JPH0451774Y2 - - Google Patents
Info
- Publication number
- JPH0451774Y2 JPH0451774Y2 JP9617688U JP9617688U JPH0451774Y2 JP H0451774 Y2 JPH0451774 Y2 JP H0451774Y2 JP 9617688 U JP9617688 U JP 9617688U JP 9617688 U JP9617688 U JP 9617688U JP H0451774 Y2 JPH0451774 Y2 JP H0451774Y2
- Authority
- JP
- Japan
- Prior art keywords
- coil
- cervical vertebrae
- subject
- magnetic field
- approximately
- 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
Links
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 claims description 9
- 229910052802 copper Inorganic materials 0.000 claims description 9
- 239000010949 copper Substances 0.000 claims description 9
- 239000004020 conductor Substances 0.000 claims description 6
- 230000003068 static effect Effects 0.000 claims description 6
- 239000011810 insulating material Substances 0.000 claims description 3
- 238000010586 diagram Methods 0.000 description 11
- 230000035945 sensitivity Effects 0.000 description 10
- 238000005481 NMR spectroscopy Methods 0.000 description 8
- 239000003990 capacitor Substances 0.000 description 8
- 210000001767 medulla oblongata Anatomy 0.000 description 6
- 238000003384 imaging method Methods 0.000 description 5
- 210000000115 thoracic cavity Anatomy 0.000 description 3
- 230000005540 biological transmission Effects 0.000 description 2
- 230000008878 coupling Effects 0.000 description 2
- 238000010168 coupling process Methods 0.000 description 2
- 238000005859 coupling reaction Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 229910052709 silver Inorganic materials 0.000 description 2
- 239000004332 silver Substances 0.000 description 2
- UFHFLCQGNIYNRP-UHFFFAOYSA-N Hydrogen Chemical compound [H][H] UFHFLCQGNIYNRP-UHFFFAOYSA-N 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000005536 corrosion prevention Methods 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 239000011888 foil Substances 0.000 description 1
- 229910052739 hydrogen Inorganic materials 0.000 description 1
- 239000001257 hydrogen Substances 0.000 description 1
- 238000009413 insulation Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 229920001296 polysiloxane Polymers 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
Landscapes
- Magnetic Resonance Imaging Apparatus (AREA)
Description
【考案の詳細な説明】
（産業上の利用分野）
本考案は、MRI（Magnetic Resonance
Imaging）装置のRF（Radio−Frequence）信号
の送受信を行う頚椎用RFコイルに関する。更に
詳しくは、RFコイルの装着感と頚椎部分の感度
領域を改善した頚椎用局所コイルに関する。[Detailed explanation of the invention] (Field of industrial application) This invention is based on MRI (Magnetic Resonance).
The present invention relates to an RF coil for cervical vertebrae that transmits and receives RF (Radio-Frequence) signals for imaging devices. More specifically, the present invention relates to a local coil for the cervical vertebrae that improves the feeling of wearing the RF coil and the sensitivity region of the cervical vertebrae.
