JPS6096236A - High-frequency magnetic field generator for nuclear magnetic resonance imaging equipment - Google Patents
High-frequency magnetic field generator for nuclear magnetic resonance imaging equipmentInfo
- Publication number
- JPS6096236A JPS6096236A JP58204325A JP20432583A JPS6096236A JP S6096236 A JPS6096236 A JP S6096236A JP 58204325 A JP58204325 A JP 58204325A JP 20432583 A JP20432583 A JP 20432583A JP S6096236 A JPS6096236 A JP S6096236A
- Authority
- JP
- Japan
- Prior art keywords
- magnetic field
- frequency magnetic
- subject
- resonance imaging
- field generator
- 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
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- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.
Description
【発明の詳細な説明】
〔発明の利用分野〕
本発明は、生体からの生化学的情報を得るのに好適な核
磁気共鳴コンピュータ断層撮影装置（以下ＮＭＲ−Ｃ！
Ｔと称す）に使用する高周波磁場発生装置に関する。DETAILED DESCRIPTION OF THE INVENTION [Field of Application of the Invention] The present invention relates to a nuclear magnetic resonance computed tomography apparatus (hereinafter referred to as NMR-C!) suitable for obtaining biochemical information from a living body.
This invention relates to a high-frequency magnetic field generator used in
〔発明の背景〕 −
従来のＮＭＲ−ＣＴ用嵩高周波磁場発生装置、仰臥した
被検者を収容する枠体内に高周波磁場発生コイルを支持
する円筒形の支持体を形成し、この支持体内に被検者の
頭部を挿入できるようにしていた。そして、高周波磁場
発生コイルは、被検者の上下方向の前記支持体の外面に
設けるようになっていた。この高筒波磁場発生コイルは
、被検者に核磁気共鳴を生起させるもので、占積率（コ
イル内断面積に占める被検体の断面積の割合）ηが核磁
気共鳴の測定精度に犬きく影響する。すなわち、詳細が
ＪＯＵＲＮＡＬ ＯＦ ＭＡＧＮＥＴＩＣＲＥ８ＯＮＡ
Ｎ（Ｊ２４．７−８５（１９７６）、Ｐ、７１ Ｔｈｅ
Ｓｌｇｎａｌ−ｔｏ−Ｎｏ１ｓｅ Ｒａｔｉｏ ｏｆ
ｔｈｅ ＮｕｃｌｅａｒＭａｇｎｅｔｉｃ Ｒｅｓ＋ｏ
ｎａｎｃｅ ｌＥｘｐｅｒｉｍｅｎｔ、 Ｄ＋ ＬＨＯ
ＵＬＴ ＡＮＤ Ｒ，Ｅ、ＲＩＣＨＡＲＤ８著に記述さ
れているように、９０度パルス後の８／Ｎ比Ｆ ｒ Ｉ
ｎ １が次式によね与えられる。[Background of the Invention] - A conventional bulky high-frequency magnetic field generator for NMR-CT includes a cylindrical support that supports a high-frequency magnetic field generating coil within a frame that accommodates a supine subject, and a cylindrical support that supports a high-frequency magnetic field generating coil. It was designed so that the examiner's head could be inserted into it. The high-frequency magnetic field generating coil is provided on the outer surface of the support in the vertical direction of the subject. This high cylindrical wave magnetic field generating coil generates nuclear magnetic resonance in the subject, and the space factor (ratio of the cross-sectional area of the subject to the cross-sectional area within the coil) η is close to the measurement accuracy of nuclear magnetic resonance. have a strong influence. In other words, the details are JOURNAL OF MAGNETICRE8ONA
N (J24.7-85 (1976), P, 71 The
Slgnal-to-No1se Ratio of
the Nuclear Magnetic Res+o
nance lExperiment, D+ LHO
8/N ratio F r I after 90 degree pulse as described in ULT AND R,E, RICHARD8
n 1 is given by the following equation.
