JPH01151438A - Intracorporeal insert utensil for measuring magnetism of living body - Google Patents
Intracorporeal insert utensil for measuring magnetism of living bodyInfo
- Publication number
- JPH01151438A JPH01151438A JP62311299A JP31129987A JPH01151438A JP H01151438 A JPH01151438 A JP H01151438A JP 62311299 A JP62311299 A JP 62311299A JP 31129987 A JP31129987 A JP 31129987A JP H01151438 A JPH01151438 A JP H01151438A
- Authority
- JP
- Japan
- Prior art keywords
- magnetism
- ring
- magnetic flux
- living body
- measure
- 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
- 230000005389 magnetism Effects 0.000 title abstract description 14
- 238000003780 insertion Methods 0.000 claims abstract description 9
- 230000037431 insertion Effects 0.000 claims abstract description 9
- 230000005668 Josephson effect Effects 0.000 claims abstract description 5
- 238000005259 measurement Methods 0.000 claims description 23
- 230000004907 flux Effects 0.000 abstract description 27
- 238000001816 cooling Methods 0.000 abstract description 18
- 241000238366 Cephalopoda Species 0.000 abstract description 5
- 239000002826 coolant Substances 0.000 abstract description 3
- 230000035945 sensitivity Effects 0.000 abstract description 3
- 239000002887 superconductor Substances 0.000 abstract description 2
- 230000008878 coupling Effects 0.000 abstract 1
- 238000010168 coupling process Methods 0.000 abstract 1
- 238000005859 coupling reaction Methods 0.000 abstract 1
- 239000007788 liquid Substances 0.000 description 7
- IJGRMHOSHXDMSA-UHFFFAOYSA-N Atomic nitrogen Chemical compound N#N IJGRMHOSHXDMSA-UHFFFAOYSA-N 0.000 description 6
- 238000003745 diagnosis Methods 0.000 description 4
- 239000000463 material Substances 0.000 description 4
- 239000003507 refrigerant Substances 0.000 description 4
- 239000004065 semiconductor Substances 0.000 description 4
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 229910052757 nitrogen Inorganic materials 0.000 description 3
- TXEYQDLBPFQVAA-UHFFFAOYSA-N tetrafluoromethane Chemical compound FC(F)(F)F TXEYQDLBPFQVAA-UHFFFAOYSA-N 0.000 description 3
- 238000010586 diagram Methods 0.000 description 2
- 239000011521 glass Substances 0.000 description 2
- 238000005286 illumination Methods 0.000 description 2
- 238000002582 magnetoencephalography Methods 0.000 description 2
- 238000012545 processing Methods 0.000 description 2
- 235000011511 Diospyros Nutrition 0.000 description 1
- 244000236655 Diospyros kaki Species 0.000 description 1
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 1
- UFHFLCQGNIYNRP-UHFFFAOYSA-N Hydrogen Chemical compound [H][H] UFHFLCQGNIYNRP-UHFFFAOYSA-N 0.000 description 1
- 230000003321 amplification Effects 0.000 description 1
- 210000000621 bronchi Anatomy 0.000 description 1
- 229910002092 carbon dioxide Inorganic materials 0.000 description 1
- 239000001569 carbon dioxide Substances 0.000 description 1
- 235000011089 carbon dioxide Nutrition 0.000 description 1
- 239000000919 ceramic Substances 0.000 description 1
- 229910010293 ceramic material Inorganic materials 0.000 description 1
- 238000005520 cutting process Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- UMNKXPULIDJLSU-UHFFFAOYSA-N dichlorofluoromethane Chemical compound FC(Cl)Cl UMNKXPULIDJLSU-UHFFFAOYSA-N 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000001839 endoscopy Methods 0.000 description 1
- 210000003238 esophagus Anatomy 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 210000004907 gland Anatomy 0.000 description 1
- 229910052739 hydrogen Inorganic materials 0.000 description 1
- 239000001257 hydrogen Substances 0.000 description 1
- 239000011810 insulating material Substances 0.000 description 1
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 1
- 210000004072 lung Anatomy 0.000 description 1
- 239000000696 magnetic material Substances 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 150000002739 metals Chemical class 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 230000003287 optical effect Effects 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 230000008054 signal transmission Effects 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 230000001360 synchronised effect Effects 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
Landscapes
- Measuring And Recording Apparatus For Diagnosis (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Endoscopes (AREA)
- Measuring Magnetic Variables (AREA)
Abstract
Description
【発明の詳細な説明】
［産業上の利用分野］
本発明はジョセフソン効果を利用した磁気計測を行う生
体磁気計測用体腔内挿入用具に関する。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a biomagnetism measurement device inserted into a body cavity that performs magnetic measurement using the Josephson effect.
