US20190235036A1 - B0 shimming device for mri - Google Patents

B0 shimming device for mri Download PDF

Info

Publication number
US20190235036A1
US20190235036A1 US16/083,973 US201716083973A US2019235036A1 US 20190235036 A1 US20190235036 A1 US 20190235036A1 US 201716083973 A US201716083973 A US 201716083973A US 2019235036 A1 US2019235036 A1 US 2019235036A1
Authority
US
United States
Prior art keywords
magnetic field
magnetic
temperature
moment density
magnetic material
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US16/083,973
Other languages
English (en)
Inventor
David Brunner
Simon Gross
Klaas Pruessmann
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Eidgenoessische Technische Hochschule Zurich ETHZ
Universitaet Zuerich
Original Assignee
Eidgenoessische Technische Hochschule Zurich ETHZ
Universitaet Zuerich
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Eidgenoessische Technische Hochschule Zurich ETHZ, Universitaet Zuerich filed Critical Eidgenoessische Technische Hochschule Zurich ETHZ
Assigned to ETH ZURICH, UNIVERSITAET ZUERICH reassignment ETH ZURICH ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BRUNNER, DAVID, GROSS, SIMON, PRUESSMANN, KLAAS
Publication of US20190235036A1 publication Critical patent/US20190235036A1/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/387—Compensation of inhomogeneities
    • G01R33/3873—Compensation of inhomogeneities using ferromagnetic bodies ; Passive shimming
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/3804—Additional hardware for cooling or heating of the magnet assembly, for housing a cooled or heated part of the magnet assembly or for temperature control of the magnet assembly
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/543—Control of the operation of the MR system, e.g. setting of acquisition parameters prior to or during MR data acquisition, dynamic shimming, use of one or more scout images for scan plane prescription

