Furthermore, the present invention relates to an improved Magnetic Resonance Imaging (MRI) system, in particular having a less confined patient space.

MRI systems consist of a magnet which provides a primary magnetic field, a set of gradient coils to superimpose a linearly varying field as a function of time over the primary magnetic field, and an RF coil transmit/receive system which is used to receive the signals that are used to construct the image. A high degree of homogeneity of the primary magnetic field in the system is essential for producing good quality images. These fields can be generated by a number of devices, such as coil magnets or permanent magnets, or a combination of the two.

Ferromagnetic material is known to be used, in addition to the above magnetic field generators, to increase the field strength, improve homogeneity, and to limit stray magnetic fields.

Where high magnetic fields are required with a magnetic induction of 0.5 Tesla or more, superconducting coils are used. Most superconducting MRI magnets consist of an assembly of coaxial superconducting coils. These coils are positioned in such a way that the required field strength and homogeneity is achieved. In these type of magnets the patient is positioned with the head-feet axis in line with the axis of the coils. The disadvantage of such an arrangement is that the

patient has to be located inside a tube, which makes the patient feel trapped and causes him stress.

Figure 1 is a known magnetic assembly 10 comprising an arrangement of coaxial pairs of superconducting coils la, lb, 2a, 2b with currents running in the opposite sense to each other. The larger diameter coils la, lb are known in the art as the drive coils and provide most of the primary magnetic field B. The pairs of coils la, 2a and lb, 2b are arranged in planes which are essentially parallel to each other. A patient 12 is located in the space between the coils and in a plane parallel to the coils. The primary magnetic field B is essentially parallel to the central axis 13 of the coils. The space between the pairs of coils must be sufficient to allow a patient to fit comfortably. In order to constrain the size of the overall MRI system, the diameter of the drive coils la, lb is limited. The combined effect of these space restrictions is a reduction in the homogeneity of the primary magnetic field B produced by the drive coils. To counter this a second pair of coils 2a, 2b is provided inside of and coaxial to the drive coils, but with a current running through them in the opposite sense from the current running through the drive coils. Each pair of compensating coils introduces higher order contaminants which adversely effects the homogeneity of the primary magnetic field.

Furthermore, the confined space in which a patient must be situated during operation of the MRI system can cause the patient stress.

It is known for MRI systems which only require low magnetic fields of less than 0.4 Tesla to adopt more open magnet structures. This has the effect of reducing the patient's feelings of confinement.

However, MRI magnet designs which aim to reduce the patient's feelings of confinement tend to restrict the freedom of position of the coils.

The addition of further coils to improve homogeneity of the primary magnet field is also restricted by these limitations on space.

Theoretically, the nesting of a series of coaxial coil pairs with currents running in the opposite sense can be arranged to compensate for higher order contaminants and thus improve the homogeneity of the primary magnetic field.

Figure 2 is a known arrangement of magnetic coils 20 comprising of a pair of drive coils la, lb with several pairs of mutually coaxial compensating coils 2a, 2b, 3a, 3b, 4a, 4b, 5a, 5b and 6a, 6b. The pairs of compensating coils are wound superconducting coils.

Theoretically a pair of coaxial coils, each with the same magnitude of current and axial dimensions but with current running in the opposite sense, can be replaced by an annular ring of ferromagnetic material which has been magnetised in the direction of the axis of rotation of the rings.

Alternatively, any permanent magnetic material similarly magnetised may be used.

It is an object of the present invention to provide a magnet comprising a series of annular rings of ferromagnetic material which has been magnetised in the direction of the axis of rotation of the rings, thereby improving the magnetic field homogeneity.

It is a further object of the present invention to provide an improved magnetic field suitable for use in an MRI system using a minimum number of superconducting coils.

Furthermore, it is an object of the present invention to provide a magnet suitable for use in an MRI system which provides a less confined patient space then is currently available with known MRI systems.

According to the present invention there is provided a ferromagnetic structure for use in a magnet assembly, the structure having a central axis

and a plurality of coaxial laminations disposed thereon about the central axis such that the structure generates a magnetic field parallel to the central axis.

