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WO2023082038A1 - Bobine de résonance magnétique - Google Patents

Bobine de résonance magnétique Download PDF

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Publication number
WO2023082038A1
WO2023082038A1 PCT/CN2021/129477 CN2021129477W WO2023082038A1 WO 2023082038 A1 WO2023082038 A1 WO 2023082038A1 CN 2021129477 W CN2021129477 W CN 2021129477W WO 2023082038 A1 WO2023082038 A1 WO 2023082038A1
Authority
WO
WIPO (PCT)
Prior art keywords
capacitor
magnetic resonance
circuit
tuning
coil
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/CN2021/129477
Other languages
English (en)
Chinese (zh)
Inventor
李烨
莫智广
李楠
罗超
杜凤
陈巧燕
刘新
郑海荣
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/CN2021/129477 priority Critical patent/WO2023082038A1/fr
Publication of WO2023082038A1 publication Critical patent/WO2023082038A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • 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 present application belongs to the technical field of magnetic resonance imaging, and in particular relates to a magnetic resonance coil.
  • Magnetic resonance imaging has become an important imaging method for clinical diagnosis due to its advantages of non-invasive, non-radiation, high resolution, high contrast, and cross-sectional imaging in any orientation.
  • the magnetic resonance system When performing magnetic resonance imaging, the magnetic resonance system sends magnetic resonance signals to the human body through the transmitting coil, and the human tissue is excited by the signal, and the feedback electromagnetic signal is fed back to the magnetic resonance system through the receiving coil.
  • the signal strength received by the receiving coil determines the quality of the magnetic resonance imaging to a certain extent.
  • the surface coil since the signal will rapidly attenuate as the distance from the coil increases, it is difficult for the surface coil to obtain high imaging quality for imaging of organs located deep inside the body. Taking prostate imaging as an example, the rectal coil needs to be inserted into the patient's rectum to bring it closer to the prostate, so as to obtain a stronger signal and better image quality than surface coils.
  • the signal-to-noise ratio is the core parameter of coil design, and a high signal-to-noise ratio means higher resolution and higher contrast, which means better image quality.
  • the coils in the prior art usually only include one channel, and the signal-to-noise ratio is small, so it is difficult to meet the high-resolution imaging requirements.
  • the single-channel coil has a relatively high signal-to-noise ratio only in the direction perpendicular to it, while the signal-to-noise ratio in other directions is low. The image is blurry.
  • the present application provides a magnetic resonance coil, aiming to solve one of the above-mentioned technical problems in the prior art at least to a certain extent.
  • a magnetic resonance coil including a receiving coil, a support and a tuning and matching circuit
  • the receiving coil includes at least two circuit loops, the at least two circuit loops are respectively distributed on the support, and the at least two circuit loops overlap each other; the tuning and matching circuit is arranged at one end of the support , and is electrically connected to the receiving coil.
  • the technical solution adopted in the embodiment of the present application further includes: further comprising a coaxial cable and an amplifier, the tuning and matching circuit is connected to the amplifier through the coaxial cable, and the amplifier is connected to the magnetic resonance system.
  • the technical solution adopted in the embodiment of the present application further includes: the at least two circuit loops are mutually independent in circuit.
  • the technical solution adopted in the embodiment of the present application further includes: the at least two circuit loops respectively correspond to a port, and the tuning and matching circuit tunes, matches and decouples the corresponding circuit loop through the port.
  • the tuning and matching circuit includes the tuning and matching circuit including a first capacitor, a third capacitor, a fourth capacitor, a fifth capacitor, a sixth capacitor, a diode, a first inductor, and a first capacitor.
  • Two inductors; the fourth capacitor, the fifth capacitor, the third capacitor and the first capacitor are connected in series, and the at least two circuit loops are decoupled through the first capacitor; the sixth capacitor, the fifth capacitor, the diode and The first inductor is connected in series, and the third capacitor, the second inductor, and the diode are connected in series to form a parallel resonant circuit; when the diode is turned on, the parallel resonant circuit starts to work, so that the corresponding circuit loop It is in an off state; when the diode is off, the second inductor does not work, and the third capacitor works, so that the corresponding circuit loop is in the state of receiving signals.
  • the technical solution adopted in the embodiment of the present application also includes: the tuning and matching process of the tuning and matching circuit is specifically: after connecting the port to a vector network analyzer through a coaxial cable for calibration, testing the S11 parameter of the port , displayed as the Smith chart mode; add the adjustment mark point as the operating frequency point of the magnetic resonance system, and adjust the size of the third capacitor, the fourth capacitor, and the fifth capacitor by replacing or adjusting the capacitor, so that the mark point moves to Smith
  • the central position of the circular diagram completes the tuning and matching of the tuning and matching circuit.
  • the technical solution adopted in the embodiment of the present application further includes: the support member is a cylinder with a set diameter.
  • the beneficial effect of the embodiment of the present application lies in that the magnetic resonance coil of the embodiment of the present application adopts a multi-channel design mode, and multiple channels overlap each other, which reduces the mutual interference between channels.
  • the embodiment of the present application has higher resolution and higher contrast, improves the signal-to-noise ratio of the rectal coil, improves the imaging quality of the magnetic resonance system, and has a wider imaging coverage , so that the imaging area of the coil better covers the entire site to be measured.
