The Iseult/Inumac Whole Body 11.7 T MRI Magnet Design

Schild, T.; Aubert, G.; Berriaud, C.; Brédy, P.; Juster, F.P.; Meuris, C.; Nunio, F.; Quettier, L.; Rey, Jean‐Michel; Védrine, P.

doi:10.1109/tasc.2008.921264

Cited by 31 publications

(12 citation statements)

References 6 publications

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“…Conductor length constraints, challenges in force transfer, limitations on the peak field or quench voltages may force the magnet designers to consider other configuration options. For example, the 11.7 tesla Iseult magnet [16] uses 170 double-pancakes (DP) in the main coils. Separation between the DP coils varies to provide the highest uniformity.…”

Section: Design Of Whole-body Mri Magnetsmentioning

confidence: 99%

Conductors for commercial MRI magnets beyond NbTi: requirements and challenges

Parizh

Lvovsky

Sumption

2016

Supercond. Sci. Technol.

127

107

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Magnetic Resonance Imaging (MRI), a powerful medical diagnostic tool, is the largest commercial application of superconductivity. The superconducting magnet is the largest and most expensive component of an MRI system. The magnet configuration is determined by competing requirements including optimized functional performance, patient comfort, ease of siting in a hospital environment, minimum acquisition and lifecycle cost including service. In this paper, we analyze conductor requirements for commercial MRI magnets beyond traditional NbTi conductors, while avoiding links to a particular magnet configuration or design decisions. Potential conductor candidates include MgB2, ReBCO and BSCCO options. The analysis shows that no MRI-ready non-NbTi conductor is commercially available at the moment. For some conductors, MRI specifications will be difficult to achieve in principle. For others, cost is a key barrier. In some cases, the prospects for developing an MRI-ready conductor are more favorable, but significant developments are still needed. The key needs include the development of, or significant improvements in: (a) conductors specifically designed for MRI applications, with form-fit-and-function readily integratable into the present MRI magnet technology with minimum modifications. Preferably, similar conductors should be available from multiple vendors; (b) conductors with improved quench characteristics, i.e. the ability to carry significant current without damage while in the resistive state; (c) insulation which is compatible with manufacturing and refrigeration technologies; (d) dramatic increases in production and long-length quality control, including large-volume conductor manufacturing technology. In-situ MgB2 is, perhaps, the closest to meeting commercial and technical requirements to become suitable for commercial MRI. Conductor technology is an important, but not the only, issue in introduction of HTS / MgB2 conductor into commercial MRI magnets. These new conductors, even when they meet the above requirements, will likely require numerous modifications and developments in the associated magnet technology.

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Section: Design Of Whole-body Mri Magnetsmentioning

confidence: 99%

Conductors for commercial MRI magnets beyond NbTi: requirements and challenges

Parizh

Lvovsky

Sumption

2016

Supercond. Sci. Technol.

127

107

View full text Add to dashboard Cite

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“…The , current density, is integrated over the thickness. The (1) was replaced by (2) where , and is a 10 12 matrix. to be directly obtained from (2) can have a large dissipation.…”

Section: E One-dimensional Inverse Problemmentioning

confidence: 99%

“…Magnets generating magnetic flux density over 30 T have been studied for an NMR spectrometer [1]. An 11.7 T-magnet with a large room temperature bore, 900 mm, has been designed for an MRI device [2]. The increases of magnetic field result in enhancement of nuclide identifications.…”

Section: Introductionmentioning

confidence: 99%

Current Distribution in Coated Conductor Under External Magnetic Field Up to 5 T

Miyazoe

Sekino

Toko

et al. 2011

IEEE Trans. Appl. Supercond.

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This paper presents current distributions consisting of transport and screening currents flowing in a YBCO coated conductor (CC) under flux densities of several tesla in liquid helium, where magnetic flux should be at center along a width of the CC. Distributions of magnetic flux densities generated by the currents in the CC were measured. In order to demonstrate the current distributions, a one dimensional inverse problem was solved using Tikhonov regularization. Sheet current density distributions near one edge with external field, where magnetic flux existed all over the width, were constant even if transport current increased. The constant current density corresponded to a critical current at the field divided by the width. Magnetic flux density distributions were asymmetric to the width of a CC under external magnetic flux density of several tesla. On the other hand, hysteresis of the magnetic flux densities above the CC shrank symmetrically to the width with increases of transport current.

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“…B Y its design [1], the 11.75 T MRI magnet [2] will operate in driven mode, i.e. the Power Supply Unit (PSU) will be permanently connected to the magnet.…”

Section: Introductionmentioning

confidence: 99%

Field Stabilization of the Iseult/Inumac Magnet Operating in Driven Mode

Sinanna

Aguiar

d'Amico

et al. 2010

IEEE Trans. Appl. Supercond.

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A neuroscience research center with very high field MRI equipments was opened in November 2006 by the CEA life sciences division. Three MRI systems operating at 3, 7 and 17 T have been already installed. One of the imaging systems will require a 11.75 T magnet with a 900 mm warm bore. The large aperture and high field strength of this magnet provide a substantial engineering challenge compared to the largest MRI systems ever built. This magnet is being developed within an ambitious R&D program, Iseult, whose focus is high field MRI. Traditional MRI magnet design principles are not readily applicable and thus concepts taken from high energy physics or fusion experiments, namely the Tore Supra tokamak magnet system, will be used. The coil will be made of a niobium-titanium conductor cooled by a He II bath at 1.8 K, permanently connected to a cryoplant. Due to its design the magnet will be operated in a non-persistent mode. As the field stability needed for MRI imaging requires a field drift of less than 0.05 ppm/h, it is hardly feasible to directly transpose these requirements in the power supply specification. Two existing solutions developed for other applications have been selected: one using a semi-persistent mode, and the other using a short-circuited superconducting coil in the inner bore. In order to make a decision on experimental basis, an ambitious R&D field stability program has been set-up based on magnet prototypes, high field test facility (Seht, a 44 H and 8 T magnet with a warm bore to 600 mm). We will present development and experimental results of the two stabilization solutions. In conclusion, the stability solution selected for the Iseult magnet is given.

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The Iseult/Inumac Whole Body 11.7 T MRI Magnet Design

Cited by 31 publications

References 6 publications

Conductors for commercial MRI magnets beyond NbTi: requirements and challenges

Conductors for commercial MRI magnets beyond NbTi: requirements and challenges

Current Distribution in Coated Conductor Under External Magnetic Field Up to 5 T

Field Stabilization of the Iseult/Inumac Magnet Operating in Driven Mode

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