According to an aspect of the present invention the ferromagnetic structure is magnetically saturated.

According to a further aspect of the present invention the ferromagnetic structure is used in a magnet assembly for use in an MRI system. The assembly may comprise a pair of drive coils arranged such that a primary magnetic field is generated in a direction parallel to a central axis of the pair of drive coils, and a pair of ferromagnetic structures disposed proximate the pair of drive coils, such that a magnetic field generated by the pair of ferromagnetic structures is parallel to the primary magnetic field and functions to improve the homogeneity of the primary magnetic field.

According to a further aspect of the present invention the magnet assembly is used in an MRI system.

According to the present invention there is provided a method of improving the homogeneity of a primary magnetic field, the method comprising the steps of arranging a plurality of coaxial ferromagnetic laminations about a central axis of a structure, disposing a pair of said structures proximate a pair of coaxial drive coils, causing said drive coils to generate a primary magnetic field parallel to the central axis, and causing said pair of structures to generate a magnetic field which is substantially parallel to the primary magnetic field such that the homogeneity of the primary magnetic field is improved.

While the principle advantages and features of the invention have been described above, a greater understanding and appreciation of the invention may be obtained by referring to the drawings and detailed

description of the preferred embodiment, presented by way of example only, in which; FIGURE 3 is a pair of ferromagnetic structures according to a further aspect of the present invention, FIGURE 4 is a ferromagnetic structure according to yet a further aspect of the present invention, FIGURE 5 is a ferromagnetic structure according to yet a further aspect of the present invention, FIGURE 6 is a cross section of the ferromagnetic structure shown in figure 5, FIGURE 7 is an alternative to the ferromagnetic structure shown in figure 6, FIGURE 8 is a ferromagnetic structure according to yet a further aspect of the present invention, FIGURE 9 is a plane view of the ferromagnetic structure shown in figure 8, FIGURE 10 is a ferromagnetic structure according to yet a further aspect of the present invention, FIGURE 11 is a ferromagnetic structure according to yet a further aspect of the present invention, and FIGURE 12 is an MRI system having an open magnet assembly incorporating the ferromagnetic structure shown in figure 10.

In figure 3 magnet assembly 30 comprises a pair of drive coils la, lb, a pair of compensating coils 2a, 2b and a pair of ferromagnetic structures 32a, 32b according to an embodiment of the present invention.

The currents running through drive coils la, lb are in the opposite sense to the currents running through compensating coils 2a, 2b respectively. In this embodiment the ferromagnetic structures are made of Iron. As will be

appreciated by those skilled in the art, other ferromagnetic material such as Cobalt, Nickel or Holmium or alloys thereof may be used, without departing from the scope of the present invention.

The ferromagnetic structures 32a, 32b consist of a series of coaxial rings 33a, 34a, 35a, 33b, 34b, 35b. As is well known in the art, the compensating coils 2a, 2b function to compensate substantially for 2nd order non-homogeneity in the primary magnetic field created by drive coils la and lb. The ferromagnetic structures 32a, 32b function to compensate for higher order non-homogeneity in the primary magnetic field. In order for structures 32a, 32b to achieve this compensation they must be magnetically saturated and magnetised in the same direction as the central axis 31 of the structure. To achieve homogeneity in the primary magnetic field to the 12th order a ferromagnetic structure consisting of three rings is required.

As will be appreciated by those skilled in the art, the ferromagnetic structures shown in figure 3 may take several forms.

In figure 4 ferromagnetic structure 40 comprises a strip of ferromagnetic material 42, such as steel, and a strip of non-ferromagnetic material 44, such as PTFE. The steel 42 and the PTFE 44 are co-wound together about a central axis to form a double layered spiral structure. This structure will function similarly to the structure shown in figure 3.

However, this type of ferromagnetic structure is difficult to manufacture and expensive.

A preferred embodiment of a ferromagnetic structure according to the present invention is shown in figure 5. In figure 5 the ferromagnetic structure-50 consists of three coaxial clusters 52,54, and 56. Each cluster has a series of coaxial laminations. For example, in the outermost cluster 52 there are fifteen laminations 61-75. As will be appreciated the number

of laminations may vary depending on the specific design of the structure.

