JPH0630165Y2 - Receiver coil for nuclear magnetic resonance imaging - Google Patents

Receiver coil for nuclear magnetic resonance imaging

Info

Publication number
JPH0630165Y2
JPH0630165Y2 JP1989020271U JP2027189U JPH0630165Y2 JP H0630165 Y2 JPH0630165 Y2 JP H0630165Y2 JP 1989020271 U JP1989020271 U JP 1989020271U JP 2027189 U JP2027189 U JP 2027189U JP H0630165 Y2 JPH0630165 Y2 JP H0630165Y2
Authority
JP
Japan
Prior art keywords
magnetic resonance
coil
subject
nuclear magnetic
receiving 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.)
Expired - Lifetime
Application number
JP1989020271U
Other languages
Japanese (ja)
Other versions
JPH02111405U (en
Inventor
幸浩 八杉
秀則 岸野
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.)
Hitachi Healthcare Manufacturing Ltd
Original Assignee
Hitachi Medical Corp
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 Hitachi Medical Corp filed Critical Hitachi Medical Corp
Priority to JP1989020271U priority Critical patent/JPH0630165Y2/en
Publication of JPH02111405U publication Critical patent/JPH02111405U/ja
Application granted granted Critical
Publication of JPH0630165Y2 publication Critical patent/JPH0630165Y2/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Description

【考案の詳細な説明】 〔産業上の利用分野〕 本考案は、核磁気共鳴(以下、NMRと略記する)を利
用して被検体の所望箇所を映像化するNMRイメージン
グ装置用高周波受信コイルに関するものである。
DETAILED DESCRIPTION OF THE INVENTION [Industrial field of use] The present invention relates to a high-frequency receiver coil for an NMR imaging apparatus that visualizes a desired portion of a subject using nuclear magnetic resonance (hereinafter abbreviated as NMR). It is a thing.

〔従来の技術〕[Conventional technology]

NMRイメージング装置では、原子核を高周波を照射し
て励起し、共鳴した原子核より放出される高周波信号
(これをNMR信号という)を検出する。高周波信号の
検出には通常、コイルが使用され、サドル型,ソレノイ
ド型及びそれらを変形した種々のコイルが考えられてい
る。この検出コイルの感度が再構成された画像のS/N
比に直接影響するため、その研究改良が多くなされてい
る。
In the NMR imaging apparatus, the atomic nuclei are excited by being irradiated with a high frequency wave, and a high frequency signal (this is called an NMR signal) emitted from the resonated atomic nuclei is detected. A coil is usually used to detect a high frequency signal, and various types of coils such as a saddle type coil, a solenoid type coil, and modifications thereof are considered. The S / N of the image in which the sensitivity of this detection coil is reconstructed
Many research improvements have been made because they directly affect the ratio.

垂直磁場方式NMRイメージング装置の場合、受信コイ
ルに感度の高いソレノイド型コイルを使用することがで
きる。また、D.I.HoultとR.E.RichardsのS/
N比を表す式によれば、高周波受信コイルの大きさ
(径)を小さくすればS/N比が向上するとされてお
り、それは実験においても確認されている。
In the case of the vertical magnetic field type NMR imaging apparatus, a solenoid coil having high sensitivity can be used as the receiving coil. Also, D.I. I. Hoult and R.H. E. Richards S /
According to the formula representing the N ratio, it is said that the S / N ratio is improved by reducing the size (diameter) of the high frequency receiving coil, which is also confirmed in the experiment.

被検体にこういつた受信コイルを装着する場合使い勝手
の向上のためにコイルが分割できたほうが望ましい。ま
た、頸椎部等では分割できなければ小径のコイルを装着
することができない。そこで、従来の装置は特願昭63-1
52341号に記載のように受信コイルをフレキシブな素材
で構成し、その一部をコネクタを用いて着脱可能とし、
被検体の検査部に応じて受信コイルの長さを可変できる
ようにして被検体に密着できるような構造としていた。
When the receiving coil is attached to the subject, it is desirable that the coil can be divided to improve the usability. In addition, a small-diameter coil cannot be attached unless it can be divided at the cervical vertebra or the like. Therefore, the conventional device is Japanese Patent Application No. 63-1.
As described in No. 52341, the receiving coil is made of a flexible material, part of which can be attached and detached using a connector,
The structure is such that the length of the receiving coil can be changed according to the inspection part of the subject so as to be in close contact with the subject.

