CRYOSTAT FOR SUPERCONDUCTIVE MAGNET

Abstract

A split cylindrical superconducting magnet system including two half magnets, each half magnet comprising superconducting magnet coils retained in an outer vacuum chamber, having a thermal radiation shield located between the magnet coils and the outer vacuum chamber, wherein the thermal radiation shield is shaped such that the axial spacing between thermal radiation shields of respective half magnets is greater at their internal diameter than at their outer diameter.

Claims

1. A split cylindrical superconducting magnet system comprising two half magnets, each half magnet having superconducting magnet coils retained in an outer vacuum chamber, a thermal radiation shield located between the magnet coils and the outer vacuum chamber, wherein the thermal radiation shield is shaped such that axial spacing between thermal radiation shields of the respective half magnets is greater at their internal diameter than at their outer diameter.

2. The split cylindrical superconducting magnet system according to claim 1, wherein the thermal radiation shield is shaped so as to be absent in a position nearest the imaging region by a step profile in a cylindrical shape of the thermal radiation shield.

3. The split cylindrical superconducting magnet system according to claim 1, wherein the thermal radiation shield and the outer vacuum chamber are similarly shaped.

4. The split cylindrical superconducting magnet system according to claim 1, wherein the thermal radiation shield is chamfered, tapering from a minimum inner diameter to an increased inner diameter.

5. The split cylindrical superconducting magnet system according to claim 1, wherein the thermal radiation shield has a concave dished shape from a minimum inner diameter to an increased inner diameter.

6. The split cylindrical superconducting magnet system according to claim 1, wherein the thermal radiation shield has a convex dished shape from a minimum inner diameter to an increased inner diameter.

7. A split cylindrical superconducting magnet system according to claim 1, wherein recesses are provided near the axially and radially inner extremities of the thermal radiation shields of respective half magnets.

8. A split cylindrical superconducting magnet system according to claim 7, wherein the recesses are employed to mount ancillary equipment or to provide improved access for an operator.

9. A split cylindrical superconducting magnet system according to claim1, further comprising structural components which are encased in the cryostat and separate the magnet coils.

10. A split cylindrical superconducting magnet system according to claim 1, further comprising structural components which support each of the magnet coils on the respective outer vacuum chamber half, and then supports the two outer vacuum chamber halves.

11. A split cylindrical superconducting magnet system according to claim 10, wherein a mechanical support structure bears against the two outer vacuum chambers at or near their outer diameters, at their axially inner extremities.

12. A split cylindrical superconducting magnet system according to claim 11, wherein the mechanical support structure is intermittent around the circumference of the cylindrical superconducting magnet system.

13. A split cylindrical superconducting magnet system according to claim 10, wherein a mechanical support structure bears against the two outer vacuum chambers at or near their inner diameters, at their axially and radially inner extremities.

14. A split cylindrical superconducting magnet system according to claim 10, wherein a mechanical support structure is attached to the two half outer vacuum chambers on their radially outer surfaces, away from their axially and radially inner extremities.

Description

BRIEF DESCRIPTION OF THE FIGURES

[0014] The above, and further, objects, characteristics and advantages of the present disclosure will become more apparent from the following description of certain embodiments thereof, given by way of non-limiting examples only, in conjunction with the appended drawings, wherein:

[0015] FIG. 1 schematically illustrates an example conventional cryostat arrangement 10 for a split superconducting magnet;

[0016] FIGS. 2-8 schematically illustrate example embodiments of the present disclosure.

DETAILED DESCRIPTION

[0017] In designing a superconducting magnet, for example a magnet for an MRI system, with a central gap, superconducting magnet coil positions must be compromised. In the example of FIG. 1, for example, coils 12 may not be positioned at or near the axial midpoint of the magnet. In embodiments of the present disclosure, it can be determined that no superconducting coil should be placed close to the magnet bore 28 near the gap 26 between the two halves of the magnet. Conventional simulation and design methodology will allow coils to be positioned elsewhere and dimensioned appropriately to achieve a required background field.

[0018] The example design 30 represented on FIG. 2 shows that superconducting coils 12 are not located near to the magnet axis A-A in the vicinity of gap 24. According to a feature of the present disclosure, the thermal radiation shield 16 is shaped so as to be absent in the position nearest the imaging region 26. This may be achieved as illustrated in the drawing, by a step profile in the cylindrical shape of the thermal radiation shield 16, including a planar annular component 16a and a cylindrical component 16b of diameter intermediate between a diameter of an inner cylindrical surface 16c and a diameter of an outer cylindrical surface 16d.

