JPH0318349A - Magnetic resonance diagnosing device - Google Patents
Magnetic resonance diagnosing deviceInfo
- Publication number
- JPH0318349A JPH0318349A JP1152104A JP15210489A JPH0318349A JP H0318349 A JPH0318349 A JP H0318349A JP 1152104 A JP1152104 A JP 1152104A JP 15210489 A JP15210489 A JP 15210489A JP H0318349 A JPH0318349 A JP H0318349A
- Authority
- JP
- Japan
- Prior art keywords
- coil
- magnetic resonance
- signal
- storage tube
- subject
- 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.)
- Granted
Links
- 238000013480 data collection Methods 0.000 abstract 1
- 238000002595 magnetic resonance imaging Methods 0.000 description 5
- 230000003068 static effect Effects 0.000 description 4
- 230000000694 effects Effects 0.000 description 3
- 238000001727 in vivo Methods 0.000 description 3
- 239000003990 capacitor Substances 0.000 description 2
- 238000001514 detection method Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000005284 excitation Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 238000004458 analytical method Methods 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 230000008878 coupling Effects 0.000 description 1
- 238000010168 coupling process Methods 0.000 description 1
- 238000005859 coupling reaction Methods 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 230000001939 inductive effect Effects 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 230000000877 morphologic effect Effects 0.000 description 1
- 210000004165 myocardium Anatomy 0.000 description 1
- 238000001208 nuclear magnetic resonance pulse sequence Methods 0.000 description 1
- 230000036285 pathological change Effects 0.000 description 1
- 231100000915 pathological change Toxicity 0.000 description 1
- 239000003507 refrigerant Substances 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 210000000689 upper leg Anatomy 0.000 description 1
Landscapes
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Description
【発明の詳細な説明】
[発明の目的]
(産業上の利用分野〉
本発明は、被検体の様々な検査部位から磁気共鳴信号(
以下、MR信号という〉を収集し診断に利用する磁気共
鳴診断装置に関し、特に、前記MR信号を送信ないし受
信検出するための高周波コイル(以下、RFコイルとい
う〉の改良に関する。[Detailed Description of the Invention] [Object of the Invention] (Industrial Application Field) The present invention provides magnetic resonance signals (
The present invention relates to a magnetic resonance diagnostic apparatus that collects MR signals and utilizes them for diagnosis, and particularly relates to improvements in a high frequency coil (hereinafter referred to as RF coil) for transmitting or receiving and detecting the MR signals.
(従来の技術)
近年、この種の磁気共鳴診断装置が医療診断装置におい
て果たす役割は大きい。(Prior Art) In recent years, this type of magnetic resonance diagnostic apparatus has played a large role in medical diagnostic equipment.
すなわち、数百〜数千Gの靜磁場中に被検体を配置し、
これに線形勾配磁場を重ね、MR信号の強さとともにそ
の信号源の位置を得て画像化する周知の磁気共鳴イメー
ジング法や、生体中の特定部位(検査部位〉にある対象
核種の化学シフト情報を得るインビボ・スペクト口メト
リー(生体MR分析法)を用いれば、無侵襲で有用な形
態情報や病態変化データ等が得られるためである。That is, the subject is placed in a quiet magnetic field of several hundred to several thousand G,
The well-known magnetic resonance imaging method, in which a linear gradient magnetic field is superimposed on this to obtain the strength of the MR signal and the location of the signal source, is used to create an image, as well as information on the chemical shift of the target nuclide at a specific site in the living body (examination site). This is because if in vivo spectrostomiometry (biological MR analysis method) is used to obtain the following information, useful morphological information, pathological change data, etc. can be obtained non-invasively.
この種の磁気共鳴診断装置においては、RFパルスで励
起された検査部位から、微量なMR信号を無駄なく検出
して、より高いS/N比のMR信号を収集することが最
大の課題である。このため、MR信号を収集するための
RFコイルは、検査部位のできるだけ近傍に配設させる
ことが必要である。In this type of magnetic resonance diagnostic equipment, the biggest challenge is to efficiently detect minute amounts of MR signals from the examination site excited by RF pulses and to collect MR signals with a higher S/N ratio. . Therefore, it is necessary to arrange the RF coil for collecting MR signals as close as possible to the examination site.