（従来の技術）
周知のようにMRI装置は、核磁気共鳴
（NMR）現象を利用して、プロトン等の特定の
原子核の密度分布や緩和時間を測定して、人体等
の断層像を得るものである。このNMR現象の測
定方法について、第４図を用いて説明する。第４
図は、従来例のMRI装置の概略図である。まず、
Ｚ方向に均一な静磁場Hpを発生している主磁場
コイル１内に被検体２を挿入設置する。次に、角
速度ωpで、ラーモア歳差運動している原子核に、
RFコイル３からXY面内にωpで回転するRFパル
ス磁界を勾配磁場コイル４によるスライス勾配磁
場と共に印加してNMR現象を誘起させる。フー
リエ法では、勾配磁場コイル４による読出し勾配
磁場及びワープ勾配磁場で位置情報を与えなが
ら、前記スライス面全体からのNMR信号をRF
コイル３によつて受信する。このようにして収集
されたMNR信号は画像再構成され、水素原子核
の密度分布像（断層像）やその他の生体化学情報
をCRT表示する。(Prior art) As is well known, an MRI device uses the nuclear magnetic resonance (NMR) phenomenon to measure the density distribution and relaxation time of specific atomic nuclei such as protons to obtain tomographic images of the human body, etc. It is. A method for measuring this NMR phenomenon will be explained using FIG. 4. Fourth
The figure is a schematic diagram of a conventional MRI apparatus. first,
The subject 2 is inserted into the main magnetic field coil 1 which generates a static magnetic field H p uniform in the Z direction. Next, the nucleus precessing Larmor with an angular velocity ω p has
An RF pulse magnetic field rotating at ω p in the XY plane from the RF coil 3 is applied together with a slice gradient magnetic field from the gradient magnetic field coil 4 to induce an NMR phenomenon. In the Fourier method, the NMR signal from the entire slice surface is converted to RF while giving position information using a readout gradient magnetic field and a warp gradient magnetic field by the gradient magnetic field coil 4.
Received by coil 3. The MNR signals collected in this way are reconstructed, and a density distribution image (tomogram) of hydrogen nuclei and other biochemical information are displayed on a CRT.
この様なMRI装置のRFコイルは、撮影部位に
応じて種々の形状のものがある。第５図ａ，ｂは
従来の頚椎の撮影に用いられていたRFコイルで
ある。第５図ａは１ターンの円形の導電材５で構
成された平面状のサーフエイス型コイルであり、
６は導電材５に直列に接続されたコンデンサであ
り、７はコンデンサ６両端に接続された導電線か
らなる給電用の端子である。尚、第５図ａにおい
て、送信用ボデイコイル（図示せず）とのデカツ
プリングのための機構は省略している。この様な
コイルは、静磁場方向（Ｚ方向とする）に仰向け
に載置された被検体の首の裏側から設置される。
この様な形状のコイルでは、被検体にコイルを密
接して配置するため、体表面ではSNR（Signal
to Noize Ratio）を向上することができる。し
かし、コイル面からの距離が大きくなるにつれて
急速に感度が低下し、頚椎のように体表面から深
い部位の受信時の信号感度が劣化する。従つて、
頚椎部全体に渡つて均一で良好な信号感度が得ら
れない。第５図ｂは、改良型の頚椎用RFコイル
であり、コイル部９は、１ターンの鞍形の形状の
銅管で構成され、その外側が発泡性の樹脂でモー
ルドされている。８はコイル側面部上方に設けら
れた給電用のコードである。第６図は、この従来
例の頚椎用RFコイルを被検体に装着した図であ
る。第６図は、第５図ｂのコイルを−Ｙ方向から
見ている。この様な形状のコイルでは、被検体２
の首の底部から耳１０の下部を通り、首のほぼ中
央を体軸方向に沿つて、肩上部から肩の底部にか
けて被検部に沿うように密接してコイル９の側面
部が配置されるため、体表面から深い頚椎部での
感度が得られる。 The RF coil of such an MRI apparatus has various shapes depending on the region to be imaged. Figures 5a and 5b show RF coils conventionally used for imaging the cervical vertebrae. FIG. 5a shows a planar surf-eight coil made of one turn of circular conductive material 5.
6 is a capacitor connected in series to the conductive material 5, and 7 is a power supply terminal made of a conductive wire connected to both ends of the capacitor 6. In FIG. 5a, a mechanism for decoupling with a transmitting body coil (not shown) is omitted. Such a coil is installed from the back side of the neck of a subject who is placed on his back in the direction of the static magnetic field (referred to as the Z direction).
