WO2013011440A1 - Helium vapor magnetic resonance magnet - Google Patents
Helium vapor magnetic resonance magnet Download PDFInfo
- Publication number
- WO2013011440A1 WO2013011440A1 PCT/IB2012/053605 IB2012053605W WO2013011440A1 WO 2013011440 A1 WO2013011440 A1 WO 2013011440A1 IB 2012053605 W IB2012053605 W IB 2012053605W WO 2013011440 A1 WO2013011440 A1 WO 2013011440A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- thermally conductive
- insulating material
- coil form
- coil
- magnetic resonance
- Prior art date
Links
- 239000001307 helium Substances 0.000 title claims description 27
- 229910052734 helium Inorganic materials 0.000 title claims description 27
- SWQJXJOGLNCZEY-UHFFFAOYSA-N helium atom Chemical compound [He] SWQJXJOGLNCZEY-UHFFFAOYSA-N 0.000 title claims description 27
- 239000012777 electrically insulating material Substances 0.000 claims abstract description 28
- 239000004593 Epoxy Substances 0.000 claims abstract description 19
- 238000004804 winding Methods 0.000 claims abstract description 18
- 239000008393 encapsulating agent Substances 0.000 claims abstract description 12
- 239000011152 fibreglass Substances 0.000 claims abstract description 7
- 238000000034 method Methods 0.000 claims description 13
- 238000003384 imaging method Methods 0.000 claims description 10
- 238000004519 manufacturing process Methods 0.000 claims description 10
- 239000000463 material Substances 0.000 claims description 10
- 239000011810 insulating material Substances 0.000 claims description 8
- 125000006850 spacer group Chemical group 0.000 claims description 8
- 238000002595 magnetic resonance imaging Methods 0.000 claims description 4
- 230000003068 static effect Effects 0.000 claims description 4
- 239000004020 conductor Substances 0.000 claims description 3
- 239000011140 metalized polyester Substances 0.000 claims description 3
- -1 polytetrafluoroethylene Polymers 0.000 claims description 3
- 229920001343 polytetrafluoroethylene Polymers 0.000 claims description 3
- 239000004810 polytetrafluoroethylene Substances 0.000 claims description 3
- 238000005452 bending Methods 0.000 claims description 2
- 238000004611 spectroscopical analysis Methods 0.000 claims description 2
- 238000010276 construction Methods 0.000 claims 2
- 239000012212 insulator Substances 0.000 claims 1
- 229920006395 saturated elastomer Polymers 0.000 claims 1
- 238000001816 cooling Methods 0.000 description 5
- 239000007788 liquid Substances 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- 239000007789 gas Substances 0.000 description 4
- 238000010292 electrical insulation Methods 0.000 description 3
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 2
- 230000004075 alteration Effects 0.000 description 2
- 229910052782 aluminium Inorganic materials 0.000 description 2
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 2
- 229910052802 copper Inorganic materials 0.000 description 2
- 239000010949 copper Substances 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 229910001220 stainless steel Inorganic materials 0.000 description 2
- 239000010935 stainless steel Substances 0.000 description 2
- 238000004140 cleaning Methods 0.000 description 1
- 239000011248 coating agent Substances 0.000 description 1
- 238000000576 coating method Methods 0.000 description 1
- 230000008602 contraction Effects 0.000 description 1
- 229920006334 epoxy coating Polymers 0.000 description 1
- 239000004744 fabric Substances 0.000 description 1
- 239000000945 filler Substances 0.000 description 1
- 238000009413 insulation Methods 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 238000004381 surface treatment Methods 0.000 description 1
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
- G01R33/381—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using electromagnets
- G01R33/3815—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using electromagnets with superconducting coils, e.g. power supply therefor
-
- 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
- G01R33/3802—Manufacture or installation of magnet assemblies; Additional hardware for transportation or installation of the magnet assembly or for providing mechanical support to components of the magnet assembly
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F6/00—Superconducting magnets; Superconducting coils
- H01F6/04—Cooling
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F6/00—Superconducting magnets; Superconducting coils
- H01F6/06—Coils, e.g. winding, insulating, terminating or casing arrangements therefor
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
- Y10T29/4902—Electromagnet, transformer or inductor
- Y10T29/49071—Electromagnet, transformer or inductor by winding or coiling
Definitions
- the present application relates to magnetic resonance magnets, cryomagnets, superconducting magnets, and specifically to the cooling of those types of magnets.