Ｆｒｍｇ−にηＭｏ（μｏＱωｏＶ−／４ＦｔＴ、Δｆ
）Ｉ／２したがって、ＳＺＮ比は占積率ηに比例するた
め、ＮＭＩ（−Ｃ’ｌ’により高感度の画像を得るため
には、占積率ηをできるだけ大きくとる必要がある。こ
の占積率ηを向上させるためには、断層像を得る部位に
高周波磁場発生コイルをできるだけ接近させる必要があ
る。そこで、従来のＮ Ｍ Ｌ（−ＣＴ用扁周波磁場発
生装置においては、高周波磁場発生コイルを支持してい
る支持体の径をできるだけ小さくしていた。このため、
被検者（被検体）の頭部は支持体内に挿入することがで
きるが、頭部より幅の広い肩部を支持体内に挿入するこ
とができない。そこで、被検者の頭部から頚部にかけて
の去状または冠状の断層像を得る場合には、支持体の一
部を切欠いて被検者の肩部を支持体の中に喰い込ませる
ような構造にし、被検者のノ一部を支持体から食み出さ
せた状態において断層１象を得ていた。しかし、被検者
のを椎部位の断層像を得る場合には、被検者を円筒状の
支持体内に挿入する必要があり、このような構造の支持
体においてはを椎部位の断層１象を得ることができない
。そして、支持体を被検者が完全に挿入できる内径を有
するようにすると、高周波磁場発生コイルの占積率が低
下し、鮮明な断層像を得ることができない欠点を有して
いる。Frmg− to ηMo(μoQωoV−/4FtT, Δf
) I/2 Therefore, since the SZN ratio is proportional to the space factor η, in order to obtain a highly sensitive image with NMI(-C'l'), it is necessary to make the space factor η as large as possible. In order to improve the product moment η, it is necessary to bring the high-frequency magnetic field generating coil as close as possible to the site where the tomographic image is obtained. The diameter of the support supporting the coil was made as small as possible.
Although the head of the subject (subject) can be inserted into the support, the shoulders, which are wider than the head, cannot be inserted into the support. Therefore, when obtaining a cross-sectional or coronal tomographic image from the head to the neck of a subject, it is necessary to cut out a part of the support and dig the shoulders of the subject into the support. A tomographic image was obtained with a part of the subject protruding from the support. However, when obtaining a tomographic image of a vertebral region of a subject, it is necessary to insert the subject into a cylindrical support, and in a support with such a structure, one tomographic image of the vertebral region can be obtained. can't get it. If the support body is made to have an inner diameter that allows the subject to completely insert it, the space factor of the high-frequency magnetic field generating coil decreases, and a clear tomographic image cannot be obtained.
本発明は、高感度の断層像を得ることができる核磁気共
鳴映像装置用高周波磁場発生装置を提供することを目的
とする。SUMMARY OF THE INVENTION An object of the present invention is to provide a high-frequency magnetic field generator for a nuclear magnetic resonance imaging apparatus that can obtain tomographic images with high sensitivity.
本発明は、一対の高周波磁場発生コイルをそれぞれ支持
する一対の支持体を、被検体を収容する枠体内に設け、
被検者を前記一対の支持体間に挿入できるようにし、高
周波Ｍｉ場発生コイルの占積率を向上させることにより
、高感度の断層像を得ることができるように構成したも
のである。The present invention provides a pair of supports each supporting a pair of high-frequency magnetic field generating coils within a frame housing a subject,
The present invention is configured so that a highly sensitive tomographic image can be obtained by allowing the subject to be inserted between the pair of supports and by improving the space factor of the high-frequency Mi field generating coil.
本発明に係る核磁気共鳴映像装置用高周波磁場発生装置
の好ましい実施例を添付図面に従って詳説する。DESCRIPTION OF THE PREFERRED EMBODIMENTS A preferred embodiment of a high-frequency magnetic field generator for a nuclear magnetic resonance imaging apparatus according to the present invention will be described in detail with reference to the accompanying drawings.
第１図は、本発明に係る核磁気共鳴映像装置用高周波磁
場発生装置の正面図である。第１図において被検者１０
が貫入できる枠体１２は、静磁場を発生させる直感コイ
ル１４に挿入、引き抜き自在となっている。この枠体１
２の内部は、磁場空間１６を構成しており、高周波磁場
発生コイル透明塩化ビニール、アルリル等の平板状の透
明体からなる支持板２５と腕２６とからなっている。FIG. 1 is a front view of a high-frequency magnetic field generator for a nuclear magnetic resonance imaging apparatus according to the present invention. In Figure 1, subject 10
The frame body 12 into which the magnetic field can be penetrated can be inserted into and pulled out from the intuition coil 14 that generates a static magnetic field. This frame 1
The interior of 2 constitutes a magnetic field space 16, which is made up of a high-frequency magnetic field generating coil, a support plate 25 made of a flat transparent material such as transparent vinyl chloride, aryl, etc., and an arm 26.
