[go: up one dir, main page]

WO2022126572A1 - Appareil à bobines pour radiofréquences à double syntonisation - Google Patents

Appareil à bobines pour radiofréquences à double syntonisation Download PDF

Info

Publication number
WO2022126572A1
WO2022126572A1 PCT/CN2020/137492 CN2020137492W WO2022126572A1 WO 2022126572 A1 WO2022126572 A1 WO 2022126572A1 CN 2020137492 W CN2020137492 W CN 2020137492W WO 2022126572 A1 WO2022126572 A1 WO 2022126572A1
Authority
WO
WIPO (PCT)
Prior art keywords
coil
differential mode
mode
radio frequency
magnetic field
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.)
Ceased
Application number
PCT/CN2020/137492
Other languages
English (en)
Chinese (zh)
Inventor
郑海荣
李烨
李楠
杜凤
陈巧燕
刘新
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shenzhen Institute of Advanced Technology of CAS
Original Assignee
Shenzhen Institute of Advanced Technology of CAS
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 Shenzhen Institute of Advanced Technology of CAS filed Critical Shenzhen Institute of Advanced Technology of CAS
Priority to PCT/CN2020/137492 priority Critical patent/WO2022126572A1/fr
Publication of WO2022126572A1 publication Critical patent/WO2022126572A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Images

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
    • 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