- Magnetic resonance (MR) scanners use superconducting magnets, which are cooled to a superconducting temperature, e.g. less than 5.2° Kelvin.
- a superconducting temperature e.g. less than 5.2° Kelvin.
- liquid Helium has been used to cool superconductive magnets because of its thermal properties.
- liquid Helium is expensive. Many areas of the world do not have a ready supply of liquid Helium or replacement liquid Helium.
- the electrical and magnetic properties of the magnet are maintained while cooling the magnet to produce a uniform static magnetic field of a magnetic resonance system. Cooling systems uniformly cool the coil without invading the integrity of the magnetic coil.
- the bore of the magnet coil used for whole body MR imaging is large enough to accommodate a patient to be imaged as well as the structures which thermally separate the patient from the extreme cold temperature of the cryogenic system.
- Manufacturing designs accommodate a room temperature in the bore of the coil assembly while maintaining a operating temperature in the surrounding magnet below the critical temperature of the magnet.
- a room temperature of 70° F is approximately 294°K, while the critical temperature of the magnet is typically below 5.2°K. This extreme temperature difference creates design and manufacturing complexities.
- the present application provides a new and improved Helium vapor magnetic resonance magnet which overcomes the above-referenced problems and others.
- a magnetic resonance magnet has a coil form, thermally conductive sheets, thermally conductive tubing sections, at least one layer of thermally conductive electrically insulating material, and a winding of superconductive wire.
- the coil form is shaped as a hollow cylinder. At least two thermally conductive sheets extend circumferentially on the coil form, separated by non-electrically conductive regions.
- a thermally conductive tubing section is thermally connected to each thermally conductive sheet.
- At least one layer of thermally conductive electrically insulating material is disposed around and bonded to the thermally conductive sheets.
- a winding of superconductive wire is disposed around and bonded together and to the electrically insulating material.
- a magnetic resonance magnet system includes at least one magnet assembly, Helium vapor which as it flows through the thermally conductive tubing around the coil cools the coil below the critical superconducting magnet temperature, and a refrigerator heat exchanger connected to the tubing which cools the Helium vapor.
- a magnet assembly has a coil form, thermally conductive sheets, thermally conductive tubing sections, at least one layer of thermally conductive electrically insulating material, and a winding of superconductive wire.
- the coil form is shaped as a hollow cylinder. At least two thermally conductive sheets extend circumferentially on the coil form, separated by non-electrically conductive regions.
- a thermally conductive tubing section is connected to each thermally conductive sheet. At least one layer of thermally conductive electrically insulating material is disposed around and bonded to the thermally conductive sheets.
- a winding of superconductive wire is disposed around and bonded together and to the electrically insulating material.
- a magnetic resonance imaging or spectroscopy system includes a magnetic resonance magnet system, a gradient coil, a gradient amplifier, a radio frequency coil, a transmitter, a transmitter, a receiver, and a processor.
- the magnetic resonance magnet system has at least one magnet assembly, Helium vapor which as it flows through the thermally conductive tubing around the coil cools the coil below the critical superconducting magnet temperature, and a refrigerator heat exchanger connected to the tubing which cools the Helium vapor.
- a magnet assembly has a coil form, thermally conductive sheets, thermally conductive tubing sections, at least one layer of thermally conductive electrically insulating material, and a winding of superconductive wire.
- a gradient coil is located within a bore of the magnetic resonance magnet system.
- a gradient amplifier is connected to the gradient coil.
- a radio frequency coil is located inside the gradient coil.
- a transmitter is connected to the radio frequency coil.
- a receiver is connected to the radio frequency coil which receives the RF signals.
- a controller connects to the gradient amplifier and to the transmitter and controls the gradient amplifier and transmitter to excite resonance in a subject.
- a processor is connected to the receiver and to the controller and processes received resonance signals into an image and/or spectroscopic information.
