CROSS REFERENCE TO RELATED APPLICATIONS

This application is a U.S. national phase application of International Application No. PCT/EP2019/060715 filed on Apr. 26, 2019, which claims the benefit of EP Application Ser. No. 18170033.7 filed on Apr. 30, 2018 and is incorporated herein by reference.

FIELD OF THE INVENTION

The invention relates to the field of MRI imaging and in particular to gradient shield coils for a MRI apparatus.

BACKGROUND OF THE INVENTION

A magnetic field is used in magnetic resonance imaging (MRI) to align the nuclear spins of atoms as part of the procedure for yielding images within the body of a patient. This magnetic field is referred to as the main magnetic field or BO field. During a MRI scan, radio frequency (RF) pulses which are generated by a transmitter or amplifier and an antenna cause perturbations to the local magnetic field and can be used to manipulate the orientation of the nuclear spins relative to the BO field. Spatial encoding of the magnetic spins may be accomplished by using so called gradient coils, which are used to superimpose a magnetic field gradient upon the BO magnetic field. RF signals emitted by the nuclear spins are detected by a receiver coil, and these RF signals are used to generate the MRI images.

The magnets used to generate the BO field typically use superconductive coils. The magnetic field generated by the gradient coils can cause eddy currents and, hence, dissipation within the superconductive coils and within electrically conducting structures inside the superconducting magnet. These eddy currents can be reduced by using gradient coils with active shielding. US 2016/0139221 A1 discloses such an active shielding in the form of gradient shield coils which surround the gradient coils of a MRI apparatus.

According to US 2016/0139221 A1 a magnetic gradient coil for a magnetic resonance imaging system is provided. The magnetic gradient coil is actively shielded, wherein the magnetic gradient coil is operable for generating a magnetic field. The magnetic field has a cylindrical axis of symmetry and the gradient coil has a length parallel with the cylindrical axis of symmetry. The magnetic gradient coil has an outer surface. The magnetic field comprises an external magnetic field outside of the outer surface. This external magnetic field has at least four reduced field regions along the length where the modulus of the magnetic field is less than the average of the modulus of the magnetic field along the length.

Further, from US 2010/0194393 A1 a gradient coil device is known which can suppress the generation of an error magnetic field and, thus, an eddy current, and which may improve the image quality of a cross-sectional image. A respective MRI device includes a first coil generating a linear magnetic field distribution at an imaging region of the MRI device, and a second coil which suppresses leakage of a magnetic field from the first coil to a static-magnetic-field coil device that generates a uniform magnetic field distribution at the imaging region.

The US patent application is designed to achieve proper shielding function for a shielded gradient coil in which the gap between the field coil and the shield coil changes with the circumferential direction. This shield gradient coil has a wiring pattern with two circumferential serpentines, at radially opposite locations near the narrow regions of the gap between the field coil and the shield coil.

SUMMARY OF THE INVENTION

It is an object of the invention to further reduce dissipation in the superconductive coils and other electrically conducting structures of the magnet of a MRI system.

According to the invention, this object is addressed by the subject matter of the independent claims. Preferred embodiments of the invention are described in the sub claims.

Therefore, according to the invention, a gradient shield coil for a MRI apparatus is provided, the gradient shield coil comprising windings around its longitudinal axis, wherein at least one winding is arranged as a meandering winding by comprising multiple contiguous sections along its circumference, wherein in each of these sections a pair of conductor loops is provided in such a way that a current in the meandering winding would run in opposite directions in the two conductor loops.

