JPH02243981A - Magnetic field detecting device - Google Patents
Magnetic field detecting deviceInfo
- Publication number
- JPH02243981A JPH02243981A JP1063649A JP6364989A JPH02243981A JP H02243981 A JPH02243981 A JP H02243981A JP 1063649 A JP1063649 A JP 1063649A JP 6364989 A JP6364989 A JP 6364989A JP H02243981 A JPH02243981 A JP H02243981A
- Authority
- JP
- Japan
- Prior art keywords
- detectors
- detector
- magnetic field
- regular
- sensitivity
- 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
- 238000005259 measurement Methods 0.000 claims abstract description 11
- 238000001514 detection method Methods 0.000 claims description 8
- 238000002582 magnetoencephalography Methods 0.000 claims description 6
- 230000035945 sensitivity Effects 0.000 abstract description 10
- 230000007246 mechanism Effects 0.000 abstract description 6
- 241000238366 Cephalopoda Species 0.000 abstract description 5
- 230000005540 biological transmission Effects 0.000 abstract description 5
- 210000004556 brain Anatomy 0.000 abstract description 5
- 239000007788 liquid Substances 0.000 abstract description 3
- 239000002887 superconductor Substances 0.000 abstract description 3
- 230000004907 flux Effects 0.000 abstract description 2
- 239000000463 material Substances 0.000 abstract description 2
- 230000005389 magnetism Effects 0.000 abstract 2
- 230000000903 blocking effect Effects 0.000 abstract 1
- 230000000694 effects Effects 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- IJGRMHOSHXDMSA-UHFFFAOYSA-N Atomic nitrogen Chemical compound N#N IJGRMHOSHXDMSA-UHFFFAOYSA-N 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 210000003625 skull Anatomy 0.000 description 2
- 230000008901 benefit Effects 0.000 description 1
- 230000003925 brain function Effects 0.000 description 1
- 239000001307 helium Substances 0.000 description 1
- 229910052734 helium Inorganic materials 0.000 description 1
- SWQJXJOGLNCZEY-UHFFFAOYSA-N helium atom Chemical compound [He] SWQJXJOGLNCZEY-UHFFFAOYSA-N 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 229910052757 nitrogen Inorganic materials 0.000 description 1
- 230000008054 signal transmission Effects 0.000 description 1
- 239000010409 thin film Substances 0.000 description 1
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/02—Measuring direction or magnitude of magnetic fields or magnetic flux
- G01R33/022—Measuring gradient
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Measuring Magnetic Variables (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は、磁場検出装置に係り、特に脳から発生する磁
場を高感度に検出する脳磁計測装置に好適な磁場検出装
置に関する。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a magnetic field detection device, and particularly to a magnetic field detection device suitable for a magnetoencephalography measurement device that detects magnetic fields generated from the brain with high sensitivity.
従来の脳磁計開用の多チヤネルスクイド磁束計について
は、バイオマグネテイズム’８７（１９８８年）第４３
０頁から第４３３頁（Ｂｉｏ −＠ａｇｎｅｔｉｓｍ８
７ （１９８７）ｐ４３０−４３３）に記述がある。こ
の例は７チヤンネルであり、各検出器間の距離を等しく
するために曲面上に描かれた正六角形の頂点と中央に検
出器が配置されている。このように曲面上に配置したの
」よ頭蓋の曲面に合わせるためである。Regarding the multi-channel Squid magnetometer used for conventional magnetoencephalography, see Biomagnetism '87 (1988) No. 43.
Pages 0 to 433 (Bio-@agnetism8
7 (1987) p. 430-433). This example has seven channels, and the detectors are arranged at the vertices and centers of a regular hexagon drawn on a curved surface to equalize the distance between each detector. It was placed on a curved surface like this to match the curved surface of the skull.
この従来例における検出器の配置を第４図に示す、この
例では各々の検出器は軸型グラジオメータの構成になっ
ている。即ち、頭蓋の球面に垂直な方向をＺ方向、これ
に垂直な方向をＸｅ’ｊ方向Ｚ
るグラジオメータとしては、ジャーナル オブアプライ
ド フィツクス ５８（１１）（１９８５）第４３２２
頁から第４３２５頁（Ｊ 、 Ａｐｐｌ Ｐｈｙｇ。The arrangement of the detectors in this conventional example is shown in FIG. 4. In this example, each detector is configured as an axial gradiometer. That is, as a gradiometer whose direction perpendicular to the spherical surface of the skull is the Z direction, and whose direction perpendicular to this is the
Pages 4325 to 4325 (J, Appl Phyg.