Definitions

  • the present invention generally relates to a magnetic resonance (MR) apparatus and a method of operating the same. More particularly, the invention relates to the task of applying shimming corrections to the main magnetic field in a MR system, particularly an MR imaging (MRI) system.
  • MR magnetic resonance
  • MRI MR imaging
  • Susceptibility induced off-resonances challenge many cutting-edge magnetic resonance applications using single shot read-outs, balanced acquisitions or high-resolution spectroscopy, in particular at ultra-high fields.
  • MRI and NMR magnets are constructed to deliver net uniformities in the region of the volume of interest of the order of 1 ppm.
  • the primary magnet itself which is either wound by resistive or superconductive wires or constructed from a permanent magnetic material, does usually not deliver the required uniformity. Therefore correction units are installed.
  • Most frequently ferromagnetic plates (shims) are distributed along the bore such that the magnetic field becomes uniform [1, 2]. This so called “shimming” procedure is typically performed at production and/or installation of the magnet.
  • the susceptible material of the subject itself distorts the magnetic field in the subject.
  • These distortions are usually measured at the beginning of a sequence and compensated by actuating a set of electromagnets typically contracted from resistive coils.
  • These shim coils are typically designed to produce fields of spherically or cylindrically harmonic fields.
  • the shim coils are either integrated in the gradient coils, or dedicated insert shim coils lining the gradient coil are used.
  • the weight and cabling size can be reduced by reducing the power requirements of the shim unit.
  • Coil conductors in close proximity to the subject [3] or even on the RF coils [4] are significantly more efficient. Thereby the size of the coil conductor windings and the power requirements are drastically reduced.
  • unwanted interactions with the RF operation of the scanner are hard to tame and also coupling to the switching gradients is an obvious problem.
  • the handling is further aggravated by the amount of conductors in the unit and the large number of high-current wires routed through the bore. Still further, highly stabilized current supplies need to be fitted into the technical room.
  • US 2006/113995 A1 discloses a magnetic field generating apparatus and a method for magnetic resonance imaging which comprises two spatially distinct sets of shim elements and means for independently regulating the temperature of at least a portion of one set of shim elements in order to compensate for B0 field variations caused by a temperature drift in the apparatus. Similar arrangements are also described in JP H08 215168 A, US 2010/045293 A1 and US 2010/207630 A1, which all aim either at compensating the effect of an overall temperature drift or at reducing magnetic field inhomogeneity present after initial set-up of an MRI arrangement.
  • a magnetic resonance (MR) apparatus comprising:
  • said magnet means comprise a primary magnetic field source providing a static magnetic field B 0 and at least one secondary magnetic field source providing an adjustable magnetic field B′;
  • said secondary magnetic field source comprises at least two spatially distinct portions of a first magnetic material and of a second magnetic material, respectively, said first magnetic material having a first magnetic moment density m 1 and said second magnetic material having a second magnetic moment density m 2 , and means for independently adjusting said second magnetic moment density m 2 by variation of an external control parameter, the apparatus further comprising means for determining an instant spatial distribution of the static magnetic field resulting from said static magnetic field B0 and said adjustable magnetic field a.
  • first magnetic material and “second magnetic material” will follow the convention that the material used for adjusting the magnetic field B′ will be denoted as “second magnetic material”.
  • second magnetic material the other (i.e. the “first”) magnetic material could also have an adjustable magnetic moment density, but this is not mandatory in the context of the present invention. It would also be possible to use an arrangement wherein the first magnetic material has a vanishingly small magnetic moment density m 1 .
  • the secondary magnetic field sources according to the present invention correspond to what is often called “shim units” in the field of MR technology.
  • Another aspect of the invention relates to a method of operating an MR apparatus as defined above, wherein said external control parameter is adjusted in such manner as to obtain a predetermined main magnetic field B resulting from the superposition of the static magnetic field B 0 and the adjustable magnetic field B′ of each secondary magnetic field source, the adjustment being carried out at the beginning of an MR sequence for forming images or spectra, after a sample or subject has been introduced into the sample region.
  • the second magnetic moment density m 2 is adjustable in a range extending from values that are smaller than the first magnetic moment density m 1 to values that are larger than the first magnetic moment density m 1 .
  • the external control parameter is selected from the group consisting of temperature, pressure, shear and light illumination prevailing at the secondary magnetic field source and electric current flowing therethrough (claim 3 ).
  • the external control parameter is the local temperature of the portion of second magnetic material and the adjusting means are configured to adjust said local temperature in a control temperature range extending from a lowest control temperature T L to a highest control temperature T H , the second magnetic material having a Curie temperature T C lying within said control temperature range.