With a coil of this type, the coil is placed closely to the subject, so the SNR (Signal
to Noize Ratio). However, as the distance from the coil surface increases, the sensitivity rapidly decreases, and signal sensitivity deteriorates when receiving a region deep from the body surface, such as the cervical vertebrae. Therefore,
Uniform and good signal sensitivity cannot be obtained over the entire cervical region. FIG. 5b shows an improved RF coil for the cervical vertebrae, in which the coil portion 9 is composed of a one-turn saddle-shaped copper tube, the outside of which is molded with foamable resin. 8 is a power supply cord provided above the side surface of the coil. FIG. 6 is a diagram showing this conventional RF coil for cervical vertebrae attached to a subject. FIG. 6 shows the coil of FIG. 5b viewed from the -Y direction. With a coil shaped like this, the object 2
The side portion of the coil 9 is placed closely along the test subject from the bottom of the neck to the bottom of the ear 10, approximately along the center of the neck in the axial direction, and from the top of the shoulder to the bottom of the shoulder. Therefore, sensitivity can be obtained from the body surface to deep cervical vertebrae.
（考案が解決しようとする課題）
しかし、前記のような頚椎用RFコイルにおい
ては、第６図のようにコイル９の側面部上部が耳
１０の下部に当たるため装着感が悪い。これは、
数十分間の撮影時間を必要とするMRIにおいて
は、被検体にとつて大きな苦痛となる。又、頚椎
の上方部で耳１０の深部にある延髄は対応するコ
イル面が無いため撮影することができず、頚椎と
関連して診断に必要な部位を同時に撮影すること
ができない。又、給電用の端子が側面に付いてい
るためコードが被検体の片側にしか出ないため、
操作者が他の操作をする反対側にコードが出る場
合があり、この場合はコードの操作のためにいち
いち被検体の反対側に回る必要があり、操作性が
悪い。(Problems to be Solved by the Invention) However, in the above-described RF coil for the cervical vertebrae, the upper part of the side surface of the coil 9 hits the lower part of the ear 10, as shown in FIG. 6, making it uncomfortable to wear. this is,
MRI, which requires several tens of minutes of imaging time, is very painful for the subject. Furthermore, the medulla oblongata located above the cervical vertebrae and deep in the ear 10 cannot be imaged because there is no corresponding coil surface, and it is not possible to simultaneously image the parts necessary for diagnosis in relation to the cervical vertebrae. Also, since the power supply terminal is attached to the side, the cord only comes out on one side of the test object.
There are cases where the cord comes out on the opposite side from where the operator performs other operations, and in this case, it is necessary to go around to the opposite side of the subject each time to operate the cord, resulting in poor operability.
本願考案の目的は、上記問題点を解決し、頚椎
撮影時において、装着感が良く、体軸方向に感度
領域が長く、操作性の良い頚椎用RFコイルを提
供することにある。 The purpose of the present invention is to solve the above-mentioned problems and provide an RF coil for the cervical vertebrae that is comfortable to wear, has a long sensitivity region in the body axis direction, and has good operability during cervical spine imaging.
（課題を解決するための手段）
上記の目的を達成するために、本考案の頚椎用
RFコイルは、以下の様な構成をしている。即ち、
頚椎用RFコイルにおいて、鞍形の導電材は垂直
方向から見た底部形状が、前記静磁場方向に直交
した水平方向に平行な辺を持つ略等脚台形、前記
水平方向から見た側部形状が略逆Ｕ字状であつ
て、前記台形の長辺１１ａが被検体頭部側、短辺
１１ｂが被検体肩部側に配置され、前記逆Ｕ字状
側部１１ｃは、前記肩側辺が略垂直、前記頭部側
辺が体軸下方向に傾斜を持つように構成され、前
記導電部周縁上に直列に接続された少なくとも１
個の容量素子を備えることを特徴とする。又、前
記容量素子は、前記長辺１１ａ又は短辺１１ｂの
略中央に設置し、前記導電部は、チユーブ状の絶
縁材で被覆された銅管で構成することを特徴とす
る。(Means for Solving the Problems) In order to achieve the above purpose, the cervical vertebrae of the present invention
The RF coil has the following configuration. That is,
In the RF coil for cervical vertebrae, the saddle-shaped conductive material has a bottom shape when viewed from the vertical direction, and a substantially isosceles trapezoidal shape with sides parallel to the horizontal direction perpendicular to the direction of the static magnetic field, and a side shape when viewed from the horizontal direction. is approximately inverted U-shaped, the long side 11a of the trapezoid is arranged on the subject's head side, the short side 11b is arranged on the subject's shoulder side, and the inverted U-shaped side part 11c is arranged on the shoulder side side. is substantially perpendicular, and the head side is configured to have an inclination in the downward direction of the body axis, and at least one conductive portion is connected in series on the periphery of the conductive portion.
