JPS59216045A - Slanting magnetic field coil - Google Patents
Slanting magnetic field coilInfo
- Publication number
- JPS59216045A JPS59216045A JP58089147A JP8914783A JPS59216045A JP S59216045 A JPS59216045 A JP S59216045A JP 58089147 A JP58089147 A JP 58089147A JP 8914783 A JP8914783 A JP 8914783A JP S59216045 A JPS59216045 A JP S59216045A
- Authority
- JP
- Japan
- Prior art keywords
- coil
- magnetic field
- fixing device
- coils
- slanting
- 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.)
- Pending
Links
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
- G01R33/3854—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils means for active and/or passive vibration damping or acoustical noise suppression in gradient magnet coil systems
-
- 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
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Description
【発明の詳細な説明】
〔発明の利用分野〕
本発明は核磁気共鳴装置を用いた検量装置に使用する傾
斜磁場発生用コイルに係る。DETAILED DESCRIPTION OF THE INVENTION [Field of Application of the Invention] The present invention relates to a gradient magnetic field generating coil used in a calibration device using a nuclear magnetic resonance apparatus.
核磁気共S(以下NMR,と記す)は有機化合物の構造
解析や物性の研究に用いられ、重要な分析手段のひとつ
となっている。Nuclear magnetic resonance (hereinafter referred to as NMR) is used for structural analysis and research on physical properties of organic compounds, and has become one of the important analysis tools.
N M Rでは、照射観察面の決定のため磁場勾配を与
える必要があジ、この目的のため、静磁場の内側には、
X、Y、Zの各方向に任意の傾斜磁場を発生する3組の
コイルが取付けられている。これらのコイルを傾斜磁場
発生用コイルと称する。In NMR, it is necessary to provide a magnetic field gradient to determine the irradiation observation surface.For this purpose, inside the static magnetic field,
Three sets of coils are attached to generate arbitrary gradient magnetic fields in each of the X, Y, and Z directions. These coils are called gradient magnetic field generating coils.
これらX、Y、Z各コイルには、独立した専用電源が接
続され、制御された電流(一般には一定の間隔を有した
パルス電流)で励磁される。ところがこれらのコイルは
非常に強力な静磁場(一般に1500から3000ガウ
ス)内におかれるため、励磁電流が流れると、静磁場の
方向と当該コイルに流れる電流方向で決まる電源で駆動
する場合には瞬間的に強力な電磁力が作用するため、コ
イルが振動しそれがコイル固定装置を通して巻枠に伝え
られ騒音(打音)源となる。Each of these X, Y, and Z coils is connected to an independent dedicated power source and is excited with a controlled current (generally a pulsed current having a constant interval). However, since these coils are placed in a very strong static magnetic field (generally 1500 to 3000 Gauss), when an excitation current flows, when driven by a power source determined by the direction of the static magnetic field and the direction of the current flowing through the coil, Because a strong electromagnetic force is instantaneously applied, the coil vibrates, which is transmitted to the winding frame through the coil fixing device and becomes a source of noise.
第1図〜第3図は従来使用されていた傾斜磁場発生用コ
イルの構造を示す。第1図は軸方向(Z軸方向)視図で
あ10,11.12は図示の如く配置され、コイル固定
装置13で巻枠9に固定されている。第2図は第1図に
対応する断面図を示す。第3図はコイル固定部の詳細で
各コイルは非磁性体でアリ、かつ電気絶縁物(例えばフ
ェノール樹脂やFRP々ど)で作られたスペーサ13a
〜13dでその位置が規定さn固定ねじ14、固定ナツ
ト15で巻枠9に固定されている。この構造においては
巻枠9に対する各コイルの機械的な位置決めは問題ない
が電磁的な振動低減については問題がある。つ゛まシス
ペーサ13の保持距離が長くなるため中央部や先端部の
機械的な固定が不十分となり、これらの部分が振動を起
し騒音(打音)の原因となる。これらを防止するために
はスペーサ13の個数を増し各コイルと巻枠9の機械的
結合を強固なものにすれば良いが、構造が複雑となり、
部品精度の向上が必要となるなど、製作、組立工数の増
加を招き問題があった。1 to 3 show the structure of a conventionally used gradient magnetic field generating coil. FIG. 1 is an axial (Z-axis) view, and 10, 11, and 12 are arranged as shown and fixed to the winding frame 9 by a coil fixing device 13. FIG. 2 shows a cross-sectional view corresponding to FIG. Figure 3 shows the details of the coil fixing part, and each coil is made of non-magnetic material and has a spacer 13a made of electrical insulator (for example, phenol resin or FRP).