〔考案が解決しようとする課題〕[Problems to be solved by the device]

前記従来技術では受信コイルに使用するコネクタに一般
のものを用いていたため、コネクタの素材やメツキに含
まれる磁性体の影響を考慮しておらず、これによつて静
磁場の均一性が乱され、得られる画像に歪みを生じると
いう問題点があつた。したがつて、受信コイルや接続コ
ネクタを磁性歪みの影響が出ない程度に被検体から離し
て装着しなければならず、結果として受信コイル径を大
きくなつてしまいS/N比の低下を招いていた。
In the above-mentioned prior art, since a general connector is used for the receiving coil, the influence of the magnetic material contained in the connector material or the mat is not taken into consideration, which disturbs the uniformity of the static magnetic field. However, there is a problem that the obtained image is distorted. Therefore, the receiving coil and the connecting connector must be mounted apart from the subject to the extent that magnetic distortion does not affect them, resulting in a large receiving coil diameter and a decrease in S / N ratio. It was

本考案は、上述したような問題点を解消するためになさ
れたもので、磁性歪みのない、S/N比の高い良質の画
像が得られるNMRイメージング装置用高周波受信コイ
ルを提供することを目的とする。
The present invention has been made to solve the above-described problems, and an object thereof is to provide a high-frequency receiver coil for an NMR imaging apparatus that can obtain a high-quality image with a high S / N ratio without magnetic distortion. And

〔課題を解決するための手段〕[Means for Solving the Problems]

前述の問題点は、受信コイルに使用するコネクタに磁性
体が含まれているものを使用しているところに起因して
いる。そこでコネクタの接点の素材にリン青銅などの接
点として使用できる性質を有し、かつ磁性体を含まない
合金を使用し、さらに接点部分の信頼性向上のために金
メツキ等を施して構成するようにした。
The above-mentioned problem is caused by the fact that the connector used for the receiving coil uses a magnetic substance. Therefore, it is recommended that the connector contact material be made of an alloy that does not contain a magnetic material and has properties such that it can be used as a contact such as phosphor bronze, and that gold plating is applied to improve the reliability of the contact part. I chose

ここで、一般的な金メツキでは剥離防止などのメツキ面
の安定化のために下地としてニツケルメツキを行わなけ
ればならない。しかし、ニツケルは磁性体であり、非磁
性化の妨げとなる。そこで、この金メツキの下地として
銅メツキや銀メツキを施し非磁性メツキとした。また、
銀メツキを施す場合は一般的には硫化防止のために微量
のニツケルを混入し、合金として用いるが、これも非磁
性化の妨げとなるので純銀を用いる。
Here, in general gold plating, nickel plating must be performed as a base in order to stabilize the plating surface such as prevention of peeling. However, nickel is a magnetic substance, which hinders demagnetization. Therefore, copper plating or silver plating is applied as a base of the gold plating to obtain a non-magnetic plating. Also,
When silver plating is applied, a small amount of nickel is generally mixed and used as an alloy to prevent sulfurization, but pure silver is used because it also prevents demagnetization.

このようにして、受信コイルに使用するコネクタをその
素材及びメツキ材から磁性体を排除した構成とすること
によつて、受信コイルを被検体に密着させても磁性歪み
のない画像を得ることが可能となる。
In this way, by making the connector used for the receiving coil the magnetic material from the material and plating material, it is possible to obtain an image without magnetic distortion even when the receiving coil is brought into close contact with the subject. It will be possible.

〔作用〕[Action]

NMRイメージング装置用受信コイルに使用するコネク
タをメツキ材を含めて非磁性素材で構成し、静磁場の均
一性への影響をなくすことによつて、被検体に受信コイ
ルを密着させて使用することが可能となり、歪みなくS
/N比の高い良質な画像を得ることができるようにな
る。
To use the receiving coil in close contact with the subject by configuring the connector used for the receiving coil for the NMR imaging device with a non-magnetic material including the plating material and eliminating the influence on the uniformity of the static magnetic field. Is possible and S without distortion
It becomes possible to obtain a high-quality image with a high / N ratio.