It is characterized by comprising a capacitive element. Further, the capacitive element is installed approximately at the center of the long side 11a or the short side 11b, and the conductive portion is formed of a copper tube covered with a tubular insulating material.
（作用）
略逆Ｕ字状の側部の頭部側１１ｃ１が体軸下方
向に傾斜を持つため、コイルを仰向けに載置され
た被検体の首の裏側から設置したとき、コイル側
面が被検体の耳に当たらず、なおかつ顎の脇から
耳の裏を通り、後頭部を通る底部の長辺１１ａに
接続しているため、頚椎部の感度領域を体軸上方
向に長くとることができる。又、給電部からのコ
ードを被検体の両側のどちらの側面へ引くことが
できる。又、導電部は銅管をチユーブ材の絶縁材
で被覆するのみのため、安価且つ軽量に構成でき
る。(Function) Since the head side 11c1 of the approximately inverted U-shaped side part is inclined in the downward direction of the body axis, when the coil is installed from the back side of the neck of a subject placed on his back, the side surface of the coil is not covered. Since it does not touch the subject's ear and is connected to the long side 11a of the bottom that passes from the side of the chin, behind the ear, and through the back of the head, the sensitivity region of the cervical vertebrae can be made longer in the axial direction. Further, the cord from the power feeding section can be drawn to either side of the subject. Furthermore, since the conductive portion only covers the copper tube with an insulating tube material, it can be constructed at low cost and light weight.
（実施例）
以下本考案の頚椎用RFコイルを図面を参照し
て説明する。始めに、形状の特長について説明す
る。第１図ａ〜ｄは、本考案の一実施例による頚
椎用RFコイルを表す図である。第１図において
各々ａは斜視図、ｂはＸ方向から見た図、ｃは−
方向から見た図、ｄは−Ｚ方向から見た図であ
る。第１図ａのように、本実施例の頚椎用RFコ
イルは、鞍形の形状をしており、１ターンの銅管
で構成されている。銅管は、腐蝕防止と絶縁及び
被検体の安全性のためシリコンのチユーブで被覆
されている。第１図ｂのように、Ｘ方向から見た
底部は長辺部１１ａと短辺１１ｂを持つ略等脚台
形状であり、台形の両斜辺の一部からなる側部１
１ｃは、第１図ｃ，ｄのようにＸ軸方向（垂直）
に伸びる略逆Ｕ字状の突起を形成している。この
突起は、−Ｚ方向に傾斜を持つた傾斜部１１ｃ１
と、底面に対してほぼ垂直に伸びた垂直部１１ｃ
２とからなる。第２図は本考案の一実施例による
頚椎用RFコイルを被検体に装着した図である。
第２図のように、仰向けに載置された被検体２の
首の裏側からコイルを設置したとき、傾斜部１１
ｃ１が−Ｚ方向に傾斜を持つているため、後頭部
から耳の裏、顎の脇を通るように首に接し、被検
体２の耳８にコイル面が当たらない。又、コイル
側部は被検体２の顎に沿つて突起を形成している
ため頚椎１２ａの上までカバーし、なおかつ、傾
斜部１１ｃ１が耳１０の裏を通り、コイル底部の
長辺部１１ａが被検体２の後頭部を通るため、頚
椎部の感度を下げることなく、体軸上方向に長い
感度領域をとることができる。即ち、コイル側部
を一辺が傾斜した逆Ｕ字状にしたため、コイル側
面が顎の脇に沿つて首に密着し、頚椎１２ａの良
好な受信信号感度を得ることができる。又、コイ
ル側部の傾斜部１１ｃ１の下部から底面の長辺部
１１ａのコイル面によつて、頚椎１２の上方部で
耳８の深部にある延髄１２ｂからのNMR信号を
受信することができる。従つて、胸椎１２ｃから
延髄１２ｂまでの断層像を一度に得ることができ
る。(Example) The RF coil for cervical vertebrae of the present invention will be described below with reference to the drawings. First, the features of the shape will be explained. FIGS. 1a to 1d are diagrams showing an RF coil for cervical vertebrae according to an embodiment of the present invention. In Figure 1, a is a perspective view, b is a view seen from the X direction, and c is a -