- a method of manufacturing a magnetic resonance magnet includes forming a cylindrical coil form. Thermally conductive tubing section is connected to thermally conductive sheets. At least one layer of electrically insulating material is bonded to the thermally conductive sheets. Superconductive wire is wound around the electrically insulating material and bonds the superconductive wire together and to the electrically insulating material.
- a method of magnetic resonance imaging includes generating a static B 0 magnetic field in an imaging region using a helium vapor cooled magnet assembly manufactured as discussed above. Gradient magnetic fields are generated in the imaging region. An RF field is transmitted into the imaging region. Magnetic resonance signals are received from the imaging region. An image is reconstructed from the received magnetic resonance signals.
- Another advantage is that helium vapor is used to cool the magnet instead of liquid helium.
- Another advantage is the simple and thermally efficient method of attaching heat exchanger plates to the coils without affecting either the coil's fabrication or the electrical performance.
- Another advantage is the simplicity of flow of Helium vapor through the system and the ability to uniformly cool the magnet coil.
- the invention may take form in various components and arrangements of components, and in various steps and arrangements of steps.
- the drawings are only for purposes of illustrating the preferred embodiments and are not to be construed as limiting the invention.
- FIGURE 1 is diagram showing one embodiment of a Helium vapor magnetic resonance magnet system.
- FIGURE 2 is diagram showing one embodiment of an enlarged view of a magnet.
- FIGURE 3 is diagram showing a cross section of one embodiment of a magnetic resonance magnet with an exploded view.
- FIGURE 4 is a flowchart illustrating a method of manufacturing a coil assembly.
- FIGURE 5 is a diagram illustrating an embodiment of a MR system with a cut-away view of a vacuum dewar showing a magnetic resonance magnet.
- the closed loop system 10 includes circulating Helium vapor which is heated by an MR magnet assembly 20 and cooled by a refrigerator heat exchanger 30 with an associated cryogenic refrigerator 40, and recirculated to the magnet assembly 20.
- a suitable refrigerator heat exchanger with associated cryogenic refrigerator is described in US 2008/0209919.
- the cooled Helium gas enters the magnet assembly 20 at the bottom and flows up a thermally conductive tubing 50 attached to thermally conductive sheets 60 or plates interior to the magnet.
- the Helium vapor is cooled in the heat exchanger 30 to approximately 4.2°K, which provides a 1°K margin below the critical temperature of the magnet.
- the cold gas from the refrigerator heat exchanger 30 is relatively dense but becomes less dense as it is warmed by the magnet assembly 20, producing a downward flow of denser helium gas from the refrigerator heat exchanger 30 to the bottom of the magnet and an upward flow of less dense warmer helium gas through the magnet and back to the refrigerator heat exchanger.
- the magnet assembly 20 is mounted on a coil form 70.
- a coil assembly 25 When manufactured, a coil assembly 25 is created using a winding fixture and then mounted on a coil form 70 or manufactured directly onto the coil form 70. Multiple coils 25 of varying widths are typically used in a MR system. Each coil assembly 25 is mounted on a corresponding coil form 70. The width of a coil 25 affects a number of windings and a strength of the magnetic field generated.
- the coils manufactured with the process described below vary in size, e.g. up to about 300 mm in width.
- the coil form 70 is manufactured from a structural metal, such as stainless steel, formed in a hollow cylinder.
- thermally conductive sheeting 60 are electrically isolated by a non-electrically conductive spacer 90.
- the region between the sheets 60 prevents circumferential currents in the thermally conductive sheeting 60 which would interfere with the operation of the MR system.
- the thermally conductive sheets are made, for example, of copper approximately .3 mm in thickness. Aluminum and other thermally conductive materials can also be used for the sheeting 60.
- the space between the thermally conductive sheets 60 is approximately 6 mm which is filled with the non- electrically conductive spacer 90, e.g. a plastic filler strip.
- the non-electrically conductive spacer 90 provides a uniform surface on which to wind the coil.
- the sheets are bent to the circumference of the coil form 70, or if a winding fixture is used during the manufacturing process to the outside diameter of the winding fixture.
- Thermally conductive tubing 50 is thermally and mechanically affixed to the thermally conductive sheets 60.
