KR101842576B1 - Magnetic resonance imaging radio frequency coil with improved rf transmit efficiency - Google Patents

Magnetic resonance imaging radio frequency coil with improved rf transmit efficiency Download PDF

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KR101842576B1
KR101842576B1 KR1020160143639A KR20160143639A KR101842576B1 KR 101842576 B1 KR101842576 B1 KR 101842576B1 KR 1020160143639 A KR1020160143639 A KR 1020160143639A KR 20160143639 A KR20160143639 A KR 20160143639A KR 101842576 B1 KR101842576 B1 KR 101842576B1
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South Korea
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coil
transmission
inductor
magnetic resonance
reception
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KR1020160143639A
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Korean (ko)
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서증훈
정준영
류연철
김경남
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가천대학교 산학협력단
(의료)길의료재단
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Priority to KR1020160143639A priority Critical patent/KR101842576B1/en
Priority to PCT/KR2017/012190 priority patent/WO2018080287A1/en
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    • 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
    • G01R15/00—Details of measuring arrangements of the types provided for in groups G01R17/00 - G01R29/00, G01R33/00 - G01R33/26 or G01R35/00
    • G01R15/14—Adaptations providing voltage or current isolation, e.g. for high-voltage or high-current networks
    • G01R15/18—Adaptations providing voltage or current isolation, e.g. for high-voltage or high-current networks using inductive devices, e.g. transformers
    • 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
    • G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
    • G01R33/34046—Volume type coils, e.g. bird-cage coils; Quadrature bird-cage coils; Circularly polarised coils

Abstract

The present invention provides a magnetic resonance RF coil capable of improving RF transmission efficiency without the reduction of signal sensitivity by replacing a conventional RF shield disposed on the outside of the RF coil. The magnetic resonance RF coil includes a loop-shaped coil (110) for transmission and reception which is connected to a cable for RF transmission and reception and includes a first inductor (111); and a loop-shaped coil (120) for power transmission which is adjacent to the first inductor (111), includes a second inductor (121), and is arranged on a different plane to be separated from the coil (110) for transmission and reception.

Description

RF 송신 효율이 개선된 자기공명 영상용 RF 코일{MAGNETIC RESONANCE IMAGING RADIO FREQUENCY COIL WITH IMPROVED RF TRANSMIT EFFICIENCY}[0001] MAGNETIC RESONANCE IMAGING RADIO FREQUENCY COIL WITH IMPROVED RF TRANSMIT EFFICIENCY [0002]

본 발명은 RF 송신 효율을 개선할 수 있는 자기공명 RF 코일에 관한 것이다.The present invention relates to a magnetic resonance RF coil capable of improving RF transmission efficiency.

자기 공명 영상(magnetic resonance imaging, MRI)은 균일한 주자기장(main magnetic field) 내에서 인체 내에 존재하는 핵종(수소, 인, 나트륨, 탄소 등)의 자화벡터(magnetization vector)에 대해 고주파 RF(radiofrequency) 펄스를 인가하여 특정 핵종(수소 등)을 공명시켜 수직평면으로 자화벡터가 재정렬되면서 발생되는 자기공명 신호를 수신하여 얻어서 컴퓨터를 통해 재구성하여 영상화하는 기술이다.BACKGROUND ART Magnetic resonance imaging (MRI) is a magnetic resonance imaging (MRI) technique that uses a radiofrequency (RF) magnetic field to magnetize a nuclide (hydrogen, phosphorus, sodium, carbon, etc.) in a human body in a homogeneous main magnetic field ) Pulses to resonate a specific nuclide (hydrogen, etc.) to obtain a magnetic resonance signal generated by rearrangement of magnetization vectors in a vertical plane, and reconstructing and imaging through a computer.

일반적으로 자화벡터를 공명시키기 위한 펄스 송신과 발생된 자기공명 신호의 수신은 RF 코일에 의해 이루어지며, 이때 RF 코일은 자화벡터를 공명시키기 위한 RF 신호를 송신(RF 송신 모드)하는 코일과 자기공명 신호를 수신(RF 수신 모드)하는 코일이 각각 따로 마련될 수 있으며, 또는 하나의 RF 코일에 의해 RF 송신 모드와 RF 수신 모드가 같이 수행될 수 있다.Generally, the pulse transmission for resonating the magnetization vector and the reception of the generated magnetic resonance signal are performed by an RF coil, where the RF coil transmits a RF signal for resonating the magnetization vector (RF transmission mode) Each of the coils for receiving a signal (RF receiving mode) may be separately provided, or an RF transmitting mode and an RF receiving mode may be performed simultaneously by one RF coil.