The structure is magnetically saturated and the laminations are arranged such that the magnetic field generated by the structure is parallel to the primary magnetic field fi generated by the drive coils. This is achieved by insuring that the radial thickness of each lamination is less than its axial height. In a preferred embodiment the ratio of the axial height to the radial thickness is greater than three.

Figure 6 shows a cross section of a portion of the structure shown in figure 5, where parts also appearing in figure 5 bear identical numerical designations. Several of the laminations 61-67 are shown arranged radially around the central axis 51 of the structure 50. The laminations 61- 67 are separated by spaces 61a-67a. In a preferred embodiment the radial thickness of a space between two consecutive laminations is less than the radial thickness of each of the two consecutive laminations immediately surrounding the space. For example, the radial thickness of space 61a is less than the radial thickness of laminations 61 and 62. The magnetic field created by the structure 50 is parallel to the direction of the primary magnetic field B created by the drive coils.

Figure 7 shows a ferromagnetic structure 57 similar to the structure 50 shown in figure 6. In figure 7 the laminations 61-67 have been made by turning deep coaxial rings into a disk 58 of ferromagnetic material. As in figure 6, the laminations 61-67 are shown increasing in diameter from the central axis 51 of the structure 57.

In the structures shown in figures 6 and 7 the laminations have at least one axis perpendicular to the direction of the primary magnetic field B. By insuring that the ratio between the axial height in the Z direction and the radial thickness in the R direction of each lamination is greater than three the direction of magnetisation of the structure will be parallel to

the central axis 51 of the structure and thus parallel to the primary magnetic field B.

As will be appreciated by those skilled in the art the laminations may be made by machining grooves or channels into a solid block of ferromagnetic material. The spaces 61a-67a between the laminations 61- 67 may be filled with a non-ferromagnetic material or left empty. As will be appreciated, the amount of material removed from between the laminations will effect the magnetic saturation of the structure.

In yet a further embodiment of the present invention the spaces 61 a- 67a are filled with shimming material. It is known in the art to use shim plates to further improve the homogeneity of the primary magnetic field.

By incorporating the shim plates within the ferromagnetic structure the patient space is advantageously increased.

In figure 8 a ferromagnetic structure 80 comprises an arrangement of rods 81,82,83.... The rods are attached to a base plate (not shown) and arranged in a pattern to create the desired ring like clusters of laminations similar to those shown in figure 5. The base plate may be made of a ferromagnetic material such as Iron. Alternatively, the base plate may be made of a non ferromagnetic material such as stainless steel.

In figure 9 the ferromagnetic structure 90 comprises a plurality of rods arranged in a series of ring like clusters 91,92,93. Each cluster has a series of laminations. For example cluster 91 has laminations 94,95,96, 97. By varying the diameter of the rods in each cluster higher order improvement in the homogeneity of the primary magnetic field can be achieved. For example, the diameter of rod 91 a in cluster 91 differs from that of rod 92a in cluster 92 which in turn differs from that of rod 93a in cluster 93.

Similarly, by varying the spacing and thickness of the laminations shown in figures 3-7, higher order improvement in the homogeneity of the primary magnetic field can be achieved. This has the advantageous effect of enabling the diameter of the drive coils to be reduces, thus reducing the overall size of the MRI system. Furthermore, improved field homogeneity enables the use of faster imaging procedures, thus advantageously reducing the amount of time a patient has to spend in the MRI system.

Figure 10 shows a ferromagnetic structure 100 according to yet a further embodiment of the present invention. The structure 100 has three series of ring like clusters of lamination 102,104,106 with the radial dimensions of some of the laminations and spaces varying.

Advantageously, this allows for yet further improvements in the homogeneity of the primary magnetic field. As will be appreciated by those skilled in the art, the radial dimensions of the laminations and spaces and the depth of the spaces will effect the magnetic field created by the structure. Mathematical and numerical models can be used to optimise these parameters to provide the optimum degree of compensation for non- homogeneity in the primary magnetic field.