［従来の技術］
近年、心磁図、脳磁図とか脳磁図等が研究され、臨床に
応用されている。例えばその例として、内用義則、小谷
誠：生体電磁場分布計測、医用電子と生体工学、 Ｖｏ
ｌ、２４ 、６． ４１１〜４１６ （１９８６）があ
る。[Prior Art] In recent years, magnetocardiography, magnetoencephalography, magnetoencephalography, and the like have been studied and applied clinically. For example, Yoshinori Naiyo, Makoto Kotani: Bioelectromagnetic Field Distribution Measurement, Medical Electronics and Bioengineering, Vo.
l, 24, 6. 411-416 (1986).
これらは、生体から発生する磁気とか生体に磁気を印加
した時の残留磁気などを測定し、各々生体の機能等の診
断を行なうというものであり、心電図どか他の診断礪能
で得られない、あるいは（９にくい生体の情報を１ｑる
為に用いられつつある。These methods measure the magnetism generated by a living body or the residual magnetism when magnetism is applied to a living body, and diagnose the functions of the living body. Alternatively, it is being used to obtain difficult biological information.
上記生体磁気の計測にはＳＱＵ ＴＤ （Ｓｕ ｐｅｒ
ｃｏｎｄｕｃｔｉｎｇ Ｑｕａｎｔｕｍ １ｎｔｅ
ｒｆｅｒｅｎｃｅ ［）ｅｖｉｃｅ）磁束計とかフラ
ックスゲート磁束計を用い、体外より３４側する方法が
とられていた。SQU TD (Super
conducting Quantum 1nte
rference [)evice) A method was used in which a magnetometer or a fluxgate magnetometer was used to measure the 34 side from outside the body.
［発明が解決しようとする問題点］
しかし、上記生体磁気は元来微弱なものであり、正確な
測定のためには、より計測部位に磁束計を近接させて測
定することが望ましいが、体外よりの測定ではおのずと
限界があり、正確な測定がしずらかった。[Problems to be solved by the invention] However, the above-mentioned biomagnetism is inherently weak, and for accurate measurement it is desirable to place the magnetometer closer to the measurement site. Naturally, there are limits to the measurement, making it difficult to make accurate measurements.
本発明は上述した点にかんがみてなされたもので、従来
より正確に生体磁気を計測することのできる生体磁気計
測用体腔内挿入具を提供することを目的とする。The present invention has been made in view of the above-mentioned points, and an object of the present invention is to provide a body cavity insertion device for measuring biomagnetism that can measure biomagnetism more accurately than before.
Ｅ問題点を解決する手段及び作用］
本発明では体腔内に挿入可能な細長の部材の先端部に、
ジョセフソン効果を利用した磁気計測手段と、冷却手段
とを設けることにより、生体内の深部にも挿入可能で、
生体内の深部の部位に対しても近接して高感度の磁気測
定を行えるようにしている。Means and operation for solving problem E] In the present invention, at the distal end of an elongated member that can be inserted into a body cavity,
By providing a magnetic measurement means that utilizes the Josephson effect and a cooling means, it can be inserted deep into the living body.
This enables highly sensitive magnetic measurements to be performed in close proximity to sites deep within the body.
［実施例コ 以下、図面を参照して本発明を具体的に説明する。[Example code] Hereinafter, the present invention will be specifically explained with reference to the drawings.
第１図ないし第３図は本発明の第１実施例に係り、第１
図は第１実施例の電気系の構成図、第２図は第１実施例
の概略の外観図、第３図はカテーテルの先端部の構造を
示す断面図である。Figures 1 to 3 relate to the first embodiment of the present invention.
FIG. 2 is a schematic diagram of the electrical system of the first embodiment, FIG. 2 is a schematic external view of the first embodiment, and FIG. 3 is a sectional view showing the structure of the distal end of the catheter.