일반적으로 주자기장의 크기가 클수록 MRI의 감도(sensitivity)는 증가하게 되며, 대략 S/N비(signal to noise ratio)는 주자기장의 크기와 비례하는 것으로 알려져 있다. 따라서 보다 세밀한 구조의 영상을 얻기 위하여 큰 자기장의 영상 시스템에서의 연구와 개발이 활발히 이루어지고 있으며, 특히 뇌과학 분야와 같이 고해상도 영상의 필요성으로 인하여 현재는 인체용 7T의 초고자장 자기공명영상 시스템까지 나와 있다.Generally, as the magnitude of the main magnetic field increases, the sensitivity of the MRI increases, and the signal to noise ratio (S / N ratio) is known to be proportional to the magnitude of the main magnetic field. Therefore, researches and developments in a large magnetic field imaging system have been actively carried out in order to obtain a more detailed structure image. Especially due to the necessity of a high resolution image like the brain science field, the 7T ultra high magnetic field magnetic resonance imaging system I'm out.

한편, 이와 같이 초고자장 자기공명영상 시스템에서의 여러 장점에도 불구하고 해결해야 될 기술적인 문제점이 있으며, 그 중에서 주요한 이슈는 RF 코일과 관련된 문제이다.Meanwhile, there are technical problems to be solved in spite of various advantages in the ultra high magnetic field imaging system. Among them, the main issue is RF coil.

도 1은 종래기술에 따른 자기공명 영상용 RF 코일을 보여주는 도면이다.1 is a view showing an RF coil for a magnetic resonance imaging according to the prior art.

도 1을 참고하면, 종래기술에 따른 자기공명 영상용 RF 코일은 케이블과 연결되어 RF 송수신이 이루어지는 송수신 코일(10)과, 송수신 코일(10) 외측으로 원통형상의 RF 쉴드(20)가 마련된다.Referring to FIG. 1, the RF coil for magnetic resonance imaging according to the related art includes a transmission / reception coil 10 connected to a cable to perform RF transmission / reception, and a cylindrical RF shield 20 outside the transmission / reception coil 10.

송수신 코일(10)의 안쪽으로 검사 대상체(1)가 위치하게 되며, 송수신 코일(10)은 케이블을 통해 RF가 인가되어 검사 대상체(1)에 RF 자기장(H1)을 발생시키며, 또한 검사 대상체(1)에서 발생된 RF 신호를 수신한다.The inspection object 1 is positioned inside the transmission and reception coil 10 and RF is applied to the transmission and reception coil 10 through the cable to generate the RF magnetic field H1 on the inspection object 1, 1).

한편 RF쉴드(20)는 도전성의 원통형상을 갖고 송수신 코일(10) 외측에 배치되어 송수신 코일(10)에서 발생한 전자기장이 바깥으로 나가는 것을 방지하고 송수신 코일(10) 바깥에 배치되는 그래디언트 코일(미도시) 사이의 커플링을 방지하며, 동시에 이를 다시 검사 대상체(1) 방향으로 반사시켜 RF 송신 효율을 개선하는 역할을 한다.On the other hand, the RF shield 20 has a conductive cylindrical shape and is disposed outside the transmission / reception coil 10 to prevent the electromagnetic field generated by the transmission / reception coil 10 from going out, and a gradient coil And at the same time, it reflects it toward the test object 1 to improve the RF transmission efficiency.

그러나 RF쉴드(20)는 도전성의 원통형 튜브이므로 와전류가 발생되어 송수신 코일(10)의 전자기장의 신호 민감도를 감소시키는 원인이 된다.However, since the RF shield 20 is a conductive cylindrical tube, an eddy current is generated, which causes the signal sensitivity of the electromagnetic field of the transmission coil 10 to be reduced.