[0019] The position nearest the magnet axis A-A and nearest the gap 24 is the position nearest to the imaging region 26 and is the region where magnetic field fluctuations will have the most deleterious effect on image quality. It is also in this region that gradient magnetic field interaction with the thermal radiation shield 16 is likely to be strongest. Eddy currents induced in surfaces like the thermal radiation shield 16 will generate their own opposing magnetic fields at the same frequency as the gradient field. These may interfere with the imaging fields in imaging region 26.

[0020] An advantage of the present disclosure is that the electrically conductive surface of the thermal radiation shield 16 is moved away from the position nearest the imaging region 26, which is also the position nearest the magnet axis A-A and nearest the gap 24. This depletes the magnitude of the induced eddy currents in the thermal radiation shield, because they are effective at a greater distance from the gradient coils 18 whose magnetic fields induce the eddy currents. The eddy currents are also induced further from the imaging region 26, and any effect of the eddy currents takes place further from the imaging region, depleting still further any deleterious effect on the magnetic field in the imaging region 26.

[0021] FIG. 2 shows an example embodiment where the profile of cryogen vessel 14, thermal radiation shield 16 and OVC 18 are changed.

[0022] As illustrated in the embodiment of FIG. 3, the present disclosure may result in a changed profile of the thermal radiation shield 16 only, in embodiments which do not include a cryogen vessel 14; or changed profile of the thermal radiation shield 16 and cryogen vessel 14, while OVC 18 remains unchanged. Alternatively, as shown in the embodiment of FIG. 2, the thermal radiation shield 16 and the OVC 18 may be similarly shaped. In the example of FIG. 2, both the thermal radiation shield 16 and the OVC 18 are absent from the position nearest the magnet axis A-A and nearest the gap 24, that is, nearest the imaging region 26.

[0023] Alternatively to the arrangements of FIGS. 2-3 in which part of the thermal radiation shield 16 has a portion near imaging volume 26 with an increased inner diameter, alternative embodiments may be employed, as shown in FIGS. 4-5.

[0024] For example, in FIG. 4, part of the thermal radiation shield is chamfered, tapering from a minimum inner diameter at 16c to an increased inner diameter at 16e.

[0025] In FIG. 5, the thermal radiation shield has a concave dished, e.g. part-spherical, shape from a minimum inner diameter at 16c to an increased inner diameter at 16e. A similar, convex dished shape could alternatively be employed.

[0026] In preferred embodiments of the present disclosure, recesses 32 are provided near the axially and radially inner extremities of the thermal radiation shields (cryoshields) of respective half magnets. These recesses 32 may be employed to mount ancillary equipment or to provide improved access for an operator.

[0027] Using the example structure of FIG. 4, FIGS. 6-8 show examples of support structure which may be employed in magnet systems according to the present disclosure. The radiation shields are typically not structural, in which case the support geometry must separate the magnet coils. This can either be through structural components which are encased in the cryostat, or support the magnet coils on the OVC half, and then supporting the two halves.

[0028] As already discussed with reference to FIG. 4, part of the thermal radiation shield is chamfered, tapering from a minimum inner diameter at 16c to an increased inner diameter at 16e. In use, the two half magnet systems will experience very strong mutual attractive forces, in the order of several tonnes. In non-split cylindrical magnets, such attractive forces are typically borne by a structure directly supporting the magnet coilssuch as a cylindrical former. In the systems of the present disclosure, a split magnet system is required, to allow access for radiation therapy equipment, or other equipment such as biopsy, CT or angiography equipment, to access the imaging region. Mechanical restraints must therefore be provided to bear the mutual attractive forces between the two half magnet systems.

[0029] In FIG. 6, OVCs of the two half magnet systems are illustrated at 18. As in FIGS. 7-8, only a half-cross-section of the relevant component is shown, the component itself being essentially rotationally symmetrical about the magnet axis, which is not visible in this drawing. Mechanical support structure 34 is shown bearing against the two OVCs 18 at or near their outer diameters, at their axially inner extremities. The attractive force between the magnet coils would be transmitted through a coil mounting structure to the structure of the half OVCs, then the attractive force may be borne by the mechanical support structure 34. The mechanical support structure 34 is preferably intermittent around the circumference of the cylindrical superconducting magnet system, for example in the form of separate bars linking the two half OVCs 18 together. This allows access for the radiation treatment apparatus 22 or other apparatus such as biopsy, CT or angiography apparatus, which may form part of the apparatus of some embodiments of the present disclosure. Such radiation treatment apparatus requires a low attenuation path for the treatment beam 20.