被検者１０は、第２図に示すように天板２４上に仰臥さ
せられ、一対の支持体２０．２０間に挿入できるように
なっている。The subject 10 is placed supine on the top plate 24, as shown in FIG. 2, and can be inserted between a pair of supports 20 and 20.
上下の支持体２０は、第３図および第４図に示すように
それぞれ４本の腕２６を介して枠体１２の内面に取り付
けられている。この腕２６は、伸縮自在に構成されてお
り、油圧駆動装置等によね一対の高周波磁場発生コイル
１８間の距離を自由に変えることができるようになって
いる。そして、同調回路２２には同調ツマミ２８が取り
付けられている。この同調ツマミ２８には、高周波磁場
発生コイルの移動位置に対応した目盛が付けられている
。すなわち、この目盛は、予め測定によって得た核磁気
共鳴周波数における同調と整合がとれる同調ツマミ２８
の回転角度を目盛ったものである。したがって、高周波
磁場発生コイルの移動に伴う回路の同調は、同調ツマミ
２８を回転することにより図示しない可変コンデンサを
介して共鳴周波数における並列共娠状態を得る出力調整
をすることができる。The upper and lower supports 20 are each attached to the inner surface of the frame 12 via four arms 26, as shown in FIGS. 3 and 4. This arm 26 is configured to be extendable and retractable, so that the distance between the pair of high-frequency magnetic field generating coils 18 can be freely changed by a hydraulic drive device or the like. A tuning knob 28 is attached to the tuning circuit 22. This tuning knob 28 is provided with a scale corresponding to the moving position of the high frequency magnetic field generating coil. That is, this scale is a tuning knob 28 that can be matched with the tuning at the nuclear magnetic resonance frequency obtained by measurement in advance.
It is a scale of rotation angle. Therefore, the tuning of the circuit accompanying the movement of the high-frequency magnetic field generating coil can be performed by rotating the tuning knob 28 and adjusting the output to obtain a parallel coexistence state at the resonant frequency via a variable capacitor (not shown).
が形成してあり、高周波磁場発生コイル１８を設けた枠
体１２を容易に電磁コイル１４内に装着し、また取り外
すことができるようになっている。電磁コイル１４内に
装着された枠体１２は、ねじ止、ワンタッチ・クランプ
等の適当な手段により固定される。is formed, so that the frame 12 provided with the high frequency magnetic field generating coil 18 can be easily attached to and removed from the electromagnetic coil 14. The frame 12 mounted within the electromagnetic coil 14 is fixed by suitable means such as screwing or one-touch clamping.
上記の如く構成した実施例にあっては、被検者が第２図
に示す如く天板２４上に仰臥させられ、一対の支持体２
０間に挿入される。そして被検者１０の高さの相違によ
り腕２６を伸縮させ、高周波磁場発生コイル１８を被検
者に近接して配置することができる。この結果占積率η
が向上し、被検者のすべての位置における高感度な断層
映像を得ることができる。したがって、被検者のを椎の
去状および冠状の断層像の感度を向上することができ、
Ｘ線ＣＴによっては原理的に断層像を得ることが不可能
であり、従来のＮＭＲ−ＣＴにおいても感度の点におい
て無理であったを椎内部の鮮明な断層像を得ることがで
きる。また、本実施例においては、枠体１２に案内溝３
２を形成したことにより、電磁コイル１４内に高周波磁
場発生コイル１８を容易に着脱でき、その装置の再現性
も向上する。しかも、支持体２０は、透明な物質をもっ
て形成されているため、被検者である患者に威圧感を与
えることがない。そして、支持体２０の中央部に窓３０
を形成したことにより、高周波磁場発生コイル１８を被
検者の顔面に近接させても被検者に息苦しさを感じさせ
ることがないとともに、被検者の呼吸による水滴が支持
体２０の内面に付着することを除去することができる。In the embodiment configured as described above, the subject is made to lie supine on the top plate 24 as shown in FIG.
