter of the object subjected to NMR is increased, the magnet bore size has to be increased therefore in the ratio of, magnet bore diameter is twice maximum subject diameter. Increasing the diameter of the coil set is costly in superconductor. The following simple analysis shows that for fixed field and conductor hoop stress, cost rises in proportion to the radius cubed. V = 2πa A n, a = coil radius, A = coil cross-section, n = nos turns Stress in a turn σ ≃ I*Bz*a/A. I = current, Bz is local axial field σ*I≃a*Bo/A,Bo≃Bz where Bo is the bore field Bo =µo*n*I/a, for a simple coil Substituting for I Cost = (2π/µ)*a 3 *Bo 2 /σ Conventional MRI magnets are not satisfactory, therefore, for examining relatively large objects where the areas of interest extend beyond the region which can be placed within the spherical homogeneous region even though the object can be placed within the coils. EP-A-0187691 discloses a magnetic assembly for use in magnetic resonance imaging apparatus, an examination assembly comprising six electrical coils arranged asymmetrically about an axis. The coils are arranged to generate a substantially uniform magnetic field at a point offset from the geometric centre of the assembly. EP-A-0404461 discloses a magnetic field assembly for generating magnetic field gradients across the region. The assembly comprises a Y gradient coil assembly, which applies gradients along a Y axis, and a X gradient coil assembly, which selectively applies gradients in the X direction. The gradient coil assemblies include two coils mounted on opposite sides of the examination region, with these coils being arranged symmetrically relative to the axis of the apparatus (conventionally designated the Z axis). In addition to these gradient assemblies, there is also provided a Z gradient coil assembly which includes a pair of annular or other conventional coils for creating gradients on the Z axis. EP-A-0134701 discloses applying a bias field to the gradient field of an NMR imaging system to offset the nil point in the gradient field from its nominal position. The bias field is induced by a separate bias coil which may take any shape, so long as the fields produce results in an essentially uniform offset in the main field. In the preferred embodiment the bias coil arrangement comprises a pair of current loops forming a Helmholz coil configuration. In accordance with the present invention, we provide magnetic field generating apparatus comprising a plurality of coaxial coils spaced apart and along an axis characterised in that the apparatus further comprises a solenoid having a plurality of turns about said axis, wherein said coils are positioned relative to each other and to said solenoid such that when working currents flow through said coils and said solenoid a magnetic field is generated within said solenoid, said magnetic field having a zero order component and a first order gradient with high order gradients being substantially balanced, wherein said magnetic field has contours of constant value extending with a radially outward component from said axis of said solenoid, and wherein regions of substantially homogeneous magnetic field for performing an NMR experiment are formed about said contours, said regions extending along said contours and having a substantially constant thickness on either side of said contours. We have realised that if an odd order gradient is applied to a solenoid, the spherical central region which is normally present at the centre of a solenoid suitable for NMR is largely removed and a set of saucer shaped high homogeneity planes are generated, there being a gradient between the planes, that extends to the diameter of the solenoid. We are then able to illuminate a subject of given diameter with a coil set of approximately the same diameter, and benefit from the r 3 cost savings. In Table 1 below conductor quantity for 2.OT, 70 MPa MRI magnets, spherical homogeneity is compared with a solenoid of similar length, planar homogeneity, where both are able to illuminate a subject 0.8 m diameter. Comparison of a solenoid for planar homogeneous zones and a "standard" MRI magnet Comparison at 2.0T 70MPa hoop stress: - "MRI array 6 coil" Mean coil radius 80cm Mean overall length 246cm Homogeneous sphere ± 100ppm 80cm Conductor at 100T cm -2 515554m - Gradient Solenoid Mean coil radius 40cm Mean overall length 400cm Homogeneous sphere ± 100ppm 80cm Conductor at 100T cm -2 122447m A further significant advantage of this apparatus is that the working regions will extend substantially fully across the diameter of the solenoid. Consequently, much larger areas of the sample can be investigated than has previously been possible. For example, inanimate objects such as polymer composites and the like can be investigated. The gradient field also breaks the symmetry which would otherwise exist on either side of the mid-plane of the solenoid so as to remove further spatial ambiguity. In contrast to conventional magnets used in NMR in which the low order field terms are balanced, in the present invention a solenoid with a relatively large aspect ratio can be used which will enable higher order error terms to be balanced with the low order error terms remaining to define the axial gradient. The invention thus envisages the use of low order axial gradients (particularly first order) which are normally eliminated in NMR magnets. It should also be noted that solenoids of practical dimensions, which will possess a positive second order axial gradient can be used. This second order governs the shape of the homogeneous regions but in "pure form" simply dishes the homogeneous regions, while a first order gradient controls the thickness of the homogeneous regions. Preferably, therefore the first order gradient is greater than or equal to the second order gradient. The invention provides an additional advantage, when considering solid state NMR, which is that the gradient between planar homogeneous zones ensures that it is easier to provide an appropriate RF field. That is an RF field that is orthogonal to the field of the magnet everywhere in the homogeneous zone and follows the same value everywhere in space as a function of time for any pulse sequence. An example of magnetic field generating apparatus according to the