第２図に示すように第１実施例の生体磁気計測用体腔内
挿入用具１は、体腔内に挿入できるように細長形状にし
たカテーテル２と、このカテーテル２の後端から延出さ
れた接続コード３が接続され、高周波を出力する高周波
（以下ＲＦと記す）発振器４と、共振回路により取出し
たＲＦ倍信号増幅するＲＦアンプ５と、このＲＦアンプ
５の出力を基準信丹に同期して増幅づるロックインアン
プ６と、このロックインアンプ６の出力を信号処理する
プロセッサ７と、このプロセッサ７の出力を表示するモ
ニタ８とからなる。As shown in FIG. 2, the biomagnetic measurement intrabody cavity insertion device 1 of the first embodiment includes a catheter 2 that is elongated so as to be inserted into the body cavity, and a connection extending from the rear end of the catheter 2. The cord 3 is connected to a high frequency (hereinafter referred to as RF) oscillator 4 which outputs a high frequency, an RF amplifier 5 which amplifies the RF signal taken out by a resonant circuit, and the output of this RF amplifier 5 is synchronized with the reference Shintan. It consists of a lock-in amplifier 6 that is an amplification system, a processor 7 that processes the output of the lock-in amplifier 6, and a monitor 8 that displays the output of the processor 7.
上記カテーテル２の先端部９は第３図に示すように冷却
室１１が設けてあり、この冷却ｖ１１内には支持部材１
２を介して磁気検出用ピックアップ部１３が固定されて
おり、このピックアップ部１３の周囲の冷却室１１内は
冷媒１４を充填でさるようにしである。The distal end 9 of the catheter 2 is provided with a cooling chamber 11 as shown in FIG.
A pickup section 13 for magnetic detection is fixed via a magnet 2, and the inside of the cooling chamber 11 around the pickup section 13 is filled with a refrigerant 14.
つまり上記冷却室１１は、例えば２＠所において外部と
連通する出入口１５．１６が設けられ、これら出入口１
５．１６から冷媒１４としての液体等を注入できるよう
にしである。これら出入口１５．１６はそれぞれ閉塞用
ねじ１７．１８によって塞ぐことができる。尚、各ねじ
１７．１８の出入口１５．１６への固定部にはＯリング
１９゜２０を介装して漏れを防止できるようにしである
。In other words, the cooling chamber 11 is provided with entrances and exits 15 and 16 that communicate with the outside at, for example, 2@ places, and these entrances and exits 1
From 5.16 onwards, liquid etc. as the refrigerant 14 can be injected. These openings 15.16 can each be closed by a closing screw 17.18. Incidentally, O-rings 19 and 20 are interposed at the fixing portions of the screws 17 and 18 to the entrances and exits 15 and 16 to prevent leakage.
上記ピックアップ部１３は第１図に示す構成である。The pickup section 13 has the configuration shown in FIG.
つまり、このピックアップ部１３は、２次勾配型磁束劃
の形をとるピックアップコイル２１と、ジョセフソン接
合２２を１箇所持ら、超伝導体（例えばＹ−Ｂａ−Ｃｕ
Ｏ系酸化物）からなるリング２３とから構成される。That is, this pickup section 13 has a pickup coil 21 in the form of a quadratic gradient type magnetic flux field, one Josephson junction 22, and a superconductor (for example, Y-Ba-Cu).
The ring 23 is made of (O-based oxide).
上記ピックアップコイル２１は、生体からの磁束をピッ
クアップするものであり、超伝導リング２３にはＲＦ発
振器４から共振回路を介してＲＦ電磁束供給される。こ
れらピックアップ部１３は液体窒素等の冷媒１４で冷却
され、リング２３は超伝導状態に保持される。The pickup coil 21 is for picking up magnetic flux from a living body, and RF electromagnetic flux is supplied to the superconducting ring 23 from the RF oscillator 4 via a resonance circuit. These pickup sections 13 are cooled with a coolant 14 such as liquid nitrogen, and the ring 23 is maintained in a superconducting state.
