Avoiding eddy-current problems in ultra-low-field MRI with self-shielded polarizing coils.

In ultra-low-field magnetic resonance imaging (ULF MRI), superconductive sensors are used to detect MRI signals typically in fields on the order of 10-100 μT. Despite the highly sensitive detectors, it is necessary to prepolarize the sample in a stronger magnetic field on the order of 10-100 mT, which has to be switched off rapidly in a few milliseconds before signal acquisition. In addition, external magnetic interference is commonly reduced by situating the ULF-MRI system inside a magnetically shielded room (MSR). With typical dipolar polarizing coil designs, the stray field induces strong eddy currents in the conductive layers of the MSR. These eddy currents cause significant secondary magnetic fields that may distort the spin dynamics of the sample, exceed the dynamic range of the sensors, and prevent simultaneous magnetoencephalography and MRI acquisitions. In this paper, we describe a method to design self-shielded polarizing coils for ULF MRI. The experimental results show that with a simple self-shielded polarizing coil, the magnetic fields caused by the eddy currents are largely reduced. With the presented shielding technique, ULF-MRI devices can utilize stronger and spatially broader polarizing fields than achievable with unshielded polarizing coils.

[1]  Stuart Crozier,et al.  The design of biplanar, shielded, minimum energy, or minimum power pulsed B0 coils , 1995, Magnetic Resonance Materials in Physics, Biology and Medicine.

[2]  D. Cohen,et al.  Large-volume conventional magnetic shields , 1970 .

[3]  C. Fermon,et al.  RF Response of Superconducting-GMR Mixed Sensors, Application to NQR , 2007, IEEE Transactions on Applied Superconductivity.

[4]  D. A. Dunnett Classical Electrodynamics , 2020, Nature.

[5]  Anthonie Hendrik Bergman,et al.  Optimization of eddy-current compensation☆ , 1990 .

[6]  Robert McDermott,et al.  Microtesla MRI with a superconducting quantum interference device. , 2004, Proceedings of the National Academy of Sciences of the United States of America.

[7]  Leif Grönberg,et al.  All-planar SQUIDs and pickup coils for combined MEG and MRI , 2011 .

[8]  P. Jehenson,et al.  Analytical method for the compensation of eddy-current effects induced by pulsed magnetic field gradients in NMR systems , 1990 .

[9]  Irreversible relaxation behaviour of a general class of magnetic systems , 1996 .

[10]  R. Mallozzi,et al.  Making MRI quieter. , 2002, Magnetic resonance imaging.

[11]  John Clarke,et al.  Nuclear quadrupole resonance detected at 30 MHz with a dc superconducting quantum interference device , 1985 .

[12]  Jaakko O. Nieminen,et al.  Hybrid MEG-MRI: Geometry and Time Course of Magnetic Fields Inside a Magnetically Shielded Room , 2010 .

[13]  G. Peeren Stream function approach for determining optimal surface currents , 2003 .

[14]  Peter B. Roemer,et al.  4737716 Self-shielded gradient coils for nuclear magnetic resonance imaging , 1989 .

[15]  R. Turner A Target Field Approach To Optimal Coil Design , 1986 .

[16]  Robert H Kraus,et al.  Microtesla MRI of the human brain combined with MEG. , 2008, Journal of magnetic resonance.

[17]  Claude Fermon,et al.  Femtotesla Magnetic Field Measurement with Magnetoresistive Sensors , 2004, Science.

[18]  C. Boesch,et al.  Temporal and spatial analysis of fields generated by eddy currents in superconducting magnets: Optimization of corrections and quantitative characterization of magnet/gradient systems , 1991, Magnetic resonance in medicine.

[19]  J. Simola,et al.  The Spatial and Temporal Distortion of Magnetic Fields Applied Inside a Magnetically Shielded Room , 2012, IEEE Transactions on Magnetics.

[20]  A. Komura,et al.  Shielding stray magnetic fields of open high field MRI magnets , 2004, IEEE Transactions on Applied Superconductivity.

[21]  P L Volegov,et al.  MRI with an atomic magnetometer suitable for practical imaging applications. , 2009, Journal of magnetic resonance.

[22]  A method to reduce eddy currents within iron pole plates of a 0.3 T NdFeB MRI magnet , 2002 .

[23]  Vittorio Foglietti,et al.  Flux dam, a method to reduce extra low frequency noise when a superconducting magnetometer is exposed to a magnetic field , 1995 .

[24]  A. Matlashov,et al.  Co-registration of MEG and ULF MRI using a 7 channel low-T c SQUID system , 2010 .

[25]  John Clarke,et al.  SQUID-detected magnetic resonance imaging in microtesla fields. , 2007, Annual review of biomedical engineering.

[26]  K. Maki,et al.  An optimal design of coaxial coils with constraints on inner and outer multipole magnetic fields , 2004, IEEE Transactions on Applied Superconductivity.

[27]  K. Yoda,et al.  Analytical design method of self‐shielded planar coils , 1990 .

[28]  A. N. Matlashov,et al.  SQUID-based instrumentation for ultralow-field MRI , 2007 .

[29]  S. Taulu,et al.  Presentation of electromagnetic multichannel data: The signal space separation method , 2005 .

[30]  J. Clarke,et al.  SQUID-Detected Magnetic Resonance Imaging in Microtesla Magnetic Fields , 2004 .

[31]  R. Turner,et al.  Passive screening of switched magnetic field gradients , 1986 .

[32]  J. B. Bronzan,et al.  The Magnetic Scalar Potential , 1971 .

[33]  L. Trahms,et al.  SQUID Systems Adapted to Record Nuclear Magnetism in Low Magnetic Fields , 2007, IEEE Transactions on Applied Superconductivity.

[34]  P. Mansfield,et al.  Active magnetic screening of coils for static and time-dependent magnetic field generation in NMR imaging , 1986 .

[35]  J. Mosher,et al.  Multi-Channel SQUID System for MEG and Ultra-Low-Field MRI , 2006, IEEE transactions on applied superconductivity.

[36]  R. Ilmoniemi,et al.  Sampling theory for neuromagnetic detector arrays , 1993, IEEE Transactions on Biomedical Engineering.