Real-time compensation of high-order concomitant magnetic fields
A method, electromagnet device, and system for reducing a higher order term of a concomitant field in an imaging magnetic field during magnetic resonance imaging is described. The electromagnet system has a first shim coil configured to be driven to generate a first compensation magnetic field during imaging according to a first second-order compensation term, the first compensation magnetic field having a similar amplitude but opposite direction as that of a first second-order concomitant magnetic field.
1. A magnetic resonance imaging (MRI) system comprising:
an electromagnet system for reducing a higher order term of a concomitant field in an imaging magnetic field during magnetic resonance imaging, the electromagnet system having:
a first shim coil configured to be driven to generate a first compensation magnetic field during imaging according to a first second-order compensation term, the first compensation magnetic field having a similar amplitude but opposite direction as that of a first second-order concomitant magnetic field; and
a z-gradient coil for generating the imaging magnetic field in the z-direction, wherein the first shim coil is designed to reduce the sensitivity of mutual inductance with the z-gradient coil.
2. The MRI system of claim 1 , wherein the first shim coil is an x 2 +y 2 shim coil and the first second-order concomitant magnetic field has an x 2 +y 2 spatial variation.
3. The MRI system of claim 1 , wherein the first shim coil is one of:
a z 2 shim coil and the first second-order concomitant magnetic field has a z 2 spatial variation,
a zx shim coil and the first second-order concomitant magnetic field has a zx spatial variation, and
a yz shim coil and the first second-order concomitant magnetic field has a yz spatial variation.
4. The MRI system of claim 2 , wherein the electromagnet system further comprises at least one of: a z 2 shim coil, a zx shim coil, or a yz shim coil,
the z 2 shim coil configured to be driven to generate a second compensation magnetic field during imaging according to a second second-order compensation term, the second compensation magnetic field having a similar amplitude but opposite direction as that of a second second-order concomitant magnetic field with a z 2 spatial variation,
the zx shim coil configured to be driven to generate a third compensation magnetic field during imaging according to a third second-order compensation term, the third compensation magnetic field having a similar amplitude but opposite direction as that of a third second-order concomitant magnetic field with a zx spatial variation, and
the yz shim coil configured to be driven to generate a fourth compensation magnetic field during imaging according to a fourth second-order compensation term, the fourth compensation magnetic field having a similar amplitude but opposite direction as that of a fourth second-order concomitant magnetic field with a yz spatial variation.
5. The MRI system of claim 4 , wherein
the second second-order compensation term is (G x 2 +G y 2 )/(2*B 0 ),
the third second-order compensation term is −G x *G z /(2*B 0 ), and
the fourth second-order compensation term is −G y *G z /(2*B 0 ).
6. The MRI system of claim 1 , wherein the first shim coil is a matrix coil.
7. A method for reducing a higher order term of a concomitant field in an imaging magnetic field during magnetic resonance imaging, the imaging magnetic field in the z-direction being generated by driving a z-gradient coil, the method comprising:
generating a first compensation magnetic field with a first shim coil during imaging according to a first second-order compensation term, the first compensation magnetic field having a similar amplitude but opposite direction as that of a first second-order concomitant magnetic field, wherein a mutual inductance constraint is applied to the first second-order compensation term for reducing the sensitivity of mutual inductance between the first shim coil and the z-gradient coil.
8. The method of claim 7 , wherein the first shim coil is an x 2 +y 2 shim coil and the first second-order concomitant magnetic field has an x 2 +y 2 spatial variation.
9. The method of claim 7 , wherein the first shim coil is one of:
a z 2 shim coil and the first second-order concomitant magnetic field has a z 2 spatial variation,
a zx shim coil and the first second-order concomitant magnetic field has a zx spatial variation, and
a yz shim coil and the first second-order concomitant magnetic field has a yz spatial variation.
10. The method of claim 8 , wherein generating the first compensation magnetic field comprises: designing and creating the x 2 +y 2 shim coil to produce the compensation magnetic field; and driving the x 2 +y 2 shim coil during magnetic resonance imaging.
11. The method of claim 8 , further comprising:
generating at least one of: a second, third, or fourth compensation magnetic field during imaging,
the second compensation magnetic field being generated with a z 2 shim coil according to a second second-order compensation term, the second compensation magnetic field having a similar amplitude but opposite direction as that of a second second-order concomitant magnetic field with a z 2 spatial variation,
the third compensation magnetic field being generated with a zx shim coil according to a third second-order compensation term, the third compensation magnetic field having a similar amplitude but opposite direction as that of a third second-order concomitant magnetic field with a zx spatial variation, and
the fourth compensation magnetic field being generated with a yz shim coil according to a fourth second-order compensation term, the fourth compensation magnetic field having a similar amplitude but opposite direction as that of a fourth second-order concomitant magnetic field with a yz spatial variation.
12. The method of claim 11 , wherein
the second second-order compensation term is (G x 2 +G y 2 )/(2*B 0 ),
the third second-order compensation term is −Gx*G z /(2*B 0 ), and
the fourth second-order compensation term is −G y *G z /(2*B 0 ).
13. An electromagnet for reducing a higher order term of a concomitant field in an imaging magnetic field during magnetic resonance imaging, the imaging magnetic field in the z-direction being generated by driving a z-gradient coil, the electromagnet configured to be driven to generate a first compensation magnetic field during imaging according to a first second-order compensation term, the first compensation magnetic field having a similar amplitude but opposite direction as that of a first second-order concomitant magnetic field, wherein a mutual inductance constraint is applied to the first second-order compensation term for reducing the sensitivity of mutual inductance between the electromagnet and the z-gradient coil.
14. The electromagnet of claim 13 , wherein the electromagnet is an x 2 +y 2 shim coil for correcting the first second-order concomitant magnetic field with an x 2 +y 2 spatial variation.
15. The electromagnet of claim 13 , wherein the electromagnet is one of:
a z 2 shim coil for correcting the first second-order concomitant magnetic field with a z 2 spatial variation,
a zx shim coil for correcting the first second-order concomitant magnetic field with a zx spatial variation, and
a yz shim coil for correcting the first second-order concomitant magnetic field with a yz spatial variation.
16. The MRI system of claim 1 , wherein the first second-order compensation term is (G z 2 )/(8*B 0 ).
17. The method of claim 7 , wherein the first second-order compensation term is (G z 2 )/(8*B 0 ).
18. The electromagnet of claim 13 , wherein the first second-order compensation term is (G z 2 )/(8*B 0 ).