」−２超伝導リング２３にはピックアップコイル２１か
らの被測定磁束と、共振回路を通したＲＦ電磁束導かれ
、このリング２３に入ろうとする磁束はリング２３を流
れる電流によって完全に打ち消され、結果的にはリング
２３内には磁束は入らない。しかしながら、外部磁界を
強めていくと、それに応じてリング電流も増加するが、
このリング電流が臨界電流と呼ばれる値に達した時、接
合部において超伝導がくずれ常伝導となり磁束がリング
内に入り、リング電流が減少りる。このときリング２３
内に入る最小磁束密度は２．０７Ｘ １０ 柿であり
、磁束伍子と呼ばれる。更に外部磁界を強めていくど、
再びリング電流が増加し、臨界電流に達すると超伝導が
くずれ、リング２３内に更に磁束ｍ子だけ磁束が入る。”-2 The magnetic flux to be measured from the pickup coil 21 and the RF electromagnetic flux through the resonant circuit are guided to the superconducting ring 23, and the magnetic flux that attempts to enter the ring 23 is completely canceled by the current flowing through the ring 23. As a result, no magnetic flux enters the ring 23. However, as the external magnetic field is strengthened, the ring current increases accordingly;
When this ring current reaches a value called the critical current, superconductivity breaks down at the junction and becomes normal conduction, allowing magnetic flux to enter the ring and reducing the ring current. At this time, ring 23
The minimum magnetic flux density that can enter inside is 2.07X 10 persimmon, which is called magnetic flux Wuji. As the external magnetic field is further strengthened,
The ring current increases again, and when it reaches a critical current, superconductivity breaks down and a magnetic flux of m magnetic flux further enters the ring 23.
このようにジョセフソン接合２２による弱結合部を持っ
た超伝導リング２３に外部から磁束を加えた場合、リン
グ２３内に入る磁束は磁束Ｍ子の整数倍である。When a magnetic flux is applied from the outside to the superconducting ring 23 having a weakly coupled portion due to the Josephson junction 22 as described above, the magnetic flux entering the ring 23 is an integral multiple of the magnetic flux M.
上記リング２３内に入る磁束の急な変化は、ＲＦ共振回
路に電圧を誘起する。この微小誘起電圧をＲＦアンプ５
側に導き増幅して微弱磁界を測定でさる５ＱＵＩＤ磁束
計を形成している。尚、第１図に示すようにロックイン
アンプ６の出力は抵抗Ｒを介して共振回路側にフィード
バックしている。A sudden change in the magnetic flux entering the ring 23 induces a voltage in the RF resonant circuit. This minute induced voltage is transferred to the RF amplifier 5.
It forms a 5QUID magnetometer that measures a weak magnetic field by guiding it to the side and amplifying it. Incidentally, as shown in FIG. 1, the output of the lock-in amplifier 6 is fed back to the resonant circuit side via a resistor R.
尚、第３図に示すように先端部９の後方側は、可撓性チ
ューブ２５で被覆されている。又、ピックアップ部１３
からリード腺２６が延出されている。Incidentally, as shown in FIG. 3, the rear side of the distal end portion 9 is covered with a flexible tube 25. Also, the pickup section 13
A lead gland 26 extends therefrom.
このように構成された第１実施例の動作を以下に説明す
る。The operation of the first embodiment configured in this way will be described below.
第３図に示す先端部９の出入口１５．１６のねじ１７．
１８を外して開き、冷媒１４を注入する。Screws 17. of the openings 15.16 of the tip 9 shown in FIG.
18, open it, and inject the refrigerant 14.