- An example is 9- 10mm OD refrigerator grade copper tubing. Other materials with good thermal conduction may be used such as aluminum.
- the size of the tubing 50 is large enough that the pressure drop in the tubing is small. With smaller diameter tubing more friction is created, and a drop in cooling capacity results. With tubing that is too small, there is greater non-uniform cooling of the magnet.
- the coil form 70 is fabricated, e.g. machined from stainless steel.
- an insulating material 100 is wrapped around the coil form 70 or a winding fixture (not shown) if used to manufacture the magnet coil.
- An example of the insulating material 100 is a layer of polytetrafluoroethylene, commonly known as TEFLONTM, sandwiched between layers of metalized polyester, commonly found as MYLARTM.
- TEFLONTM polytetrafluoroethylene
- MYLARTM metalized polyester
- the thermally conductive tubing 50 is soldered or welded to the sheets 60 and the sheets and tubing are bent to the radius of the coil form.
- the tubing 50 may be attached prior to the bending of the sheets 60 or can be bent first and the thermally conductive sheets and tubing attached in their bent state.
- the thermally conductive sheet 60 and tubing is position over the insulating layer 100.
- the thermally conductive sheet 60 preferably, is not affixed to the electrically insulating sheet to accommodate thermal expansion/contraction differences.
- the electrically insulating spacers 90 are positioned on the electrically insulating material 100 between the thermally conductive sheets and the top and bottom of the coil assembly.
- the sheeting 60 is cleaned to remove any oxide present to provide for a thermally conductive bond.
- a layer of electrical insulation 110 which is thermally conductive.
- Electrically insulating spacers 120 are disposed on either side of where the coil is to be wound. Flanges may be added to the coil form 70 when formed to limit movement of the sheeting 60 during operation of the magnet 20 and to affix coverings and other structural components. If a flange is present, then the electrically insulating spacer is placed between the flange and the sheeting 60 prior to wrapping in step 402. The layer of electrical insulation 110 is applied after cleaning the sheeting.
- a thermally conductive, electrically insulating epoxy encapsulant is applied, followed by a layer of material 110 which electrically insulates the coil from the thermally conductive sheets 60, allows good thermal conductivity, and binds with the epoxy.
- a suitable material 100 is bi-directional fiber glass cloth with a surface treatment to improve bonding with the epoxy. Both sides of the fiber glass material 110 are coated with the epoxy to provide strong bonding and good thermal conduction and the fiber glass material is wrapped around the thermal conductive sheet 60. The process can be repeated with more epoxy coatings and fiber glass material 110 to ensure that any irregularities are taken up and provide structural rigidity.
- Other thin flexible materials which provide electrical insulation, and permit coating and saturation of the epoxy encapsulant are also contemplated.
- the superconducting wire 80 is wound around the layer of encapsulated fiber glass material 110 before the epoxy dries.
- additional thermally conductive epoxy encapsulant is applied to securely bond the wire coil 80 together and to the layer of electrically insulating material 110 which is in turn bonded to the thermally conductive sheets 60.
- All the interstitial spaces in the wire coil 80 are filled with epoxy encapsulate to ensure a strong and thermally efficient bond with the sheets 60.
- the epoxy, the sheets 60, and the tubing 50 act as efficient heat exchangers.
- the thickness of the wire coil 80 is dictated by the magnetic field to be generated and is generally 2.5 - 5 cm.
- the mechanical bond of the coil assembly 25 or coil should withstand liftoff or hoop forces when current is applied.
- the thermally conductive sheets 60 bonded to the coil winding with an epoxy have a high peel strength and good thermal conductivity.
- a vacuum dewar 515 contains the magnet assembly 20 which generates a static B 0 field during operation.
- the covering of vacuum dewar attaches, e.g., using the flange previously described, and encloses the coil form 70, sheets 60, and coil winding 80.
- a gradient coil 505 and a radio frequency (RF) coil 510 are concentrically located within the bore of the vacuum dewar.
- the gradient coil 505 generates gradient G x G y G z magnetic fields powered by a gradient amplifier 550 during the imaging process.