Definitions

  • the embodiments of the present application relate to the field of medical equipment, for example, to a double-tuned radio frequency coil device.
  • Magnetic resonance imaging is an imaging technique that uses the signal generated by the resonance of atomic nuclei in a strong magnetic field to reconstruct the image.
  • the basic principle is: some atoms containing singular protons in human tissues, such as hydrogen atoms, can spin and generate magnetic moments. Under normal conditions, the spin directions of these small magnets are irregular, but under the action of a fixed static magnetic field At this time, when a radio frequency pulse of the same frequency as the static magnetic field is applied, these hydrogen atoms absorb a certain amount of energy and generate resonance, and the spin direction is deflected under the action of the radio frequency pulse, and is regularly arranged, that is, the occurrence of Magnetic resonance phenomenon. After the radio frequency pulse disappears, these hydrogen atoms will return to their original state.
  • the radio frequency coil is mainly used to transmit radio frequency pulses and collect magnetic resonance radio frequency signals.
  • double-tuned coils the H channel is usually used for shimming, which requires that the magnetic field distributions of the two frequency channels are similar.
  • double-tuned RF coils first, using a single-frequency tunable coil; second, switching the resonant frequency of the automatic tuning coil with the help of an external computer program; third, by rearranging the quadrature mode of the birdcage coil into two separate linear modes and tuned to 1H/19F frequency to achieve double resonance.
  • the use of a single-frequency adjustable coil must be manually adjusted to different frequencies to achieve the acquisition of the target signal in turn, but the F signal is weak, usually increasing the acquisition time to maximize the signal-to-noise ratio (SNR), resulting in additional time costs.
  • SNR signal-to-noise ratio
  • the signal attenuation caused by 1H/19F misregistration will blur the image; the automatic tuning of the coil with the help of an external computer program is complicated and costly to switch the resonant frequency; these two methods are used in common.
  • the 1H/19F signal shows some limitations in terms of sensitivity and inaccuracy; achieving double resonance by rearranging the quadrature modes of the birdcage coil into two separate linear modes in the design of the birdcage structure will result in two
  • the signal-to-noise ratio (SNR) loss of the core is about 30%, which reduces the RF transmit power efficiency and reduces the B1 field uniformity.
  • Embodiments of the present application provide a double-tuned radio frequency coil device, so as to improve the efficiency of signals excited and received by the radio frequency coil, thereby improving the signal-to-noise ratio of an image obtained based on the signals.
  • the embodiment of the present application provides a double-tuned radio frequency coil device, which includes at least two differential mode common mode resonance structures, and a decoupling loop is provided between the adjacent differential mode common mode resonance structures;
  • the differential mode common mode resonance structure includes a common mode coil and a differential mode coil, the common mode coil is used to generate a first magnetic field, the differential mode coil is used to generate a second magnetic field, and the main magnetic field direction of the first magnetic field is perpendicular to the main magnetic field direction of the second magnetic field;
  • the decoupling loop is used for decoupling the adjacent differential mode common mode resonance structures.
  • the differential mode coil is within the common mode coil.
  • the centerlines of the common mode coil and the differential mode coil are on the same straight line.
  • the differential mode coil and the common mode coil are microstrip line structures.
  • the differential mode coil and/or the common mode coil are rectangular.
  • the common mode coil is provided with at least two tuning capacitors and at least one second coordination capacitor
  • the first tuning capacitor is provided at the drive port of the differential mode coil
  • the second coordination capacitor is arranged between the parallel copper strips on the differential mode coil and the ground, and the first coordination capacitor and the second coordination capacitor are used to adjust the resonance frequency of the differential mode coil.
  • the differential mode coil includes a third coordination capacitor and a fourth coordination capacitor
  • the third coordination capacitor is provided at the drive port of the differential mode coil
  • the fourth coordination capacitor is provided at the connection of the parallel strip conductors of the differential mode coil.
  • the decoupling loop is a decoupling structure based on an induced current compensation method, and the decoupling loop includes at least two uniformly distributed decoupling capacitors.
  • the double-tuned radio frequency coil device is disposed on a substrate, and the substrate is a body coil structure.
  • the double-tuned radio frequency coil device includes at least two differential-mode common-mode resonant structures, and a decoupling loop is arranged between adjacent differential-mode common-mode resonant structures; the differential-mode common-mode resonant structures It includes a common mode coil and a differential mode coil, the common mode coil is used to generate a first magnetic field, the differential mode coil is used to generate a second magnetic field, and the main magnetic field direction of the first magnetic field is the same as the main magnetic field direction of the second magnetic field.
  • the magnetic field directions are perpendicular to each other; the decoupling loop is used to decouple the adjacent differential mode common mode resonant structures, and the decoupling between adjacent differential mode common mode resonant structures is realized through the decoupling loop, which improves the The excitation and reception efficiency of elemental NMR signals, in turn, improves the signal-to-noise ratio of images generated based on the signals.
  • FIG. 1 is a schematic structural diagram of a double-tuned radio frequency coil device provided by an embodiment of the present application
  • FIG. 2 is a schematic structural diagram of another double-tuned radio frequency coil device provided by an embodiment of the present application.
  • FIG. 3 is a schematic structural diagram of a dual-core radio frequency array coil device provided by an embodiment of the present application.
  • the common mode and differential mode coils realized by using the microstrip transmission line and the decoupling structure based on the induced current compensation method in the embodiment of the present application realize the common mode and differential mode respectively.
  • the decoupling between the mode coils and the decoupling between adjacent common mode and differential mode structures improves the excitation and reception efficiency of NMR signals of different elements, thereby improving the signal-to-noise ratio of images generated based on the signals.
  • FIG. 1 is a schematic structural diagram of a dual-tuned radio frequency coil device provided by an embodiment of the present application.
  • the dual-core radio frequency coil provided by this embodiment can be applied to a multi-nuclide magnetic resonance imaging system.
  • the double-tuned radio frequency coil device includes: at least two differential-mode common-mode resonant structures 110 , and a decoupling loop 120 is provided between adjacent differential-mode common-mode resonant structures 110 .