  • the adjusting means are configured to adjust said local temperature in a control temperature range extending from a lowest control temperature T L to a highest control temperature T H , the second magnetic material having a Curie temperature T C lying within said control temperature range.
  • the Curie temperature is a material-dependent property that varies over a wide range. It is also known that e.g. in certain alloys it is possible to adjust the Curie temperature over a considerable range by variation of the composition. For many instances where the present invention may be useful, it will be advantageous to use compounds with a Curie temperature that is somewhat higher than ambient temperature, meaning that one could switch between ferromagnetic and paramagnetic behavior by raising the temperature by a certain amount above ambient temperature. Therefore, according to one embodiment (claim 5 ) the Curie temperature T C of the second magnetic material is in the range from 300K to 450K. For example, one can use a nickel-copper alloy with a composition Ni75Cu25, which has a Curie temperature of about 80° C.
  • the secondary magnetic field source is formed as an elongated body having a longitudinal axis wherein a plurality of spatially distinct portions are arranged at distinct positions along said longitudinal axis.
  • each spatially distinct portion can be electrically heated by driving a current through a resistor. Its temperature is locally measured via a thermocouple.
  • Each of these units is thermally isolated and RF shielded.
  • optical fibers can be employed to deliver heat to the magnetic material and reading out the temperature (i.e. fluoro-optically). This offers the advantage of very good decoupling of the shim units from the RF and the gradient switching in the scanner, albeit at a higher complexity.
  • Peltier or an equivalent type of elements allowing heating and cooling can be employed.
  • each secondary magnetic field source comprises means for determining an instant value of the external control parameter (claim 8 ).
  • the determining means can be selected from known temperature sensor types such as e.g. thermistors or thermocouples.
  • the temperature is advantageously controlled via a close loop controlling system.
  • the controller can be positioned in the bore of the MR system, e.g. an MRI system.
  • the controller consists of a small multichannel PWM current low-side driver, multichannel thermocouple read-out units and a microcontroller.
  • the microcontroller has a data link out of the bore. The microcontroller reads the data obtained from the thermocouple and adjusts the PWM ratio of the current source.
  • a PID controller can be used for this purpose.
  • the materials to be used as first and/or second magnetic materials could be selected from a large variety of magnetic materials.
  • the second magnetic material is formed of an alloy containing Fe, Ni, Ga, Mn, Gd, Sm, Nd, Dy, Eu or Co.
  • the adjustable magnetic field B′ of each secondary magnetic field source in an axial direction z of the static magnetic field B 0 can be switched between positive and negative values as a function of the external control parameter. This is particularly useful for achieving an appropriate shimming action over a wide adjustment range.
  • the magnetic moment of the material is hereby controlled by controlling the temperature, the pressure/shear [5], light illumination [6] and/or the electric current and or field through a portion of magnetic material.
  • the magnetization of a portion of the magnetic material is controlled by a heater.
  • the heat is applied by an electric current through a resistor or resistor wire that is regulated using a temperature sensor measuring the temperature of said portion of magnetic material.
  • the electric current can be provided by a DC, AC or a modulated source.
  • the temperature dependence of the material is thereby a design parameter in the system.
  • a high Curie point gives a large range for control while a Curie point close to room temperature is in particular energy efficient.
  • the Curie point of materials can be controlled via the stoichiometry of the alloy, e.g. [7].
  • the adaptive shimming will be achieved by the field produced by the magnetic material.
  • typically net shimming fields with both signs are required, but materials with susceptibilities that can be altered with both signs are typically not available.
  • the controllable materials can be arranged such that the magnetic field produced by the arrangement outside the magnetic material can have both signs dependent on the magnetism of one portion of the material. Thereby both polarities of shim fields can be generated.
  • a particular example is a substantially cylindrical, arrangement with its axis along the external magnetic field that is longer than the volume of interest. If the magnetic moment density of the arrangement is constant, the field induced by the arrangement outside the cylinder is substantially zero. Locally increasing the magnetic moment density of portion of the arrangement produces an additional net field outside the cylinder of said increase in magnetic moment, conversely a reduction produces a field with opposite sign.
  • the energy efficiency of the approach is furthermore determined by the provided thermal isolation of the controlled magnetic material portion.
  • Materials with very low thermal conductivity such as foams, glass, vacuum capsules or aerogels can be employed.
  • materials with high thermal conductivity but preferentially low electrical conductivity can be employed for thermal grounding of the structure i.e. avoiding spreading of the heat and reducing heat transfer through the thermal isolation by flattening hot spots.
  • Such materials are typically very hard crystals or ceramics such as aluminum oxide, aluminum nitrate.
  • the power efficiency is, given a high thermal isolation, much lower than with resistive shim coils. Furthermore, coupling to the switching gradient fields and field distortions induced by eddy currents running on the shim units are intrinsically very low due to the small size of the shimming units.