Inserted between 0. The arm 26 can be expanded and contracted depending on the height of the subject 10, and the high-frequency magnetic field generating coil 18 can be placed close to the subject. As a result, the space factor η
It is possible to obtain highly sensitive tomographic images at all positions of the subject. Therefore, the sensitivity of vertebral and coronal tomograms of the subject can be improved,
In principle, it is impossible to obtain tomographic images using X-ray CT, and it is possible to obtain clear tomographic images of the interior of the vertebrae, which was impossible with conventional NMR-CT due to its sensitivity. Further, in this embodiment, the guide groove 3 is provided in the frame 12.
2, the high-frequency magnetic field generating coil 18 can be easily attached and detached within the electromagnetic coil 14, and the reproducibility of the device is also improved. Moreover, since the support body 20 is made of a transparent material, it does not give a feeling of intimidation to the patient who is the subject. A window 30 is provided in the center of the support 20.
By forming the high-frequency magnetic field generating coil 18 close to the subject's face, the subject will not feel suffocated, and water droplets caused by the subject's breathing will not reach the inner surface of the support 20. Adhering can be removed.
第６図は、支持体の他の実施例を示したものである。本
実施例において支持体２０は、窓３０を設けるかわりに
２つに分割されている。このように構成することにより
、被検者の圧迫感を一層取り除くことができる。FIG. 6 shows another embodiment of the support. In this embodiment, the support body 20 is divided into two parts instead of providing the window 30. With this configuration, the feeling of pressure on the subject can be further removed.
なお、前記実施例においては枠体１２を断面が楕円形の
場合を示したが、枠体１２の形状は元型でも多角形でも
よい。また、前記実施例においては支持体２０の支持板
２５は平板の場合について説明したが、支持板２５を湾
曲させることにより、占積率を一層向上することができ
る。さらに、前記実施例においては案内溝３２が１箇所
に設けられている場合を示したが、案内溝３２を２箇所
以上設けてもよい。そして、案内溝３２の形状も矩形に
限定されず台形、三角形、半月形等種々の形状をとるこ
とができる。なお、前記実施例においては、窓３０が上
側の支持板２５に形成された場合について説明したが、
下側の支持板にも窓を形成し、上側の支持板と共用化を
図るとともに、下側の窓から通信ケーブル等を引き出す
のに利用することができる。また、腕２６の数は、支持
体２０の固に方法により自由に変更することができる。In addition, although the case where the cross section of the frame 12 was elliptical was shown in the said Example, the shape of the frame 12 may be a prototype or a polygon. Furthermore, in the embodiment described above, the case where the support plate 25 of the support body 20 is a flat plate has been described, but by curving the support plate 25, the space factor can be further improved. Further, in the embodiment described above, the guide groove 32 is provided at one location, but the guide groove 32 may be provided at two or more locations. Further, the shape of the guide groove 32 is not limited to a rectangle, but can take various shapes such as a trapezoid, a triangle, and a half-moon shape. In the above embodiment, the case where the window 30 is formed on the upper support plate 25 has been described.
A window is also formed on the lower support plate so that it can be used in common with the upper support plate, and can also be used to pull out communication cables and the like through the lower window. Further, the number of arms 26 can be freely changed depending on the stiffness of the support body 20.
以上説明したように本発明によればＮＭＲ−ＣＴの断層
像の感度を同上することができる。As explained above, according to the present invention, it is possible to increase the sensitivity of NMR-CT tomographic images.
