US20060006865A1 - Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils - Google Patents
Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils Download PDFInfo
- Publication number
- US20060006865A1 US20060006865A1 US11/224,436 US22443605A US2006006865A1 US 20060006865 A1 US20060006865 A1 US 20060006865A1 US 22443605 A US22443605 A US 22443605A US 2006006865 A1 US2006006865 A1 US 2006006865A1
- Authority
- US
- United States
- Prior art keywords
- coil
- mtl
- coils
- mri
- transmission line
- 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
Links
Images
Classifications
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01Q—ANTENNAS, i.e. RADIO AERIALS
- H01Q17/00—Devices for absorbing waves radiated from an antenna; Combinations of such devices with active antenna elements or systems
-
- 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
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
- G01R33/345—Constructional details, e.g. resonators, specially adapted to MR of waveguide type
-
- 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
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
- G01R33/34007—Manufacture of RF coils, e.g. using printed circuit board technology; additional hardware for providing mechanical support to the RF coil assembly or to part thereof, e.g. a support for moving the coil assembly relative to the remainder of the MR system
-
- 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
-
- 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
- Y10T29/49073—Electromagnet, transformer or inductor by assembling coil and core
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Apparatus and method for MRI imaging using a coil constructed of microstrip transmission line (MTL coil) are disclosed. In one method, a target is positioned to be imaged within the field of a main magnetic field of a magnet resonance imaging (MRI) system, a MTL coil is positioned proximate the target, and a MRI image is obtained using the main magnet and the MTL coil. In another embodiment, the MRI coil is used for spectroscopy. MRI imaging and spectroscopy coils are formed using microstrip transmission line. These MTL coils have the advantageous property of good performance while occupying a relatively small space, thus allowing MTL coils to be used inside restricted areas more easily than some other prior art coils. In addition, the MTL coils are relatively simple to construct of inexpensive components and thus relatively inexpensive compared to other designs. Further, the MTL coils of the present invention can be readily formed in a wide variety of coil configurations, and used in a wide variety of ways. Further, while the MTL coils of the present invention work well at high field strengths and frequencies, they also work at low frequencies and in low field strengths as well.
Description
- This application is a continuation application of U.S. patent application Ser. No. 09/974,184, filed Oct. 9, 2001, which is a continuation of provisional application Ser. No. 60/239,185, filed, Oct. 9, 2000, and entitled “Microstrip Resonator RF Surface and Volume Coils and Methods for NMR Imaging and Spectroscopy at High Fields.” The entire contents of U.S. application Ser. No. 60/239,185 are hereby incorporated herein by reference.
- This invention was partially supported by NIH grants NS38070 (W.C.), NS39043 (W.C.), P41 RR08079 (a National Research Resource grant from NIH), Keck Foundation, National Foundation for Functional Brain Imaging and the US Department of Energy. The Government may have certain rights in the invention.
- This invention pertains generally to magnetic resonance imaging (MRI) and more specifically to surface and volume coils for MRI imaging and spectroscopy procedures.
- Surface and volume coils are used in MRI imaging or spectroscopy procedures in order to obtain more accurate or detailed images of tissue under investigation. Preferably, a MRI coil performs accurate imaging or spectroscopy across a wide range of resonant frequencies, is easy to use, and is affordable. Further, the operating volume inside the main magnet of many MRI systems is relatively small, often just large enough for a patient's head or body. As a result, there is typically little space available for a coil in addition to the patient. Accordingly, it is advantageous if a surface or volume coil itself occupies as little space as possible.
- In high fields (3 Tesla and beyond), due to the high Larmour frequencies required, radiation losses of RF coils become significant which decreases a coil's quality factor or Q factor, and a low Q factor can result in low signal-to-noise ratio (SNR) in MRI procedures. One existing solution to reducing radiation losses is adding a RF shielding around the coil(s). The RF shielding, however, usually makes the physical size of RF coil much larger, which as noted above is not desired in the MR studies, especially in the case of high field operations.
- According to certain example embodiments of the invention there are provided a MRI coil formed of microstrip transmission line. According to various embodiments of the invention, MRI coils according the present invention are easy to manufacture with relatively low cost components, and compact in design. In addition, the coil's distributed element design provides for operation at relatively high quality factors and frequencies and in high field (4 Tesla or more) environments. Further, microstrip coils according to the present invention exhibit relatively low radiation losses and require no RF shielding. As a result of not requiring RF shielding, the coils may be of compact size while having high operating frequencies for high field MR studies, thus saving space in the MRI machine. Further, the methods and apparatus of the present invention are not just good for high frequency MR studies, but also good for low frequency cases.
-
FIG. 1 illustrates a method according to one example embodiment of the invention. -
FIGS. 2-14 illustrate various example embodiments of the apparatus of the invention. - In the following detailed description of the preferred embodiments, reference is made to the accompanying drawings that form a part hereof, and in which is shown by way of illustration specific preferred embodiments in which the invention may be practiced. These embodiments are described in sufficient detail to enable those skilled in the art to practice the invention, and it is to be understood that other embodiments may be utilized and that logical, mechanical and electrical changes may be made without departing from the spirit and scope of the present invention. The following detailed description is, therefore, not to be taken in a limiting sense, and the scope of the present invention is defined only be the appended claims.
- According to a first method embodiment of the invention, as illustrated in
FIG. 1 , a target is positioned within the field of a main magnetic field of a magnet resonance imaging (MRI) system, at least one coil is positioned proximate the target wherein the coil is constructed using at least one microstrip transmission line, and the main magnet and the MTL coil are used to obtain MRI images from the target. According to one use of the microstrip transmission line (MTL) coil, it is operated as a receiver (pickup coil) or a transmitter (excitation coil) or both during an imaging procedure. As used herein the term “MTL coil” generally refers to any coil formed using a microstrip transmission line. - The microstrip transmission line, according to one example design, is formed of a strip conductor, a ground plane and a dielectric material that may be air, a vacuum, low loss dielectric sheets such as Teflon or Duroid, or liquid Helium or liquid Nitrogen. Further, the strip conductor or ground plane are, in one embodiment, formed in whole or in part from a non-magnetic conductive material such as copper or silver. According to another example embodiment of the invention, the ground planes for multiple strip conductors are arranged in one single piece foil so as to reduce radiation loss.
- In another example embodiment, the MTL coil is a volume MTL coil having a plurality of microstrip transmission lines. In still another example embodiment, the volume MTL coil is detuned using PIN diodes. In yet another example embodiment, the MTL coil includes bisected ground planes and the PIN diodes are positioned in the gap of the bisected ground planes.
- According to still other example embodiments of the methods of the invention, a MTL coil is tuned by varying capacitive termination of the MTL coil wherein, for example but not by way of limitation, the MTL coil is tuned by varying capacitive termination on each end of the MTL coil.
- In still other example embodiments of the method, the microstrip transmission line is arranged in a rectangular or circular configuration, or, in the alternative, in an S shape. In one advantageous embodiment, the MTL coil is constructed using at least two turns to improve the homogeneity of the magnetic field characteristics.
- In still other example embodiments, one or more lumped elements are connected to the transmission line and operated so as to match the impedance of the line.
- In yet still another embodiment, an MTL coil is operated in a resonant mode by bisection of the ground plane and tuning of the resonance by adjusting displacement of the ground planes. In another embodiment, at least two of the MTL coils are operated in a quadrature mode. In still another embodiment, a coil is arranged so as to operate as a ladder MTL coil. In yet another embodiment, at least two MTL coils are arranged and operated as a half volume MTL coil.
- In still another example embodiment, an inverted imaging MTL coil is formed wherein the dielectric material is positioned in a plane on the side of the strip conductor plane in the direction of the field, and wherein coupling is capacitive.
- In yet another example embodiment of the methods of the invention, the MTL coil is driven using a capacitive impedance matching network. In still another example embodiment of the methods of the invention, the dielectric constant Er is adjusted to change the resonant frequency of the MTL coil.
- In yet still another example embodiment of the method, the coil dielectric substrate is flexible, and the MTL coil is formed and used in more than one configuration allowing a single coil to be adapted to multiple purposes. According to still another embodiment, the substrate is formed of thin layers of Teflon or other dielectric material allowing the substrate to be bent or twisted.
- Referring first to
FIGS. 2A and 2B , there is illustrated in diagrammatic form an example embodiment of a microstrip transmission line (MTL) 20 having astrip conductor 21 with a width W andground plane 22, on either side of adielectric substrate 23 having a height H and dielectric coefficient Er. Magnetic field lines H are shown surroundingstrip conductor 21 and emanating outward in the Y direction orthogonal toground plane 22 and along the length ofstrip conductor 21. As illustrated, the field is contained in whole or in part on one side of thestrip conductor 21 by theground plane 22, and extends outwardly beyond the plane of the strip conductor in a direction extending away from the ground plane. - According to a first embodiment of the apparatus of the invention, as illustrated in
FIGS. 2C and 2D , there is provided a single turn MRI imaging orspectroscopy MTL coil 23 constructed using at least one microstrip transmission line. The microstrip transmission line coil, according to one example design, is formed of astrip conductor 24, aground plane 25 and asubstrate 26 made of a dielectric material that may be air, a vacuum, a single or multilayer low loss dielectric sheets such as Teflon or Duroid materials, or liquid Helium or Nitrogen. According to one example embodiment, such coil is 9 cm×9 cm, has asubstrate 26 that is 5-7 mm, usescopper foil 36 microns in thickness (for example an adhesive-backed copper tape such as is available from 3M Corporation of St. Paul, Minn.) for the strip conductors and ground plane, and has a resonant frequency of 300 MHz. According to one example embodiment, the MRI signal intensity is proportional to H when H<5 mm and reaches a maximum when H 5 mm. These results indicate that the optimized H value is about 5-7 mm for the above embodiments of the microstrip MTL coils according to the present invention. Further, the dielectric material thickness H, or more accurately, the ratio W/H, is an important parameter that affects the B1 penetration in air. If H is too small, or W/H too large, most of electromagnetic fields will be compressed around the strip conductor. Although the B1 penetration will increase with the increase of dielectric material thickness H, or the decrease of the ratio W/H, a thickness of 5-7 mm is suggested in practice because the radiation loss can become significant when the substrate is much thicker. This optimized H makes it possible to build a very thin surface coil at extremely high fields, where the coil thickness can, in certain circumstances, be less than the conventional surface coil with RF shielding. - Further, the strip conductor or ground plane are, in one embodiment, formed in whole or in part from a non-conductive material such as copper or silver. As also illustrated, the strip conductor and ground plane, in this embodiment and others described below, is connected to a source of electrical excitation or RF detection circuitry, for example through a coax or other connector (not shown). According to still another example embodiment, because corners of the coil tend to radiate surface waves and thus have a potential to cause hot spots in images and degrade the Q value of coils, the corners may be chamfered to reduce the radiation loss and improve B1 distribution. According to another
example embodiment 30 of the invention as illustrated inFIGS. 3A and 3B , a two turn coil is illustrated. As shown, asingle ground plane 32 is shared by thestrip conductors 34, wherein the ground planes are formed for example with a single sheet of foil so as to reduce radiation loss.FIGS. 3C and 3D illustrateadditional embodiments embodiment 35 has one turn andembodiment 36 has twoturns 102 to improve the homogeneity of the magnetic field characteristics. - In still other configurations, the coils may assume an “S” shape, as may be advantageously used for example in a volume coil design, or any other arbitrary shape. Further, as illustrated in
FIGS. 2C and 3A , one ormore elements - In another example embodiment as illustrated in
FIGS. 4A and 4B , theMTL coil 42 is a half-volume coil having a plurality of microstrip transmission lines each having aground plane 46 andstrip conductor 48. - In still another example embodiment illustrated in
FIGS. 5A and 5B , theMTL coil 50 includes a bisectedground plane 52. In this configuration, tuning of the resonance frequency is accomplished by adjustingdisplacement 54 of at least one of the ground planes. As illustrated inFIG. 6 , in yet anotherembodiment 60,PIN diodes 64 are positioned in thegap 66 of the bisected ground planes 62, and used to detune the coil. - According to still other example embodiments of the apparatus of the invention illustrated in
FIG. 7A , aMTL coil 70 is tuned by varyingcapacitive termination elements 72 on one end of the coil.FIG. 7B illustrates a hypothetical plot of magnetic field profile vs. capacitive termination value for a range of capacitances. As illustrated, increasing capacitive termination raises the magnetic field profile at the end of the coil at which the termination is applied.FIGS. 7C and 7D illustrate an example embodiment and field profile for tuning aMTL coil 74 by varying capacitive termination on eachend 75 of the coil. Further, fine tuning can also be accomplished by slightly changing the length of the strip conductor. - In yet still another embodiment illustrated in
FIG. 8A , at least two of the MTL coils 80 are arranged to be operated in a quadrature mode. The equivalent electrical circuit forMTL coil 80 is illustrated inFIG. 8B . In this example schematic, Z0 is the characteristic impedance of each microstrip element. In the impendence jX, jX1, jX2, jX15, X, X1, X2, X15 are positive real numbers. For themode 1, the current on each microstrip resonant element is modulated by a cosine function cos(npie/8) where n=0, 1, 2, . . . , 15. L denotes the length of thevolume coil 80. - In another example embodiment shown in
FIG. 9 , anMTL coil 90 is formed as arranged and operated as a ladder MTL coil. In yet another embodiment illustrated in schematic form inFIGS. 10A and 10B , avolume coil 100 is provided.Coil 100 includes ground planes 102 on the outside of a cylinder of dielectric material (for example Acrylic) having a diameter of 260 mm, a length of 210 mm, and amaterial thickness 104 of 6.35 mm.Strip conductors 106 are placed on the inside of thecoil 100 running parallel to the axis. Coaxial connectors 108 are provided to connect the ground planes and strip conductors to a source of electrical excitation or RF detectors, as is conventionally done in use of a MRI volume or surface coil. According to one example embodiment of the apparatus, the high permittivity of the human head, the dielectric resonance effect results in higher signal intensity in the central region of the image. This higher intensity can be taken into account in the design of a large volume coil at high fields. In one example embodiment, in order to achieve a relatively uniform MR image in the human head, an inhomogeneous B1 distribution in the transaxial plane in free space is intentionally designed to compensate for the dielectric resonance effect in the human head. - According to still another embodiment, for the individual microstrip resonant element, the resonant frequency can be modified by choosing appropriate dielectric substrate with different relative dielectric constant. Therefore, doubly tuned frequency operation can be easily achieved by making two different resonant frequencies for the microstrip elements in the volume coil, alternatively. Namely, one set of microstrip resonant elements with even numbers can be set to one resonance frequency while another set of microstrip resonant elements with odd numbers set to a different resonance frequency. Multiple tuned RF coils also can be designed using the same approach. Each resonance can be quadraturely driven with an appropriate quadrature hybrid.
- In still another example embodiment shown in
FIG. 11 , aninverted MTL coil 110 is illustrated, wherein is coupling is capacitive adjacent microstrip elements to provide lower resonant frequency operation. - Still another
example embodiment 120 of the invention is illustrated inFIG. 12 , wherein thestrip conductors 122 have ‘T’ shaped ends 124 andcoupling gap 126 betweentips 128 of the ends are adjusted to change the current and E field at the end of the coil, and thus allow the operating frequency to be raised. - In yet still another example embodiment of the apparatus shown in
FIG. 13 , theMTL coil 130 substrate dielectric is formed of one or more relatively thinflexible layers 132 so that the coil may be bent or twisted or otherwise formed. Such layers may be formed of Teflon, for example. According to this embodiment, thecoil 130 may be bent or formed into a first configuration, and thereafter formed into a second or third or more different configurations, wherein the coil may be used in more than one configuration and thus have a multipurpose nature. - Referring now to
FIG. 14 , there is illustrated a photograph of yet one more example embodiment of a volume coil 140 according to the present invention. - According to still yet another example embodiment, the MTL coil is formed as a dome-shaped coil which offers an increased filling factor and a great sensitivity and homogeneity in the top area of the human head. By applying the microstrip resonator volume coil technique, the dome-shaped coil can be constructed for higher field applications.
- According to still another embodiment of the invention, the unbalanced circuit of the microstrip coil provides that there is no need to use the balun circuit commonly used in surface coils and balanced volume coils to stabilize the coil's resonance and diminish the so-called ‘cable resonance’.
- Thus, there has been described above method and apparatus for forming MRI imaging and spectroscopy coils using microstrip transmission line. Due to its specific semi-open transmission line structure, substantial electromagnetic energy is stored in the dielectric material between the thin conductor and the ground plane, which results in a reduced radiation loss and a reduced perturbation of sample loading to the RF coil, compared to conventional surface coils. The MTL coils of the present invention are also characterized by a high Q factor, no RF shielding, small physical coil size, lower cost and easy fabrication. These MTL coils have the advantageous property of good performance while occupying a relatively small space, thus allowing MTL coils to be used inside restricted areas more easily than some other prior art coils. Further, the MTL coils of the present invention can be readily formed in a wide variety of coil configurations, and used in a wide variety of ways. Further, while the MTL coils of the present invention work well at high field strengths and frequencies, they also work at low frequencies and in low field strengths as well.
- Further information concerning the design, operation and theory of MTL coils is found in Zhang, X. et al., “Microstrip RF Surface Coil Design for Extremely High-Field MRI and Spectroscopy”, Magn. Reson. Med. 2001 September; 46(3):443-50 and Zhang X. et al., “A Novel RF Volume Coil Design Using Microstrip Resonator for NMR Imaging and Spectroscopy”, submitted for publication. The entire contents of both of the aforementioned papers are incorporated herein by reference.
Claims (1)
1. A method, comprising:
positioning a target to be imaged within the field of a main magnetic field of a magnet resonance imaging (MRI) system;
positioning at least one coil proximate the target wherein the coil is constructed using at least one microstrip transmission line;
imaging the target using the main magnet and the coil with MRI.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/224,436 US20060006865A1 (en) | 2000-10-09 | 2005-09-12 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
US11/436,197 US20060277749A1 (en) | 2000-10-09 | 2006-05-17 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US23918500P | 2000-10-09 | 2000-10-09 | |
US09/974,184 US7023209B2 (en) | 2000-10-09 | 2001-10-09 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
US11/224,436 US20060006865A1 (en) | 2000-10-09 | 2005-09-12 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/974,184 Continuation US7023209B2 (en) | 2000-10-09 | 2001-10-09 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/436,197 Continuation US20060277749A1 (en) | 2000-10-09 | 2006-05-17 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
Publications (1)
Publication Number | Publication Date |
---|---|
US20060006865A1 true US20060006865A1 (en) | 2006-01-12 |
Family
ID=22900994
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/974,184 Expired - Lifetime US7023209B2 (en) | 2000-10-09 | 2001-10-09 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
US11/224,436 Abandoned US20060006865A1 (en) | 2000-10-09 | 2005-09-12 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
US11/436,197 Abandoned US20060277749A1 (en) | 2000-10-09 | 2006-05-17 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/974,184 Expired - Lifetime US7023209B2 (en) | 2000-10-09 | 2001-10-09 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/436,197 Abandoned US20060277749A1 (en) | 2000-10-09 | 2006-05-17 | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
Country Status (5)
Country | Link |
---|---|
US (3) | US7023209B2 (en) |
EP (1) | EP1344076A1 (en) |
JP (2) | JP2004511278A (en) |
AU (1) | AU2001296738A1 (en) |
WO (1) | WO2002031522A1 (en) |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060158191A1 (en) * | 2003-08-21 | 2006-07-20 | Insight Neuroimaging Systems, Llc | Microstrip coil design for MRI apparatus |
US20060277749A1 (en) * | 2000-10-09 | 2006-12-14 | Regents Of The University Of Minnesota | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
US20070192103A1 (en) * | 2006-02-14 | 2007-08-16 | Nobuo Sato | Conversational speech analysis method, and conversational speech analyzer |
US20110204890A1 (en) * | 2008-10-29 | 2011-08-25 | Hitachi Medical Corporation | Antenna device and magnetic resonance imaging device |
WO2016172650A1 (en) * | 2015-04-24 | 2016-10-27 | Massachusetts Institute Of Technology | Micro magnetic resonance relaxometry |
US9599685B2 (en) | 2010-10-07 | 2017-03-21 | Hitachi, Ltd. | Antenna device and magnetic resonance imaging device for suppressing absorption rate of irradiated waves |
Families Citing this family (63)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6335622B1 (en) * | 1992-08-25 | 2002-01-01 | Superconductor Technologies, Inc. | Superconducting control elements for RF antennas |
US6633161B1 (en) * | 1999-05-21 | 2003-10-14 | The General Hospital Corporation | RF coil for imaging system |
US7598739B2 (en) | 1999-05-21 | 2009-10-06 | Regents Of The University Of Minnesota | Radio frequency gradient, shim and parallel imaging coil |
AU2001277234A1 (en) * | 2000-07-31 | 2002-02-13 | Regents Of The University Of Minnesota | Open TEM resonators for MRI |
US6727703B2 (en) * | 2002-05-17 | 2004-04-27 | General Electric Company | Method and apparatus for decoupling RF detector arrays for magnetic resonance imaging |
US6980000B2 (en) * | 2003-04-29 | 2005-12-27 | Varian, Inc. | Coils for high frequency MRI |
US7560927B2 (en) * | 2003-08-28 | 2009-07-14 | Massachusetts Institute Of Technology | Slitted and stubbed microstrips for high sensitivity, near-field electromagnetic detection of small samples and fields |
US7908690B2 (en) * | 2003-09-30 | 2011-03-22 | Sentinelle Medical, Inc. | Supine patient support for medical imaging |
US7379769B2 (en) | 2003-09-30 | 2008-05-27 | Sunnybrook Health Sciences Center | Hybrid imaging method to monitor medical device delivery and patient support for use in the method |
US7970452B2 (en) | 2003-09-30 | 2011-06-28 | Hologic, Inc. | Open architecture imaging apparatus and coil system for magnetic resonance imaging |
DE112004002117T5 (en) * | 2003-11-19 | 2006-10-05 | General Electric Co. | Phased Array Spinal coil with spatially displaced coil elements |
DE102004006322B4 (en) | 2004-02-10 | 2013-09-12 | RAPID Biomedizinische Geräte RAPID Biomedical GmbH | Imaging device for use of nuclear magnetic resonance |
WO2005111645A2 (en) | 2004-05-07 | 2005-11-24 | Regents Of The University Of Minnesota | Multi-current elements for magnetic resonance radio frequency coils |
DE602004010247T2 (en) * | 2004-07-30 | 2008-10-02 | Nexans | Cylindrically shaped superconducting device and its use as a resistive current limiter |
JP4682981B2 (en) * | 2004-08-03 | 2011-05-11 | ダイキン工業株式会社 | Fluorine-containing urethane compound |
EP1624314A1 (en) * | 2004-08-05 | 2006-02-08 | Max-Planck-Gesellschaft zur Förderung der Wissenschaften e.V. | Helmet-shaped TEM antenna for magnetic resonance measurements |
US7427861B2 (en) * | 2005-04-11 | 2008-09-23 | Insight Neuroimaging Systems, Llc | Dual-tuned microstrip resonator volume coil |
JP2008539903A (en) * | 2005-05-06 | 2008-11-20 | リージェンツ オブ ザ ユニバーシティ オブ ミネソタ | Wirelessly coupled magnetic resonance coil |
JP2009511232A (en) * | 2005-10-18 | 2009-03-19 | ターシオップ テクノロジーズ リミテッド ライアビリティ カンパニー | Method and apparatus for high gain nuclear magnetic resonance imaging |
US7420371B2 (en) * | 2006-01-04 | 2008-09-02 | Enh Research Institute | Slab-selective RF coil for MR system |
JP5179019B2 (en) * | 2006-04-04 | 2013-04-10 | 株式会社日立製作所 | Coil device and nuclear magnetic resonance imaging apparatus using the same |
US7498813B2 (en) * | 2006-05-04 | 2009-03-03 | General Electric Company | Multi-channel low loss MRI coil |
CN101454685B (en) * | 2006-05-30 | 2012-09-05 | 皇家飞利浦电子股份有限公司 | Detuning a radio-frequency coil |
JP2010517595A (en) * | 2006-08-15 | 2010-05-27 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Tunable and / or detunable MR receiver coil device |
RU2491568C2 (en) * | 2007-02-26 | 2013-08-27 | Конинклейке Филипс Электроникс, Н.В. | Double-resonant radio frequency strong field surface coils for magnetic resonance |
CN101675352A (en) * | 2007-05-03 | 2010-03-17 | 皇家飞利浦电子股份有限公司 | Transverse electromagnetic radio-frequency coil |
US7816918B2 (en) * | 2007-05-24 | 2010-10-19 | The Johns Hopkins University | Optimized MRI strip array detectors and apparatus, systems and methods related thereto |
ATE505736T1 (en) * | 2007-09-28 | 2011-04-15 | Max Planck Gesellschaft | STRIP GUIDE ANTENNA AND ANTENNA ARRANGEMENT FOR A MAGNETIC RESONANCE DEVICE |
US8290569B2 (en) | 2007-11-23 | 2012-10-16 | Hologic, Inc. | Open architecture tabletop patient support and coil system |
US8559186B2 (en) * | 2008-04-03 | 2013-10-15 | Qualcomm, Incorporated | Inductor with patterned ground plane |
JP5658656B2 (en) * | 2008-04-09 | 2015-01-28 | コーニンクレッカ フィリップス エヌ ヴェ | Double-layer multi-element RF strip coil antenna for high-field MR with reduced SAR |
US20110074422A1 (en) * | 2008-05-02 | 2011-03-31 | The Regents Of The University Of California The Office Of The President | Method and apparatus for magnetic resonance imaging and spectroscopy using multiple-mode coils |
US8299681B2 (en) | 2009-03-06 | 2012-10-30 | Life Services, LLC | Remotely adjustable reactive and resistive electrical elements and method |
EP2445413B1 (en) | 2009-06-23 | 2020-02-12 | Invivo Corporation | Variable angle guide holder for a biopsy guide plug |
US8125226B2 (en) * | 2009-07-02 | 2012-02-28 | Agilent Technologies, Inc. | Millipede surface coils |
US8854042B2 (en) | 2010-08-05 | 2014-10-07 | Life Services, LLC | Method and coils for human whole-body imaging at 7 T |
US8604791B2 (en) | 2010-09-09 | 2013-12-10 | Life Services, LLC | Active transmit elements for MRI coils and other antenna devices |
US9332926B2 (en) | 2010-11-25 | 2016-05-10 | Invivo Corporation | MRI imaging probe |
US9097769B2 (en) | 2011-02-28 | 2015-08-04 | Life Services, LLC | Simultaneous TX-RX for MRI systems and other antenna devices |
US9057767B2 (en) * | 2011-05-07 | 2015-06-16 | The University Of Utah | Linear phase microstrip radio frequency transmit coils |
US9160079B2 (en) * | 2011-09-14 | 2015-10-13 | William N. Carr | Compact multi-band antenna |
WO2013054235A1 (en) * | 2011-10-10 | 2013-04-18 | Koninklijke Philips Electronics N.V. | Transverse -electromagnetic (tem) radio - frequency coil for magnetic resonance |
WO2013065480A1 (en) | 2011-11-01 | 2013-05-10 | 株式会社 日立メディコ | Magnetic resonance imaging apparatus and antenna apparatus |
US9500727B2 (en) | 2012-04-20 | 2016-11-22 | Regents Of The University Of Minnesota | System and method for control of RF circuits for use with an MRI system |
US20140049259A1 (en) * | 2012-08-17 | 2014-02-20 | Lockheed Martin Corporation | Resonant magnetic ring antenna |
CN103767705B (en) | 2012-10-23 | 2017-12-22 | 三星电子株式会社 | Magnetic resonance imaging system and MR imaging method |
US9646376B2 (en) | 2013-03-15 | 2017-05-09 | Hologic, Inc. | System and method for reviewing and analyzing cytological specimens |
EP2967423B1 (en) | 2013-03-15 | 2021-06-30 | Synaptive Medical Inc. | Insert imaging device for surgical procedures |
US10191128B2 (en) | 2014-02-12 | 2019-01-29 | Life Services, LLC | Device and method for loops-over-loops MRI coils |
KR101541236B1 (en) * | 2014-03-11 | 2015-08-03 | 울산대학교 산학협력단 | Radio frequency resonator and magnetic resonance imaging apparatus comprising the same |
KR101635641B1 (en) * | 2014-04-22 | 2016-07-20 | 한국표준과학연구원 | Microstrip-based RF surface receive coil for the acquisition of MR images and RF resonator having thereof |
US9891299B1 (en) * | 2014-05-19 | 2018-02-13 | General Electric Company | Methods and systems for correcting B0 field in MRI imaging using shim coils |
KR102324731B1 (en) | 2014-09-19 | 2021-11-10 | 삼성전자주식회사 | Receiving coil for magnetic resonance imaging device |
US10288711B1 (en) | 2015-04-30 | 2019-05-14 | Life Services, LLC | Device and method for simultaneous TX/RX in strongly coupled MRI coil loops |
US11024454B2 (en) * | 2015-10-16 | 2021-06-01 | Qualcomm Incorporated | High performance inductors |
US10827948B1 (en) | 2015-11-25 | 2020-11-10 | Life Services, LLC | Method and apparatus for multi-part close fitting head coil |
US10324146B2 (en) * | 2016-01-12 | 2019-06-18 | Life Services, LLC | Method and apparatus for multi-part body coil |
JP7150415B2 (en) | 2017-04-27 | 2022-10-11 | コーニンクレッカ フィリップス エヌ ヴェ | Medical device for magnetic resonance imaging guided radiation therapy |
JP6914812B2 (en) * | 2017-11-16 | 2021-08-04 | 日本電子株式会社 | Probe and relay coil for nuclear magnetic resonance measurement |
US11333731B2 (en) * | 2018-04-13 | 2022-05-17 | Canon Medical Systems Corporation | Magnetic resonance imaging apparatus, RF coil, and magnetic resonance imaging method |
KR102287230B1 (en) * | 2019-11-05 | 2021-08-09 | 가천대학교 산학협력단 | Double tuned RF coil for MRI based on Microstrip-based line |
WO2022155457A1 (en) * | 2021-01-15 | 2022-07-21 | Hyperfine, Inc. | Flexible radio frequency coil apparatus and methods for magnetic resonance imaging |
DE102021001593A1 (en) | 2021-03-26 | 2022-09-29 | Giesecke+Devrient Currency Technology Gmbh | Sensor element, test device and method for testing data carriers with a spin resonance feature |
Citations (42)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4439733A (en) * | 1980-08-29 | 1984-03-27 | Technicare Corporation | Distributed phase RF coil |
US4620155A (en) * | 1984-08-16 | 1986-10-28 | General Electric Company | Nuclear magnetic resonance imaging antenna subsystem having a plurality of non-orthogonal surface coils |
US4626800A (en) * | 1984-06-05 | 1986-12-02 | Sony Corporation | YIG thin film tuned MIC oscillator |
US4679015A (en) * | 1985-03-29 | 1987-07-07 | Sony Corporation | Ferromagnetic resonator |
US4686473A (en) * | 1984-07-10 | 1987-08-11 | Thomson-Cgr | Device for creating and/or receiving an alternating magnetic field for an apparatus using nuclear magnetic resonance |
US4704739A (en) * | 1984-06-05 | 1987-11-03 | Sony Corporation | Receiving circuit for converting signals comprising at least two ferromagnetic resonators |
US4712067A (en) * | 1983-12-30 | 1987-12-08 | U.S. Philips Corporation | R.F. coil system for generating and/or receiving alternating magnetic fields |
US4751464A (en) * | 1987-05-04 | 1988-06-14 | Advanced Nmr Systems, Inc. | Cavity resonator with improved magnetic field uniformity for high frequency operation and reduced dielectric heating in NMR imaging devices |
US4792760A (en) * | 1986-02-07 | 1988-12-20 | Thomson-Cgr | Reception antenna for optical image formation device using nuclear magnetic resonance |
US4835472A (en) * | 1987-08-13 | 1989-05-30 | Siemens Aktiengesellschaft | Local coil for detecting nuclear magnetic resonance signals from an examination subject |
US4839594A (en) * | 1987-08-17 | 1989-06-13 | Picker International, Inc. | Faraday shield localized coil for magnetic resonance imaging |
US4983936A (en) * | 1986-07-02 | 1991-01-08 | Sony Corporation | Ferromagnetic resonance device |
US5006805A (en) * | 1988-09-23 | 1991-04-09 | Siemens Aktiengesellschaft | Surface coil arrangement for use in a nuclear magnetic resonance apparatus |
US5185573A (en) * | 1991-04-16 | 1993-02-09 | Hewlett-Packard Company | Method for focusing of magnetic resonance images |
US5270656A (en) * | 1992-04-24 | 1993-12-14 | The Trustees Of The University Of Pennsylvania | Biplanar RF coils for magnetic resonance imaging or spectroscopy |
US5363113A (en) * | 1987-05-07 | 1994-11-08 | General Electric Cgr S.A. | Electromagnetic antenna and excitation antenna provided with such electromagnetic antenna for a nuclear magnetic resonance apparatus |
US5514337A (en) * | 1994-01-11 | 1996-05-07 | American Research Corporation Of Virginia | Chemical sensor using eddy current or resonant electromagnetic circuit detection |
US5530424A (en) * | 1994-09-16 | 1996-06-25 | General Electric Company | Apparatus and method for high data rate communication in a computerized tomography system |
US5530425A (en) * | 1994-09-16 | 1996-06-25 | General Electric Company | Radiation shielded apparatus for high data rate communication in a computerized tomography system |
US5557247A (en) * | 1993-08-06 | 1996-09-17 | Uab Research Foundation | Radio frequency volume coils for imaging and spectroscopy |
US5646962A (en) * | 1994-12-05 | 1997-07-08 | General Electric Company | Apparatus for reducing electromagnetic radiation from a differentially driven transmission line used for high data rate communication in a computerized tomography system |
US5739812A (en) * | 1996-07-18 | 1998-04-14 | Cipher Co. Ltd. | System for inputting image and commond using three-dimensional mouse capable of generating, in real time, three-dimensional image |
US5757189A (en) * | 1996-11-27 | 1998-05-26 | Picker International, Inc. | Arbitrary placement multimode coil system for MR imaging |
US5886596A (en) * | 1993-08-06 | 1999-03-23 | Uab Research Foundation | Radio frequency volume coils for imaging and spectroscopy |
US5898306A (en) * | 1997-04-09 | 1999-04-27 | Regents Of The University Of Minnesota | Single circuit ladder resonator quadrature surface RF coil |
US5903198A (en) * | 1997-07-30 | 1999-05-11 | Massachusetts Institute Of Technology | Planar gyrator |
US5949311A (en) * | 1997-06-06 | 1999-09-07 | Massachusetts Institute Of Technology | Tunable resonators |
US5990681A (en) * | 1997-10-15 | 1999-11-23 | Picker International, Inc. | Low-cost, snap-in whole-body RF coil with mechanically switchable resonant frequencies |
US5998999A (en) * | 1996-12-12 | 1999-12-07 | Picker International, Inc. | Volume RF coils with integrated high resolution focus coils for magnetic resonance imaging |
US6023166A (en) * | 1997-11-19 | 2000-02-08 | Fonar Corporation | MRI antenna |
US6054856A (en) * | 1998-04-01 | 2000-04-25 | The United States Of America As Represented By The Secretary Of The Navy | Magnetic resonance detection coil that is immune to environmental noise |
US6054854A (en) * | 1996-07-31 | 2000-04-25 | Kabushiki Kaisha Toshiba | Arrangement of coil windings for MR systems |
US6060882A (en) * | 1995-12-29 | 2000-05-09 | Doty Scientific, Inc. | Low-inductance transverse litz foil coils |
US6133737A (en) * | 1997-05-26 | 2000-10-17 | Siemens Aktiengesellschaft | Circularly polarizing antenna for a magnetic resonance apparatus |
US6215307B1 (en) * | 1998-04-14 | 2001-04-10 | Picker Nordstar Oy | Coils for magnetic resonance imaging |
US6232779B1 (en) * | 1999-08-25 | 2001-05-15 | General Electric Company | NMR RF coil with improved resonant tuning and field containment |
US20020018043A1 (en) * | 2000-06-14 | 2002-02-14 | Masahiro Nakanishi | Electrophoretic display device and process for production thereof |
US6369570B1 (en) * | 2000-12-21 | 2002-04-09 | Varian, Inc. | B1 gradient coils |
US6396271B1 (en) * | 1999-09-17 | 2002-05-28 | Philips Medical Systems (Cleveland), Inc. | Tunable birdcage transmitter coil |
US6420871B1 (en) * | 2001-03-02 | 2002-07-16 | Varian, Inc. | Multiple tuned birdcage coils |
US6501274B1 (en) * | 1999-10-15 | 2002-12-31 | Nova Medical, Inc. | Magnetic resonance imaging system using coils having paraxially distributed transmission line elements with outer and inner conductors |
US6633161B1 (en) * | 1999-05-21 | 2003-10-14 | The General Hospital Corporation | RF coil for imaging system |
Family Cites Families (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3668569A (en) * | 1970-05-27 | 1972-06-06 | Hazeltine Corp | Distributed-constant dispersive network |
US4543543A (en) * | 1982-12-03 | 1985-09-24 | Raytheon Company | Magnetically tuned resonant circuit |
JP2503993B2 (en) | 1986-08-29 | 1996-06-05 | オムロン株式会社 | Paper processing equipment |
JP3079592B2 (en) | 1991-01-31 | 2000-08-21 | 株式会社島津製作所 | Surface coil for MRI |
JPH07321514A (en) * | 1994-05-25 | 1995-12-08 | Sony Corp | Ferromagnetic resonator |
FR2749286B1 (en) | 1996-06-04 | 1998-09-04 | Bernard Frederic | DEVICE FOR CONVEYING OBJECTS PROVIDED WITH A CHUTE OR THE LIKE SUCH AS FOR EXAMPLE BOTTLES, BOTTLES OR THE LIKE AND DEVICE FOR LOADING SUCH OBJECTS DESIGNED FOR SAID CONVEYOR |
JP2002512376A (en) | 1998-04-22 | 2002-04-23 | サウスウエスト・リサーチ・インスティチュート | Method for measuring porosity and permeability of crude oil-containing underground layer using EPR response data |
JP2000171208A (en) * | 1998-12-04 | 2000-06-23 | Toyota Motor Corp | Slide type position detecting device |
AU2001296738A1 (en) * | 2000-10-09 | 2002-04-22 | Regents Of The University Of Minnesota | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
US6771070B2 (en) * | 2001-03-30 | 2004-08-03 | Johns Hopkins University | Apparatus for magnetic resonance imaging having a planar strip array antenna including systems and methods related thereto |
-
2001
- 2001-10-09 AU AU2001296738A patent/AU2001296738A1/en not_active Abandoned
- 2001-10-09 US US09/974,184 patent/US7023209B2/en not_active Expired - Lifetime
- 2001-10-09 EP EP01977633A patent/EP1344076A1/en not_active Withdrawn
- 2001-10-09 WO PCT/US2001/031520 patent/WO2002031522A1/en active Application Filing
- 2001-10-09 JP JP2002534856A patent/JP2004511278A/en not_active Withdrawn
-
2005
- 2005-04-26 JP JP2005128758A patent/JP2005270674A/en active Pending
- 2005-09-12 US US11/224,436 patent/US20060006865A1/en not_active Abandoned
-
2006
- 2006-05-17 US US11/436,197 patent/US20060277749A1/en not_active Abandoned
Patent Citations (42)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4439733A (en) * | 1980-08-29 | 1984-03-27 | Technicare Corporation | Distributed phase RF coil |
US4712067A (en) * | 1983-12-30 | 1987-12-08 | U.S. Philips Corporation | R.F. coil system for generating and/or receiving alternating magnetic fields |
US4626800A (en) * | 1984-06-05 | 1986-12-02 | Sony Corporation | YIG thin film tuned MIC oscillator |
US4704739A (en) * | 1984-06-05 | 1987-11-03 | Sony Corporation | Receiving circuit for converting signals comprising at least two ferromagnetic resonators |
US4686473A (en) * | 1984-07-10 | 1987-08-11 | Thomson-Cgr | Device for creating and/or receiving an alternating magnetic field for an apparatus using nuclear magnetic resonance |
US4620155A (en) * | 1984-08-16 | 1986-10-28 | General Electric Company | Nuclear magnetic resonance imaging antenna subsystem having a plurality of non-orthogonal surface coils |
US4679015A (en) * | 1985-03-29 | 1987-07-07 | Sony Corporation | Ferromagnetic resonator |
US4792760A (en) * | 1986-02-07 | 1988-12-20 | Thomson-Cgr | Reception antenna for optical image formation device using nuclear magnetic resonance |
US4983936A (en) * | 1986-07-02 | 1991-01-08 | Sony Corporation | Ferromagnetic resonance device |
US4751464A (en) * | 1987-05-04 | 1988-06-14 | Advanced Nmr Systems, Inc. | Cavity resonator with improved magnetic field uniformity for high frequency operation and reduced dielectric heating in NMR imaging devices |
US5363113A (en) * | 1987-05-07 | 1994-11-08 | General Electric Cgr S.A. | Electromagnetic antenna and excitation antenna provided with such electromagnetic antenna for a nuclear magnetic resonance apparatus |
US4835472A (en) * | 1987-08-13 | 1989-05-30 | Siemens Aktiengesellschaft | Local coil for detecting nuclear magnetic resonance signals from an examination subject |
US4839594A (en) * | 1987-08-17 | 1989-06-13 | Picker International, Inc. | Faraday shield localized coil for magnetic resonance imaging |
US5006805A (en) * | 1988-09-23 | 1991-04-09 | Siemens Aktiengesellschaft | Surface coil arrangement for use in a nuclear magnetic resonance apparatus |
US5185573A (en) * | 1991-04-16 | 1993-02-09 | Hewlett-Packard Company | Method for focusing of magnetic resonance images |
US5270656A (en) * | 1992-04-24 | 1993-12-14 | The Trustees Of The University Of Pennsylvania | Biplanar RF coils for magnetic resonance imaging or spectroscopy |
US5886596A (en) * | 1993-08-06 | 1999-03-23 | Uab Research Foundation | Radio frequency volume coils for imaging and spectroscopy |
US5557247A (en) * | 1993-08-06 | 1996-09-17 | Uab Research Foundation | Radio frequency volume coils for imaging and spectroscopy |
US5514337A (en) * | 1994-01-11 | 1996-05-07 | American Research Corporation Of Virginia | Chemical sensor using eddy current or resonant electromagnetic circuit detection |
US5530424A (en) * | 1994-09-16 | 1996-06-25 | General Electric Company | Apparatus and method for high data rate communication in a computerized tomography system |
US5530425A (en) * | 1994-09-16 | 1996-06-25 | General Electric Company | Radiation shielded apparatus for high data rate communication in a computerized tomography system |
US5646962A (en) * | 1994-12-05 | 1997-07-08 | General Electric Company | Apparatus for reducing electromagnetic radiation from a differentially driven transmission line used for high data rate communication in a computerized tomography system |
US6060882A (en) * | 1995-12-29 | 2000-05-09 | Doty Scientific, Inc. | Low-inductance transverse litz foil coils |
US5739812A (en) * | 1996-07-18 | 1998-04-14 | Cipher Co. Ltd. | System for inputting image and commond using three-dimensional mouse capable of generating, in real time, three-dimensional image |
US6054854A (en) * | 1996-07-31 | 2000-04-25 | Kabushiki Kaisha Toshiba | Arrangement of coil windings for MR systems |
US5757189A (en) * | 1996-11-27 | 1998-05-26 | Picker International, Inc. | Arbitrary placement multimode coil system for MR imaging |
US5998999A (en) * | 1996-12-12 | 1999-12-07 | Picker International, Inc. | Volume RF coils with integrated high resolution focus coils for magnetic resonance imaging |
US5898306A (en) * | 1997-04-09 | 1999-04-27 | Regents Of The University Of Minnesota | Single circuit ladder resonator quadrature surface RF coil |
US6133737A (en) * | 1997-05-26 | 2000-10-17 | Siemens Aktiengesellschaft | Circularly polarizing antenna for a magnetic resonance apparatus |
US5949311A (en) * | 1997-06-06 | 1999-09-07 | Massachusetts Institute Of Technology | Tunable resonators |
US5903198A (en) * | 1997-07-30 | 1999-05-11 | Massachusetts Institute Of Technology | Planar gyrator |
US5990681A (en) * | 1997-10-15 | 1999-11-23 | Picker International, Inc. | Low-cost, snap-in whole-body RF coil with mechanically switchable resonant frequencies |
US6023166A (en) * | 1997-11-19 | 2000-02-08 | Fonar Corporation | MRI antenna |
US6054856A (en) * | 1998-04-01 | 2000-04-25 | The United States Of America As Represented By The Secretary Of The Navy | Magnetic resonance detection coil that is immune to environmental noise |
US6215307B1 (en) * | 1998-04-14 | 2001-04-10 | Picker Nordstar Oy | Coils for magnetic resonance imaging |
US6633161B1 (en) * | 1999-05-21 | 2003-10-14 | The General Hospital Corporation | RF coil for imaging system |
US6232779B1 (en) * | 1999-08-25 | 2001-05-15 | General Electric Company | NMR RF coil with improved resonant tuning and field containment |
US6396271B1 (en) * | 1999-09-17 | 2002-05-28 | Philips Medical Systems (Cleveland), Inc. | Tunable birdcage transmitter coil |
US6501274B1 (en) * | 1999-10-15 | 2002-12-31 | Nova Medical, Inc. | Magnetic resonance imaging system using coils having paraxially distributed transmission line elements with outer and inner conductors |
US20020018043A1 (en) * | 2000-06-14 | 2002-02-14 | Masahiro Nakanishi | Electrophoretic display device and process for production thereof |
US6369570B1 (en) * | 2000-12-21 | 2002-04-09 | Varian, Inc. | B1 gradient coils |
US6420871B1 (en) * | 2001-03-02 | 2002-07-16 | Varian, Inc. | Multiple tuned birdcage coils |
Cited By (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060277749A1 (en) * | 2000-10-09 | 2006-12-14 | Regents Of The University Of Minnesota | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils |
US20060158191A1 (en) * | 2003-08-21 | 2006-07-20 | Insight Neuroimaging Systems, Llc | Microstrip coil design for MRI apparatus |
US7202668B2 (en) * | 2003-08-21 | 2007-04-10 | Insight Neuroimaging Systems, Llc | Microstrip coil design for MRI apparatus |
US20070192103A1 (en) * | 2006-02-14 | 2007-08-16 | Nobuo Sato | Conversational speech analysis method, and conversational speech analyzer |
US8036898B2 (en) | 2006-02-14 | 2011-10-11 | Hitachi, Ltd. | Conversational speech analysis method, and conversational speech analyzer |
US8423369B2 (en) | 2006-02-14 | 2013-04-16 | Hitachi, Ltd. | Conversational speech analysis method, and conversational speech analyzer |
US20110204890A1 (en) * | 2008-10-29 | 2011-08-25 | Hitachi Medical Corporation | Antenna device and magnetic resonance imaging device |
US8947084B2 (en) | 2008-10-29 | 2015-02-03 | Hitachi Medical Corporation | Antenna device and magnetic resonance imaging device |
US9599685B2 (en) | 2010-10-07 | 2017-03-21 | Hitachi, Ltd. | Antenna device and magnetic resonance imaging device for suppressing absorption rate of irradiated waves |
WO2016172650A1 (en) * | 2015-04-24 | 2016-10-27 | Massachusetts Institute Of Technology | Micro magnetic resonance relaxometry |
US10393684B2 (en) | 2015-04-24 | 2019-08-27 | Massachusetts Institute Of Technology | Micro magnetic resonance relaxometry |
Also Published As
Publication number | Publication date |
---|---|
US20020079996A1 (en) | 2002-06-27 |
EP1344076A1 (en) | 2003-09-17 |
JP2004511278A (en) | 2004-04-15 |
US7023209B2 (en) | 2006-04-04 |
AU2001296738A1 (en) | 2002-04-22 |
WO2002031522A1 (en) | 2002-04-18 |
US20060277749A1 (en) | 2006-12-14 |
JP2005270674A (en) | 2005-10-06 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7023209B2 (en) | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils | |
US4641097A (en) | Elliptical cross-section slotted-tube radio-frequency resonator for nuclear magnetic resonance imaging | |
US4636730A (en) | NMR spectroscopy body probes with at least one surface coil | |
EP0180121B1 (en) | Mutual inductance nmr rf coil matching device | |
Zhang et al. | A microstrip transmission line volume coil for human head MR imaging at 4 T | |
CA1230922A (en) | Nuclear magnetic resonance radio frequency antenna | |
EP1687653B1 (en) | Rf coil system for super high field (shf) mri | |
US4751464A (en) | Cavity resonator with improved magnetic field uniformity for high frequency operation and reduced dielectric heating in NMR imaging devices | |
US6396271B1 (en) | Tunable birdcage transmitter coil | |
Zhang et al. | An inverted-microstrip resonator for human head proton MR imaging at 7 tesla | |
US4725779A (en) | NMR local coil with improved decoupling | |
US4740751A (en) | Whole body MRI resonator | |
US20070007964A1 (en) | RF coil for imaging system | |
US20050264291A1 (en) | Multi-current elements for magnetic resonance radio frequency coils | |
US20050062472A1 (en) | Mri tunable antenna and system | |
US6169401B1 (en) | Flexible open quadrature highpass ladder structure RF surface coil in magnetic resonance imaging | |
US20190339344A1 (en) | Magnetic resonance scanner and local coil matrix for operation at low magnetic field strengths | |
EP1269211B1 (en) | Magnetic resonance imaging apparatus with means to screen rf fields | |
US6175237B1 (en) | Center-fed paralleled coils for MRI | |
US6788059B2 (en) | RF detector array for magnetic resonance imaging | |
JP2005523094A (en) | Radio frequency gradient and shim coil | |
US8125226B2 (en) | Millipede surface coils | |
Zhang et al. | Method and apparatus for magnetic resonance imaging and spectroscopy using microstrip transmission line coils | |
Dürr et al. | A dual‐frequency circularly polarizing whole‐body MR antenna for 69/170 MHz | |
Rajendran et al. | Wideband Tapered Microstrip Transmission Line (MTL) Volume Coil for 1.5 T MRI Scanner |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |
|
AS | Assignment |
Owner name: NATIONAL INSTITUTES OF HEALTH (NIH), U.S. DEPT. OF Free format text: CONFIRMATORY LICENSE;ASSIGNOR:REGENTS OF THE UNIVERSITY OF MINNESOTA;REEL/FRAME:030175/0372 Effective date: 20130403 |