공개특허공보 제10-2015-0081108호(공개일자: 2015.07.13)Japanese Patent Application Laid-Open No. 10-2015-0081108 (publication date: 2015.07.13)

본 발명은 이러한 종래기술의 문제점을 개선하고자 하는 것으로, 종래에 RF 코일의 외측에 배치되는 RF쉴드를 대체하여 신호 민감도의 감소 없이 RF 송신 효율을 개선할 수 있는 자기공명 RF 코일을 제공하고자 하는 것이다.An object of the present invention is to provide a magnetic resonance RF coil capable of improving the RF transmission efficiency without reducing the signal sensitivity by replacing the RF shield disposed outside the RF coil .

이러한 목적을 달성하기 위한 본 발명에 따른 자기공명 영상용 RF 코일은, RF 송수신을 위한 케이블과 연결되며, 제1인덕터가 구비되는 루프 형태의 송수신용 코일과; 상기 제1인덕터와 인접하여 제2인덕터가 구비되며, 상기 송수신용 코일과 서로 다른 평면 상에 이격되어 배치되는 루프 형태의 전력송신용 코일을 포함한다.According to an aspect of the present invention, there is provided an RF coil for a magnetic resonance imaging (MRI), including: a loop-shaped transmission coil connected to a cable for RF transmission and reception and having a first inductor; And a loop-shaped power transmission coil disposed adjacent to the first inductor and provided with a second inductor and spaced apart from the transmission coil.

바람직하게는, 상기 송수신용 코일과 상기 전력송신용 코일은 적어도 일부가 서로 대면하여 배치된다.Preferably, at least a part of the coil for transmitting and receiving and the coil for transmitting power are disposed facing each other.

바람직하게는, 상기 송수신용 코일은 복수 개로 구성되어 원통 구조로 배치되며, 상기 전력송신용 코일은 상기 송수신용 코일의 외측에서 원통 구조로 배치된다.Preferably, the plurality of transmission / reception coils are arranged in a cylindrical structure, and the power transmission coils are arranged in a cylindrical structure outside the transmission / reception coils.

보다 바람직하게는, 상기 전력송신용 코일은 상기 송수신용 코일과 동일한 숫자로 동일 방향에 배치된다.More preferably, the power transmission coils are arranged in the same direction with the same numbers as the transmission and reception coils.

본 발명에 따른 자기공명 영상용 RF 코일은, RF 송수신을 위한 케이블과 연결되며, 제1인덕터가 구비되는 루프 형태의 송수신용 코일과, 제1인덕터와 인접하여 제2인덕터가 구비되고 송수신용 코일과 서로 다른 평면 상에 이격되어 배치되는 루프 형태의 전력송신용 코일을 포함하므로써, 종래기술의 RF쉴드를 대체하여 신호 민감도의 감소 없이 RF 송신 효율을 개선할 수 있는 효과가 있다.The RF coil for magnetic resonance imaging according to the present invention includes a coil for transmitting and receiving in the form of a loop having a first inductor connected to a cable for RF transmission and reception, a second inductor adjacent to the first inductor, The RF transmission efficiency can be improved without reducing the signal sensitivity by replacing the RF shield of the related art by including the loop transmission power coil disposed on a different plane from the RF shield.

도 1은 종래기술에 따른 자기공명 영상용 RF 코일을 보여주는 도면,
도 2는 본 발명에 따른 자기공명 영상용 RF 코일의 구성도,
도 3은 본 발명에 따른 자기공명 영상용 RF 코일의 단위 코일만을 예시하여 보여주는 도면.1 is a view showing an RF coil for a magnetic resonance imaging according to the related art,
FIG. 2 is a configuration diagram of an RF coil for magnetic resonance imaging according to the present invention,
3 is a view illustrating only a unit coil of an RF coil for magnetic resonance imaging according to the present invention.