〔実施例〕〔Example〕

以下、本考案の実施例を添付図面に基づいて詳細に説明
する。
Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

第3図は本考案に係るNMRイメージング装置の全体構
成図を示すブロツク図である。このNMRイメージング装
置は、核磁気共鳴(NMR)現象を利用して被検体6の
断層画像を得るもので、静磁場発生磁石10と、中央処
理装置(以下CPUという)11と、シーケンサー12
と、送信系13と、磁場勾配発生系14と、受信系15
と、信号処理系16とからなる。上記静磁場発生磁石1
0は、被検体6の周りにその体軸と直交する方向に強く
均一な静磁場を発生させるもので、上記被検体6の周り
のある広がりをもつた空間に永久磁石方式又は常電導方
式あるいは超電導方式の磁場発生手段が配置されてい
る。上記シーケンサ12は、CPU11の制御で動作
し、被検体6の断層画像のデータ収集に必要な種々の命
令を送信系13及び磁場勾配発生系14並びに受信系1
5に送るものである。上記送信系13は、高周波発生器
17と変調器18と高周波増幅器19と送信側の高周波
コイル20aとからなり、上記高周波発生器17から出
力された高周波パルスをシーケンサ12の命令に従つて
変調器18で振幅変調し、この振幅変調された高周波パ
ルスを高周波増幅器19で増幅した後に被検体6に近接
して配置された高周波コイル20aに供給することによ
り、電磁波が上記被検体6に照射されるようになつてい
る。上記磁場勾配発生系14は、X,Y,Zの三軸方向
に巻かれた傾斜磁場コイル21と、それぞれのコイルを
駆動する傾斜磁場電源22とからなり、上記シーケンサ
12からの命令に従つてそれぞれのコイルの傾斜磁場電
源22を駆動することにより、X,Y,Zの三軸方向の
傾斜磁場G,G,Gを被検体6に印加するように
なつている。この傾斜磁場の加え方により、被検体6に
対するスライス面を設定することができる。上記受信系
15は、受信側の高周波コイル20bと増幅器23と直
交位相検波器24とA/D変換器25とからなり、上記
送信側の高周波コイル20aから照射された電磁波によ
る被検体6の応答の電磁波(NMR信号)は被検体6に
近接して配置された高周波コイル20bで検出され、増
幅器23及び直交位相検波器24を介してA/D変換器
25に入力してデジタル量に変換され、さらにシーケン
サ12からの命令によるタイミングで直交位相検波器2
4によりサンプリングされた二系統の収集データとさ
れ、その信号が信号処理系16に送られるようになつて
いる。この信号処理系16は、CPU11と、磁気デイ
スク26及び磁気テープ27等の記録装置と、CRT等
のデイスプレイ28とからなり、上記CPU11でフー
リエ変換、補正係数計算像再構成等の処理を行ない、任
意断面の信号強度分布あるいは複数の信号に適当な演算
を行なつて得られた分布を画像化してデイスプレイ28
に表示するようになつている。
FIG. 3 is a block diagram showing the overall configuration of the NMR imaging apparatus according to the present invention. This NMR imaging apparatus obtains a tomographic image of the subject 6 by utilizing a nuclear magnetic resonance (NMR) phenomenon, and includes a static magnetic field generating magnet 10, a central processing unit (hereinafter referred to as CPU) 11, and a sequencer 12.
, Transmission system 13, magnetic field gradient generation system 14, and reception system 15
And a signal processing system 16. The static magnetic field generating magnet 1
0 is for generating a strong and uniform static magnetic field around the subject 6 in a direction orthogonal to the body axis thereof. The permanent magnet system, the normal conducting system, or the normal conduction system in a space with a certain space around the subject 6 is used. A superconducting magnetic field generating means is arranged. The sequencer 12 operates under the control of the CPU 11 and sends various commands necessary for collecting tomographic image data of the subject 6 to the transmission system 13, the magnetic field gradient generation system 14, and the reception system 1.
To send to 5. The transmission system 13 includes a high frequency generator 17, a modulator 18, a high frequency amplifier 19, and a high frequency coil 20a on the transmission side. The high frequency pulse output from the high frequency generator 17 is modulated by a sequencer 12 in accordance with a command. The electromagnetic wave is applied to the subject 6 by amplitude-modulating 18 and amplifying the amplitude-modulated high-frequency pulse by a high-frequency amplifier 19 and then supplying the amplified high-frequency pulse to a high-frequency coil 20a arranged close to the subject 6. It is becoming like this. The magnetic field gradient generation system 14 is composed of a gradient magnetic field coil 21 wound in three directions of X, Y, and Z, and a gradient magnetic field power source 22 for driving each coil, and according to a command from the sequencer 12. By driving the gradient magnetic field power source 22 of each coil, the gradient magnetic fields G X , G Y , and G Z in the triaxial directions of X , Y , and Z are applied to the subject 6. The slice plane for the subject 6 can be set by the method of applying the gradient magnetic field. The reception system 15 includes a high frequency coil 20b on the reception side, an amplifier 23, a quadrature phase detector 24, and an A / D converter 25, and the response of the subject 6 to the electromagnetic wave emitted from the high frequency coil 20a on the transmission side. Of the electromagnetic wave (NMR signal) is detected by the high-frequency coil 20b arranged close to the subject 6, is input to the A / D converter 25 via the amplifier 23 and the quadrature phase detector 24, and is converted into a digital amount. , And the quadrature detector 2 at the timing according to the command from the sequencer
The collected data of two systems sampled by 4 are sent, and the signals thereof are sent to the signal processing system 16. The signal processing system 16 includes a CPU 11, a recording device such as a magnetic disk 26 and a magnetic tape 27, and a display 28 such as a CRT. The CPU 11 performs processing such as Fourier transform and correction coefficient calculation image reconstruction. The signal intensity distribution of an arbitrary cross section or the distribution obtained by performing an appropriate calculation on a plurality of signals is imaged to display 28
It is supposed to be displayed in.