前記インビボ スペクト口メトリイにおいても、検査部
位にRFコイルを近接させることが必要ではあるが、こ
のインビボ・スペクト口メトリイにおいては、検査部位
が被検体体内の特定の組織に限局して設定されることが
多いため、RFコイルとして表面コイルが用いられるこ
とが多い。すなわち、この表面コイルは、コイル直下の
ほぼ半球または円板型の部分のみからMR信号を収集で
きるもので、前記検査部位に対して一番近接するように
表面コイルを被検体の体表面に密接配置することで、あ
る程度高いS/N比のMR信号を収集できる。In the aforementioned in-vivo spectrostomiometry, it is necessary to bring the RF coil close to the test site, but in this in-vivo spectrostometry, the test site is set to be localized to a specific tissue within the subject's body. Therefore, surface coils are often used as RF coils. In other words, this surface coil is capable of collecting MR signals only from a roughly hemispherical or disc-shaped portion directly below the coil, and the surface coil is placed close to the body surface of the subject so as to be closest to the examination site. By arranging them, it is possible to collect MR signals with a relatively high S/N ratio.
(発明が解決しようとする課題)
しかしながら、例えば心筋等、体表面から比較的深部の
部位を検査部位とする際には、表面コイルを体表面に密
接配置しても、この配置位置直下の検査部位までの距離
が大きく、良好なS/N比のMR信号が得られないとい
う問題があった。(Problem to be Solved by the Invention) However, when a region relatively deep from the body surface is to be examined, such as the myocardium, even if the surface coil is placed closely to the body surface, the area directly under this placement position cannot be inspected. There was a problem in that the distance to the site was large and MR signals with a good S/N ratio could not be obtained.
本発明は従来のかかる問題点を解決するためになされた
ものであり、体表面から比較的深部の検査部位であって
も良好なS/N比のMR信号を得ることができる磁気共
鳴診断装置を提供することを目白勺とする。The present invention has been made to solve these conventional problems, and is a magnetic resonance diagnostic apparatus that can obtain MR signals with a good S/N ratio even for examination sites relatively deep from the body surface. Our goal is to provide the following.
[発明の槽戒]
(課題を解決するための手段〉
上記目的を達戒するために本発明にかかる磁気共鳴診断
装置においては、湾曲自在であるとともに微小な内外径
を有するコイル収納管と、このコイル収納管の一方の端
部開口からの突出自在にこのコイル収納管に収納される
第1のコイルと、この第1のコイルを用いて検査部位か
らの磁気共鳴信号を受信検出する手段と、を具備するこ
とを要旨としている。[Tank of the Invention] (Means for Solving the Problem) In order to achieve the above object, a magnetic resonance diagnostic apparatus according to the present invention includes a coil storage tube that is bendable and has a minute inner and outer diameter; a first coil housed in the coil housing tube such that it can freely protrude from an opening at one end of the coil housing tube; and means for receiving and detecting magnetic resonance signals from an examination site using the first coil. The main point is to have the following.
また、別の本発明は、湾曲自在であるとともに微小な内
外径を有するコイル収納管と、このコイル収納管の一方
の端部開口からの突出自在にこのコイル収納管に収納さ
れる第1のコイルと、この第1のコイルと誘導結合し得
る第2のコイルと、この第2のコイルを用いて検査部位
からの磁気共鳴信号を受信検出する手段と、を具備する
ことを要旨としている。Another aspect of the present invention provides a coil storage tube that is bendable and has a minute inner and outer diameter, and a first coil storage tube that is stored in the coil storage tube so as to be able to protrude from an opening at one end of the coil storage tube. The gist of the present invention is to include a coil, a second coil that can be inductively coupled to the first coil, and means for receiving and detecting magnetic resonance signals from an examination site using the second coil.