- the gradient magnetic fields are generated under control of a sequence control 520.
- the illustrated RF coil 510 is a whole body coil which transmits a Bi magnetic field when turned on by an RF transmitter 530.
- the sequence control 520 determines when the RF coil 510 operates in a transmit mode and when the RF coil 510 operates in a receive mode.
- a receiver 570 demodulates the RF signals.
- the RF signals are then reconstructed by a processor 580 and may displayed as an image on an output device 590 or stored for other access.
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Engineering & Computer Science (AREA)
- Power Engineering (AREA)
- Electromagnetism (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US14/233,642 US9575150B2 (en) | 2011-07-20 | 2012-07-13 | Helium vapor magnetic resonance magnet |
CN201280035972.3A CN103688185B (zh) | 2011-07-20 | 2012-07-13 | 氦蒸汽磁共振磁体 |
EP12741099.1A EP2734856B1 (en) | 2011-07-20 | 2012-07-13 | Helium vapor magnetic resonance magnet |
IN669CHN2014 IN2014CN00669A (GUID-C5D7CC26-194C-43D0-91A1-9AE8C70A9BFF.html) | 2011-07-20 | 2012-07-13 | |
JP2014520761A JP6214098B2 (ja) | 2011-07-20 | 2012-07-13 | ヘリウム蒸気磁気共鳴磁石 |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US201161509604P | 2011-07-20 | 2011-07-20 | |
US61/509,604 | 2011-07-20 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2013011440A1 true WO2013011440A1 (en) | 2013-01-24 |
Family
ID=46598893
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/IB2012/053605 WO2013011440A1 (en) | 2011-07-20 | 2012-07-13 | Helium vapor magnetic resonance magnet |
Country Status (6)
Families Citing this family (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB2579074B (en) * | 2018-11-19 | 2021-02-17 | Siemens Healthcare Ltd | A self-supporting flexible thermal radiation shield |
US11977139B2 (en) | 2019-05-21 | 2024-05-07 | Koninklijke Philips N.V. | Accelerated cooldown of low-cryogen magnetic resonance imaging (MRI) magnets |
CN112366058A (zh) * | 2020-11-25 | 2021-02-12 | 宁波健信核磁技术有限公司 | 一种超导磁体低温系统 |
CN113053615B (zh) * | 2021-06-01 | 2021-08-24 | 潍坊新力超导磁电科技有限公司 | 一种用于超导磁体的氦微循环制冷杜瓦系统 |
CN119230241B (zh) * | 2024-10-31 | 2025-08-22 | 江西联创光电超导应用有限公司 | 一种具有气流导向通道的高导热超导线圈 |
Citations (5)
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US4726199A (en) * | 1984-09-17 | 1988-02-23 | Kabushiki Kaisha Toshiba | Superconducting apparatus |
WO2006122594A1 (en) * | 2005-05-18 | 2006-11-23 | Siemens Magnet Technology Ltd | Apparatus and method for installing cooling tubes on a cooled former |
US20080209919A1 (en) | 2007-03-01 | 2008-09-04 | Philips Medical Systems Mr, Inc. | System including a heat exchanger with different cryogenic fluids therein and method of using the same |
US20100295642A1 (en) * | 2009-05-20 | 2010-11-25 | Robert Hahn | Magnetic field generating device |
JP2011125686A (ja) * | 2009-10-30 | 2011-06-30 | General Electric Co <Ge> | 超伝導マグネット向けの冷却システム及び方法 |
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US3427391A (en) * | 1967-09-20 | 1969-02-11 | Avco Corp | Composite superconductive conductor |
US3801942A (en) * | 1972-03-27 | 1974-04-02 | Siemens Ag | Electric magnet with superconductive windings |
JPS6213010A (ja) * | 1985-07-11 | 1987-01-21 | Toshiba Corp | 超電導電磁石 |
JPH0738339B2 (ja) | 1991-10-18 | 1995-04-26 | 株式会社東芝 | 超電導装置 |