５８（１１） １９８５ ｐ４３２２−４３２５）に記
述がある。このような平面型グラジオメータでは、゛検
出コイルと薄膜スクイド素子が同一平面上に形成できる
ため構成が簡単になるうえ、検出器からスクイド素子ま
での信号の伝達効率がよいという利点がある。58 (11) 1985 p4322-4325). Such a planar gradiometer has the advantage that the detection coil and the thin-film SQUID element can be formed on the same plane, which simplifies the configuration and also improves the efficiency of signal transmission from the detector to the SQUID element.
ところが、上記前者の従来技術において、脳磁計測装置
が蔽えるのは人体頭部のごく一部にすぎない（第５図）
、脳機能の計測を行って生理学的。However, in the former conventional technology, the magnetoencephalography measuring device covers only a small part of the human head (Figure 5).
, physiological measurements of brain function.
医学的に応用するためには２０チャネル以上のセンサー
を用いて頭部全体を蔽う必要がある。また。For medical applications, it is necessary to cover the entire head using sensors with 20 channels or more. Also.
スクイド磁束計では各々の検出器の感度が他の検出器と
の距離によって変化するため、隣接する検出器との距離
は各々等しくなるように構成する必要がある。さらに、
各検出器のＳ／Ｎを向上させるためにはその受信する信
号量を大きくせねばならず、検出器の面積を大きくする
必要がある。In the SQUID magnetometer, the sensitivity of each detector changes depending on the distance from other detectors, so it is necessary to configure the detector so that the distances from adjacent detectors are equal. moreover,
In order to improve the S/N of each detector, it is necessary to increase the amount of signal received by each detector, and it is necessary to increase the area of the detector.
本発明の目的は頭部を蔽う形で検出器を配置するため１
０個以上の検出器を球状に均等分布させた配置とするこ
とにある。The object of the present invention is to arrange the detector in a manner that covers the head.
The purpose is to arrange zero or more detectors in a spherically evenly distributed arrangement.
本発明の他の目的は、このときの各検出器の面積を最大
限にとることにある。Another object of the present invention is to maximize the area of each detector at this time.
上記目的を達成するため、本発明においては検出器の全
部または一部を、正多面体の頂点に配置したものである
。In order to achieve the above object, in the present invention, all or part of the detector is arranged at the vertices of a regular polyhedron.
また、均等分布している各検出器のｍＭを最大にするた
め、検出器を正多面体の面上に配置し、その形状を正多
面体の各面と等しくすることにより各検出器の面積を技
術的にｎｆ能な限り大きくすることができる。In addition, in order to maximize the mm of each detector that is evenly distributed, the area of each detector is can be made as large as possible.
さらに平面型グラジオメータを球状に均等分布するため
、正多面体の隣接する二面を一つの平面型グラジオメー
タとし、ｚｕｒｉ間の差分をとるようにしたものである
。Furthermore, in order to uniformly distribute the planar gradiometers in a spherical shape, two adjacent surfaces of the regular polyhedron are used as one planar gradiometer, and the difference between the zuri is calculated.
、正多面体では各頂点間の距離は相等しく、ここに検出
器を配置すれば、球状に均等分布させることができる。In a regular polyhedron, the distances between the vertices are equal, and if a detector is placed here, it can be distributed evenly in a spherical shape.
実装上すべての頂点に配置できなくても検出器間の距離
による感度のアンバランスは最低限にとどめることがで
きる。Even if the detectors cannot be placed at all vertices due to implementation, the unbalance in sensitivity due to the distance between the detectors can be kept to a minimum.
また、各検出器の形状と面積を正多面体の各面に等しく
すれば等面積の検出器を球状に均等分布させる場合の一
個あたりの面積は最大になる。Furthermore, if the shape and area of each detector are made equal to each face of a regular polyhedron, the area per detector when equal area detectors are uniformly distributed spherically becomes maximum.
さらに正多面体の隣接する２面を一つの平面型グラジオ
メータとすれば、平面型グラジオメータを球状に均等分
布させることができる。Furthermore, if two adjacent faces of the regular polyhedron are used as one planar gradiometer, the planar gradiometers can be evenly distributed in a spherical shape.
以下、本発明の一実施例を第１図に示したＫＡ磁針によ
り説明する。被験者６から発生した脳磁の信号をグラジ
オメータをなす検出器１で検出し。Hereinafter, one embodiment of the present invention will be explained using the KA magnetic needle shown in FIG. A magnetic brain signal generated from a subject 6 is detected by a detector 1 forming a gradiometer.