[0030] FIG. 7 illustrates a similar structure, but in which a mechanical support structure 36 is shown bearing against the two half OVCs at or near their inner diameters, at their axially and radially inner extremities. The attractive force between the magnet coils would be transmitted through a coil mounting structure to the structure of the half OVCs, then the attractive force may be borne by the mechanical support structure 36.

[0031] FIG. 8 illustrates an alternative structure, but in which mechanical support structure 36 is shown attached to the two half OVCs on their radially outer surfaces, away from their axially and radially inner extremities. The attractive force between the magnet coils would be transmitted through a coil mounting structure to the structure of the half OVCs, then the attractive force may be borne by the mechanical support structure 38. An advantage of such arrangement may be in that a cylindrical space 40 may be created, and that radiation treatment apparatus 22 may be provided in that cylindrical space 40, and be free to rotate about the magnet axis A-A.

[0032] In consideration of the effect on magnetic field quality in the imaging region 26, the worst (most troublesome) place to create eddy currents is near the axial midpoint of the magnet in the middle, nearest the imaging volume 26. That part of the cryoshield is removed in the present disclosure, to a more distant location, where interaction with gradient fields is reduced, and the effect of mechanically-induced magnetic field variations has little effect in the imaging region 26.

[0033] As provided in the present disclosure, the absence of conductive materials of the thermal radiation shield removes the need for the gradient coil to have effective magnetic shielding in the volume nearest the imaging region 26.

[0034] Mechanical vibrations which may occur in the thermal shield generate eddy currents due to interaction with the magnetic field of the superconducting magnet. Such eddy currents produce magnetic field fluctuations in the imaging region 26 of the magnet. By recessing the thermal radiation shield (cryoshield), it is moved further away from the imaging volume 26 and such eddy current induced fields are correspondingly displaced away from the imaging region.

[0035] By integrating the field contribution along the thermal shield, a reduction by a factor of 2 may be achieved relative to an integrated field contribution of a conventional non-recessed thermal shield. The energy absorbed by the thermal shield is created by an accumulation of the gradient stray field along the whole length of the bore due to the eddy currents induced. If significant portions of this bore tube are removed, or transferred to a larger diameter, as proposed in the present disclosure, the eddy current power dissipation is reduced.

[0036] The recessed shape also improves mechanical stiffness of the thermal radiation shield, which should also contribute to a reduction in eddy current generation by reduction in magnitude of mechanical oscillations.

[0037] The recess feature can apply to the thermal radiation shield only (and any cryogen vessel) or to the OVC as well. Although the OVC is typically made of a relatively resistive material such as stainless steel, which will not suffer greatly from eddy current effects, some OVCs are made of a more conductive material such as aluminium. Such OVC may suffer from eddy current effects, and so may benefit from the recessed shape proposed by the present disclosure.

[0038] For wet magnet systems which include a cryogen vessel, the cryogen vessel must also be recessed, to provide space for the recess in the thermal radiation shield.

[0039] In all embodiments, however, the thermal radiation shield (cryoshield) is shaped such that, at its closest point, it is further from the imaging region 26 than it would be if it were of simple rectangular half-cross-section.

[0040] The disclosure accordingly provides a split cylindrical superconducting magnet system such as may be employed in a combined MRI-radiation therapy system, comprising two half magnets, each half magnet comprising superconducting magnet coils 12 retained in an outer vacuum chamber 18, having a thermal radiation shield (cryoshield) 16 located between the magnet coils 12 and the outer vacuum chamber 18, wherein the thermal radiation shield (cryoshield) 16 is shaped such that the axial spacing between thermal radiation shields (cryoshields) 16 of respective half magnets is greater at their internal diameter 16a than at their outer diameter 16d. Such shaping of the thermal radiation shields (cryoshields) of respective half magnets relaxes the requirement for shielding of the thermal radiation shields (cryoshields) of respective half magnets from oscillating magnetic fields of the gradient coils 18. This may simplify design of gradient field coils and/or gradient shield coils. The effect of eddy currents generated by mechanical vibration of the thermal radiation shields (cryoshields) within a static background field may be reduced by a factor of two, so improving the stability of the magnetic field for imaging.