본 발명의 실시예에서 제시되는 특정한 구조 내지 기능적 설명들은 단지 본 발명의 개념에 따른 실시예를 설명하기 위한 목적으로 예시된 것으로, 본 발명의 개념에 따른 실시예들은 다양한 형태로 실시될 수 있다. 또한 본 명세서에 설명된 실시예들에 한정되는 것으로 해석되어서는 아니 되며, 본 발명의 사상 및 기술 범위에 포함되는 모든 변경물, 균등물 내지 대체물을 포함하는 것으로 이해되어야 한다.The specific structure or functional description presented in the embodiment of the present invention is merely illustrative for the purpose of illustrating an embodiment according to the concept of the present invention, and embodiments according to the concept of the present invention can be implemented in various forms. And should not be construed as limited to the embodiments described herein, but should be understood to include all modifications, equivalents, and alternatives falling within the spirit and scope of the invention.

한편, 본 발명에서 제1 및/또는 제2 등의 용어는 다양한 구성 요소들을 설명하는데 사용될 수 있지만, 상기 구성 요소들은 상기 용어들에 한정되지는 않는다. 상기 용어들은 하나의 구성요소를 다른 구성요소들과 구별하는 목적으로만, 예컨대 본 발명의 개념에 따른 권리 범위로부터 벗어나지 않는 범위 내에서, 제1구성요소는 제2구성요소로 명명될 수 있고, 유사하게 제2구성요소는 제1구성요소로도 명명될 수 있다.Meanwhile, in the present invention, the terms first and / or second etc. may be used to describe various components, but the components are not limited to the terms. The terms may be referred to as a second element only for the purpose of distinguishing one element from another, for example, to the extent that it does not depart from the scope of the invention in accordance with the concept of the present invention, Similarly, the second component may also be referred to as the first component.

어떠한 구성요소가 다른 구성요소에 "연결되어"있다거나 "접속되어"있다고 언급된 때에는, 그 다른 구성요소에 직접적으로 연결되어 있거나 접속되어 있을 수도 있지만, 중간에 다른 구성요소가 존재할 수도 있다고 이해되어야 할 것이다. 반면에, 어떠한 구성요소가 다른 구성요소에 "직접 연결되어"있다거나 또는 "직접 접촉되어"있다고 언급된 때에는, 중간에 다른 구성요소가 존재하지 않는 것으로 이해되어야 할 것이다. 구성요소들 간의 관계를 설명하기 위한 다른 표현들, 즉 "~사이에"와 "바로 ~사이에"또는 "~에 인접하는"과 "~에 직접 인접하는"등의 표현도 마찬가지로 해석되어야 한다.Whenever an element is referred to as being "connected" or "connected" to another element, it may be directly connected or connected to the other element, but it should be understood that other elements may be present in between something to do. On the other hand, when it is mentioned that an element is "directly connected" or "directly contacted" to another element, it should be understood that there are no other elements in between. Other expressions for describing the relationship between components, such as "between" and "between" or "adjacent to" and "directly adjacent to" should also be interpreted.

본 명세서에서 사용하는 용어는 단지 특정한 실시예를 설명하기 위해 사용된 것으로서, 본 발명을 한정하려는 의도가 아니다. 단수의 표현은 문맥상 명백하게 다르게 뜻하지 않는 한, 복수의 표현을 포함한다. 본 명세서에서 "포함한다" 또는 "가지다"등의 용어는 실시된 특징, 숫자, 단계, 동작, 구성 요소, 부분품 또는 이들을 조합한 것이 존재함을 지정하려는 것이지, 하나 또는 그 이상의 다른 특징이나 숫자, 단계, 동작, 구성 요소, 부분품 또는 이들을 조합한 것들의 존재 또는 부가 가능성을 미리 배제하지 않는 것으로 이해되어야 한다.The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The singular expressions include plural expressions unless the context clearly dictates otherwise. It will be further understood that the terms " comprises ", or "having ", and the like in the specification are intended to specify the presence of stated features, integers, But do not preclude the presence or addition of steps, operations, elements, parts, or combinations thereof.

이하, 본 발명의 실시예를 첨부 도면을 참고하여 상세히 설명하도록 한다.Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

도 2는 본 발명에 따른 자기공명 영상용 RF 코일의 구성도이다.2 is a configuration diagram of an RF coil for magnetic resonance imaging according to the present invention.