d is a view seen from the -Z direction. As shown in FIG. 1a, the cervical vertebra RF coil of this embodiment has a saddle shape and is made of a single turn of copper tube. The copper tube is coated with a silicone tube for corrosion prevention, insulation, and specimen safety. As shown in FIG. 1b, the bottom when viewed from the X direction has a substantially isosceles trapezoidal shape with a long side 11a and a short side 11b, and the side 1 consists of a part of both hypotenuses of the trapezoid.
1c is the X-axis direction (vertical) as shown in Figure 1c and d.
It forms a roughly inverted U-shaped protrusion that extends to . This protrusion has an inclined portion 11c1 having an inclination in the -Z direction.
and a vertical portion 11c extending almost perpendicularly to the bottom surface.
It consists of 2. FIG. 2 is a diagram showing a cervical spine RF coil according to an embodiment of the present invention attached to a subject.
As shown in FIG. 2, when the coil is installed from the back side of the neck of the subject 2 placed on his back,
Since c1 has an inclination in the −Z direction, it comes into contact with the neck from the back of the head to the back of the ear and the side of the chin, and the coil surface does not come into contact with the ear 8 of the subject 2. In addition, since the coil side part forms a protrusion along the jaw of the subject 2, it covers the top of the cervical vertebrae 12a, and the inclined part 11c1 passes behind the ear 10, and the long side part 11a of the bottom of the coil Since it passes through the back of the head of the subject 2, it is possible to have a long sensitive region in the axial direction without reducing the sensitivity of the cervical vertebrae. That is, since the side portion of the coil is formed into an inverted U-shape with one side slanted, the side surface of the coil comes into close contact with the neck along the side of the chin, making it possible to obtain good reception signal sensitivity of the cervical vertebrae 12a. Further, the NMR signal from the medulla oblongata 12b located deep in the ear 8 in the upper part of the cervical vertebrae 12 can be received by the coil surface from the lower part of the inclined part 11c1 of the coil side part to the long side part 11a of the bottom surface. Therefore, a tomographic image from the thoracic vertebrae 12c to the medulla oblongata 12b can be obtained at once.