(作用〉 上述の楕戒によれば次のような作用を奏する。(effect) According to the above-mentioned elliptical precepts, the following effects are produced.
すなわち、前記コイル収納管は微小な内外径を有しかつ
第1のコイルを収納し得るものであり、このコイル収納
管をその一方の先端が被検体内の検査部位に位置するよ
うに被検体内に挿入し、その先端より第1のコイルを突
出させれば、この第1のコイルにより前記検査部位の磁
気共鳴信号を受信検出できるため、体表面から比較的深
部に位置する検査部位であっても、良好なS/N比のM
R信号を得ることができる。That is, the coil storage tube has a small inner and outer diameter and can accommodate the first coil, and the coil storage tube is inserted into the subject so that one end thereof is located at the examination site within the subject. If the first coil is inserted into the body and the first coil is protruded from the tip, the magnetic resonance signal of the test site can be received and detected by the first coil, so the test site can be located relatively deep from the body surface. M with good S/N ratio even if
An R signal can be obtained.
また、前記第1のコイルが前記被検体内検査部位で開か
れ配置された際に、第2のコイルを前記第1のコイルと
誘導結合可能に被検体外部に配置させれば、前記第1の
コイルが被検体内にあって良好に同調がとれない状況で
あっても、第2のコイルは被検体外にあって同調をとり
やすいため、第2のコイルにより被検体の磁気共鳴信号
を受信検出して、良好なS/N比のMR信号を得ること
ができる。Further, when the first coil is opened and placed at the examination site within the subject, the second coil may be placed outside the subject so as to be inductively coupled to the first coil. Even if the first coil is inside the subject and cannot be well tuned, the second coil is outside the subject and can easily be tuned, so the second coil can capture the subject's magnetic resonance signals. Through reception and detection, an MR signal with a good S/N ratio can be obtained.
(実施例〉
以下、本発明にかかる磁気共鳴診断装置を磁気共鳴イメ
ージング装置(以下、MRI装置という)に適用したー
実施例について、第1図ないし第4図を参照にしながら
説明する。(Example) Hereinafter, an example in which the magnetic resonance diagnostic apparatus according to the present invention is applied to a magnetic resonance imaging apparatus (hereinafter referred to as an MRI apparatus) will be described with reference to FIGS. 1 to 4.
第1図は、前記MHI装置の概略構戒を示している。こ
のMRI装置は、被検体Pを内部に収容できる構成がと
られるマグネットアセンブリとして、常電導または超電
導方式による静磁場コイル(靜磁場補正用シムコイルが
付加されていることもある。)1と、MR信号の誘起部
位の位置情報付与のための傾斜磁場を発生する傾斜磁場
コイル2と、励起用の回転高周波磁場を送信する図示し
ない送信コイルと、励起されたMR信号を受信検出する
後述の第IRFコイル(第1のコイル)3および第2R
Fコイル(第2のコイル)4とを具備している。FIG. 1 shows the general structure of the MHI device. This MRI apparatus includes a static magnetic field coil (sometimes a shim coil for quiet magnetic field correction is added) 1 using a normal conduction or superconducting method as a magnet assembly configured to accommodate a subject P therein, and an MR. A gradient magnetic field coil 2 that generates a gradient magnetic field for providing positional information of a signal-induced region, a transmitting coil (not shown) that transmits a rotating high-frequency magnetic field for excitation, and a later-described IRF that receives and detects the excited MR signal. Coil (first coil) 3 and second R
An F coil (second coil) 4 is provided.