  • the speed at which the shimming fields can be ramped depends on the steepness of temperature dependence of the magnetism, the thermal capacity of the shim unit and the heating or cooling power that can be supplied.
  • the thermal capacity can be kept low by choosing materials with high magnetization mass density.
  • a magnetic material with high heat conduction can be chosen.
  • the magnetic material can be structured (by thin layering or cladding) with a material with high heat conduction in order to accelerate the heat transport in the magnetic material.
  • the thermal capacity is optimized by choosing a material. Therefore micromachining, plating or sputtering of magnetic materials on highly heat conductive materials, or vice-versa can be beneficial.
  • heat pumps such as Peltier elements can be employed in order to heat and cool the material. This would not only speed up the slewing of the magnetic shimming fields but would also allow using materials with Curie temperatures close to room temperature improving the energy efficiency maintaining high slew rates.
  • FIG. 1 A schematic representation of one embodiment of a secondary magnetic field source providing an adjustable magnetic field.
  • FIG. 2 A schematic representation of a further embodiment of a secondary magnetic field source providing an adjustable magnetic field.
  • FIG. 3 An exemplary arrangement of an MRI apparatus including a plurality of adjustable magnetic field elements.
  • FIG. 4 a Typical temperature dependence of the magnetic moment density (m) of a ferromagnetic particle in a strong external field. Towards the Curie temperature (T C ) the strong ferromagnetic moment diminishes. Above T C the paramagnetism scales still down with temperature. b) T C of cupric alloys can be adjusted by the admixture of copper. Thereby the temperature range in which a magnetic particle has to be controlled can be adjusted.
  • FIG. 5 Spatial distribution of magnetic material.
  • the distribution of the static material (m) and the controllable units (m c (T)) settled at half of their maximum moment provides zero magnetic field outside the cylindrical structure given it is much longer than the volume of interest. Lowering one unit's temperature provides then a net field of a paramagnet and increasing the temperature that of a net strong diamagnet. The shim units can thereby adjust the fields with both signs (bipolarly).
  • FIG. 6 Setup.
  • the controllable units (a) were made of a (3 mm) 3 Ni75Cu25 shot thermally coupled to SMD resistors.
  • a Pt500 measures its temperature. 50 ⁇ m diameter wires are used for connecting.
  • a wrapper of foam is applied for isolation and aluminum foil for RF shielding.
  • FIG. 7 a Field as recorded by the field probes heating m 1 -m 3 sequentially.
  • temperature T as a representative example of an external control parameter that influences the magnetic moment density of a material of interest.
  • control parameter instead of temperature, so the following examples shall not be construed as a limitation to the use of temperature as the control parameter.
  • FIG. 1 The basic principle of an adjustable secondary magnetic field source is illustrated in FIG. 1 .
  • the device is placed in an external magnetic field B 0 oriented in z-direction.
  • FIG. 1 b shows the situation where the temperature of the central section has been set to establish a local magnetic moment density that is higher than that of the surrounding parts of the rod, i.e. m 2 (T)>m.
  • This situation corresponds to an arrangement wherein one magnetic dipole is located in the central part of the rod-like object.
  • FIG. 1 c shows the situation where the temperature of the central section has been set to establish a local magnetic moment density that is lower than that of the surrounding parts of the rod, i.e. m 2 (T) ⁇ m.
  • This situation corresponds to having a pair of magnetic dipoles located at the two ends of the rod-like object with a gap in the central part having a magnetic field distribution corresponding to an arrangement with one centrally arranged magnetic dipole now pointing in the opposite direction as compared to FIG. 1 b .
  • the two terminal magnetic dipoles shown in FIG. 1 c would be longitudinally stretched and thus the resulting field surrounding the object would be substantially zero. This would effectively lead to a situation as shown in FIG. 1 d.
  • the high magnetic moment situation shown in FIG. 1 b can be established by keeping the local temperature T below the Curie temperature T C whereas the low magnetic moment situation shown in FIG. 1 c can be established by keeping the local temperature T above the Curie temperature T c .
  • the portions shown at the left and right, respectively are set to different temperatures T low and T high , respectively.
  • T low and T high can be adjusted to be below and above the Curie temperature T C , respectively. With such an arrangement it is possible to generate secondary magnetic fields with disparate local patterns.
  • the secondary magnetic field in the neighborhood of the portion at z a has a component B z (z a ) directed in positive z-direction
  • the secondary magnetic field has a component B z (z b ) directed in negative z-direction
  • FIG. 3 An exemplary arrangement of an MRI apparatus including a plurality of adjustable magnetic field elements acting as secondary magnetic field sources for providing an adjustable magnetic field B′ is shown in FIG. 3 .
  • the arrangement comprises a radiofrequency (RF) coil 1 and a cylindrically formed element 2 made of a first magnetic material M 1 and provided with a plurality of distinct shimming portions 3 of a second magnetic material M 2 .
  • the element 2 is arranged surrounding a schematically shown sample or object zone 4 .
  • the RF coil 1 is provided with a plurality of capacitor elements 5 .