Its position is defined by 13d, and it is fixed to the winding frame 9 with a fixing screw 14 and a fixing nut 15. In this structure, there is no problem in mechanically positioning each coil with respect to the winding frame 9, but there is a problem in reducing electromagnetic vibration. However, since the holding distance of the spacer 13 becomes long, the mechanical fixation of the central part and the tip part becomes insufficient, and these parts vibrate, causing noise (hitting sound). In order to prevent these problems, it is possible to increase the number of spacers 13 and strengthen the mechanical connection between each coil and the winding frame 9, but this increases the complexity of the structure.
There were problems, such as the need to improve the accuracy of parts, which led to an increase in manufacturing and assembly man-hours.
したがって本NMRは人体の測定を目的とし1被検前者
は傾斜磁場の内部に入ることになるため、これらの打音
が発生すると心理的な圧迫感を与える原因となシ好まし
くない。Therefore, since this NMR is aimed at measuring the human body and the subject is placed inside a gradient magnetic field, the generation of these tapping sounds is undesirable as it gives a psychological feeling of pressure.
本発明は騒音打音が発生することのない傾斜磁場コイル
を提供するにある。The object of the present invention is to provide a gradient magnetic field coil that does not generate noise or hammering sounds.
このような目的を達成するために、本発明は、核磁気共
鳴装置を用いた検査装置に使用される傾斜磁場発生用コ
イルにおいて、巻枠、コイル固定装置、コイル間に適当
な弾性を有するバッキングを介在させ、巻枠、コイル固
定装置、コイル相互間の空間を適当な弾性を有する充填
物で充填したものである。In order to achieve such an object, the present invention provides a winding frame, a coil fixing device, and a backing having appropriate elasticity between the coils in a gradient magnetic field generating coil used in an inspection device using a nuclear magnetic resonance apparatus. The space between the winding frame, coil fixing device, and coils is filled with a filler having appropriate elasticity.
以下本発明の一実施例を図面を用いて説明する。 An embodiment of the present invention will be described below with reference to the drawings.
第4図はNMRの構成を示す。制御装置1は、各装置へ
種々の命令を一定のタイミングで出力するようになって
いる。高周波パルス発生器2の出力は電力増巾器3で増
巾されコイル4を励振するようになっている。コイル4
は受信コイルを兼用しており、信号成分は増巾器5を通
シ、検波器6で検波された後、信号処理装置7で画像に
変換されるようになっている。傾斜磁場発生コイル8は
、巻枠9とZ方向コイル10とその外側に互いに直交し
て配置されるX方向コイル11.Y方向コイル12から
成シそれぞれ励振電源14で駆動されるようになってい
る。静磁場の発生はコイル15で行い励振電源16で駆
動されるようになっている。被検査者17はこれらの磁
石の中心部におかれる。FIG. 4 shows the configuration of NMR. The control device 1 is configured to output various commands to each device at a constant timing. The output of the high frequency pulse generator 2 is amplified by a power amplifier 3 to excite a coil 4. coil 4
also serves as a receiving coil, and the signal components are passed through an amplifier 5, detected by a detector 6, and then converted into an image by a signal processing device 7. The gradient magnetic field generating coil 8 includes a winding frame 9, a Z-direction coil 10, and an X-direction coil 11. Each of the Y-direction coils 12 is driven by an excitation power source 14. A static magnetic field is generated by a coil 15 and driven by an excitation power source 16. The subject 17 is placed at the center of these magnets.