また、電気系としては、以下のような構成になっている
。すなわち、静磁場コイル1が超電導方式であれば冷媒
の供給制御系を含むものであって、主として静磁場電源
の通電制御を行う静磁場制御系5、X軸,Y軸,Z軸傾
斜磁場電源6,7,8、送信器9、受信器10−所定の
パルスシーケンスを実施するシーケンサ11、これらを
制御するとともに検出信号の信号処理およびその表示を
行うコンピュータシステム12およびディスプレイ13
を具備している。The electrical system has the following configuration. That is, if the static magnetic field coil 1 is a superconducting type, it includes a refrigerant supply control system, a static magnetic field control system 5 that mainly controls the energization of the static magnetic field power source, and an X-axis, Y-axis, and Z-axis gradient magnetic field power source. 6, 7, 8, transmitter 9, receiver 10-sequencer 11 for implementing a predetermined pulse sequence, computer system 12 and display 13 for controlling these and for processing the detected signal and displaying it.
Equipped with:
補記第IRFコイル3は、第2図(a),(b)に示す
ように、小型のコンデンサ21にその両端を接続されて
ループ状を呈するとともに、細長く縮まることができる
等形状変化自在になされている。そして、この第IRF
コイル3は、湾曲自在であるとともに微小な内外径を有
しかつ両端部が解放されたコイル収納菅22に、このコ
イル収納管22の一方の端部開口〈図示せず〉における
操作によりもう一方の端部23の開口から突出自在に収
納されている。すなわち、第IRFコイル3は、前記コ
イル収納菅22が、被検体P外部より被検体P内に奥深
くあるいは長距離にわたって挿入されるように適宜設定
される長さを有するものであれば、その長さ以上の全長
を有するとともに湾曲自在かつ導電性であるコイル導入
部24の先端に形状自在に配設されるものである。Supplementary note: As shown in FIGS. 2(a) and 2(b), the IRF coil 3 has both ends connected to a small capacitor 21 to form a loop shape, and is also capable of changing its shape such that it can be contracted into a long and thin shape. ing. And this IRF
The coil 3 is inserted into a coil storage tube 22 which is bendable, has a small inner and outer diameter, and has both ends open, and is inserted into the coil storage tube 22 by operating an opening (not shown) at one end of the coil storage tube 22. It is housed in such a way that it can freely protrude from the opening of the end portion 23 of. That is, the IRF coil 3 has a length that is appropriately set so that the coil storage tube 22 is inserted deep into the subject P from outside the subject P or over a long distance. The coil introducing section 24 has a total length of more than 300 mm, is bendable, and is electrically conductive.
また、第IRFコイル3は、前記コンデンサ21ととも
に、使用する励起用の回転高周波磁場の周波数(共鳴周
波数)に対応する共振回路を形成していることが望まし
いが、上述のように形状自在であるため、また、後述す
る第2RFコイル4がより正確に前記共鳴周波数に対応
する共振回路を形戒する構成をとられるため、必ずしも
前記共鳴周波数に対応する共振回路を形戒している必要
はない。なお、前記コイル収納管22は、医療分野でカ
テーテルとして知られているプラスチック製あるいは金
属製の細管を用いることができる。Further, the IRF coil 3 preferably forms a resonant circuit corresponding to the frequency (resonance frequency) of the rotating high-frequency magnetic field for excitation used together with the capacitor 21, but as described above, the shape can be freely formed. Therefore, since the second RF coil 4, which will be described later, is configured to form a resonant circuit corresponding to the resonant frequency more accurately, it is not necessarily necessary to form a resonant circuit corresponding to the resonant frequency. . Note that the coil storage tube 22 may be a plastic or metal thin tube known as a catheter in the medical field.
また、前記第2RFコイル4は、前記第IRFコイル3
と誘導結合して、被検休Pの検査部位からMR信号を取
り出すためのもので、第3図に示すように、同調コンデ
ンサ26およびマッチングコンデンサ27と接続されて
おり、これらの要素により前記共鳴周波数に極力正確に
対応する共振回路を形成している。なお、符号28は同
軸ケーブルである。Further, the second RF coil 4 is the second IRF coil 3 .
This is for extracting the MR signal from the examination site of the patient P by inductive coupling with the patient P. As shown in FIG. A resonant circuit is formed that corresponds to the frequency as accurately as possible. In addition, the code|symbol 28 is a coaxial cable.