  • Example 1 Magnetic Pebbles—Materials with Controllable Magnetism for Compact, Low-Power Shim Units
  • the magnetic moment density (m) of a ferromagnetic particle in a strong external magnetic field can be controlled by its temperature ([10], FIG. 4 a ).
  • T C Curie temperature
  • the ferromagnetism vanishes and renders the material paramagnetic.
  • the secondary fields nearly vanishes.
  • a shim field can be tailored.
  • Nickel and Copper were alloyed to shots in a Ni75Cu25 stoichiometry [7] resulting in a T C of 350° K ( FIG. 4 b ).
  • Each shot of ⁇ (3 mm) 3 is restively heated, its temperature is measured by a Pt500 thermistor and it is thermally isolated and shielded ( FIGS. 6 a and b ).
  • the magnetic material is arranged in a matrix such that its net secondary field is uniform when the magnetization of the heated particles is roughly halved (e.g. FIG. 5 ).
  • 35 particles were arranged on the axis of the main magnetic field by press fitting in a wooden bar with 16 mm distance ( FIG. 6 c ).
  • Three controllable magnetic particles (having 2 m at low temperatures) were mounted in the center-slots, obtaining from each a net field outside the cylinder of approximately a dipole with a magnetic moment of ⁇ m to +m.
  • the secondary field of the shim unit was measured by B 0 mapping (Philips 3T Achieva, Best Netherlands) with 3 ms echo-spacing in a phantom bottle placed directly on top of the unit. 3 magnetic field probes (Skope MRT, Zurich, Switzerland) were each placed about 1 cm from each unit and 2 on top of the bottle.
  • FIGS. 7 a and 7 b show the net B 0 fields induced by the three shim units temporally and spatially. Voltages from 0-10 V were applied in steps resulting in a temperature range from 293-420° K. The surface of the unit did warm up hardly noticeably. The slew rate was about 1 ⁇ T/s.
  • FIG. 7 b shows field profiles in about 4 cm distance from the units. The ripples in the shim field next to the unit in the sagittal images result from the discretization of the magnetic moment distribution from a continuous cylinder into individual shots. They are expected to be drastically reduced once the NiCu is cast into a cylindrical geometry.
  • Particles with controllable magnetism produce shim-field patterns with high spatial degrees of freedom. Since the source of the field is not an electric current but the magnetism of the material, smaller form factors and lower current consumptions are achieved and the particles are well decoupled from gradient and shim as well as from RF coils. Opposed to passive shims, rearranging the material is not required to fit subject specific susceptibility distributions.
  • the heat required to control the units can be administered by DC and AC currents as well as optically tunable materials can be employed [11]. Furthermore the power delivery for the heating can be efficiently modulated by switched mode schemes such as by PWM current sources similarly as used for LED lightings where tens of channels can be housed in a single IC package. This allows placing the required electronics in the bore which dramatically reduces the involved cabling efforts.
  • the dependence and spatial pattern of the fields induced by the individual shim units in the volume of interest in the subject have to be known in advance. There are various methods for obtaining this information. Typically this information will be gathered during the design or installation/maintenance procedure of the device.
  • the field patterns can be either obtained by magnetostatic field simulations/calculations using the knowledge of the geometrical distribution of the employed materials and its magnetic properties.
  • the fields can be measured using a field camera, a scanning magnetic field probe or an MRI based tomographic procedure (B0 mapping sequence, [12, 13]) performed on a phantom or in-vivo/in-situ.
  • B0 mapping sequence [12, 13]
  • the field can be measured with different control parameter values or with and without shimming unit present and the measurements can subsequently be compared.
  • the dependence of the induced shimming field on the control parameter can be directly measured in an MRI scanner using one of the method mentioned above. Thereby it might be sufficient in many cases to acquire a calibration curve for the employed material and using this information together with the spatial distribution of the material to calculate an estimate of the induced fields.
  • the spatial distribution of the induced fields is linearly dependent on the magnetic moment of the employed material at the given control variable. Therefore the acquisition/estimate of the field distribution can be separated from the estimation of the magnetic moment of the material. Consequently, only few field maps covering the entire volume are required.
  • the B0 field in the volume of interest is measured in-situ. I.e. the subject/sample is positioned in the scanner as suitable for the subsequent scanning procedure.
  • Well known measurement procedures for active shimming can be employed [13-16] by which the field is obtained on full grid or on projections to appropriate basis functions.
  • the position of the shim units or at least the entire array has to be determined. This can be achieved either by optical markers for positioning or referencing to light visors, direct mechanical or optical measurements or by acquiring and evaluating the signal from NMR active fiducial markers or field probes during positioning scans.
  • the control value for each shim unit can be calculated such that the field distribution in the volume of interest will approximate the given target distribution (typically a uniform field) best.
  • target distribution typically a uniform field
  • well-known optimization techniques can be employed. In most cases it will be beneficial to employ constrained optimization algorithms incorporating the maximum fields that can be induced by each shimming unit.
  • the calculated control values are then applied to the shim units.