  • Fig. 1 is a schematic structural diagram of a magnetic resonance coil according to an embodiment of the present application
  • Fig. 2 is a circuit connection diagram of the receiving coil 1 of the embodiment of the present application.
  • Fig. 3 is a flowchart of a magnetic resonance coil imaging method according to an embodiment of the present application.
  • FIG. 1 is a schematic structural diagram of a magnetic resonance coil according to an embodiment of the present application.
  • the magnetic resonance coil of the embodiment of the present application includes a receiving coil 1 , a support 2 , a tuning and matching circuit 3 , a coaxial cable 4 and an amplifier 5 .
  • the receiving coil 1 includes at least two circuit loops. In the embodiment of the present application, three circuit loops are taken as an example, which are respectively the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13. The first circuit loop 11, the second circuit loop The second circuit loop 12 and the third circuit loop 13 are respectively distributed on the support member 2 .
  • the support member 2 is a cylinder with a set diameter (the set diameter is 25 mm in the embodiment of the present application, which can be set according to actual application), and is used to provide support for the receiving coil 1 .
  • the tuning and matching circuit 3 is arranged at one end of the support member 2 and is electrically connected to the receiving coil 1 for performing, tuning, matching and decoupling processing on the receiving coil 1 .
  • the tuning and matching circuit 3 is connected to the amplifier 5 through the coaxial cable 4, and the amplifier 5 is connected to the magnetic resonance system (not shown) through the cable.
  • FIG. 2 is a circuit connection diagram of the receiving coil 1 according to the embodiment of the present application.
  • the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13 are independent of each other on the circuit, and the first circuit loop 11 and the second circuit loop 12, the second circuit loop 12 and the third circuit loop 13 alternate in pairs overlap to achieve the purpose of overlap decoupling.
  • the first capacitor C41 is used for decoupling between the first circuit loop 11 and the third circuit loop 13 , and the second capacitor C21 and the tuning and matching circuit of the second circuit loop 12 play a tuning role together.
  • the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13 correspond to the first port, the second port and the third port respectively, and the tuning and matching circuit 3 passes through the first port, the second port and the third port respectively.
  • the third port adjusts the first circuit loop 11 , the second circuit loop 12 and the third circuit loop 13 to achieve the effects of tuning, matching and preamplifier decoupling.
  • the tuning and matching circuit structures of the first circuit loop 11, the second circuit loop 12 and the third circuit loop 13 are the same.
  • the circuit structure of the tuning and matching circuit 3 includes: the third capacitor C12, the fourth capacitor Cf1, the fifth capacitor Cp1, the sixth capacitor Cs1, the diode D1, the first inductor L11 and the second inductor L12; the fourth capacitor Cf1, the fifth capacitor Cp1, the third capacitor C12 and the first capacitor C41 are connected in series.
  • the six capacitors Cs1, the fifth capacitor Cp1, the diode D1 and the first inductor L11 are connected in series, and the third capacitor C12, the second inductor L12 and the diode D1 are connected in series to form a parallel resonant circuit; the diode D1 functions as a direct current, AC isolation; the fourth capacitor Cf1, the fifth capacitor Cp1 and the sixth capacitor Cs1 jointly determine the tuning and matching of the circuit.
  • the parallel resonant circuit composed of the third capacitor C12 and the second inductance L12 starts to work, and the first circuit loop 11 is in a disconnected state at this time, so as to avoid the excitation signal of the magnetic resonance system from damaging the circuit; when the diode D1 When disconnected, the second inductor L12 does not work, the third capacitor C12 works, and the first circuit loop 11 is in a normal state of receiving signals.
  • the tuning and matching circuit structures of the second circuit loop 12 and the third circuit loop 13 are the same as those of the first circuit loop 11 , and will not be repeated in this application.
  • the tuning and matching process of the tuning and matching circuit is specifically: after connecting the first port to a vector network analyzer through a coaxial cable for calibration, then testing the first port S11 parameter, displayed as Smith chart mode, add the adjustment mark point marker as the working frequency point of the magnetic resonance system, adjust the size of Cf1, Cp1 and Cs1 by replacing the capacitor or adjusting the adjustable capacitor, so that the marker point marker moves to Smith
  • the center position of the circular diagram completes the tuning and matching of the tuning matching circuit.
  • the tuning and matching processes of the second circuit loop 12 and the third circuit loop 13 are the same as those of the first circuit loop 11 , which will not be repeated in this application.
  • FIG. 3 is a flow chart of the magnetic resonance coil imaging method according to the embodiment of the present application.
  • the magnetic resonance coil imaging method of the embodiment of the present application includes the following steps:
  • the coil is inserted into the rectum of the subject to be tested.
  • S2 Detect whether the tuning, matching and cross-coupling of the receiving coil are normal, if not, go to S3; otherwise, go to S4;
  • S4 Connect the receiving coil to the magnetic resonance system, and perform magnetic resonance scanning imaging of the part to be measured through the magnetic resonance system.
  • the magnetic resonance coil of the embodiment of the present application adopts a multi-channel design mode, and multiple channels are overlapped in pairs to reduce mutual interference between channels.
  • the embodiment of the present application has higher resolution and higher contrast, improves the signal-to-noise ratio of the rectal coil, improves the imaging quality of the magnetic resonance system, and has a wider imaging coverage , so that the imaging area of the coil better covers the entire site to be measured.