伝送線５を通じて５ＱＵＩＩ）素子に人力する。この信
号を例えば？’ＬＬ（フラックス・ロックド・ループ）
を用いた計測器で計測する。また制御器は計測器や後に
説明する回転機構を制御する。Power is applied to the 5QUII) element through the transmission line 5. For example, what is this signal? 'LL (Flux Locked Loop)
Measure with a measuring device that uses Further, the controller controls a measuring instrument and a rotation mechanism which will be explained later.
１００は本脳磁計の機構部を表わす。検出器１や伝送線
５は超伝導体であり、５ＱＵＩＤ素子も超伝導デバイス
であるため、必要に応じて１００内部を液体ヘリウムま
たは液体窒素等の塞材に浸漬する。第１図の例では正１
２ｉｆｎ体１０のすべての頂点上に検出器１を配置した
例を示している。Reference numeral 100 represents a mechanical section of the present magnetoencephalograph. Since the detector 1 and the transmission line 5 are superconductors, and the 5QUID element is also a superconductor device, the inside of the detector 100 is immersed in a filling material such as liquid helium or liquid nitrogen as necessary. In the example in Figure 1, positive 1
An example is shown in which the detectors 1 are placed on all vertices of the 2ifn body 10.
この場合、検出器１は最大２０個配置できるが、実装上
配置できない頂点がある場合もある。正１２面体１０は
単に検出器を配置する位置を示すもので、実際に装置が
この形状を有する必要はない。In this case, a maximum of 20 detectors 1 can be arranged, but there may be some vertices that cannot be arranged due to implementation. The regular dodecahedron 10 simply indicates the position where the detector is placed, and the device does not actually need to have this shape.
より多くの測定点が必要な場合は次の２つの方法がある
。一つは廟磁計の機構全体を適当な軸を選んで被験首の
回りに回転させながら測定を行う方法である。この方法
では全く等しい感度で任意の数の測定を行うことができ
る。If more measurement points are required, there are two methods: One method is to select an appropriate axis and rotate the entire mechanism of the mausoleum magnetometer around the subject's neck while taking measurements. This method allows any number of measurements to be made with exactly equal sensitivity.
もう一つの検出器配置については第２図を用いて説明す
る。この配置は多１０ｉ体の頂点のほかに各面の中心を
通る、１１０に垂直な線上の点にも検出器を配置する方
法である。第２図では正１２面体の一つの而である正５
角形ＡＢＣＤＥを示している。Another detector arrangement will be explained with reference to FIG. In this arrangement, detectors are arranged not only at the vertices of the polygon 10i but also at points on a line perpendicular to 110 passing through the center of each face. In Figure 2, the regular 5 is one of the regular dodecahedrons.
A square ABCDE is shown.
面の中心Ｏを通る垂直線ＰＱ上の点Ｓにも検出器を配置
する。点Ｓは、点Ｓ上の検出器の感度が、頂点上の検出
器の感度−と等しくなる点を選ぶ。A detector is also placed at a point S on a vertical line PQ passing through the center O of the surface. The point S is selected such that the sensitivity of the detector on the point S is equal to the sensitivity of the detector on the vertex.
このとき例えばＡＢ＝ＡＳとした場合について考察する
。このように配置した場合、頂点上の検出器の最近接検
出器数は６個であり、正１２面体上に等価な点が１２個
ある点Ｓ上の検出器の最近接検出器数は５個であるため
多少の差異はあるが、なおかなりの対称性を保って、検
出器数を増やすことができる。At this time, consider, for example, the case where AB=AS. In this arrangement, the number of nearest detectors to the detector on the vertex is 6, and the number of nearest detectors to the detector at point S, which has 12 equivalent points on the regular dodecahedron, is 5. Although there are some differences because of the number of detectors, it is possible to maintain considerable symmetry and increase the number of detectors.
次に第３図により本発明の他の実施例を示す。Next, FIG. 3 shows another embodiment of the present invention.
第３図（ａ）に示す正２０面体２０の各面上に配置する
検出器や５ＱＴＪＩＩ）素子を第３図（ｂ）〜（ｄ）に
示しており、これ以外の部分は省略している。The detectors and 5QTJII) elements arranged on each surface of the icosahedron 20 shown in FIG. 3(a) are shown in FIGS. 3(b) to (d), and other parts are omitted. .