According to the invention, large circulating currents in cylindrical magnet parts are transformed into a multitude of local eddy-currents, which cause less dissipation and less mechanical excitation of these parts. The optimum current distribution for the active shield layer of a z-gradient coil usually has low current density at the ends and near the mid plane of the coil. Approximating this ideal current distribution by a set of discrete turns with empty spaces in between leads to external field imperfections that cause significant circulating current in structures like the radiation screen or an inner bore liner of the magnet. These currents lead to dissipation and mechanical excitation of these components. By transforming these circular windings into at least one meandering winding, as described before, the induced currents in the magnet can be transformed into a pattern of very local circulating currents. These eddy-currents decay faster, dissipate less and cause less mechanical excitation. Thus, according to the invention, the dissipation in the magnet can be reduced by at least a factor of 2.

The two conductor loops may, in general, be closed or almost closed loops. However, when it is referred to these conductor loops and to the feature that the current runs in opposite directions in these conductor loops this also comprises any case in which these conductor loops are only formed by parts of the meandering winding which partially run in different, preferably opposite, directions, preferably at the same length of the circumference of the meandering winding, i.e. in the same section of the meandering winding.

In general, the conductor loops can be arranged in different ways within the sections. However, according to a preferred embodiment of the invention, in each section the two conductor loops are arranged adjacent to each other at the same length along the circumference of the winding.

The positive effect of the invention may already achieved by providing a single pair of conductor loops in each section. Alternatively, according to a preferred embodiment of the invention, in each section multiple pairs of loops are provided in such a way that a current in the meandering winding would run in opposite directions in the two conductor loops of a respective pair. In that situation it is preferred that in each section the conductor loops are arranged adjacent to each other at the same length along the circumference of the winding.

Different arrangements of the sections along the circumference of the meandering winding may be used in order to achieve the positive effects of the invention. However, according to a preferred embodiment of the invention, the sections with the pairs of conductor loops are arranged with a regular spacing from each other along the circumference of the meandering winding.

Further, it is preferred that the gradient coil has a cylindrical shape with two open ends, and that the at least one meandering winding is arranged at one of these open ends. It is further preferred that at least one meandering winding is arranged at both of these open ends, respectively. It is further preferred that at least one meandering winding is arranged near the midplane of the coil. Preferably, the winding density is smaller at the area of the open ends and in the area of the midplane. Further, according to a preferred embodiment of the invention, at least two meandering windings are arranged in its middle region.

Preferably, at least one curved winding is provided adjacent to a meandering winding, wherein the curved winding does not run straight but does not comprise any conductor loops as the meandering windings, either. Preferably, adjacent to each meandering winding a curved winding which is arranged.

According to a preferred embodiment of the invention, the meandering winding is manufactured from a copper plate using a method such as punching or water jet cutting. Alternatively, according to a preferred embodiment of the invention, meandering winding is wound from a hollow conductor.

The invention also relates to a MRI apparatus comprising a superconductive magnet for generating a main magnetic field of the MRI apparatus and at least one gradient coil for generating a gradient magnetic field superimposing the main magnetic field, wherein the gradient coil is surrounded by the superconductive magnet and wherein the superconductive magnet is shielded from the gradient magnetic field by a gradient field coil as described above which is arranged between the superconductive magnet and the gradient coil.

According to a preferred embodiment of the MRI apparatus, the gradient coil comprises saddle windings near the mid plane of the gradient coil and the at least one meandering winding is arranged over the saddle windings near the mid plane of the gradient coil in a region of lower winding density than in the other regions, in such a way that the superconducting magnet is shielded from these saddle windings.

The invention also relates to a method of shielding a superconductive magnet from the gradient magnetic field generated by a gradient coil of a MRI apparatus by arranging a gradient shield coil between the superconductive magnet and the gradient coil, the gradient shield coil comprising windings around its longitudinal axis, wherein at least one winding is arranged as a meandering winding by comprising multiple contiguous sections along its circumference, wherein in each of these sections a pair of conductor loops is provided in which a current in the meandering winding runs in opposite directions in the two conductor loops.

Preferred embodiments of the MRI apparatus and the method of shielding a superconductive magnet from the gradient magnetic field generated by a gradient coil of a MRI apparatus also result from the preferred embodiments of the gradient shield coils as described further above.