도 2에 예시된 것과 같이 본 발명의 자기공명 영상용 RF 코일은, RF 송수신을 위한 케이블과 연결되며, 제1인덕터(111)가 구비되는 루프 형태의 송수신용 코일(110)과; 상기 제1인덕터(111)와 인접하여 제2인덕터(121)가 구비되며, 상기 송수신용 코일(110)과 서로 다른 평면 상에 이격되어 배치되는 루프 형태의 전력송신용 코일(120)을 포함한다.As illustrated in FIG. 2, the RF coil for magnetic resonance imaging of the present invention includes a coil 110 for transmitting and receiving a loop, connected to a cable for RF transmission and reception, and having a first inductor 111; And a coil 120 for power transmission in the form of a loop, which is disposed adjacent to the first inductor 111 and has a second inductor 121 and is spaced apart from the transmission coil 110 .

본 실시예에서 송수신용 코일(110)은 복수 개로 구성되어 원통형 구조로 배치되어 다채널 RF 코일로 사용될 수 있으며, 이때 전력송신용 코일(120)은 송수신용 코일(110)의 외측에서 원통 구조로 배치된다.In this embodiment, the transmitting and receiving coils 110 are arranged in a cylindrical structure and can be used as multi-channel RF coils. In this case, the coils 120 for power transmission are arranged outside the transmitting and receiving coils 110 in a cylindrical structure .

바람직하게는, 송수신용 코일(110)과 전력송신용 코일(120)은 동일한 숫자로 등방적으로 동일 방향에 배치될 수 있다.Preferably, the transmitting and receiving coils 110 and the power transmitting coils 120 may be equidistantly arranged in the same direction.

도 3은 본 발명에 따른 자기공명 영상용 RF 코일의 단위 코일만을 예시하여 보여주는 도면이다.3 is a view illustrating only a unit coil of an RF coil for magnetic resonance imaging according to the present invention.

도 3을 참고하면, 송수신용 코일(110)의 상부에 전력송신용 코일(120)이 대면하여 위치하며, 제1인덕터(111)와 제2인덕터(121)는 서로 인접하여 위치한다.Referring to FIG. 3, a coil 120 for power transmission is disposed on an upper portion of a coil 110 for transmission and reception, and a first inductor 111 and a second inductor 121 are positioned adjacent to each other.

따라서, 케이블(미도시)을 통해 송수신용 코일(110)에 RF 전력이 인가되면, 송수신용 코일(110)은 수직 방향으로 전자기장(RF1)(RF2)을 발생시키며, 이때 송수신용 코일(110)의 제1인덕터(111)의 전류 변화에 의해 제2인덕터(112)에 유도 기전력이 발생되는 상호유도작용에 의해 전력송신용 코일(120)에도 전자기장(RF1)(RF4)이 발생되며, 따라서 송수신용 코일(110)을 통하여 조사 대상체에 전달되는 유효 전자기장(RFef=RF1+RF2)을 증가시킬 수 있다.Therefore, when RF power is applied to the transmitting / receiving coil 110 through a cable (not shown), the transmitting / receiving coil 110 generates the electromagnetic fields RF1 and RF2 in the vertical direction, The electromagnetic fields RF1 and RF4 are generated in the coil 120 for power transmission by the mutual induction action in which the induction electromotive force is generated in the second inductor 112 by the current change of the first inductor 111 of the first inductor 111, It is possible to increase the effective electromagnetic field (RFef = RF1 + RF2) transmitted to the irradiation target object through the use coil 110. [

한편, 제1인덕터(111)와 제2인덕터(121)의 권선(turn수)을 조절하여 송수신 코일로부터 전력송신용 코일(120)에 인가되는 RF 출력의 크기를 조절할 수 있다.The number of turns of the first inductor 111 and the second inductor 121 may be adjusted to adjust the magnitude of the RF output applied to the coil 120 for power transmission from the transmission coil.