第３図（ａ）は正２０ ｔｈｉ体の２０の各自に配置Ｚ
ためにコイルの形状を正三角形とし、正２０面体２０の
各面の面積と等しくしている。同図（ｂ）は、平面上に
８２を検出するマグネトメータ２と５ＱＵＩＬ）索子４
を一体で形成した例である。この場合も感度を上げるた
めマグネトメータの面積は正２０面体２０の各面の＋ｆ
＋ｉ積と等しくとっており、こ九を各向上に配置する。In FIG. 3(a), the shape of the coil is an equilateral triangle, and the area of each face of the regular icosahedron 20 is made equal to the shape of the coil in order to arrange each of the 20 coils Z in a regular 20 thi body. The same figure (b) shows magnetometer 2 and 5QUIL) which detect 82 on a plane.
This is an example in which the two are integrally formed. In this case as well, in order to increase the sensitivity, the area of the magnetometer is +f of each face of the regular icosahedron 20.
It is taken equal to +i product, and this number is placed in each improvement.
また同図（ｃ）は正２０而体２０の隣接する２ ＋ｆ＋
ｒ間の差分をとる平面型グラジオメータ３と５ＱＵＬＩ
）素子４を一体で形成した例である。これを多面体２０
上に配置すると最大３０個配置できる。これら第３図に
示す例でも適当な軸のまわりに機構群を同転させること
により等感度の測定を増やすことができるのはいうまで
もない。Also, in the same figure (c), the adjacent 2 +f+ of the positive 20 physical body 20
Planar gradiometers 3 and 5QULI that take the difference between r
) This is an example in which the element 4 is integrally formed. This is polyhedron 20
If you place it on top, you can place up to 30 pieces. It goes without saying that even in the examples shown in FIG. 3, it is possible to increase the number of equal-sensitivity measurements by rotating the mechanism group around an appropriate axis.
本発明によれば、脳磁測定用の検出器を均等に球状に配
置できるため、各々の検出器の感度が等しくなる効果が
ある。また、このとき各々の検出器に入力する脳磁の信
号層が最大になる効果がある。According to the present invention, since the detectors for magnetoencephalography measurement can be arranged evenly in a spherical shape, there is an effect that the sensitivity of each detector becomes equal. Further, at this time, there is an effect that the signal layer of the brain magnetic field input to each detector is maximized.
第１図は本発明の一実施例の脳磁計測装置の模増やす場
合の配置方法を示す説明図、第３図は本発明の別の実施
例における検出器配置を示す多面体の斜視図および検出
器の斜視図ならびにグラジオメータと５ＱＵＩＤ素子の
平面図、第４図、第５図は従来の装置の検出器配置の説
明図である。
１・・・検出器（＠型グラジオメータ）、２・・・検出
器（平向型マグネットメータ）、３・・・検出器（平曲
型グラジオメータ）、４・・・５ＱＵＩＩ）索子、５・
・・伝送線、６・・・被験者（頭部）、１０・・・検出
器の配置を示す正１２１ｍ体、２０・・・検出器の配置
を示す正２０面体、１００・・・脳磁計＋ｌｌ’ｌ装置
の構造体。
竿 ／ｉ
猶
（幻
（Ｃ）
第
■
（幻
（ｂ）
＜ｂ＞
（ｃｌ）
弔
ダ
凹FIG. 1 is an explanatory diagram showing an arrangement method for increasing the number of magnetoencephalogram measuring devices according to an embodiment of the present invention, and FIG. 3 is a perspective view of a polyhedron showing a detector arrangement and detection in another embodiment of the present invention. A perspective view of the device, a plan view of the gradiometer and the 5QUID element, and FIGS. 4 and 5 are explanatory diagrams of the detector arrangement of the conventional device. 1... Detector (@-type gradiometer), 2... Detector (flat magnet meter), 3... Detector (flat curved gradiometer), 4... 5 QUII) cord, 5.