第１図は本発明に係る核磁気共鳴映像装置用高周波磁場
発生装置の実施例の正面図、第２図は前記実施例の断面
図、第３図および第４図は前記実施例の支持体の枠体へ
の取り付は状態を示す図、第５図は前記実施例の支持体
の詳細図、第６図は本発明に係る核磁気共鳴映像装置用
高周波磁場発生装置に使用する支持体の他の実施例を示
す図である。
１０・・・被検者、１２・・・枠体、１４・・・電磁コ
イル、（９）
１８・・・高周波磁場発生コイル、２０・・・支持体、
２６・・・腕。
代理人 弁理士 鵜沼辰之
（１０）
＄ １ 目
１４
第２ 口
／４FIG. 1 is a front view of an embodiment of a high-frequency magnetic field generator for a nuclear magnetic resonance imaging apparatus according to the present invention, FIG. 2 is a sectional view of the embodiment, and FIGS. 3 and 4 are a support of the embodiment. FIG. 5 is a detailed view of the support of the above embodiment, and FIG. 6 is a support used in the high-frequency magnetic field generator for nuclear magnetic resonance imaging apparatus according to the present invention. It is a figure which shows another Example of. DESCRIPTION OF SYMBOLS 10... Subject, 12... Frame body, 14... Electromagnetic coil, (9) 18... High frequency magnetic field generation coil, 20... Support body,
26...arm. Agent Patent attorney Tatsuyuki Unuma (10) $1 14th 2nd mouth/4
Claims (1)
する筒状の枠体と、この枠体内に相対して設けた一対の
高周波磁場コイルと、この一対の高周波磁場コイルを支
持している支持体とを有する核磁気共鳴映像装置用高周
波磁場発生装置において、前記支持体は、前記一対の高
周波磁場コイルの各々をそれぞれ独立して支持している
一対からなることを特徴とする核磁気共鳴映像装置用高
周波磁場発生装置。 ２、前記一対の支持体は、それぞれ支持体間の距離を調
節する間隔調節ａ構を備えたことを特徴とする特許請求
の範囲第１項記載の核磁気共鳴映像装置用高周波磁場発
生装置。[Claims] 1. A cylindrical frame for accommodating a subject provided in an electromagnetic coil for generating a static magnetic field, a pair of high-frequency magnetic field coils provided oppositely within this frame, and In a high-frequency magnetic field generator for a nuclear magnetic resonance imaging apparatus, the support body includes a support body supporting a high-frequency magnetic field coil, the support body consisting of a pair of supports each independently supporting each of the pair of high-frequency magnetic field coils. A high-frequency magnetic field generator for a nuclear magnetic resonance imaging apparatus, characterized in that: 2. The high-frequency magnetic field generator for a nuclear magnetic resonance imaging apparatus according to claim 1, wherein each of the pair of supports is provided with a spacing adjustment mechanism for adjusting the distance between the supports.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP58204325A JPS6096236A (en) | 1983-10-31 | 1983-10-31 | High-frequency magnetic field generator for nuclear magnetic resonance imaging equipment |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP58204325A JPS6096236A (en) | 1983-10-31 | 1983-10-31 | High-frequency magnetic field generator for nuclear magnetic resonance imaging equipment |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPS6096236A true JPS6096236A (en) | 1985-05-29 |
Family
ID=16488618
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP58204325A Pending JPS6096236A (en) | 1983-10-31 | 1983-10-31 | High-frequency magnetic field generator for nuclear magnetic resonance imaging equipment |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS6096236A (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS61117208U (en) * | 1984-12-31 | 1986-07-24 | ||
| JPH01166747A (en) * | 1987-12-23 | 1989-06-30 | Hitachi Medical Corp | Nuclear magnetic resonance imaging apparatus |
| JPH03231634A (en) * | 1990-02-07 | 1991-10-15 | Toshiba Corp | Coil apparatus for magnetic resonance imaging |
| JP2013545573A (en) * | 2010-12-16 | 2013-12-26 | コーニンクレッカ フィリップス エヌ ヴェ | Passive B1 field shimming |
-
1983
- 1983-10-31 JP JP58204325A patent/JPS6096236A/en active Pending
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS61117208U (en) * | 1984-12-31 | 1986-07-24 | ||
| JPH01166747A (en) * | 1987-12-23 | 1989-06-30 | Hitachi Medical Corp | Nuclear magnetic resonance imaging apparatus |
| JPH03231634A (en) * | 1990-02-07 | 1991-10-15 | Toshiba Corp | Coil apparatus for magnetic resonance imaging |
| JP2013545573A (en) * | 2010-12-16 | 2013-12-26 | コーニンクレッカ フィリップス エヌ ヴェ | Passive B1 field shimming |
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