次に本考案の頚椎用RFコイルの回路構成につ
いて説明する。第３図は本実施例の頚椎用RFコ
イルの等価回路図である。第３図において、第５
図と同じ機能のものは、同じ記号を用いている。
６ａ，６ｂ，１４は底辺部１１ａ又は１１ｂのほ
ぼ中央に直列に接続された共振用コンデンサであ
り、コンデンサ６ａ及び１４によりインピーダン
ス変換を行つている。７はコンデンサ６ａの両端
に接続された受信用の端子、１３はコイル１１の
持つ固有のインダクタンス、１５は受信用の頚椎
用RFコイルとその外側に配置される送信用のボ
デイコイルとの磁気的カツプリングを防止するデ
カツプリング回路である。このデカツプリング回
路１５は、クロスダイオード１５ａとインダクタ
ンス１５ｂからなり、ボデイコイル送信時にイン
ダクタンス１３に生じる誘導起電力でクロスダイ
オード１５ａの両端に電位差が生じ、これらがオ
ンになる。この結果、インダクタンス１５ｂとコ
ンデンサ６ｂが並列共振回路となり、インダクタ
ンス１３に流れる電流を阻止するため、２つのコ
イルの磁気的カツプリングを防ぐことができる。
受信時はNMR信号が微弱なため、インダクタン
ス１３に生じる誘導起電力がダイオード１５ａを
オンするほど大きくないため、デカツプリング回
路１５は動作しない。本実施例の頚椎用RFコイ
ルでは、給電部７をコイルの底面部１１ａ又は１
１ｂのどちらかの一方の中央に配置するため、給
電部からのコードを被検体の両側のどちらの側面
へ引くことができる。 Next, the circuit configuration of the RF coil for cervical vertebrae of the present invention will be explained. FIG. 3 is an equivalent circuit diagram of the RF coil for cervical vertebrae of this embodiment. In Figure 3, the fifth
The same symbols are used for items with the same function as in the figure.
Resonant capacitors 6a, 6b, and 14 are connected in series approximately at the center of the bottom portion 11a or 11b, and the capacitors 6a and 14 perform impedance conversion. 7 is a receiving terminal connected to both ends of the capacitor 6a, 13 is the inherent inductance of the coil 11, and 15 is a magnetic coupling between the receiving RF coil for the cervical vertebrae and the transmitting body coil placed outside of the receiving terminal. This is a decoupling circuit that prevents this. This decoupling circuit 15 consists of a cross diode 15a and an inductance 15b, and the induced electromotive force generated in the inductance 13 during body coil transmission creates a potential difference between both ends of the cross diode 15a, turning them on. As a result, the inductance 15b and the capacitor 6b form a parallel resonant circuit to block current flowing through the inductance 13, thereby preventing magnetic coupling between the two coils.
During reception, since the NMR signal is weak, the induced electromotive force generated in the inductance 13 is not large enough to turn on the diode 15a, so the decoupling circuit 15 does not operate. In the cervical vertebra RF coil of this embodiment, the power feeding part 7 is connected to the bottom part 11a or 1 of the coil.
1b, the cord from the power feeding section can be drawn to either side of the subject.
尚本願考案は上記実施例に限ることなく、実用
新案登録請求の範囲内で種々の変形が可能であ
る。上記実施例では受信専用に用いたが、送受信
両方に用いても良い。この場合、デカツプリング
回路１５は省略できる。又、コイルの入出力部に
は、一般的に用いられている平衡不平衡変換のた
めのバラン（balanced unbalanced
transformor）回路を前記コンデンサ６ａと端子
７の間に接続しても良い。更に、コイル１１は、
銅以外でも、電気伝導性の良い材質、例えば、銀
又は銅に銀メツキを施したもの等で作り、形状は
管状でなく、棒又は箔で構成することも可能であ
る。 The present invention is not limited to the above-mentioned embodiments, and various modifications can be made within the scope of the claims of the utility model registration. In the above embodiment, it is used only for reception, but it may be used for both transmission and reception. In this case, the decoupling circuit 15 can be omitted. In addition, the input/output section of the coil is equipped with a balun (balanced unbalanced
A transformer circuit may be connected between the capacitor 6a and the terminal 7. Furthermore, the coil 11 is
In addition to copper, it can be made of a material with good electrical conductivity, such as silver or copper plated with silver, and the shape is not tubular, but can be made of a rod or foil.
（考案の効果）
以上、説明の通り、本考案の頚椎用RFコイル
によれば、以下の効果が得られる。(Effects of the invention) As explained above, according to the RF coil for cervical vertebrae of the invention, the following effects can be obtained.