  • the differential mode common mode resonant structure 110 includes a common mode coil 111 and a differential mode coil 112, the common mode coil 111 is used to generate a first magnetic field, the differential mode coil 112 is used to generate a second magnetic field, the first The main magnetic field direction of the magnetic field is perpendicular to the main magnetic field direction of the second magnetic field; the decoupling loop 120 is used for decoupling the adjacent differential mode common mode resonance structures 110 .
  • the differential mode common mode resonant structure generates a first magnetic field and a second magnetic field whose main magnetic field directions are perpendicular to each other through the differential mode coil and the common mode coil, and realizes the differential mode common mode through the mutually orthogonal first and second magnetic fields.
  • the decoupling of the differential mode coil and the common mode coil in the resonant structure improves the shim efficiency at the same time.
  • the differential-mode common-mode resonant structure can independently coordinate the required operating frequencies in each mode. It can be understood that, in order to generate the magnetic field, the differential mode coil and the common mode coil are loop structures. Among them, the required working frequency is the Larmor frequency of the corresponding element under the magnetic resonance imaging system.
  • the Larmor frequency of 1H under the 7T MRI system is 300Mhz
  • the Larmor frequency of 31P under the 7T MRI system is 121Mhz
  • the 1H channel corresponds to
  • the radio frequency coil is a differential mode coil
  • the radio frequency coil corresponding to the 31P channel is a common mode coil
  • the operating frequency of the differential mode coil is 300Mhz
  • the operating frequency of the common mode coil is 121Mhz
  • the double-tuned radio frequency coil device in this embodiment may be a differential mode common mode resonance structure and a decoupling loop arranged in an array, and may also be a differential mode common mode resonance structure and a decoupling loop arranged by a body coil structure.
  • the coupling loop is not limited here.
  • an insulating layer can be arranged between the differential mode coil and the common mode coil to eliminate the situation that the magnetic field is unstable due to wrong contact between the differential mode coil and the common mode coil, and to ensure the stability of the magnetic field, so as to make the magnetic field stable.
  • the excitation and reception of resonance signals are more stable.
  • the double-tuned radio frequency coil device includes a common mode coil and a differential mode coil, the common mode coil is used to generate a first magnetic field, the differential mode coil is used to generate a second magnetic field, the first magnetic field
  • the main magnetic field direction of the second magnetic field is perpendicular to the main magnetic field direction of the second magnetic field;
  • the decoupling loop is used to decouple the adjacent differential mode common mode resonance structures, wherein the differential mode common mode resonance structures are generated by generating
  • the first magnetic field and the second magnetic field whose main magnetic field directions are perpendicular to each other make the structure of differential mode and common mode realize decoupling due to the existence of the orthogonal first magnetic field and second magnetic field, and realize the adjacent differential mode common mode through the decoupling loop.
  • the decoupling between the resonant structures improves the excitation and reception efficiency of NMR signals of different elements, thereby improving the signal-to-noise ratio of images generated based on the signals.
  • the positional relationship between the differential mode coil and the common mode coil is not limited.
  • the differential mode coil is inside the common mode coil.
  • the differential mode coil can be arranged in the common mode coil. That is, the size of the common mode coil is larger than that of the differential mode coil.
  • the shapes of the common mode coil and the differential mode coil are not limited. However, on the basis of the above solution, in order to improve the stability of the magnetic field, the center lines of the common mode coil and the differential mode coil may be set on the same straight line.
  • the common mode coil and the differential mode coil are regular shapes.
  • the common mode coil and the differential mode coil may be circular, the common mode coil and the differential mode coil may be rectangular, and the common mode coil and the differential mode coil may be square.
  • the center line of the common mode coil is a straight line passing through the center of the common mode coil
  • the center line of the differential mode coil is a straight line passing through the center of the differential mode coil
  • the common mode coil and the differential mode coil are rectangular, regular in shape and simple in structure, so that the structure of the double-tuned radio frequency coil device is regular and simple, and the robustness of the double-tuned radio frequency coil device is improved.
  • the differential mode coil and the common mode coil are microstrip line structures.
  • a resonant structure with two resonant frequencies can be generated by using the microstrip line structure and the common mode differential mode technology.
  • the common mode is the second harmonic mode of the microstrip resonator, which is driven by the coaxial coil in the center of the microstrip.
  • the differential mode mode is the main resonant mode of the microstrip resonator, driven by a square inductive loop. In this mode the currents on the two parallel strip conductors of the microstrip resonator are in opposite directions.
  • the two modes of the differential mode coil and the common mode coil are driven by current sources with equal amplitude and 90 phase difference respectively, and the input power is set to 1w, and the electromagnetic field distribution of each channel under each nuclide can be obtained.
  • the common mode coil is provided with at least two tuning capacitors and at least one second coordination capacitor
  • the first tuning capacitor is provided at the drive port of the differential mode coil
  • the second coordination capacitor is provided at the drive port of the differential mode coil.
  • the first coordination capacitor and the second coordination capacitor are used to adjust the resonance frequency of the differential mode coil.
  • FIG. 2 is a schematic structural diagram of another double-tuned radio frequency coil device provided by an embodiment of the present application. As shown in FIG. 2 , the first tuning capacitor Ccm-t1 is located at the driving port, and the second coordination capacitor Ccm-t2 is an auxiliary tuning capacitor located between the parallel copper strips and the ground plane. The first tuning capacitor and the second coordination capacitor work together to tune the CM operating frequency to a desired operating frequency.
  • the differential mode coil includes a third coordination capacitor and a fourth coordination capacitor
  • the third coordination capacitor is set at the drive port of the differential mode coil
  • the fourth coordination capacitor is set at the differential mode coil junctions of parallel strip conductors.
  • the fourth coordination capacitor Cdm-t is located at the connection of the parallel strip conductors
  • the third coordination capacitor Cdm-m is located at the drive port to tune the DM operating frequency to the desired operating frequency. In this mode the currents on the two parallel strip conductors of the microstrip resonator are in opposite directions.