Figure 11 shows an alternative to the embodiment shown in figure 10. In figure 11 the ferromagnetic structure 110 has three ring like cluster 111,112,113. Each cluster has a series of laminations with varying azimuthal lengths. For example, cluster 111 has laminations 114-119 each with a different azimuthal length. By varying the azimuthal length of the laminations further improvements may be made to the homogeneity of the primary magnetic field.

As will be appreciated by those skilled in the art, various combination of the previously described embodiments of ferromagnetic

structure may be used without departing from the scope of the present invention.

Figure 12 shows a magnet assembly 120 for use in an MRI system which includes a pair of the ferromagnetic structure 100 shown in figure 10. The magnet assembly 120 includes a pair of drive coils la, lb which function to provide the primary magnetic field B and a pair of compensating coils 2a, 2b which function to compensate substantially for 2nd order non homogeneity in the magnetic field B. The drive coil 1 a and the compensating coil 2a are disposed in substantially the same plane as are the drive coil lb and compensating coil 2b. Coils la, lb, 2a and 2b are coaxial about a central axis 125. The plane of coils la and 2a is parallel to the plane of coils lb and 2b and to the plane of the patient 12. The system further comprises a pair of gradient coils 122a, 122b for superimposing a linearly varying magnetic field over the primary magnetic field and a pair of RF coils 123a, 123b which form part of a transceiver system for signals which are used to construct an image. The system also comprise a pair of shielding coils 130a, 130b. The shielding coils function to reduce the leakage of magnetic fields in to the surround area. The coils la, 2a, 130a and lb, 2b, 130b are arranged on formers 200a and 200b respectively.

The system also includes a pair of ferromagnetic structure 100a, 100b disposed coaxial about the central axis 125. The structures function to provide compensation for higher order non-homogeneity in the magnetic field B. The ferromagnetic structures are preferably disposed in the same plane as the drive coils, thereby reducing the overall space required for each magnet assembly. This arrangement also facilitates the manufacture of a temperature controlling unit for the system.

As was previously stated, the ferromagnetic structures are preferably magnetically saturated and are arranged such that the magnetic field

generated by the structures is parallel to the direction of the primary magnetic field B.

As will be appreciated by those skilled in the art, the ferromagnetic structures lOOa, lOOb shown in figure 12, may be replaced with any of the embodiments of ferromagnetic structures previously described and shown in figures 2-11.

It is well known that a change in temperature within a magnet assembly will adversely effect the operation of an MRI system. In an alternative embodiment of the present invention the ferromagnetic structures are temperature controlled. This may be achieved with a Peltier device or other temperature controlling means. The ferromagnetic structures may be temperature controlled separately. Alternatively, the ferromagnetic structures may be incorporated within the temperature cooled device used on the drive coils. This may be a cryostat structure.

By incorporating the ferromagnetic structures within the cryostat temperature stability is further improved.

In yet another embodiment, a further pair of ferromagnetic structures are included in the magnet assembly. This will further improve the homogeneity of the primary magnetic field.

As is well known in the art, the building in which an MRI system is housed can adversely effect the homogeneity of the primary magnetic field. In yet a further embodiment, the ferromagnetic structures 100a, 100b are adjustable in both the axial and radial planes. By adjusting the position of the ferromagnetic structures an optimum position can be found which reduces these effects. As will be appreciated other degrees freedom, such as tip and tilt, may be incorporated into the adjustment means.

The open magnet assembly shown in figure 12 may further include a pair of shim plates 121a, 121b which function to further improve the

homogeneity of the primary magnetic field. Alternatively, the shim plates may be incorporated into the ferromagnetic structures 100a, 100b. This will advantageously increase the space surrounding the patient 12.

As will be appreciated by those skilled in the art, the ferromagnetic structures previously described and according to the present invention, may be incorporated into an open MRI system as shown in figure 12.

Alternatively, the ferromagnetic structures may be incorporated into a C type MRI system.

As will be appreciated by those skilled in the art, various modifications may be made to the embodiment hereinbefore described without departing from the scope of the present invention.