... Transmission line, 6... Subject (head), 10... Regular 121m body showing the arrangement of the detector, 20... Regular icosahedron showing the arrangement of the detector, 100... Magnetoencephalography +ll 'l device structure. Rod /i Yu (Illusion (C) No. ■ (Illusion (b) <b> (cl) Souda concave
Claims (1)
出器の全部または一部を正多面体の頂点に配置したこと
を特徴とする磁場検出装置。 ２、複数の検出器を有する磁場検出装置において検出器
の全部または一部を正多面体の面上に設置し、その形状
を正多面体の各面と等しくしたことを特徴とする磁場検
出装置。 ３、複数の検出器を有する磁場検出装置において正多面
体の隣接する各々の２面に鎖交する磁気信号の差分を計
測する手段を有すること特徴とする磁場検出装置。 ４、特許請求の範囲第１項乃至第３項記載の磁場検出装
置を用いたことを特徴とする脳磁計測装置。[Scope of Claims] 1. A magnetic field detection device having a plurality of magnetic field detectors, characterized in that all or part of the detectors are arranged at vertices of a regular polyhedron. 2. A magnetic field detection device having a plurality of detectors, characterized in that all or part of the detectors are installed on the faces of a regular polyhedron, and the shape thereof is made equal to each face of the regular polyhedron. 3. A magnetic field detection device having a plurality of detectors, characterized in that it has means for measuring a difference between magnetic signals interlinking between two adjacent faces of a regular polyhedron. 4. A magnetoencephalography measurement device characterized by using the magnetic field detection device according to claims 1 to 3.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1063649A JPH02243981A (en) | 1989-03-17 | 1989-03-17 | Magnetic field detecting device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1063649A JPH02243981A (en) | 1989-03-17 | 1989-03-17 | Magnetic field detecting device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH02243981A true JPH02243981A (en) | 1990-09-28 |
Family
ID=13235409
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1063649A Pending JPH02243981A (en) | 1989-03-17 | 1989-03-17 | Magnetic field detecting device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH02243981A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0479208A2 (en) * | 1990-09-30 | 1992-04-08 | Agency Of Industrial Science And Technology | Method and apparatus for measuring vector magnetic flux |
| WO2010140484A1 (en) * | 2009-06-01 | 2010-12-09 | 株式会社システムロード | Device for measuring optical characteristic of light source, measuring method, and examining device provided with the measuring device |
| CN103536308A (en) * | 2013-10-23 | 2014-01-29 | 许剑锋 | Launching and imaging device |
-
1989
- 1989-03-17 JP JP1063649A patent/JPH02243981A/en active Pending
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0479208A2 (en) * | 1990-09-30 | 1992-04-08 | Agency Of Industrial Science And Technology | Method and apparatus for measuring vector magnetic flux |
| WO2010140484A1 (en) * | 2009-06-01 | 2010-12-09 | 株式会社システムロード | Device for measuring optical characteristic of light source, measuring method, and examining device provided with the measuring device |
| CN103536308A (en) * | 2013-10-23 | 2014-01-29 | 许剑锋 | Launching and imaging device |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US5444372A (en) | Magnetometer and method of measuring a magnetic field | |
| US8155726B2 (en) | Magnetic detection coil and apparatus for magnetic field measurement | |
| FI89131C (en) | MAGNETOMETER DETECTOR OVER DERAS MONTAGE I EN FLORKANALIG ANORDNING FOER MAETNING AV MAENSKANS HJAERNFUNKTIONER ALSTRANDE MAGNETFAELT | |
| JP3204542B2 (en) | Magnetic field source measurement device | |
| US11317843B2 (en) | Biomagnetism measuring device | |
| CN109152545A (en) | Biomagnetic measurement device | |
| US5469056A (en) | Planar gradiometers arranged on non-parallel surfaces for determination of a gradient tensor of a magnetic field | |
| Uehara et al. | Multi-channel SQUID systems for biomagnetic measurement | |
| JPH02243981A (en) | Magnetic field detecting device | |
| Burghoff et al. | A vector magnetometer module for biomagnetic application | |
| JPH04309869A (en) | Pickup coil | |
| JP7227609B2 (en) | Marker coil and magnetic measuring device | |
| GB2171523A (en) | Magnetic gradient detection | |
| Kraus Jr et al. | Performance of a novel SQUID-based superconducting imaging-surface magnetoencephalography system | |
| Oyama et al. | Evaluation of an isosceles-triangle-coil phantom for magnetoencephalography | |
| Higuchi et al. | System integration and trade-offs of SQUID system for biomagnetic applications | |
| Ahlfors et al. | A 24-SQUID gradiometer for magnetoencephalography | |
| JPS62187267A (en) | Measuring instrument for superconducting magnetic field | |
| JPH045590A (en) | Multichannel plane type gradiometer | |
| JPH057561A (en) | Magnetic measuring apparatus | |
| Overton et al. | Theoretical and experimental verification of the properties of superconductor surface imaging | |
| JPH0295336A (en) | Biomagnetic measuring device | |
| Fagaly et al. | Magnetometer Calibration Methods | |
| JPH05297091A (en) | Biomagnetism measuring device | |
| JPH0499979A (en) | Squid fluxmeter |