  • the double-tuned radio frequency coil device is disposed on a substrate, and the substrate is a body coil structure.
  • FIG. 3 is a schematic structural diagram of a dual-core radio frequency array coil device provided by an embodiment of the present application.
  • 16 channels are taken as an example, and the structure of the double-coordinated radio frequency coil of the body coil structure is schematically shown.
  • differential mode common mode resonance structures are evenly distributed on the inner side of the body coil structure substrate, and a decoupling loop is provided between adjacent differential mode common mode resonance structures.
  • the other marks except the marks 110 and 120 are tuning capacitors.
  • the excitation amplitude and phase of each channel can be adjusted freely, so that the excitation phase between adjacent units differs by 45 degrees to achieve quadrature excitation.
  • the embodiments of the differential-mode common-mode resonance structure and the decoupling loop may refer to the above-mentioned embodiments, which will not be repeated here.
  • the double-tuned radio frequency coil device is embodied as an HF double-tuned radio frequency coil system, and the double-tuned radio frequency coil device is described.
  • the HF double-tuned radio frequency coil system includes common mode and differential mode coil units (corresponding to the differential mode common mode resonance structure in the above-mentioned embodiment) realized by using a microstrip transmission line, and a compensation method based on induced current (based on inductive current compensation, ICE) decoupling structure (corresponding to the decoupling loop in the above embodiment).
  • common mode and differential mode coil units corresponding to the differential mode common mode resonance structure in the above-mentioned embodiment
  • ICE inductive current compensation
  • the common mode and differential mode coil units in this embodiment utilize the microstrip line structure and the common mode (CM) differential mode (DM) technology to generate a resonance structure with two resonance frequencies. That is to say, the common-mode and differential-mode coil units can independently tune the operating frequencies required by the common-mode and differential-mode operating modes, that is, the required operating frequencies in each mode can be independently tuned under the coil array structure.
  • the common-mode and differential-mode coil units can essentially generate mutually orthogonal magnetic fields with similar distributions, excellent decoupling of nuclides is achieved, and the shimming efficiency is improved.
  • the ICE decoupling structure arranged between adjacent units of the coil array realizes superior electromagnetic decoupling between channels. Compared to the related art, due to the simple rectangular geometry of the array, it provides a simple and robust implementation for HF double-tuned RF coils.
  • the CM structure is tuned to the H element frequency and the DM structure is tuned to the F element frequency.
  • the common-mode and differential-mode structures are decoupled due to the existence of the orthogonal magnetic field, so the electromagnetic fields of the two HF nuclides are orthogonal to each other and do not affect each other;
  • the above characteristics are the key to improve the excitation and reception efficiency of proton and non-hydrogen magnetic resonance signals.
  • the induced current compensation method suitable for the design of non-overlapping coil arrays is used to solve the problem.
  • the problem of coupling between CMDM arrays is to use a single ICE decoupling unit to realize the decoupling of HF nuclide units at the same time. Because the array system has a regular and simple rectangular geometry and the magnetic fields are orthogonal, decoupling between adjacent channels is achieved, thereby improving the excitation and reception efficiency of 1H proton and 19F NMR signals.
  • a 5mm wide copper tape is used to make a CMDM resonant unit, the CM structure unit is a rectangle with a size of 4.4cm*9.6cm, and the DM structure unit is a rectangle with a size of 2.6cm*39cm.
  • the decoupling between adjacent CMDM units is realized by the resonant unit ICE structure.
  • the size of the resonant unit ICE structure is 1.6 cm*9.4 cm, and the distance between the adjacent CMDM resonant units is 0.3 cm.
  • the microstrip line dual resonant coil structure provided by the embodiment of the present application has a total of 8 channels, including a 4-channel CM structural unit and a 4-channel DM structural unit.
  • the CM structural unit is used to collect 1H signals
  • the DM structural unit is used to implement 19F. signal acquisition.
  • the CM common mode is the second harmonic mode of the microstrip resonator, which is driven by the coaxial coil in the center of the microstrip. In this operating mode, the current directions of the two parallel copper strip conductors of the resonator are the same.
  • the tuning capacitor Ccm-t1 is located at the drive port of the CM structural unit, and another auxiliary tuning capacitor Ccm-t2 is located between the parallel copper strip and the ground plane.
  • the two work together to tune the CM operating frequency to the 7T system.
  • the resonant frequency of H is 298MHz.
  • the matching capacitor Ccm-m is connected in series to the drive port, and the shielding layer of the coaxial cable and the copper ground plane are both grounded.
  • the DM differential mode is the main resonance mode of the microstrip resonator, which is driven by a square inductive loop.
  • the tuning capacitor Cdm-t is located at the connection of the parallel strip conductors, and the DM operating frequency is tuned to 282MHz, the resonant frequency of 19F in the 7T system.
  • the matching capacitor Cdm-m is at the drive port of the DM structure unit, and the current directions on the two parallel strip conductors of the microstrip resonator are opposite in this mode.
  • the above two modes are driven by current sources with equal amplitude and 90 phase difference respectively, and the input power can be set according to actual needs.
  • the independent coil type ICE decoupling structure loop is used as the decoupling element.
  • the main function is to compensate or eliminate the induced current caused by mutual coupling between adjacent CDMD microstrip line elements.
  • the capacitance value in the independent coil loop By adjusting the capacitance value in the independent coil loop, the solution is changed.
  • the induced current in the coupling coil loop can be effectively decoupled between adjacent units of the CMDM.
  • the HF double-tuned radio frequency coil system provided in the embodiment of the present application is used for 1H/19F nuclide imaging under magnetic resonance, and the common mode and differential mode (CMDM) technology is used to make the microstrip transmission line simultaneously generate H and F nuclide double resonance with close frequencies , the orthogonal field distribution of two nuclides shows the essential decoupling ability between common mode and differential mode, and the decoupling structure of induced current compensation method (ICE) is used to realize the simultaneous decoupling of common mode and differential mode structure.
  • CMDM common mode and differential mode
  • ICE induced current compensation method
  • the array system has a regular and simple rectangular geometry, and the magnetic field is orthogonal, decoupling between adjacent channels is realized, the excitation and reception efficiency of 1H proton and 19F NMR signals are improved, and the sensitivity to 1H/19F signal detection is improved. as well as the robustness of dual-tuned RF array coils.