(1) 略逆Ｕ字状の側部の傾斜部１１ｃ１が体軸下
方向に傾斜を持つているため、仰向けに載置さ
れた被検体の首の裏側から設置したとき、コイ
ル側面が被検体の耳に当たらず、装着感が向上
し、撮影時の患者の苦痛を軽減することができ
る。(1) Since the inclined portion 11c1 of the approximately inverted U-shaped side section is inclined in the downward direction of the body axis, when the coil is installed from the back side of the neck of a subject placed on his/her back, the side surface of the coil is It does not hit the patient's ear, improves the feeling of wearing it, and reduces patient pain during imaging.
(2) コイル側面部の導電部が顎の脇から耳の裏を
通り、後頭部を通る底部の長辺１１ａに接続し
ているため、頚椎部の感度を下げることなく、
感度領域を体軸上方向に長くとることができ
る。従つて、頚椎の上部で耳の深部にある延髄
からのNMR信号も受信することができ、胸椎
から延髄までの断層像を一度に得ることがで
き、診断能が向上する。(2) The conductive part on the side of the coil passes from the side of the chin, behind the ear, and connects to the long side 11a of the bottom, which passes through the back of the head, without reducing the sensitivity of the cervical vertebrae.
The sensitive region can be made longer along the body axis. Therefore, it is possible to receive NMR signals from the medulla oblongata located deep in the ear at the upper part of the cervical vertebrae, and a tomographic image from the thoracic vertebrae to the medulla oblongata can be obtained at once, improving diagnostic performance.
(3) 給電部からのコードを被検体の両側のどちら
の側面へ引くことができ、操作性が向上する。(3) The cord from the power supply unit can be pulled to either side of the subject, improving operability.
(4) 導電部は銅管からなる導電体をチユーブ状の
絶縁材で被覆するのみのため、安価且つ軽量に
構成できる。(4) Since the conductive part is simply a conductor made of a copper tube and covered with a tube-shaped insulating material, it can be constructed at low cost and lightweight.
第１図ａ〜ｄは、本考案の一実施例による頚椎
用RFコイルを表わす図、第２図は本考案の一実
施例による頚椎用RFコイルを被検体に装着した
図、第３図は本考案の一実施例の頚椎用RFコイ
ルの等価回路図、第４図は従来例のMRI装置の
概略図、第５図ａ，ｂは従来例の頚椎用RFコイ
ルを表す図、第６図は従来例の頚椎用RFコイル
を被検体に装着した図である。
１……静磁場マグネツト、２……被検体、３…
…RFコイル、４……勾配磁場コイル、５……導
電部、６，６ａ，６ｂ，１４……共振用コンデン
サ、７……給電端子、８……コード、９，１１…
…コイル、１０……耳、１１ａ……長辺部、１１
ｂ……短辺部、１１ｃ……側面部、１１ｃ１……
傾斜部、１１ｃ２……垂直部、１２ａ……頚椎、
１２ｂ……延髄、１２ｃ……胸椎、１３，１５ｂ
……インダクタンス、１５ａ……クロスダイオー
ド、１５……デカツプリング回路。
1A to 1D are diagrams showing an RF coil for the cervical vertebrae according to an embodiment of the present invention, FIG. 2 is a diagram of the RF coil for the cervical vertebrae according to an embodiment of the present invention attached to a subject, and FIG. An equivalent circuit diagram of an RF coil for the cervical vertebrae according to an embodiment of the present invention, Fig. 4 is a schematic diagram of a conventional MRI apparatus, Figs. 5 a and b are diagrams representing a conventional RF coil for the cervical vertebrae, and Fig. 6 1 is a diagram showing a conventional RF coil for cervical vertebrae attached to a subject. 1... Static magnetic field magnet, 2... Subject, 3...
...RF coil, 4... Gradient magnetic field coil, 5... Conductive part, 6, 6a, 6b, 14... Resonance capacitor, 7... Power supply terminal, 8... Cord, 9, 11...