第5図、第6図は傾斜@場発生用コイルの基本構造を示
す。第5図はZ方向コイルloの取付を示す。10は巻
枠9の両端部に円周方向に巻かれた2組のコイルから成
シ、端子・10′は各コイルの端末に接続され外部配線
との結合を行っている。Figures 5 and 6 show the basic structure of the gradient @ field generating coil. FIG. 5 shows the installation of the Z-direction coil lo. Reference numeral 10 consists of two sets of coils wound in the circumferential direction at both ends of the winding frame 9, and terminals 10' are connected to the terminals of each coil for coupling with external wiring.
第6図はX方向コイル11及びY方向コイル12の取付
を示す。11及び12は図示のような鞍形のコイルで1
0の外側に重ね、更に機械的に90度ずらせて取付けら
れている。端子11′。FIG. 6 shows the installation of the X-direction coil 11 and the Y-direction coil 12. 11 and 12 are saddle-shaped coils as shown in the figure.
It is mounted on the outside of the 0 and mechanically shifted by 90 degrees. Terminal 11'.
12′は各コイルの端末に接続されている。12' is connected to the terminal of each coil.
第7図は軸方向視図、第8図は断面図、第9図はコイル
固定部の詳細図を示す。第1図ないし第3図と同符号の
ものは同材料を示している。FIG. 7 is an axial view, FIG. 8 is a sectional view, and FIG. 9 is a detailed view of the coil fixing part. The same reference numerals as in FIGS. 1 to 3 indicate the same materials.
第7図、第8図において、10,11.12はコイル固
定装置16で巻枠9に固定された後、適当な弾性を有す
る充填接着剤17で固化接着されている。In FIGS. 7 and 8, coils 10, 11, and 12 are fixed to the winding frame 9 by a coil fixing device 16, and then hardened and bonded with a filler adhesive 17 having appropriate elasticity.
第9図はコイル固定部の詳細でコイル10゜11.12
はその上下に適当な弾性を有するバッキング(例えばゴ
ムなど)16a、16bをはさみ、スペーサ16C,1
6d及び14.15で9に固定される。Figure 9 shows details of the coil fixing part, coil 10° 11.12
sandwich backings 16a and 16b having appropriate elasticity (for example, rubber) on the upper and lower sides, and spacers 16C and 1
6d and fixed at 9 at 14.15.
このような構造によれば各コイルの振動は16a。 According to this structure, the vibration of each coil is 16a.
16b、17で規制、減衰させられるため9に伝逐され
る振動の強度を著しく低下させ得る。またコイル固定部
の部品数も減少し、組立工数の増加もなく低騒音の傾斜
磁場発生用コイルを得ることができる。Since the vibrations 16b and 17 are regulated and attenuated, the intensity of the vibration transmitted to 9 can be significantly reduced. Furthermore, the number of parts for the coil fixing part is reduced, and a low-noise gradient magnetic field generating coil can be obtained without increasing the number of assembly steps.