Landscapes

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

Abstract

L'invention concerne un appareil à bobines pour radiofréquences à double syntonisation. L'appareil à bobines pour radiofréquences à double syntonisation comporte au moins deux structures résonantes à mode commun et mode différentiel, une boucle de découplage étant disposée entre des structures résonantes adjacentes à mode commun et mode différentiel; chaque structure résonante à mode commun et mode différentiel comporte une bobine de mode commun et une bobine de mode différentiel, la bobine de mode commun étant utilisée pour générer un premier champ magnétique, la bobine de mode différentiel étant utilisée pour générer un second champ magnétique, et la direction principale de champ magnétique du premier champ magnétique et la direction principale de champ magnétique du second champ magnétique étant perpendiculaires l'une à l'autre; et la boucle de découplage étant utilisée pour découpler les structures résonantes adjacentes à mode commun et mode différentiel.
PCT/CN2020/137492 2020-12-18 2020-12-18 Appareil à bobines pour radiofréquences à double syntonisation Ceased WO2022126572A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/CN2020/137492 WO2022126572A1 (fr) 2020-12-18 2020-12-18 Appareil à bobines pour radiofréquences à double syntonisation

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2020/137492 WO2022126572A1 (fr) 2020-12-18 2020-12-18 Appareil à bobines pour radiofréquences à double syntonisation

Publications (1)

Publication Number Publication Date
WO2022126572A1 true WO2022126572A1 (fr) 2022-06-23

Family

ID=82059991

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2020/137492 Ceased WO2022126572A1 (fr) 2020-12-18 2020-12-18 Appareil à bobines pour radiofréquences à double syntonisation

Country Status (1)