Landscapes

  • Physics & Mathematics (AREA)
  • Condensed Matter Physics & Semiconductors (AREA)
  • General Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Signal Processing (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Magnetic Resonance Imaging Apparatus (AREA)
US16/083,973 2016-01-17 2017-01-17 B0 shimming device for mri Abandoned US20190235036A1 (en)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
EP16151629.9 2016-01-17
EP16151629.9A EP3193184A1 (de) 2016-01-17 2016-01-17 B0-abgleichsvorrichtung für mrt
PCT/EP2017/050862 WO2017121906A1 (en) 2016-01-17 2017-01-17 B0 shimming device for mri

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2017/050862 A-371-Of-International WO2017121906A1 (en) 2016-01-17 2017-01-17 B0 shimming device for mri

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US17/390,985 Continuation US11733329B2 (en) 2016-01-17 2021-08-01 B0 shimming device for MRI

Publications (1)

Publication Number Publication Date
US20190235036A1 true US20190235036A1 (en) 2019-08-01

Family

ID=55173805

Family Applications (2)

Application Number Title Priority Date Filing Date
US16/083,973 Abandoned US20190235036A1 (en) 2016-01-17 2017-01-17 B0 shimming device for mri
US17/390,985 Active US11733329B2 (en) 2016-01-17 2021-08-01 B0 shimming device for MRI

Family Applications After (1)

Application Number Title Priority Date Filing Date
US17/390,985 Active US11733329B2 (en) 2016-01-17 2021-08-01 B0 shimming device for MRI

Country Status (3)

Country Link
US (2) US20190235036A1 (de)
EP (2) EP3193184A1 (de)
WO (1) WO2017121906A1 (de)

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6477398B1 (en) * 1997-11-13 2002-11-05 Randell L. Mills Resonant magnetic susceptibility imaging (ReMSI)
US20060113995A1 (en) * 2004-11-30 2006-06-01 Peter Jarvis Magnetic field generating apparatus and method for magnetic resonance imaging
US8581585B2 (en) * 2008-02-12 2013-11-12 Hitachi Medical Corporation Magnetic resonance imaging apparatus, initial state creation method, optimum intensity determination method, and magnetic resonance imaging method

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
NL8303535A (nl) * 1983-10-14 1985-05-01 Philips Nv Kernspinresonantie apparaat.
JPH08215168A (ja) * 1995-02-17 1996-08-27 Ge Yokogawa Medical Syst Ltd 磁場均一度調整方法および装置
GB2439749B (en) * 2006-07-06 2010-03-03 Siemens Magnet Technology Ltd Passive shimming of magnet systems
JP4908960B2 (ja) * 2006-07-27 2012-04-04 株式会社日立製作所 超伝導磁石装置および磁気共鳴イメージング装置
JP5060151B2 (ja) * 2007-04-10 2012-10-31 株式会社日立製作所 磁場均一度調整装置、およびこれを用いた超伝導磁石装置、並びに磁気共鳴撮像装置
US7962019B2 (en) * 2007-11-09 2011-06-14 General Electric Company System, method and apparatus for controlling drift of a main magnetic field in an MRI system