이상에서 설명한 본 발명은 전술한 실시예 및 첨부된 도면에 의해 한정되는 것이 아니고, 본 발명의 기술적 사상을 벗어나지 않는 범위 내에서 여러 가지 치환, 변형 및 변경이 가능함은 본 발명이 속하는 기술분야에서 통상의 지식을 가진 자에게 명백할 것이다. 예를 들어, 본 실시예에서는 복수의 루프 형태의 표면 코일로 구성된 다채널 RF 코일을 예시하여 설명하였으나, 이에 한정되는 것은 아니며 루프 형태의 단일 표면 코일에도 동일하게 적용될 수 있으며, 이때 송수신용 코일이 검사 대상체와 직접 대면하고 전력송신용 코일은 송수신용 코일의 뒷면에 배치됨이 바람직하다.It will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the spirit or scope of the inventions. It will be apparent to those of ordinary skill in the art. For example, in the present embodiment, a multi-channel RF coil composed of a plurality of loop-shaped surface coils has been described. However, the present invention is not limited to this and is also applicable to a single surface coil in a loop shape. It is preferable that the coils for power transmission and the coils for power transmission are arranged on the rear surface of the coil for transmission and reception.

110 : 송수신용 코일 111 : 제1인덕터
120 : 전력송신용 코일 121 : 제2인덕터110: coil for transmitting / receiving 111: first inductor
120: coil for power transmission 121: second inductor

Claims (4)

RF 송수신을 위한 케이블과 연결되며, 일측에 코일 형태의 제1인덕터(111)가 구비되는 루프 형태의 송수신용 코일(110)과;
상기 제1인덕터(111)와 인접하여 나란하게 코일 형태의 제2인덕터(121)가 구비되며, 상기 송수신용 코일(110)과 서로 다른 평면 상에 이격되어 배치되는 폐루프 형태의 전력송신용 코일(120)을 포함하며,
상기 송수신용 코일(110)은 복수 개로 구성되어 임의 직경을 갖는 원통형상의 표면에 배치되며, 상기 전력송신용 코일(120)은 상기 송수신용 코일(110)과 동일한 숫자로 동일 방향에 적어도 일부가 대면하도록 상기 송수신용 코일의 외측에서 임의 직경을 갖는 원통형상의 표면에 배치되어 상기 송수신용 코일(110)이 상기 전력송신용 코일(120) 보다 피검체에 더 인접하게 배치됨을 특징으로 하는 자기공명 영상용 RF 코일.Receiving coil 110 connected to a cable for RF transmission and reception and having a coil-shaped first inductor 111 at one side thereof;
A second inductor 121 in the form of a coil is disposed adjacent to and in parallel with the first inductor 111, and a coil for power transmission in the form of a closed loop, which is disposed on a different plane from the transmission coil 110, (120)
Receiving coils 110 are arranged on a cylindrical surface having an arbitrary diameter, and the power transmitting coil 120 has the same number as that of the transmitting and receiving coils 110, at least a part of which faces in the same direction Receiving coil is disposed on a cylindrical surface having an arbitrary diameter outside the transmitting and receiving coil so that the transmitting and receiving coil is disposed closer to the subject than the power transmitting coil. RF coil. 삭제delete 삭제delete 삭제delete
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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2007325826A (en) 2006-06-09 2007-12-20 Hitachi Ltd Double-tuned rf coil
JP5179588B2 (en) 2008-08-18 2013-04-10 株式会社日立メディコ High frequency coil and magnetic resonance imaging apparatus
US20130119991A1 (en) 2010-08-17 2013-05-16 Yoshihisa Soutome High-frequency coil and magnetic resonance imaging device employing same
JP5247214B2 (en) * 2008-04-04 2013-07-24 株式会社日立製作所 High frequency magnetic field coil and magnetic resonance imaging apparatus

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3197262B2 (en) * 1990-02-28 2001-08-13 株式会社東芝 Magnetic resonance imaging
JP5664015B2 (en) * 2010-08-23 2015-02-04 Tdk株式会社 Coil device and non-contact power transmission device

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2007325826A (en) 2006-06-09 2007-12-20 Hitachi Ltd Double-tuned rf coil
JP5247214B2 (en) * 2008-04-04 2013-07-24 株式会社日立製作所 High frequency magnetic field coil and magnetic resonance imaging apparatus
JP5179588B2 (en) 2008-08-18 2013-04-10 株式会社日立メディコ High frequency coil and magnetic resonance imaging apparatus
US20130119991A1 (en) 2010-08-17 2013-05-16 Yoshihisa Soutome High-frequency coil and magnetic resonance imaging device employing same

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