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  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Surgery (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Condensed Matter Physics & Semiconductors (AREA)
  • General Physics & Mathematics (AREA)
  • Magnetic Resonance Imaging Apparatus (AREA)

Abstract

L'invention concerne une bobine de résonance magnétique. La bobine de résonance magnétique comprend une bobine de réception (1), un élément de support (2), et un circuit de réglage et d'adaptation (3) ; la bobine de réception (1) comprend au moins deux boucles de circuit (11, 12, 13), et les au moins deux boucles de circuit (11, 12, 13) sont réparties séparément sur l'élément de support (2) ; le circuit de réglage et d'adaptation (3) est disposé à une extrémité de l'élément de support (2) et est électriquement connecté à la bobine de réception (1). Un mode de conception multicanal est utilisé pour la bobine de résonance magnétique, et la pluralité de canaux se chevauchent par paires, réduisant ainsi l'interférence mutuelle entre les canaux. Par comparaison avec une bobine endorectale à canal unique, la bobine de résonance magnétique a une résolution plus élevée et un contraste plus élevé, le rapport signal-bruit d'une bobine endorectale est amélioré, et la qualité d'imagerie du système de résonance magnétique est améliorée ; de plus, la bobine de résonance magnétique a une couverture d'imagerie plus large, et ainsi la zone d'imagerie de la bobine couvre mieux la totalité de la partie à examiner.
PCT/CN2021/129477 2021-11-09 2021-11-09 Bobine de résonance magnétique Ceased WO2023082038A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/CN2021/129477 WO2023082038A1 (fr) 2021-11-09 2021-11-09 Bobine de résonance magnétique