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6477398B1 (en) * 1997-11-13 2002-11-05 Randell L. Mills Resonant magnetic susceptibility imaging (ReMSI)
US20060113995A1 (en) * 2004-11-30 2006-06-01 Peter Jarvis Magnetic field generating apparatus and method for magnetic resonance imaging
US8581585B2 (en) * 2008-02-12 2013-11-12 Hitachi Medical Corporation Magnetic resonance imaging apparatus, initial state creation method, optimum intensity determination method, and magnetic resonance imaging method

Also Published As

Publication number Publication date
EP3193184A1 (de) 2017-07-19
WO2017121906A1 (en) 2017-07-20
US20220018921A1 (en) 2022-01-20
US11733329B2 (en) 2023-08-22
EP3403111A1 (de) 2018-11-21

Similar Documents

Publication Publication Date Title
US7961067B2 (en) Superconducting magnet apparatus and magnetic resonance imaging apparatus
US20020171424A1 (en) MRI gradient coil with variable field of view and apparatus and methods employing the same
JP2005505316A (ja) 不連続に又は連続的に可変な視野で効率的に遮蔽されたｍｒｉ傾斜磁場コイル
Lother et al. Design of a mobile, homogeneous, and efficient electromagnet with a large field of view for neonatal low-field MRI
Schmitt The gradient system
US6853855B2 (en) Magnetic resonance tomography apparatus with improved spatial and time stabilization of the homogeneity of the magnetic basic field
CN103983929B (zh) 具有脉冲式均衡磁场梯度的磁共振设备
US6825663B2 (en) Magnetic resonance apparatus and operating method therefor for actively regulating heating in the apparatus
Gudino et al. Advancements in gradient system performance for clinical and research MRI
US9671479B2 (en) Method and apparatus for shimming a superconducting magnet
US11733329B2 (en) B0 shimming device for MRI
US8198897B2 (en) Superconductive magnetic device, magnetic resonance imaging apparatus and magnetic field inhomogeneity compensation method
Brunner et al. B 0 shimming device for MRI
Neuberger et al. Radiofrequency coils for magnetic resonance microscopy
Wang et al. Highly shielded gradient coil design for a superconducting planar MRI system
Tamada et al. Experimental evaluation of the magnetization process in a high Tc bulk superconducting magnet using magnetic resonance imaging
Gilbert et al. Evaluation of a positron emission tomography (PET)‐compatible field‐cycled MRI (FCMRI) scanner
CA3012161A1 (en) Systems and methods for magnetic field-dependent relaxometry using magnetic resonance imaging
JP2008125928A (ja) シムトレイ温度制御装置を備えた磁気共鳴イメージング装置
Alford et al. Design and construction of a prototype high‐power B0 insert coil for field‐cycled imaging in superconducting MRI systems
Shirai et al. Development of a compact mouse MRI using a yokeless permanent magnet
JP6104631B2 (ja) 磁気共鳴イメージング装置
Fishbein et al. Hardware for magnetic resonance imaging
Oh et al. Experimental temperature and specific absorption rate mapping using MRI in a transmit-receive head coil at 3.0 t
Goodrich et al. Design, fabrication, and testing of an insertable double‐imaging‐region gradient coil

Legal Events

Date Code Title Description
AS Assignment

Owner name: ETH ZURICH, SWITZERLAND

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:BRUNNER, DAVID;GROSS, SIMON;PRUESSMANN, KLAAS;REEL/FRAME:046837/0853

Effective date: 20180907

Owner name: UNIVERSITAET ZUERICH, SWITZERLAND

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:BRUNNER, DAVID;GROSS, SIMON;PRUESSMANN, KLAAS;REEL/FRAME:046837/0853

Effective date: 20180907

STPP Information on status: patent application and granting procedure in general

Free format text: DOCKETED NEW CASE - READY FOR EXAMINATION

STPP Information on status: patent application and granting procedure in general

Free format text: NON FINAL ACTION MAILED

STPP Information on status: patent application and granting procedure in general

Free format text: RESPONSE TO NON-FINAL OFFICE ACTION ENTERED AND FORWARDED TO EXAMINER

STCV Information on status: appeal procedure

Free format text: NOTICE OF APPEAL FILED

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION