WO2010018535A1 - Réseau de bobines tem à émission rf multicanaux (multix) doté d’un découplage de ligne microruban inductive n’émettant aucune onde radio électrique - Google Patents

Réseau de bobines tem à émission rf multicanaux (multix) doté d’un découplage de ligne microruban inductive n’émettant aucune onde radio électrique Download PDF

Info

Publication number
WO2010018535A1
WO2010018535A1 PCT/IB2009/053518 IB2009053518W WO2010018535A1 WO 2010018535 A1 WO2010018535 A1 WO 2010018535A1 IB 2009053518 W IB2009053518 W IB 2009053518W WO 2010018535 A1 WO2010018535 A1 WO 2010018535A1
Authority
WO
WIPO (PCT)
Prior art keywords
stripline
striplines
decoupling
coil array
inductor
Prior art date
Application number
PCT/IB2009/053518
Other languages
English (en)
Inventor
Christoph Leussler
Original Assignee
Koninklijke Philips Electronics N.V.
Philips Intellectual Property & Standards Gmbh
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 Koninklijke Philips Electronics N.V., Philips Intellectual Property & Standards Gmbh filed Critical Koninklijke Philips Electronics N.V.
Publication of WO2010018535A1 publication Critical patent/WO2010018535A1/fr

Links

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
    • G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
    • G01R33/341—Constructional details, e.g. resonators, specially adapted to MR comprising surface coils
    • G01R33/3415—Constructional details, e.g. resonators, specially adapted to MR comprising surface coils comprising arrays of sub-coils, i.e. phased-array coils with flexible receiver channels
    • 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
    • G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
    • G01R33/3642—Mutual coupling or decoupling of multiple coils, e.g. decoupling of a receive coil from a transmission coil, or intentional coupling of RF coils, e.g. for RF magnetic field amplification
    • G01R33/365—Decoupling of multiple RF coils wherein the multiple RF coils have the same function in MR, e.g. decoupling of a receive coil from another receive coil in a receive coil array, decoupling of a transmission coil from another transmission coil in a transmission coil array

Definitions

  • MULTI-CHANNEL RF-TRANSMIT MULTIX TEM COIL ARRAY WITH NON-RADIATING INDUCTIVE STRIPLINE DECOUPLING
  • the present innovation finds particular application in magnetic resonance imaging (MRI) systems.
  • MRI magnetic resonance imaging
  • the described techniques may also find application in other imaging systems, other magnetic resonance scenarios, other image data collection techniques, and the like.
  • the coil elements of transverse electromagnetic mode (TEM) transmit or receive coils which are used primarily at higher field strengths, tend to couple.
  • TEM transverse electromagnetic mode
  • large numbers of transmit channels e.g., more than one
  • Capacitors have been used for decoupling, particularly by capacitively decoupling ends of stripline conductors with the capacitors.
  • a ring of capacitors at each end of the RF coil results.
  • the use of capacitors has several drawbacks. The ring of capacitors creates unwanted local Bl fields.
  • the capacitors also introduced additional resonance modes into the RF coil assembly. Further, because high RF currents are applied, capacitors that are capable of withstanding high currents are utilized, which tend to be expensive and bulky. Also, capacitive decoupling using decoupling rings involves difficult and tedious tuning for coils with high number of elements.
  • capacitive decoupling includes capacitive limiting of high RF current, local high SAR hot spots, difficulty in suppressing unwanted modes, and highly disturbing Bl radiation generated by the decoupling ring contributing to a Bl field of linear independent conductors. Moreover, local RF shimming in peripheral regions is not optimal. Another drawback resides in unwanted narrowband decoupling.
  • the present application provides new and improved systems and methods for decoupling coil elements in an imaging device, which overcome the above -referenced problems and others.
  • an inductively decoupled transverse electromagnetic (TEM) coil array comprises a first stripline having at least a first stripline inductor coupled thereto, and a second stripline having at least a second stripline inductor coupled thereto.
  • the first stripline inductor is inductively coupled to the second stripline inductor to form a first decoupling transformer between the first and second striplines.
  • a method of inductively decoupling a plurality of striplines in a TEM coil array comprises inductively coupling N striplines to each other using decoupling transformers, and tuning the decoupling transformer until adjacent pairs of striplines are inductively decoupled.
  • Another advantage is that B 1 shimming is not hampered.
  • Another advantage resides in mitigating unwanted electrical modes.
  • Another advantage resides in increasing RF operating power levels. Another advantage resides in a reliable and quick tuning strategy for decoupling.
  • Another advantage resides in reducing local SAR hotspots.
  • FIGURE 1 illustrates a TEM resonator coil array that employs distributed transformer sections to provide inductive decoupling between neighboring stripline coil elements.
  • FIGURE 2 illustrates an embodiment of the TEM coil array in which stripline conductors are arranged in a triangular or trapezoidal orientation.
  • FIGURE 3 illustrates an embodiment of the TEM coil array in which a pair of serially oriented stripline inductors is positioned near each end of each stripline.
  • FIGURE 4A illustrates an embodiment of the TEM coil array in stripline inductors are disposed at the ends of each stripline.
  • FIGURE 4B illustrates an embodiment of the TEM coil array in which an RF shield is employed to further reduce SAR hotspots and/or feedback.
  • FIGURE 5 illustrates an embodiment of the TEM coil array in which the decoupling transformers are positioned at or near the centers of neighboring striplines.
  • FIGURE 6 illustrates an embodiment of the TEM coil array in which a combination of inductive and capacitive decoupling techniques is used.
  • FIGURE 7 shows an embodiment of the TEM coil array in which striplines are inductively decoupled from vertically (e.g., in an axial direction) neighboring striplines.
  • FIGURE 8 illustrates an embodiment of the TEM coil array in which a plurality of striplines are vertically and horizontally (e.g., in the relative plane of the page) decoupled from each other.
  • FIGURE 9 illustrates an embodiment in which decoupling transformers are tuned.
  • FIGURE 10 illustrates an embodiment in which homogeneous RF current distribution over the inductors is achieved by connecting capacitors in series.
  • FIGURE 1 IA shows a frequency split ⁇ fl that can occur when employing two resonant TEM elements (e.g., striplines) without inductive decoupling.
  • FIGURE HB illustrates a convergence of resonant frequencies that is achieved by using the decoupling transformers described herein.
  • FIGURE HC illustrates frequency characteristics associated with increased coupling between two striplines, as shown by the frequency split ⁇ f2.
  • FIGURE 12 illustrates a transversal view of a cylindrical TEM coil array, such as may be employed in a bore of an MRI imaging device or the like to generate magnetic resonance image data of a subject.
  • FIGURE 13 illustrates a transversal view of an asymmetrical TEM coil array, such as may be employed in a bore of an MRI imaging device or the like to generate magnetic resonance image data of a subject.
  • FIGURE 14 illustrates an embodiment of a segmented transmit and receive coil array, such as may be oriented along a z-axis of a magnetic resonance imaging system, in which a plurality of decoupling loops are employed to couple multiple striplines to each other.
  • FIGURE 15 illustrates an embodiment of a transformer that is made discretely switchable by a plurality of PIN diodes coupled to a plurality of external DC sources such that a defined coupling between the inductors can be adjusted.
  • FIGURE 16 illustrates an embodiment of a transformer in which the transformer can be switched once during a calibration or production process using a plurality of fuses.
  • FIGURE 17 illustrates an embodiment of a transformer in which first and second inductors (e.g., inductor strips or the like) are coupled.
  • first and second inductors e.g., inductor strips or the like
  • the described inductive decoupling mechanisms and techniques optimally and reliably decouple individual coil elements (e.g., stripline coils, or "striplines") of a transverse electromagnetic (TEM) coil.
  • TEM transverse electromagnetic
  • Non-radiating, low-loss decoupling network layouts are applied for a high number of parallel transmit channels while mitigating uncontrolled local Bl field disturbances and SAR hot spots that occur with capacitive decoupling.
  • the TEM coil array is decoupled and optimized by employing local inductive stripline transformers.
  • Inductive decoupling mitigates spurious modes of operation and permits the use of higher radio frequency (RF) power and lower disturbing Bl and SAR contributions than can be achieved using capacitive decoupling, which facilitates improving parametric optimization in parallel transmit coil design with multiple elements and broadband decoupling for other nuclei.
  • RF radio frequency
  • capacitive decoupling Different arrangements of loop and stripline transformer designs are described in greater detail below.
  • the components of the array e.g., striplines, coils, capacitors, transformers, etc.
  • PCB printed circuit board
  • FIGURE 1 illustrates a TEM resonator coil array 10 that employs distributed transformer sections 12 to provide inductive decoupling between neighboring stripline coil elements 14.
  • the stripline(s) described herein are shielded with respective local shields or screens (e.g., RF shields, TEM shields, etc.).
  • Each transformer section includes a transformer comprising a pair of decoupling inductors 16 that are coupled to each other and to a variable capacitor 18.
  • Each decoupling inductor 16 is inductively coupled to a stripline inductor 20 such that the decoupling inductors 16 of a single inductive decoupler 12 are each coupled to a stripline inductor 20 on a different stripline coil element 14.
  • each stripline includes a capacitor 22 at each end thereof, which provide resonance to the TEM coil array and couple the striplines 14 to ground on a PCB (not shown).
  • transformer sections are positioned between first and second striplines. The properties of the transformer sections 12 for a given type of stripline 14 at a given resonance frequency are calculated and the transformer section is specifically designed with appropriate reactance for decoupling the given type of stripline at a given resonance frequency. The transformer section is then built and tuned for the striplines it is decoupling. For instance, once the transformer sections 12 are positioned between the first and second striplines, the transformer formed by the decoupling inductors 16 is tuned.
  • variable capacitor 18 is tuned to optimize decoupling of the first and second striplines.
  • Transformer sections between the second stripline and a third stripline are then tuned, and so on until the entire TEM coil array is tuned and striplines 14 therein are linearly independent and decoupled from each other.
  • striplines 14 described herein are approximately 7 cm wide, although they may be wider or narrower depending on design constraints, designer preferences, etc.
  • FIGURE 2 illustrates an embodiment of the TEM coil array 10 in which stripline conductors 14 are arranged in a triangular or trapezoidal orientation. Such asymmetric arrangements improve signal-to-noise ratio.
  • Each stripline 14 includes a pair of stripline inductors 20, where a stripline inductor on a first stripline is coupled to a stripline inductor on a next (second) stripline to form a tunable decoupling transformer 30, and so on, to connect all striplines in the array in an inductively decoupled manner.
  • the decoupling transformers are designed such that their Bl field is orthogonal to a main BO field generated by the main magnets in the MRI device in which the array is employed.
  • FIGURE 3 illustrates an embodiment of the TEM coil array 10 in which a pair of serially oriented stripline inductors 20 is positioned near each end of each stripline 14. Inductors 20 at a first end of a given stripline inductively couple with, e.g. overlap, inductors of a first neighboring stripline, and inductors near a second end of the given stripline overlap inductors of a second neighboring stripline to form a tunable decoupling transformer 30 between each pair of striplines.
  • Striplines 14 are coupled to a ground plane on a PCB (not shown) by one or more capacitors 22 disposed at each end of each stripline.
  • multiple striplines 14 are connected to form the TEM coil array with distributed tunable decoupling transformer sections therebetween to ensure that each stripline is linearly independent from its neighbors to reduce Bl field disturbances and SAR hotspots.
  • FIGURE 4A illustrates an embodiment of the TEM coil array 10 in which stripline inductors 20 are disposed at the ends of each stripline 14.
  • Each inductor 20 is coupled to two capacitors 40, which respectively couple each inductor to the stripline 14 and a ground plane on a PCB (not shown) or the like.
  • the striplines are positioned approximately 20 mm from an RF or TEM screen or shield (not shown), and the PCB is positioned between the striplines and the screen.
  • Each stripline inductor 20 is paired to a stripline inductor on a neighboring stripline to form a tunable decoupling transformer therebetween. The transformers formed by the pairs of neighboring inductors 20 make the striplines linearly independent to fully decouple the striplines.
  • FIGURE 4B illustrates an embodiment of the TEM coil array 10 in which an
  • the RF shield 50 is employed to further reduce SAR hotspots and/or feedback.
  • the RF shield 50 is a strip coil connected to the inductors 20 of a stripline 14 by capacitors 40 and acts as a current return path.
  • TEM elements comprising the striplines 14 and associated components (e.g., inductors 20, capacitors 22, etc.) can be removably coupled to a screen or PCB (not shown). If desired, individual TEM elements can be removed from the screen or PCB to increase space in a bore or examination region of an MRI device in which the TEM coil array is employed. Removal of one or more elements is facilitated by the inductive manner in which elements are associated with one another. That is, since there are no wired electrical connections between the striplines or TEM elements, removal thereof is made easier than can be achieved with capacitive decoupling mechanisms.
  • FIGURE 5 illustrates an embodiment of the TEM coil array 10 in which the decoupling transformers 30 are positioned at or near the centers of neighboring striplines 14.
  • each stripline comprises a pair of inductors 20 at or near its longitudinal center.
  • Each inductor 20 is disposed adjacent another inductor on a different neighboring stripline to form an inductive coupling, so that each stripline forms a decoupling transformer 30 with each of two neighboring striplines.
  • local electric fields are mitigated by the transformers 30. That is, there is little or no current flowing at the center of the striplines. Therefore by positioning the transformers near the center of the striplines, little or no electric field is generated thereat. This aspect reduces SAR near the center of the stripline, which typically corresponds to a center of an examination region in an MRI device in which the TEM coil array is employed.
  • Striplines 14 are coupled to a ground plane (not shown) by capacitors 22.
  • FIGURE 6 illustrates an embodiment of the TEM coil array 10 in which a combination of inductive and capacitive decoupling techniques is used.
  • Each stripline 14 is joined to a first neighboring stripline by a decoupling transformer 30, and to a second neighboring stripline by a decoupling capacitor 60.
  • Striplines 14 are coupled to a ground plane (not shown) by capacitors 22. In this manner capacitively decoupled pairs of striplines are further inductively decoupled from each other.
  • FIGURE 7 shows an embodiment of the TEM coil array 10 in which striplines 14 are inductively decoupled from vertically (e.g., in an axial or z-direction) neighboring striplines.
  • each stripline 14 is coupled to a terminal stripline inductor 20 by a capacitor 70, and to a ground plane (not shown) by a capacitor 22.
  • capacitors 70 are similar or identical to capacitors 22.
  • Each stripline inductor 20 is paired to a neighboring stripline's inductor to generate a "vertical" decoupling transformer 30', which is tuned to decouple the neighboring striplines from each other.
  • each stripline segment has a dedicated transmitter and the transmit frequency is modulated along a z-direction.
  • the transformers provide functionality as, for example, solenoids, toroids, etc.
  • FIGURE 8 illustrates an embodiment of the TEM coil array 10 in which a plurality of striplines 14 are vertically and horizontally (e.g., in the relative plane of the page) decoupled from each other.
  • the depicted arrangement employs striplines with stripline inductors 20 positioned near the centers thereof as described with regard to Figure 5, as well as stripline inductors positioned at the ends thereof as described with regard to Figure 7.
  • Each stripline 14 is inductively decoupled from horizontally neighboring striplines by decoupling transformers 30 and from vertically neighboring striplines by decoupling transformers 30'.
  • FIGURE 9 illustrates an embodiment in which the decoupling transformers 30 (or 30') are tuned.
  • the decoupling transformers are automatically adjusted by an electronic drive 90 (e.g., a piezo-motor, cardan, PIN diode switching of metallic shield sections, etc.).
  • a local shield 92 e.g., a loop of wire, copper plate, etc. changes the inductivity of the inductors 20. For instance, a mirror current flows through the shield.
  • a magnetic flux adjustment of the transformer permits remote adjustment of the transformer, which facilitates tuning and/or servicing the transformer.
  • the shield is adjustable for production by means of laser cutting of the conductor material or for removing conductors using high peak DC current.
  • FIGURE 10 illustrates an embodiment in which homogeneous RF current distribution over the inductors 20 is achieved by connecting capacitors 100 in series.
  • the capacitors have capacitances in the range of approximately 50-300 pF at 127 MHz.
  • FIGURES HA-C illustrate examples of frequency characteristics that are related to the striplines described herein.
  • FIGURE 1 IA shows a frequency split Af 1 that can occur when employing two resonant TEM elements (e.g., striplines) without inductive decoupling.
  • FIGURE HB illustrates a convergence 110 of resonant frequencies that is achieved by using the decoupling transformers 30, 30' described herein. For instance, the frequency split Af 1 has been eliminated by a decoupling transformer and the frequencies of the two resonating striplines have converged.
  • FIGURE HC illustrates frequency characteristics associated with increased coupling between two striplines, as shown by the frequency split Af 2 .
  • the transformers 30, 30' can be employed to increase coupling between the TEM elements so that a volume TEM coil resonator has better mode spectra.
  • the transformers can be electronically switched such that the TEM coil function can be switched between a volume coil and a coil array.
  • the current distribution of the TEM volume coil can be electronically changed to improve the homogeneity of a patient-loaded RF field.
  • FIGURE 12 illustrates a transverse view of a cylindrical TEM coil array 140, such as may be employed in a bore of an MRI imaging device or the like to generate magnetic resonance image data of a subject.
  • a plurality of inductively decoupled TEM elements or striplines (labelled a-h) are arranged circumferentially, and are surrounded by a shield 142 that reduces interference, etc.
  • FIGURE 13 illustrates a transversal view of an asymmetrical TEM coil array 150, such as may be employed in a bore of an MRI imaging device or the like to generate magnetic resonance image data of a subject.
  • a plurality of inductively decoupled TEM elements or striplines are arranged circumferentially, while additional inductively decoupled TEM elements or striplines (labelled i-k) are arranged linearly. Elements i-k are thus positioned below and closer to patient or subject inserted into the bore of the MRI device to increase signal-to-noise ratio and improve MRI data collected thereby.
  • the TEM elements are surrounded by a shield 152 that reduces interference, etc.
  • the active elements and transformers 30, 30' for the described striplines 14 are etched on a PCB.
  • capacitors are employed to couple the transformers 30, 30' to the striplines, such capacitors reduce electric fields around, and provide constant current to, the transformers.
  • shielded inductive transformer layouts are employed.
  • the coil array 10 is employed as a head coil, optionally with an open shield.
  • FIGURE 14 illustrates an embodiment of a segmented transmit and receive coil array, such as may be oriented along a z-axis of a magnetic resonance imaging system, in which a plurality of decoupling loops 160 are employed to couple multiple striplines 14 to each other.
  • Each loop 160 comprises a plurality of inductors 20 separated by capacitors 162.
  • the inductors couple with neighboring stripline inductors to form decoupling transformers
  • transformers 30, 30' provide the herein described decoupling.
  • the transformers are strongly coupled, if desired.
  • Each loop 160 can also be an individual resonant loop coil element for reception and transmission in combination with the
  • FIGURE 15 illustrates an embodiment of a transformer 30 (or 30') that is made discretely switchable by a plurality of PIN diodes 170 coupled to a plurality of external
  • DC sources (labelled 1-4) such that a defined coupling between the inductors 20 can be adjusted.
  • Each loop in the inductors is coupled to a capacitor 172, which in turn is coupled to a pair of PIN diodes and to a respective DC source.
  • FIGURE 16 illustrates an embodiment of a transformer 30 (or 30') in which the transformer can be switched once during a calibration or production process using a plurality of fuses 180.
  • Each loop of each inductor 20 is coupled to a capacitor 172, which in turn is coupled to a pair of fuses 180 and to a respective external DC source (labelled 1-4).
  • a high current burst is provided by manipulating one or more of the DC sources.
  • FIGURE 17 illustrates an embodiment of a transformer 30 (or 30') in which first and second inductors 20 (e.g., inductor strips or the like) are coupled.
  • Each inductor 20 includes a plurality of switching components 190, which in turn comprise a fuse 192 and a PIN diode 194.
  • Each switching component 190 is coupled to a respective DC source (labelled 1-4) and to a capacitor 196.
  • PIN diodes are switched by the external DC sources such that a defined coupling between the inductors 20 can be adjusted.
  • the resulting transformer can be switched once during a calibration or production process using the fuses. In order to destroy one or more of the fuses to create a desired current path, a high current burst is provided by manipulating one or more of the DC sources.
  • stripline elements are connected to a spectrometer (e.g., in an MRI device).
  • the individual TEM stripline elements are used for excitation or for reception of nuclear spins to quantify the nuclear magnetization of the sample or subject. Therefore, the elements are connected via impedance networks to a transmitter or a receiver.
  • the impedance networks can be connected at any position of the strip, such as in the center of the strip due to the low electric field thereat, or at the end of the strip between capacitor and ground.
  • the impedance network matches the stripline impedance to the required impedance of the transmitter.
  • the transmitter element can be connected close to the strip element to reduce losses that can arise in the feeding cable.
  • the balancing impedance matching can include a pi matching network or an inductive transformer network.
  • Inductive transformer impedance matching has the advantage of being broadband.
  • balancing circuits such as transformers, baluns, or resonant high impedance devices transform signals from a balanced stripline to unbalanced coaxial cable.
  • Preamplifiers are connected close to a stripline antenna to reduce SNR losses and are protected by electronic or electromechanical electronic switches.
  • Each strip can be connected individually to a separate transmitter or receiver, or strips can be connected only to a transmitter while an adjacent strip is connected to only a receiver.
  • excitation of the individual strips is realized by individually driving the strips with different individual complex transmit pulses, or by driving with individual amplitude, phase, or frequency.
  • the array 10 is employed for MR imaging or as a stirring device for therapy applications such as hyperthermia or drug release in the body.
  • the array is used in combination with an existing MR system or in a combined hybrid diagnostic imaging or therapy system such as PET/MR, radiation therapy/MR, etc.
  • a first frequency is employed for MR and a second frequency is employed for therapy applications or for different nuclei (e.g., 13C, 23Na, 3 IP, etc.).
  • the elements can be made multiresonant.
  • a double resonance is obtained by connecting a further impedance network parallel to a capacitor of the stripline element.
  • Such an impedance network comprises a capacitor and an inductor in series.

Landscapes

  • Physics & Mathematics (AREA)
  • Condensed Matter Physics & Semiconductors (AREA)
  • General Physics & Mathematics (AREA)
  • Magnetic Resonance Imaging Apparatus (AREA)

Abstract

Lors de la fabrication d’un réseau (10) de bobines transverses électromagnétiques (TEM) pour un dispositif d’imagerie à résonance magnétique (IRM) à champ élevé, des bobines de ligne microruban (14) sont reliées par couplage inductif à l’aide de transformateurs de découplage (30, 30'). Les transformateurs de découplage (30, 30') sont séquentiellement syntonisés pour découpler les bobines de ligne microruban les unes des autres. L’utilisation du découplage inductif supprime le besoin d’une connexion électrique câblée entre lesdites bobines (14), facilitant de ce fait le retrait d’une ou de plusieurs bobines en cas de remplacement ou en vue d’augmenter la place dans l’intérieur du dispositif IRM.
PCT/IB2009/053518 2008-08-14 2009-08-11 Réseau de bobines tem à émission rf multicanaux (multix) doté d’un découplage de ligne microruban inductive n’émettant aucune onde radio électrique WO2010018535A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP08162345.6 2008-08-14
EP08162345 2008-08-14

Publications (1)

Publication Number Publication Date
WO2010018535A1 true WO2010018535A1 (fr) 2010-02-18

Family

ID=41119479

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IB2009/053518 WO2010018535A1 (fr) 2008-08-14 2009-08-11 Réseau de bobines tem à émission rf multicanaux (multix) doté d’un découplage de ligne microruban inductive n’émettant aucune onde radio électrique

Country Status (1)

Country Link
WO (1) WO2010018535A1 (fr)

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2011148278A1 (fr) * 2010-05-27 2011-12-01 Koninklijke Philips Electronics N.V. Découplage de plusieurs canaux d'un réseau de bobines radiofréquence d'irm
WO2013008116A1 (fr) * 2011-07-04 2013-01-17 Koninklijke Philips Electronics N.V. Système d'imagerie par résonance magnétique à réseau multicanaux d'adaptation d'impédance
WO2013054235A1 (fr) * 2011-10-10 2013-04-18 Koninklijke Philips Electronics N.V. Bobine de frequence-radio electromagnetique transversale (tem)pour la resonance magnetique
EP2618171A1 (fr) * 2012-01-17 2013-07-24 Koninklijke Philips Electronics N.V. Antenne T/R à résonnance multiple pour génération d'image RM
WO2014111777A1 (fr) * 2013-01-17 2014-07-24 Koninklijke Philips N.V. Dispositif d'antenne rf de type résonateur tem pour système d'imagerie par résonance magnétique
WO2016166609A3 (fr) * 2015-04-15 2016-12-08 Jeol Ltd. Sonde de résolution magnétique nucléaire à haute résolution par couplage magnétique et son procédé d'utilisation
US10241165B2 (en) 2016-03-14 2019-03-26 Jeol Ltd Inductive coupling in multiple resonance circuits in a nuclear magnetic resonance probe and methods of use
US10908239B1 (en) 2020-04-14 2021-02-02 Jeol Ltd. Broad band inductive matching of a nuclear magnetic resonance circuit using inductive coupling
US11726152B1 (en) 2022-08-26 2023-08-15 Jeol Ltd. Solid sample magnetic coupling high resolution nuclear magnetic resolution probe and method of use

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5489847A (en) * 1993-06-08 1996-02-06 Hitachi, Ltd. RF probe for MRI
WO2002095435A1 (fr) * 2001-05-19 2002-11-28 Koninklijke Philips Electronics N.V. Bobine de transmission et de reception pour appareil mr
US20040124840A1 (en) * 2002-09-23 2004-07-01 Arne Reykowski Antenna arrangement and coupling method for a magnetic resonance apparatus
WO2005050237A1 (fr) * 2003-11-18 2005-06-02 Koninklijke Philips Electronics, N.V. Bobinage hybride transverse electromagnetique/cage d'oiseaux pour irm
WO2005111645A2 (fr) * 2004-05-07 2005-11-24 Regents Of The University Of Minnesota Elements a courant multiple pour bobines radiofrequences pour resonance magnetique
WO2008064364A1 (fr) * 2006-11-24 2008-05-29 Mr. Instruments, Inc. Bobine volumique rf ouverte pour imagerie par résonance magnétique

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5489847A (en) * 1993-06-08 1996-02-06 Hitachi, Ltd. RF probe for MRI
WO2002095435A1 (fr) * 2001-05-19 2002-11-28 Koninklijke Philips Electronics N.V. Bobine de transmission et de reception pour appareil mr
US20040124840A1 (en) * 2002-09-23 2004-07-01 Arne Reykowski Antenna arrangement and coupling method for a magnetic resonance apparatus
WO2005050237A1 (fr) * 2003-11-18 2005-06-02 Koninklijke Philips Electronics, N.V. Bobinage hybride transverse electromagnetique/cage d'oiseaux pour irm
WO2005111645A2 (fr) * 2004-05-07 2005-11-24 Regents Of The University Of Minnesota Elements a courant multiple pour bobines radiofrequences pour resonance magnetique
WO2008064364A1 (fr) * 2006-11-24 2008-05-29 Mr. Instruments, Inc. Bobine volumique rf ouverte pour imagerie par résonance magnétique

Non-Patent Citations (6)

* Cited by examiner, † Cited by third party
Title
B.WU ET AL.: "Design of a Strip Transmit Coil/Array for Low Field Open MR", PROC.INTL.SOC.MAG.RESON.MED. 16, May 2008 (2008-05-01), pages 1092, XP002548659 *
DESHMUKH A A ET AL: "Compact broadband S-shaped microstrip antennas", ELECTRONICS LETTERS, IEE STEVENAGE, GB, vol. 42, no. 5, 2 March 2006 (2006-03-02), pages 260 - 261, XP006026257, ISSN: 0013-5194 *
E.B.BOSKAMP ET AL.: "The efficiency of 3T body transmit array coils", PROC.INTL.SOC.MAG.RESON.MED. 15, 2007, pages 1046, XP002548658 *
N.M.MALIK ET AL.: "A 16-element coil array optimized for multi-dimensionally accelerated parallel brain imaging using multi-oblique imaging planes", PROC.INTL.SOC.MAG.RESON.MED. 13, 2005, pages 912, XP002548660 *
VAUGHAN J ET AL: "The Head Cradle: An Open Faced, High Performance TEM Coil", INTERNATIONAL SOCIETY FOR MAGNETIC RESONANCE IN MEDICINE.SCIENTIFIC MEETING AND EXHIBITION. PROCEEDINGS, INTERNATIONAL SOCIETY FOR MAGNETIC RESONANCE IN MEDICINE, US, vol. 9, 1 January 2001 (2001-01-01), pages 15, XP002991301, ISSN: 1524-6965 *
WU ET AL: "Design of an inductively decoupled microstrip array at 9.4T", JOURNAL OF MAGNETIC RESONANCE, ACADEMIC PRESS, ORLANDO, FL, US, vol. 182, no. 1, 1 September 2006 (2006-09-01), pages 126 - 132, XP005624286, ISSN: 1090-7807 *

Cited By (25)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9229076B2 (en) 2010-05-27 2016-01-05 Koninklijke Philips N.V. Decoupling of multiple channels of an MRI RF coil array
CN103026251A (zh) * 2010-05-27 2013-04-03 皇家飞利浦电子股份有限公司 Mri rf线圈阵列的多个通道的解耦
WO2011148278A1 (fr) * 2010-05-27 2011-12-01 Koninklijke Philips Electronics N.V. Découplage de plusieurs canaux d'un réseau de bobines radiofréquence d'irm
CN103026251B (zh) * 2010-05-27 2016-05-11 皇家飞利浦电子股份有限公司 Mri rf线圈阵列的多个通道的解耦
WO2013008116A1 (fr) * 2011-07-04 2013-01-17 Koninklijke Philips Electronics N.V. Système d'imagerie par résonance magnétique à réseau multicanaux d'adaptation d'impédance
US9733324B2 (en) 2011-07-04 2017-08-15 Koninklijke Philips N.V. Magnetic resonance imaging system with a multi-channel impedance matching network
US10324145B2 (en) 2011-10-10 2019-06-18 Koninklijke Philips N.V. Transverse-electromagnetic (TEM) radio-frequency coil for magnetic resonance
WO2013054235A1 (fr) * 2011-10-10 2013-04-18 Koninklijke Philips Electronics N.V. Bobine de frequence-radio electromagnetique transversale (tem)pour la resonance magnetique
CN104011556A (zh) * 2011-10-10 2014-08-27 皇家飞利浦有限公司 用于磁共振的横向电磁（tem）射频线圈
EP2618171A1 (fr) * 2012-01-17 2013-07-24 Koninklijke Philips Electronics N.V. Antenne T/R à résonnance multiple pour génération d'image RM
CN104067136A (zh) * 2012-01-17 2014-09-24 皇家飞利浦有限公司 用于mr图像生成的多谐振t/r天线
US10451692B2 (en) 2012-01-17 2019-10-22 Koninklijke Philips N.V. Multi-resonant T/R antenna for MR image generation
WO2013108142A1 (fr) 2012-01-17 2013-07-25 Koninklijke Philips N.V. Antenne d'émission-réception à résonance multiples pour la génération d'images rm
JP2016503704A (ja) * 2013-01-17 2016-02-08 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． 磁気共鳴撮像システムに対するｔｅｍ共振器型ｒｆアンテナ
CN104919329B (zh) * 2013-01-17 2019-03-08 皇家飞利浦有限公司 用于磁共振成像系统的tem谐振器型射频天线装置
WO2014111777A1 (fr) * 2013-01-17 2014-07-24 Koninklijke Philips N.V. Dispositif d'antenne rf de type résonateur tem pour système d'imagerie par résonance magnétique
CN104919329A (zh) * 2013-01-17 2015-09-16 皇家飞利浦有限公司 用于磁共振成像系统的tem谐振器型射频天线装置
US10989772B2 (en) 2013-01-17 2021-04-27 Koninklijke Philips N.V. TEM resonator-type RF antenna device for a magnetic resonance imaging system
WO2016166609A3 (fr) * 2015-04-15 2016-12-08 Jeol Ltd. Sonde de résolution magnétique nucléaire à haute résolution par couplage magnétique et son procédé d'utilisation
US10241063B2 (en) 2015-04-15 2019-03-26 Jeol Ltd. Magnetic coupling high resolution nuclear magnetic resolution probe and method of use
US10656107B2 (en) 2015-04-15 2020-05-19 JOEL, Ltd. Magnetic coupling high resolution nuclear magnetic resolution probe and method of use
US10241165B2 (en) 2016-03-14 2019-03-26 Jeol Ltd Inductive coupling in multiple resonance circuits in a nuclear magnetic resonance probe and methods of use
US10620282B2 (en) 2016-03-14 2020-04-14 Jeol, Ltd. Inductive coupling in multiple resonance circuits in a nuclear magnetic resonance probe and methods of use
US10908239B1 (en) 2020-04-14 2021-02-02 Jeol Ltd. Broad band inductive matching of a nuclear magnetic resonance circuit using inductive coupling
US11726152B1 (en) 2022-08-26 2023-08-15 Jeol Ltd. Solid sample magnetic coupling high resolution nuclear magnetic resolution probe and method of use

Similar Documents

Publication Publication Date Title
WO2010018535A1 (fr) Réseau de bobines tem à émission rf multicanaux (multix) doté d’un découplage de ligne microruban inductive n’émettant aucune onde radio électrique
US7345481B2 (en) Hybrid TEM/birdcage coil for MRI
JP6145115B2 (ja) Ｍｒ画像生成のためのマルチ共振ｔ／ｒアンテナ
US6980000B2 (en) Coils for high frequency MRI
US6633161B1 (en) RF coil for imaging system
US8022705B2 (en) Microstrip coil designs for MRI devices
US7414402B2 (en) Coil apparatus and nuclear magnetic resonance apparatus using the same
US20100253333A1 (en) Dual tuned volume coils adapted to provide an end ring mode
KR20140059575A (ko) 위상 배열형 고주파 코일 및 이를 채용한 자기공명영상 장치
CN110168393B (zh) 低磁场强度下运行的磁共振断层成像设备和局部线圈矩阵
CN104422912A (zh) 用于接收磁共振信号的天线设备
CN110366688B (zh) 对用于磁共振成像的线圈进行感应性馈送
Wang et al. $ B_1 $ homogenization in MRI by multilayer coupled coils
US20100109667A1 (en) Transverse electromagnetic radio-frequency coil
US20130134979A1 (en) Volume Array Coil with Enforced Uniform Element Currents for Improved Excitation Homogeneity
EP3807666B1 (fr) Barrière d'onde de gaine pour applications de résonance magnétique (rm)
US20100277168A1 (en) Multi-channel tem coils with auxiliary decoupling elements
JP6886908B2 (ja) アレイコイル及び磁気共鳴撮像装置
Webb Radiofrequency coils
RU225852U1 (ru) Беспроводная радиочастотная катушка для магнитно-резонансной маммографии
CN212137625U (zh) 用于局部线圈的对称组件和局部线圈
EP3617730A1 (fr) Barrière d'onde de gaine pour applications de résonance magnétique (rm)
Kozlov et al. Influence of loop array geometry on near field transmit properties at 300 MHz

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 09786886

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 09786886

Country of ref document: EP

Kind code of ref document: A1