Country Link
WO (1) WO2022126572A1 (fr)

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101315416A (zh) * 2007-05-31 2008-12-03 株式会社日立制作所 磁场线圈以及磁共振摄像装置
WO2009134920A2 (fr) * 2008-05-02 2009-11-05 The Regents Of The University Of California Procédé et appareil pour imagerie par résonance magnétique et spectroscopie utilisant des bobines à modes multiples
CN108646203A (zh) * 2018-05-04 2018-10-12 中国科学技术大学 一种纳米尺度的微波磁场测量方法

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101315416A (zh) * 2007-05-31 2008-12-03 株式会社日立制作所 磁场线圈以及磁共振摄像装置
WO2009134920A2 (fr) * 2008-05-02 2009-11-05 The Regents Of The University Of California Procédé et appareil pour imagerie par résonance magnétique et spectroscopie utilisant des bobines à modes multiples
CN108646203A (zh) * 2018-05-04 2018-10-12 中国科学技术大学 一种纳米尺度的微波磁场测量方法

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
PANG, YONG ET AL.: "Common-Mode Differential-Mode (CMDM) Method for Double-Nuclear MR Signal Excitation and Reception at Ultrahigh Fields", IEEE TRANSACTIONS ON MEDICAL IMAGING, vol. 30, no. 11, 30 November 2011 (2011-11-30), XP011369676, DOI: 10.1109/TMI.2011.2160192 *

Similar Documents

Publication Publication Date Title
US5194811A (en) Radio frequency volume resonator for nuclear magnetic resonance
US9459331B2 (en) RF coil and magnetic resonance imaging device
JP5368641B2 (ja) 高周波コイルおよびそれを用いた磁気共鳴撮像装置
US5202635A (en) Radio frequency volume resonator for nuclear magnetic resonance
US8089280B2 (en) RF coil and MRI system
EP0151726B1 (fr) Ecran pour découpler des bobines à hautes fréquences et à gradient dans un appareil NMR
US8380266B2 (en) Coil element decoupling for MRI
CN113608155B (zh) 磁共振多核射频线圈装置及控制方法、磁共振成像系统
US20200300946A1 (en) Dual-nuclear rf coil device and dual-nuclear rf coil array device
US12276713B2 (en) Quad-core radio-frequency coil circuit
CN103809138A (zh) 用于磁共振成像的相控阵列rf线圈
CN111965577B (zh) 一种多频线圈
IL99772A (en) Radio frequency resonator for use in nuclear magnetic resonance
US9520636B2 (en) Linear resonator of a high-frequency antenna for a nuclear magnetic resonance imaging apparatus
KR102287230B1 (ko) 마이크로스트립 라인 기반의 자기공명 영상용 이중 튜닝 rf 코일
EP3535594A1 (fr) Tomographe à résonance magnétique et matrice de bobines locale permettant un fonctionnement à des intensités de champ magnétique peu élevées
US6927575B2 (en) Surface coil decoupling means for MRI systems
WO2023000500A1 (fr) Système de bobine radiofréquence en cage d'oiseau à quatre anneaux d'extrémité prenant en charge l'imagerie à trois nucléides
CN214954037U (zh) 一种双调谐射频线圈装置
WO2021097940A1 (fr) Dispositif multicanal à bobines radiofréquences et système d'imagerie par résonance magnétique
CN112649774A (zh) 一种双调谐射频线圈装置
WO2022126572A1 (fr) Appareil à bobines pour radiofréquences à double syntonisation
CN211878152U (zh) 多通道射频线圈装置及核磁共振成像系统
CN107526049A (zh) 一种用于超高场的多核代谢成像双频头线圈
CA2244847C (fr) Bobines paralleles a alimentation centrale pour imagerie rmn

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: 20965588

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: 20965588

Country of ref document: EP

Kind code of ref document: A1

122 Ep: pct application non-entry in european phase

Ref document number: 20965588

Country of ref document: EP

Kind code of ref document: A1

32PN Ep: public notification in the ep bulletin as address of the adressee cannot be established

Free format text: NOTING OF LOSS OF RIGHTS PURSUANT TO RULE 112(1) EPC (EPO FORM 1205A DATED 27/05/2024)

122 Ep: pct application non-entry in european phase

Ref document number: 20965588

Country of ref document: EP

Kind code of ref document: A1