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2021/129477 WO2023082038A1 (fr) 2021-11-09 2021-11-09 Bobine de résonance magnétique

Publications (1)

Publication Number Publication Date
WO2023082038A1 true WO2023082038A1 (fr) 2023-05-19

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PCT/CN2021/129477 Ceased WO2023082038A1 (fr) 2021-11-09 2021-11-09 Bobine de résonance magnétique

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WO (1) WO2023082038A1 (fr)

Citations (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5050607A (en) * 1987-03-04 1991-09-24 Huntington Medical Research Institutes High resolution magnetic resonance imaging of body cavities
US5355087A (en) * 1989-02-27 1994-10-11 Medrad, Inc. Intracavity probe and interface device for MRI imaging and spectroscopy
US5451232A (en) * 1991-10-07 1995-09-19 Medrad, Inc. Probe for MRI imaging and spectroscopy particularly in the cervical region
EP0841575A2 (fr) * 1996-11-12 1998-05-13 GEC-Marconi Limited Imagerie par résonance magnétique
JPH10262946A (ja) * 1997-03-24 1998-10-06 Olympus Optical Co Ltd Ｎｍｒ計測用アンテナ装置
JP2001525685A (ja) * 1995-06-01 2001-12-11 ザ ジョンズ ホプキンス ユニバーシティ スクール オブ メディシン 内部磁気共鳴像の形成及び分光分析の方法並びに関連する装置
CN1330526A (zh) * 1998-11-18 2002-01-09 卡迪亚克M·R·I·公司 可膨胀的磁共振成像接收线圈
US20030187347A1 (en) * 2001-02-15 2003-10-02 Robin Medical Inc. Endoscopic examining apparatus particularly useful in MRI, a probe useful in such apparatus, and a method of making such probe
US20040004477A1 (en) * 2002-07-03 2004-01-08 Krzysztof Nesteruk Intraluminal MRI probe
CN1561907A (zh) * 2004-03-29 2005-01-12 北京大学 磁共振成像体腔射频线圈
CN2699832Y (zh) * 2004-03-29 2005-05-18 北京大学 磁共振成像体腔射频线圈
US20060267586A1 (en) * 2004-11-16 2006-11-30 Kabushiki Kaisha Toshiba Radio frequency coil assembly and magnetic resonance imaging apparatus
CN1913826A (zh) * 2004-02-02 2007-02-14 西门子公司 用于前列腺癌、子宫颈癌和直肠癌成像诊断的组合mr－光学线圈
US20090082664A1 (en) * 2007-09-26 2009-03-26 Schleifring Und Apparatebau Gmbh Endorectal Coil for Magnetic Resonance Tomograph
CN101482600A (zh) * 2008-01-08 2009-07-15 西门子（中国）有限公司 一种磁共振成像系统的接收装置
CN102018512A (zh) * 2010-12-17 2011-04-20 上海辰光医疗科技有限公司 用于磁共振成像的盆部射频线圈
CN102707249A (zh) * 2012-07-03 2012-10-03 汤丽萍 一种核磁共振成像仪器的射频线圈
CN102970924A (zh) * 2010-07-01 2013-03-13 梅德拉公司 多通道直肠内线圈和其接口设备
CN203773037U (zh) * 2014-01-28 2014-08-13 上海辰光医疗科技股份有限公司 用于磁共振成像系统的乳腺磁共振射频接收线圈
CN104541177A (zh) * 2012-08-08 2015-04-22 皇家飞利浦有限公司 具有针对外科手术仪器的开放进入的直肠内前列腺线圈
CN204649945U (zh) * 2015-05-27 2015-09-16 上海辰光医疗科技股份有限公司 乳腺磁共振射频接收线圈电路结构
CN111830447A (zh) * 2020-07-24 2020-10-27 深圳市一康云智慧科技有限责任公司 用于磁共振成像的前列腺和直肠射频线圈装置