第1図ないし第3図は、それぞれ従来の傾斜磁場コイル
の一例を示す軸方向視図、断面図、コイル固定部詳細図
、第4図は本発明による傾斜磁場コイルが適用される核
磁気共鳴装置を示す概略図、第5図および第6図は本発
明による傾斜磁場コイルの基本構造を示す図、第7図な
いし第9図はそれぞれ本発明による傾斜磁場コイルの一
実施例を示す軸方同視図、断面図、コイル固定部詳細図
である。
1・・・制御装置、2・・・高周波パルス発生器、3・
・・電力増[1]器、4・・・コイル、5・・・増巾器
、6・・・検波器、7・・・18号処理装置、8・・・
傾斜磁場発生用コイル、9・・・巻枠、10・・・Z方
向コイル、10′・・・端子、11・・・X方向コイル
、11′・・パ端子、12・・・Y方向コイル、12′
・・・端子、13・・・コイル固定装置、13a・・・
スペーサ、13b・・・スペーサ、13C・・・スペー
サ、13d・・・スペーサ、14・・・[lネL、、1
5・・・固定ナツト、16・・・コイル固定装置、16
a・・・バッキング、16b・・・バッキング、16c
・・・スペーサ、16d・・・スペーサ、17・・・充
填接着剤。
代理人 弁理士 高橋明夫
僧1(2) 弔2目
弔3図1 to 3 are an axial view, a sectional view, and a detailed view of a coil fixing part showing an example of a conventional gradient magnetic field coil, respectively, and FIG. 4 is a nuclear magnetic resonance to which a gradient magnetic field coil according to the present invention is applied. 5 and 6 are diagrams showing the basic structure of the gradient magnetic field coil according to the present invention, and FIGS. 7 to 9 are axial diagrams each showing an embodiment of the gradient magnetic field coil according to the present invention. They are a perspective view, a sectional view, and a detailed view of a coil fixing part. 1... Control device, 2... High frequency pulse generator, 3.
... Power booster [1], 4... Coil, 5... Amplifier, 6... Detector, 7... No. 18 processing device, 8...
Gradient magnetic field generation coil, 9... Winding frame, 10... Z direction coil, 10'... terminal, 11... X direction coil, 11'... Pa terminal, 12... Y direction coil , 12'
...Terminal, 13...Coil fixing device, 13a...
Spacer, 13b...Spacer, 13C...Spacer, 13d...Spacer, 14...[lneL,,1
5... Fixing nut, 16... Coil fixing device, 16
a...Backing, 16b...Backing, 16c
... Spacer, 16d... Spacer, 17... Filling adhesive. Proxy Patent Attorney: Priest Akio Takahashi 1 (2) Funeral 2nd Funeral 3rd Illustration
Claims (1)
磁場発生用コイルにおいて、巻枠、コイル固定装置、コ
イル間に適当な弾性を有するバッキングを介在式せ、巻
枠、コイル固定装置、コイル相互間の空間を適当な弾性
を有・する充填物で充填したことを特徴とする傾斜磁場
コイル。1. In a gradient magnetic field generating coil used in an inspection device using a nuclear magnetic resonance apparatus, a winding frame, a coil fixing device, and a backing having appropriate elasticity are interposed between the coils, and the winding frame, coil fixing device, A gradient magnetic field coil characterized in that the space between the coils is filled with a filler having appropriate elasticity.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP58089147A JPS59216045A (en) | 1983-05-23 | 1983-05-23 | Slanting magnetic field coil |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP58089147A JPS59216045A (en) | 1983-05-23 | 1983-05-23 | Slanting magnetic field coil |
Publications (1)
Publication Number | Publication Date |
---|---|
JPS59216045A true JPS59216045A (en) | 1984-12-06 |
Family
ID=13962751
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP58089147A Pending JPS59216045A (en) | 1983-05-23 | 1983-05-23 | Slanting magnetic field coil |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS59216045A (en) |
Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS61278741A (en) * | 1985-06-04 | 1986-12-09 | Mitsubishi Electric Corp | Inclining magnetic field coil for nuclear magnetic resonance image diagnosis system |
JPS61279238A (en) * | 1985-06-06 | 1986-12-10 | 三菱電機株式会社 | Inclined magnetic field coil for nuclear magnetic resonance imaging diagnostic apparatus |
JPS63209637A (en) * | 1987-02-27 | 1988-08-31 | 株式会社東芝 | Magnetic resonance imaging apparatus |