...Coil, 10...Ear, 11a...Long side, 11
b... Short side part, 11c... Side part, 11c1...
Inclined part, 11c2...vertical part, 12a...cervical vertebrae,
12b...medulla oblongata, 12c...thoracic vertebrae, 13, 15b
...Inductance, 15a...Cross diode, 15...Decoupling circuit.
Claims (1)
ら設置され、鞍形の導電材で構成されるMRI
装置の頚椎用RFコイルにおいて、前記鞍形の
導電材は垂直方向から見た底部形状が、前記静
磁場方向に直交した水平方向に平行な辺を持つ
略等脚台形、前記水平方向から見た側部形状が
略逆Ｕ字状であつて、前記台形の長辺１１ａが
被検体頭部側、短辺１１ｂが被検体肩部側に配
置され、前記逆Ｕ字状側部１１ｃは、前記肩側
辺１１ｃ２が略垂直、前記頭部側辺１１ｃ１が
体軸下方向に傾斜を持つように構成され、前記
導電部周縁上に直列に接続された少なくとも１
個の容量素子を備えることを特徴とする頚椎用
RFコイル。 (2) 前記容量素子は、前記長辺１１ａ又は短辺１
１ｂの略中央に設置されていることを特徴とす
る請求項１記載の頚椎用RFコイル。 (3) 前記導電部は、チユーブ状の絶縁材で被覆さ
れた銅管で構成されていることを特徴とする請
求項１記載の頚椎用RFコイル。[Claims for Utility Model Registration] (1) MRI that is installed from the back of the neck of the subject placed in the direction of the static magnetic field and is constructed of a saddle-shaped conductive material.
In the RF coil for cervical vertebrae of the device, the bottom shape of the saddle-shaped conductive material when viewed from the vertical direction is approximately an isosceles trapezoid with sides parallel to the horizontal direction orthogonal to the direction of the static magnetic field, and when viewed from the horizontal direction The side part shape is approximately an inverted U-shape, the long side 11a of the trapezoid is arranged on the subject's head side, the short side 11b is arranged on the subject's shoulder side, and the inverted U-shaped side part 11c is arranged on the subject's shoulder side. The shoulder side 11c2 is substantially vertical, the head side 11c1 is inclined in the downward direction of the body axis, and at least one conductive portion is connected in series on the periphery of the conductive portion.
For cervical vertebrae, characterized by comprising a number of capacitive elements.
RF coil. (2) The capacitive element has the long side 11a or the short side 1
The RF coil for cervical vertebrae according to claim 1, wherein the RF coil is installed approximately in the center of the RF coil for the cervical vertebrae. (3) The RF coil for cervical vertebrae according to claim 1, wherein the conductive portion is composed of a copper tube covered with a tubular insulating material.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP9617688U JPH0451774Y2 (en) | 1988-07-20 | 1988-07-20 |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP9617688U JPH0451774Y2 (en) | 1988-07-20 | 1988-07-20 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH0217112U JPH0217112U (en) | 1990-02-05 |
| JPH0451774Y2 true JPH0451774Y2 (en) | 1992-12-07 |
Family
ID=31321014
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP9617688U Expired JPH0451774Y2 (en) | 1988-07-20 | 1988-07-20 |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0451774Y2 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112566591A (en) * | 2018-08-06 | 2021-03-26 | 崔钟洙 | Auxiliary device for supporting mandible angle and mandible angle correcting device comprising same |
-
1988
- 1988-07-20 JP JP9617688U patent/JPH0451774Y2/ja not_active Expired
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112566591A (en) * | 2018-08-06 | 2021-03-26 | 崔钟洙 | Auxiliary device for supporting mandible angle and mandible angle correcting device comprising same |
| US20210290423A1 (en) * | 2018-08-06 | 2021-09-23 | Jong-Soo Choi | Brace for supporting jaw angle, and jaw angle correcting apparatus including same |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0217112U (en) | 1990-02-05 |
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