なお、第3図において、送信側及び受信側の高周波コイ
ル20a,20bと傾斜磁場コイル21は、被検体6の
周りの空間に配置された静磁場発生磁石10の磁場空間
内に配置されている。
In FIG. 3, the high frequency coils 20a and 20b and the gradient magnetic field coil 21 on the transmitting side and the receiving side are arranged in the magnetic field space of the static magnetic field generating magnet 10 arranged in the space around the subject 6. .

ここで、本考案に係る高周波コイル20bの一実施例を
第1図及び第2図に示す。第1図は高周波受信コイルの
全体構成を示す図である。コイル線材30は柔軟な材質
であり、ここにコネクタ31,32とNMR信号周波数
に同調させるための同調回路33及びプリアンプに接続
するための出力コネクタ34が取り付けられている。
An embodiment of the high frequency coil 20b according to the present invention is shown in FIGS. FIG. 1 is a diagram showing the overall configuration of a high frequency receiving coil. The coil wire 30 is a flexible material, and has connectors 31, 32, a tuning circuit 33 for tuning to the NMR signal frequency, and an output connector 34 for connecting to a preamplifier attached thereto.

第2図は使用例の説明図である。高周波受信コイル20
bは撮像の際、まず被検体の検査部位に沿つてコイル線
材30を巻き、次にコネクタ31と32を接続する。こ
のとき、コネクタ31に対するコネクタ32がコイル線
材上に複数箇所取り付けてあるため、検査部位の周囲長
に合わせて適当に選択できる構造となつている。第2図
(a)は検査部位が大きい場合であり、(b)は小さい
場合である。
FIG. 2 is an explanatory diagram of a usage example. High frequency receiving coil 20
At the time of imaging, b, first, winds the coil wire 30 along the inspection site of the subject, and then connects the connectors 31 and 32. At this time, since the connector 32 for the connector 31 is attached at a plurality of positions on the coil wire, the structure is such that it can be appropriately selected according to the peripheral length of the inspection site. FIG. 2 (a) shows the case where the inspection site is large, and FIG. 2 (b) shows the case where it is small.

このように本受信コイルは被検体に密着できる構造とな
つているために、その構成部材は全て非磁性体でなけれ
ばならない。そこで、コネクタ31,32及び出力コネ
クタ34の接点部を素材にリン青銅を使用し、表面安定
化のためのメツキ処理は銅メツキを下地とした金メツキ
として非磁性化している。
As described above, since the present receiving coil has a structure capable of being brought into close contact with the subject, all its constituent members must be non-magnetic materials. Therefore, phosphor bronze is used as a material for the contact portions of the connectors 31 and 32 and the output connector 34, and the plating treatment for surface stabilization is made non-magnetic as gold plating with the copper plating as a base.

従来はここに一般のコネクタを使用していたため、磁性
体の影響で均一磁場が乱されて再構成された画像上に歪
みを生じるという問題点があつた。本発明によつてこの
問題を解決し、被検体の検査部位に適した形状の受信コ
イルの使用が可能となり、S/N比の高い良質な画像を
得ることができる。
Conventionally, since a general connector is used here, there is a problem in that the uniform magnetic field is disturbed by the influence of the magnetic substance and distortion occurs on the reconstructed image. According to the present invention, this problem can be solved, and it becomes possible to use a receiving coil having a shape suitable for the examination site of the subject, and a high-quality image with a high S / N ratio can be obtained.