次に、本実施例の作用について説明する。Next, the operation of this embodiment will be explained.
まず、コイル収納管22の一方の端部開口でコイル導入
部24の端部を牽引する等してコイル収納管22に第I
RFコイル3を収納した状態で、コイル収納管22のも
う一方の端部23を太腿等の被検体Pの一部より挿入し
、この端部23を被検休Pの検査部位に向けて体内を通
過させる。この端部23が、検査部位、例えば心11P
Hまで達したことをX線診断装置等で確認したら、コイ
ル収納管22の手元側端部開口でコイル導入部24の端
部を押す等してコイル収納管22端部23から第IRF
コイル3を突出させる。First, the end of the coil introduction part 24 is pulled by the opening at one end of the coil storage tube 22, and the I
With the RF coil 3 stored, the other end 23 of the coil storage tube 22 is inserted through a part of the subject P such as the thigh, and this end 23 is directed toward the test site of the subject P. pass through the body. This end 23 is the test site, for example, the heart 11P.
After confirming that it has reached H using an X-ray diagnostic device, etc., push the end of the coil introduction part 24 with the proximal end opening of the coil storage tube 22 to remove the IRF from the end 23 of the coil storage tube 22.
Coil 3 is made to protrude.
次に、第2RFコイル4を、第IRFコイル3と誘導結
合可能に、心1iPHにある第IRFコイル3の被検体
P外側の対応する部位体表面に密接配置し、この第2R
Fコイル4により被検体Pの磁気共鳴信号を受信検出す
る。Next, the second RF coil 4 is closely arranged on the body surface of the corresponding part of the outside of the subject P of the second IRF coil 3 at the heart 1iPH so as to be inductively coupled to the second IRF coil 3.
The F coil 4 receives and detects the magnetic resonance signal of the subject P.
したがって、本実施例においては、コイル収納管22が
微小な内外径を有しており、血管等を通して体表面から
比較的深部に位置する検査部位へも第IRFコイル3を
挿入しやすく、また、第IRFコイル3が被検体P内に
あって良好に同調がとれない状況であっても、第2RF
コイル4は被検体P外にあって第IRFコイル3より正
確に共鳴周波数に対応する共振回路を形戒できるため、
検査部位にある第IRFコイル3と誘導結合する第2R
Fコイル4により、検査部位が体表面から比較的深部に
位置しても、MR信号を良好なS/N比で受信検出でき
、このため、データ収集時間も短縮される。Therefore, in this embodiment, the coil storage tube 22 has a small inner and outer diameter, which makes it easy to insert the IRF coil 3 into an examination site located relatively deep from the body surface through a blood vessel or the like. Even if the 2nd IRF coil 3 is inside the subject P and cannot be well tuned, the 2nd RF coil 3
Since the coil 4 is located outside the object P and can form a resonant circuit corresponding to the resonant frequency more accurately than the IRF coil 3,
2nd R inductively coupled with the 2nd IRF coil 3 located at the test site
The F coil 4 allows reception and detection of MR signals with a good S/N ratio even if the examination site is located relatively deep from the body surface, and therefore the data acquisition time is also shortened.
[発明の効果]
以上詳細に説明したように、本発明にかかる磁気共鳴診
断装置において、コイル収納管は微小な内外径を有しか
つ第1のコイルを収納し得るものであり、このコイル収
納管をその一方の先端が被検体内の検査部位に位置する
ように被検体内に挿入し、その先端より第1のコイルを
突出させれば、この第1のコイルにより前記検査部位の
磁気共鳴信号を受信検出できるため、体表面から比較的
深部に位置する検査部位であっても、良好なS/N比の
MR信号を得ることができる。[Effects of the Invention] As explained above in detail, in the magnetic resonance diagnostic apparatus according to the present invention, the coil storage tube has a minute inner and outer diameter and can accommodate the first coil. If the tube is inserted into the subject so that one end of the tube is located at the test site within the test subject, and a first coil protrudes from the end, this first coil will generate magnetic resonance at the test site. Since signals can be received and detected, an MR signal with a good S/N ratio can be obtained even for an examination site located relatively deep from the body surface.