present invention will now be described according to the accompanying drawings, in which:- Figure 1 illustrates the field profile within a conventional solenoid; Figure 2 illustrates the field profile within the same solenoid but modified by the addition of a gradient magnetic field generator in accordance with the invention; Figures 3A-3J illustrate the effect of different Z 1 and Z 2 gradients on the homogeneous regions; Figure 4 illustrates the coil dimensions referred to in Table 4; and, Figure 5 shows a cross section through the conductor of the coil of Figure 4. Figure 1 illustrates contours of constant field which exist in a simple solenoid. The plot is of radius R in cm against axial length Z in cm from mid plane or origin of magnet. The dimensions of the solenoid whose field is illustrated are inner radius = 30cm, outer radius = 31.72cm, length to the mid plane = 75cm and current density = 10,050 A/cm 2 . In this Figure, the contours are shown at three different field values separated by 100 gauss (2000, 19900 and 19800 Gauss 1,2,3). The thicknesses of regions of homogeneity centred at ±10 gauss from the nominal value are shown. These regions are generally deeply dished and because of the symmetry about the mid-plane, together with the central spherical region of field homogeneity, the central sections of the regions are thickened and merge with their partners in symmetry. This is unsatisfactory if attempts are made to use the dish shaped regions by reason of ambiguity due to the symmetry, the extreme curvature of the working regions, and also their varying thicknesses. Figure 2 illustrates the effect of modifying the solenoid so that at least the first order terms are not balanced and a steady linear, axial field gradient is generated. Firstly, the symmetry between the regions on either side of the mid-plane is removed. Secondly, the thickness of the working regions becomes determined more by the gradient and less by the properties of the solenoid. This is shown in Figure 2 in the case of applying a gradient of 10 gauss/cm for 19800, 19900, 20000 Gauss 4,9;5;8;6,7. It can be seen also that the gradient has a beneficial effect on the flatness of the working regions which have substantially constant thicknesses and extend close to the inner circumference of the solenoid. Lines 10,11,12 illustrate the results for application of a gradient of 60 Gauss cm for 19800, 19900 and 20000 Gauss. A gradient will exist in the axial direction so that when an NMR experiment is performed, it is necessary dynamically to cancel that gradient but this can be done using conventional NMR technniques. Tables 2 and 3 below set out the coil configurations used to achieve the field profiles shown in Figures 1 and 2 respectively. In these Tables, a1 and a2 are the internal and external radii of the solenoid, while b1 and b2 are the positions of the ends of the solenoid relative to the mid-plane. The affect of Z1 and Z2 gradients can be seen from Figure 3 which illustrates plots obtained by computer simulation of contours defining a field variation of ±100ppm relative to the centre of the region. Figures 3A-3E relate to a Z1 component with a homogeneity of 500ppm at a 25cm radius with Z2 varying from 100 to 500ppm in steps of 100ppm starting at 100 pp, at 3A. Figures 3F-3J were obtained for a component with a homogeneity Z1 of 1000 ppm and Z2 varying from 200ppm to 1000ppm in 200ppm steps starting at 200ppm for 3F. The dark plot indicates positive distortion and the light plot negative distortion. It can be seen that an increase in the Z2 component causes an increased dishing of the homogeneous region while an increase in the Z1 gradient causes the region to narrow. An example of a coil configuration suitable for this invention is set out in Table 4 below. The dimensions quoted are illustrated in Figure 4. Figure 5 is a cross section through the conductor. The reference numerals in Figures 4 and 5 refer to dimensions shown in the table as follows. B 1 ; 13; B 2 , 14; midplane 15; centre line 16; A 1 ; 18; A 2 ; 17; δ r ; 19; δ z , 20. AA = (A 2 - A 1 ) /2 ΔB = B 2 - B 1 BA = (B 2 + B 1 ) /2 The system of Table 4 is effectively a combined dipole (coils 1 and 2) and quadrupole (coils 3-5). The dipole is essentially a solenoid (coil 1) with correcting pair (coil 2). This system produces Z0 = 48.5 Gauss/Amp ≡ 2 Tesla at 412.33 Amps Z2 = 41 ppm on 25 cm radius Z4 = 26 ppm Z6 = -105 ppm Z8 = -15 ppm Z10, Z12 are <|1|ppm The quadrupole is essentially a "z gradient" coil set, outside the dipole. The field harmonics are Z1 = 0.4144 Gauss/Amp on 25cm radius ≡ ± 100ppm of 2T in 5.6mm δz Z3 = -1 ppm Z5 = -5 ppm Z7 = -10 ppm Z9 = -1.5 ppm Z11 = -1.4 ppm

Claims: A magnetic field generating apparatus, comprising: a plurality of coaxial coils spaced apart and along an axis characterised in that the apparatus further comprises a solenoid having a plurality of turns about said axis, wherein said coils are positioned relative to each other and to said solenoid such that when working currents flow through said coils and said solenoid a magnetic field is generated within said solenoid, said magnetic field having a zero order component and a first order gradient with high order gradients being substantially balanced, wherein said magnetic field has contours of constant value extending with a radially outward component from said axis of said solenoid, and wherein regions of substantially homogeneous magnetic field for performing an NMR experiment are formed about said contours, said regions extending along said contours and having a substantially constant thickness on either side of said contours. The magnetic field generating apparatus according to claim 1, wherein said magnetic field generated by said solenoid and said coils further includes a second order gradient, said first order being at least equal to said second order gradient. The magnetic field generating apparatus according to any of the preceding claims, wherein said coils are positioned radially outwardly from said solenoid.

Inventors: HANLEY PETER, HAWKES ROBERT CARTER, MCDOUGALL IAN LEITCH, HANLEY, PETER, HAWKES, ROBERT CARTER, MCDOUGALL, IAN LEITCH
Applicants: OXFORD INSTR UK LTD, OXFORD INSTRUMENTS (UK) LIMITED
Application year: 1992
Main classification: G01R33
IPC codes: A61B5, G01R33