DE4300023B4 (de) | 1993-01-02 | 2004-04-08 | Robert Bosch Gmbh | Kraftstoffeinspritzpumpe für Brennkraftmaschinen |
US5461873A (en) | 1993-09-23 | 1995-10-31 | Apd Cryogenics Inc. | Means and apparatus for convectively cooling a superconducting magnet |
JPH07240310A (ja) * | 1994-03-01 | 1995-09-12 | Mitsubishi Electric Corp | 核磁気共鳴分析装置用超電導マグネット |
JPH09306723A (ja) | 1996-05-10 | 1997-11-28 | Sumitomo Heavy Ind Ltd | 冷凍機冷却型超電導磁石装置 |
WO2000020795A2 (en) * | 1998-09-14 | 2000-04-13 | Massachusetts Institute Of Technology | Superconducting apparatuses and cooling methods |
US6725683B1 (en) * | 2003-03-12 | 2004-04-27 | General Electric Company | Cryogenic cooling system for rotor having a high temperature super-conducting field winding |
EP1477822A1 (en) * | 2003-05-07 | 2004-11-17 | Hitachi, Ltd. | Nuclear magnetic resonance spectrometer for liquid-solution |
US7626477B2 (en) * | 2005-11-28 | 2009-12-01 | General Electric Company | Cold mass cryogenic cooling circuit inlet path avoidance of direct conductive thermal engagement with substantially conductive coupler for superconducting magnet |
JP4788377B2 (ja) | 2006-02-13 | 2011-10-05 | 株式会社日立製作所 | 超電導コイル |
CN101236239B (zh) * | 2007-01-30 | 2012-01-25 | 西门子(中国)有限公司 | 磁共振系统的超导磁体的电流引线 |
JP5823116B2 (ja) * | 2010-11-15 | 2015-11-25 | 株式会社東芝 | 超電導コイル |
GB2490478B (en) * | 2011-04-20 | 2014-04-23 | Siemens Plc | Superconducting magnets with thermal radiation shields |
GB2490325B (en) * | 2011-04-21 | 2013-04-10 | Siemens Plc | Combined MRI and radiation therapy equipment |
EP2761237B1 (en) * | 2011-09-28 | 2019-05-08 | Koninklijke Philips N.V. | Very efficient heat exchanger for cryogen free mri magnet |
-
2012
- 2012-07-13 US US14/233,642 patent/US9575150B2/en active Active
- 2012-07-13 EP EP12741099.1A patent/EP2734856B1/en active Active
- 2012-07-13 IN IN669CHN2014 patent/IN2014CN00669A/en unknown
- 2012-07-13 WO PCT/IB2012/053605 patent/WO2013011440A1/en active Application Filing
- 2012-07-13 CN CN201280035972.3A patent/CN103688185B/zh active Active
- 2012-07-13 JP JP2014520761A patent/JP6214098B2/ja active Active
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4726199A (en) * | 1984-09-17 | 1988-02-23 | Kabushiki Kaisha Toshiba | Superconducting apparatus |
WO2006122594A1 (en) * | 2005-05-18 | 2006-11-23 | Siemens Magnet Technology Ltd | Apparatus and method for installing cooling tubes on a cooled former |
US20080209919A1 (en) | 2007-03-01 | 2008-09-04 | Philips Medical Systems Mr, Inc. | System including a heat exchanger with different cryogenic fluids therein and method of using the same |
US20100295642A1 (en) * | 2009-05-20 | 2010-11-25 | Robert Hahn | Magnetic field generating device |
JP2011125686A (ja) * | 2009-10-30 | 2011-06-30 | General Electric Co <Ge> | 超伝導マグネット向けの冷却システム及び方法 |
Also Published As
Publication number | Publication date |
---|---|
EP2734856B1 (en) | 2016-01-20 |
IN2014CN00669A (GUID-C5D7CC26-194C-43D0-91A1-9AE8C70A9BFF.html) | 2015-04-03 |
US9575150B2 (en) | 2017-02-21 |
JP2014523783A (ja) | 2014-09-18 |
JP6214098B2 (ja) | 2017-10-18 |
US20140159726A1 (en) | 2014-06-12 |
EP2734856A1 (en) | 2014-05-28 |
CN103688185A (zh) | 2014-03-26 |
CN103688185B (zh) | 2016-05-25 |
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