また、前記第1のコイルが前記被検体内検査部位で突出
されて配置された際に、第2のコイルを前記第1のコイ
ルと誘導結合可能に被検体外部に配置させれば、前記第
1のコイルが被検体内にあって良好に同調がとれない状
況であっても、第2のコイルは被検体外部にあって同調
をとりやすいため、第2のコイルにより被検体の磁気共
鳴信号を検出して、良好なS/N比のMR信号を得るこ
とができる。Further, when the first coil is protruded and placed at the examination site within the subject, if the second coil is placed outside the subject so as to be inductively coupled to the first coil, Even if the first coil is inside the subject and cannot be well tuned, the second coil is outside the subject and can be easily tuned. can be detected and an MR signal with a good S/N ratio can be obtained.
第1図は本発明を適用し得るMRI装置の概略構成説明
図、第2図(a>,(b)それそれは第IRFコイルの
コイル収納管からの突出時およびコイル収納管への収納
時の各状態の一実施例を示す説明図、第3図は第IRF
コイルおよび第2RFコイルの一使用例を示す説明図で
ある。FIG. 1 is a schematic configuration explanatory diagram of an MRI apparatus to which the present invention can be applied, and FIG. 2 (a>, (b) shows the IRF coil when it is projected from the coil storage tube and when it is stored in the coil storage tube. An explanatory diagram showing an example of each state, FIG. 3 is an IRF
It is an explanatory view showing an example of use of a coil and a second RF coil.
Claims (2)
イル収納管と、このコイル収納管の一方の端部開口から
の突出自在にこのコイル収納管に収納される第1のコイ
ルと、この第1のコイルを用いて検査部位からの磁気共
鳴信号を受信検出する手段と、を具備することを特徴と
する磁気共鳴診断装置。(1) A coil storage tube that is bendable and has minute inner and outer diameters; a first coil that is stored in the coil storage tube so as to be able to protrude from one end opening of the coil storage tube; 1. A magnetic resonance diagnostic apparatus comprising: means for receiving and detecting magnetic resonance signals from an examination site using one coil.
イル収納管と、このコイル収納管の一方の端部開口から
の突出自在にこのコイル収納管に収納される第1のコイ
ルと、この第1のコイルと誘導結合し得る第2のコイル
と、この第2のコイルを用いて検査部位からの磁気共鳴
信号を受信検出する手段と、を具備することを特徴とす
る磁気共鳴診断装置。(2) a coil storage tube that is bendable and has a minute inner and outer diameter; a first coil that is stored in the coil storage tube such that it can protrude from an opening at one end of the coil storage tube; 1. A magnetic resonance diagnostic apparatus comprising: a second coil that can be inductively coupled to the first coil; and means for receiving and detecting magnetic resonance signals from an examination site using the second coil.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP1152104A JPH0318349A (en) | 1989-06-16 | 1989-06-16 | Magnetic resonance diagnosing device |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP1152104A JPH0318349A (en) | 1989-06-16 | 1989-06-16 | Magnetic resonance diagnosing device |
Publications (2)
Publication Number | Publication Date |
---|---|
JPH0318349A true JPH0318349A (en) | 1991-01-25 |
JPH0570459B2 JPH0570459B2 (en) | 1993-10-05 |
Family
ID=15533143
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP1152104A Granted JPH0318349A (en) | 1989-06-16 | 1989-06-16 | Magnetic resonance diagnosing device |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPH0318349A (en) |
Families Citing this family (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2905631A1 (en) * | 2007-12-21 | 2015-08-12 | T2 Biosystems, Inc. | Magnetic resonance system with implantable components and methods of use thereof |
-
1989
- 1989-06-16 JP JP1152104A patent/JPH0318349A/en active Granted
Also Published As
Publication number | Publication date |
---|---|
JPH0570459B2 (en) | 1993-10-05 |
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