〔考案の効果〕[Effect of device]

以上述べたように本考案は、NMRイメージング装置に
おける高周波受信コイルに使用するコネクタを非磁性化
することにより、磁性歪みの問題を解決することがで
き、被検体に密着した設置が可能となり、S/N比の高
い、良質の画像が得られるという効果がある。
As described above, the present invention can solve the problem of magnetic distortion by demagnetizing the connector used for the high-frequency receiving coil in the NMR imaging apparatus, and enables the installation close to the subject. There is an effect that a high-quality image having a high / N ratio can be obtained.

【図面の簡単な説明】[Brief description of drawings]

第1図は本考案の一実施例の高周波受信コイルの全体構
成を示す説明図、第2図は上記高周波受信コイルの使用
状態を示す説明図、第3図は本考案に係るNMRイメー
ジング装置の全体構成を示すブロツク図である。 6…被検体、20b…高周波受信コイル、30…コイル
線材、31,32…コネクタ、33…同調回路、34…
出力コネクタ。
FIG. 1 is an explanatory view showing the overall structure of a high frequency receiving coil according to an embodiment of the present invention, FIG. 2 is an explanatory view showing a usage state of the high frequency receiving coil, and FIG. 3 is an NMR imaging apparatus according to the present invention. It is a block diagram which shows the whole structure. 6 ... Subject, 20b ... High frequency receiving coil, 30 ... Coil wire, 31, 32 ... Connector, 33 ... Tuning circuit, 34 ...
Output connector.

Claims (1)

【実用新案登録請求の範囲】[Scope of utility model registration request] 【請求項1】静磁場を発生する手段と、傾斜磁場を発生
する手段と、被検体の組織を構成する原子の原子核に核
磁気共鳴を起こさせるために高周波パルスを発生する手
段と、前記核磁気共鳴による信号を検出する核磁気共鳴
信号検出手段と、前記核磁気共鳴信号を用いて画像再構
成を行う演算手段とを備えてなる核磁気共鳴イメージン
グ装置の前記信号検出手段である高周波受信コイルであ
って、この高周波受信コイルの前記被検体への装着を、
コネクタの接続によって密着して可能とした核磁気共鳴
イメージング装置用受信コイルにおいて、前記コネクタ
を磁性体を含まない材料で構成し、かつ、磁性体を含ま
ないメッキを施したことを特徴とする核磁気共鳴イメー
ジング装置用受信コイル。
1. A means for generating a static magnetic field, a means for generating a gradient magnetic field, a means for generating a high-frequency pulse for causing nuclear magnetic resonance in atomic nuclei of atoms constituting a tissue of a subject, and the nucleus. A high frequency receiving coil which is the signal detecting means of the nuclear magnetic resonance imaging apparatus, which comprises a nuclear magnetic resonance signal detecting means for detecting a signal by magnetic resonance and an arithmetic means for performing image reconstruction using the nuclear magnetic resonance signal. The mounting of this high-frequency receiving coil on the subject is
In a receiving coil for a nuclear magnetic resonance imaging apparatus which is capable of closely contacting by connecting a connector, the connector is made of a material containing no magnetic substance, and a plating containing no magnetic substance is applied. Receiver coil for magnetic resonance imaging.
JP1989020271U 1989-02-27 1989-02-27 Receiver coil for nuclear magnetic resonance imaging Expired - Lifetime JPH0630165Y2 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP1989020271U JPH0630165Y2 (en) 1989-02-27 1989-02-27 Receiver coil for nuclear magnetic resonance imaging

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
JP1989020271U JPH0630165Y2 (en) 1989-02-27 1989-02-27 Receiver coil for nuclear magnetic resonance imaging

Publications (2)

Publication Number Publication Date
JPH02111405U JPH02111405U (en) 1990-09-06
JPH0630165Y2 true JPH0630165Y2 (en) 1994-08-17

Family

ID=31236498

Family Applications (1)

Application Number Title Priority Date Filing Date
JP1989020271U Expired - Lifetime JPH0630165Y2 (en) 1989-02-27 1989-02-27 Receiver coil for nuclear magnetic resonance imaging

Country Status (1)

Country Link
JP (1) JPH0630165Y2 (en)

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS62172940A (en) * 1986-01-24 1987-07-29 株式会社東芝 Magnetic resonance imaging apparatus
JPS63146612U (en) * 1987-03-16 1988-09-27

Also Published As

Publication number Publication date
JPH02111405U (en) 1990-09-06

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