JPS6470032A (en) * | 1987-08-19 | 1989-03-15 | Philips Nv | Inclined coil system for magnetic vibration apparatus |
JPH01503359A (en) * | 1987-06-02 | 1989-11-16 | ジエネラル エレクトリツク セージェーエール エス.アー. | Fixing and adjusting device for mandrel that holds gradient coils |
US4954781A (en) * | 1988-06-14 | 1990-09-04 | Kabushiki Kaisha Toshiba | Nuclear magnetic resonance imaging apparatus with reduced acoustic noise |
JPH02141410U (en) * | 1989-04-28 | 1990-11-28 | ||
US5256969A (en) * | 1989-12-04 | 1993-10-26 | Hitachi, Ltd. | Gradient magnetic field coil for magnetic resonance imaging system |
US5309105A (en) * | 1991-07-10 | 1994-05-03 | Hitachi, Ltd. | Vibration reduction system for magnetic-resonance imaging apparatus |
US5331281A (en) * | 1991-09-04 | 1994-07-19 | Hitachi, Ltd. | Gradient magnetic field generating coil assembly of magnetic resonance imaging apparatus |
JP2004173722A (en) * | 2002-11-25 | 2004-06-24 | Hitachi Ltd | Magnetic resonance imaging device |
EP2388610A1 (en) * | 2010-05-20 | 2011-11-23 | Koninklijke Philips Electronics N.V. | Magnetic Resonance Imaging Gradient Coil, Magnet Assembly, and System |
-
1983
- 1983-05-23 JP JP58089147A patent/JPS59216045A/en active Pending
Cited By (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS61278741A (en) * | 1985-06-04 | 1986-12-09 | Mitsubishi Electric Corp | Inclining magnetic field coil for nuclear magnetic resonance image diagnosis system |
JPS61279238A (en) * | 1985-06-06 | 1986-12-10 | 三菱電機株式会社 | Inclined magnetic field coil for nuclear magnetic resonance imaging diagnostic apparatus |
JPH0370490B2 (en) * | 1985-06-06 | 1991-11-07 | Mitsubishi Electric Corp | |
JPS63209637A (en) * | 1987-02-27 | 1988-08-31 | 株式会社東芝 | Magnetic resonance imaging apparatus |
JPH01503359A (en) * | 1987-06-02 | 1989-11-16 | ジエネラル エレクトリツク セージェーエール エス.アー. | Fixing and adjusting device for mandrel that holds gradient coils |
JPS6470032A (en) * | 1987-08-19 | 1989-03-15 | Philips Nv | Inclined coil system for magnetic vibration apparatus |
US4954781A (en) * | 1988-06-14 | 1990-09-04 | Kabushiki Kaisha Toshiba | Nuclear magnetic resonance imaging apparatus with reduced acoustic noise |
JPH02141410U (en) * | 1989-04-28 | 1990-11-28 | ||
US5256969A (en) * | 1989-12-04 | 1993-10-26 | Hitachi, Ltd. | Gradient magnetic field coil for magnetic resonance imaging system |
US5309105A (en) * | 1991-07-10 | 1994-05-03 | Hitachi, Ltd. | Vibration reduction system for magnetic-resonance imaging apparatus |
US5331281A (en) * | 1991-09-04 | 1994-07-19 | Hitachi, Ltd. | Gradient magnetic field generating coil assembly of magnetic resonance imaging apparatus |
JP2004173722A (en) * | 2002-11-25 | 2004-06-24 | Hitachi Ltd | Magnetic resonance imaging device |
EP2388610A1 (en) * | 2010-05-20 | 2011-11-23 | Koninklijke Philips Electronics N.V. | Magnetic Resonance Imaging Gradient Coil, Magnet Assembly, and System |
WO2011145029A1 (en) | 2010-05-20 | 2011-11-24 | Koninklijke Philips Electronics N.V. | Magnetic resonance imaging gradient coil, magnet assembly, and system |
CN102906588A (en) * | 2010-05-20 | 2013-01-30 | 皇家飞利浦电子股份有限公司 | Magnetic resonance imaging gradient coil, magnet assembly, and system |
CN102906588B (en) * | 2010-05-20 | 2015-12-02 | 皇家飞利浦电子股份有限公司 | Magnetic resonance imaging gradient coil, magnet assembly and system |
US9274192B2 (en) | 2010-05-20 | 2016-03-01 | Koninklijke Philips N.V. | Magnetic resonance imaging gradient coil, magnet assembly, and system |
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