Patent Citations (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5050607A (en) * 1987-03-04 1991-09-24 Huntington Medical Research Institutes High resolution magnetic resonance imaging of body cavities
US5355087A (en) * 1989-02-27 1994-10-11 Medrad, Inc. Intracavity probe and interface device for MRI imaging and spectroscopy
US5451232A (en) * 1991-10-07 1995-09-19 Medrad, Inc. Probe for MRI imaging and spectroscopy particularly in the cervical region
JP2001525685A (ja) * 1995-06-01 2001-12-11 ザ ジョンズ ホプキンス ユニバーシティ スクール オブ メディシン 内部磁気共鳴像の形成及び分光分析の方法並びに関連する装置
EP0841575A2 (fr) * 1996-11-12 1998-05-13 GEC-Marconi Limited Imagerie par résonance magnétique
JPH10262946A (ja) * 1997-03-24 1998-10-06 Olympus Optical Co Ltd Ｎｍｒ計測用アンテナ装置
CN1330526A (zh) * 1998-11-18 2002-01-09 卡迪亚克M·R·I·公司 可膨胀的磁共振成像接收线圈
US20030187347A1 (en) * 2001-02-15 2003-10-02 Robin Medical Inc. Endoscopic examining apparatus particularly useful in MRI, a probe useful in such apparatus, and a method of making such probe
US20040004477A1 (en) * 2002-07-03 2004-01-08 Krzysztof Nesteruk Intraluminal MRI probe
CN1913826A (zh) * 2004-02-02 2007-02-14 西门子公司 用于前列腺癌、子宫颈癌和直肠癌成像诊断的组合mr－光学线圈
CN2699832Y (zh) * 2004-03-29 2005-05-18 北京大学 磁共振成像体腔射频线圈
CN1561907A (zh) * 2004-03-29 2005-01-12 北京大学 磁共振成像体腔射频线圈
US20060267586A1 (en) * 2004-11-16 2006-11-30 Kabushiki Kaisha Toshiba Radio frequency coil assembly and magnetic resonance imaging apparatus
US20090082664A1 (en) * 2007-09-26 2009-03-26 Schleifring Und Apparatebau Gmbh Endorectal Coil for Magnetic Resonance Tomograph
CN101482600A (zh) * 2008-01-08 2009-07-15 西门子（中国）有限公司 一种磁共振成像系统的接收装置
CN102970924A (zh) * 2010-07-01 2013-03-13 梅德拉公司 多通道直肠内线圈和其接口设备
CN102018512A (zh) * 2010-12-17 2011-04-20 上海辰光医疗科技有限公司 用于磁共振成像的盆部射频线圈
CN102707249A (zh) * 2012-07-03 2012-10-03 汤丽萍 一种核磁共振成像仪器的射频线圈
CN104541177A (zh) * 2012-08-08 2015-04-22 皇家飞利浦有限公司 具有针对外科手术仪器的开放进入的直肠内前列腺线圈
CN203773037U (zh) * 2014-01-28 2014-08-13 上海辰光医疗科技股份有限公司 用于磁共振成像系统的乳腺磁共振射频接收线圈
CN204649945U (zh) * 2015-05-27 2015-09-16 上海辰光医疗科技股份有限公司 乳腺磁共振射频接收线圈电路结构
CN111830447A (zh) * 2020-07-24 2020-10-27 深圳市一康云智慧科技有限责任公司 用于磁共振成像的前列腺和直肠射频线圈装置

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