その後、ねじ１７，１８を締め、冷部室１１を密閉する
。しかる後、このカテーテル２を体腔内に挿入し、先端
部９を測定部位に近い位置まで送り込む。例えば食道を
通して心臓の近くに挿入したり、気管支を通して肺の内
部又はその近くに挿入して、これらの臓器の磁気を測定
する。しかして、測定部位が磁気を発する部位であると
、その磁束がピックアップコイル２１を通る。また、Ｒ
Ｆ発振器４からも共振回路にＲＦ雷電流供給され、リン
グ２３には磁束が通ろうとする。この場合、ピックアッ
プコイル２１に誘起される電流の大きさに応じて、リン
グ２３には電流変化が生じる。この電流変化のタイミン
グはピックアップコイル２１に誘起される電流の大きさ
に応じてずれる。この変化はバ振回路の゛辻圧変化とな
り、ＲＦアンプ５で増幅され、ロックインアンプ６によ
り位相検波される。このロックインアンプ６の出力は抵
抗Ｒを介して共振回路にフィードバックする。このフィ
ードバック電流を取り出し、プロセッサ７により処理し
、モニタ８上に第１図に示すように画像化する。Thereafter, screws 17 and 18 are tightened to seal the cold compartment 11. Thereafter, this catheter 2 is inserted into the body cavity, and the distal end portion 9 is sent to a position close to the measurement site. For example, it is inserted through the esophagus near the heart or through the bronchus into or near the lungs to measure the magnetism of these organs. Therefore, if the measurement site is a site that emits magnetism, the magnetic flux passes through the pickup coil 21. Also, R
RF lightning current is also supplied from the F oscillator 4 to the resonant circuit, and magnetic flux attempts to pass through the ring 23. In this case, a current change occurs in the ring 23 depending on the magnitude of the current induced in the pickup coil 21. The timing of this current change is shifted depending on the magnitude of the current induced in the pickup coil 21. This change becomes a cross-pressure change in the vibration circuit, is amplified by the RF amplifier 5, and phase-detected by the lock-in amplifier 6. The output of this lock-in amplifier 6 is fed back to the resonant circuit via a resistor R. This feedback current is taken out, processed by the processor 7, and displayed as an image on the monitor 8 as shown in FIG.
この第１実施例によれば、５ＱＬＩＩＤ磁束計を体腔内
に挿入し、磁気計測できる構造にしであるので、今まで
測定が困難であった体内深部での磁気を体腔内に挿入し
て近い位置にて高感度で測定ザることができる。According to this first embodiment, since the 5QLIID magnetometer is inserted into the body cavity and has a structure that allows magnetic measurement, magnetism deep inside the body, which has been difficult to measure until now, can be measured at a nearby position by inserting it into the body cavity. Measurements can be made with high sensitivity.
第４図は本発明の第２実施例を示す。FIG. 4 shows a second embodiment of the invention.
この第２実施例は内視鏡４１にピックアップ部１３を設
けた構造にしている。This second embodiment has a structure in which an endoscope 41 is provided with a pickup section 13.
上記内視ｔＡ４１は、細長の挿入部４２内に照明光を伝
送するライトガイド４３が例えば上部側に偏心して挿通
され、挿入部先端部４４に固定された出射端面から照明
光を出射づる。先端部４４にはライトガイド４３に隣接
して、対物レンズ４５が取付けられ、この対物レンズ４
５の焦点面にはファイババンドルで形成したイメージガ
イド４６の入射端面が配置され、このイメージガイド４
６により光学像を伝送し、図示しない接眼側の出射端面
に対向配置した接眼レンズを介して肉眼観察できるよう
にしである。In the endoscopic view tA41, a light guide 43 for transmitting illumination light is inserted into the elongated insertion portion 42, for example, eccentrically toward the upper side, and emits illumination light from an output end face fixed to the insertion portion distal end portion 44. An objective lens 45 is attached to the tip 44 adjacent to the light guide 43.
The incident end surface of an image guide 46 formed of a fiber bundle is arranged at the focal plane of the image guide 4.
6, the optical image is transmitted so that it can be observed with the naked eye through an eyepiece (not shown) disposed opposite to the output end face on the eyepiece side.
上記先端部４４における下部側には、冷却室５１が設け
られ、この冷ｆＪＩ室５１内にはピックアップ部１３が
収納され、このピックアップ部１３は固定部材５２を介
して冷却室５１に固定される。A cooling chamber 51 is provided on the lower side of the tip portion 44, and the pickup section 13 is housed in the cold fJI chamber 51, and the pickup section 13 is fixed to the cooling chamber 51 via a fixing member 52. .
この固定部材５２は例えばパイプ状で、その内側にはピ
ックアップ部１３とＲＦアンプ５等とを接続する信号伝
送線５３が通しである。This fixing member 52 has a pipe shape, for example, and a signal transmission line 53 connecting the pickup section 13 and the RF amplifier 5 etc. is passed through the inside thereof.
上記冷却室５１内には、液体窒素等の冷媒５４を注入可
能にする出入口５５．５６が設けである。The cooling chamber 51 is provided with ports 55 and 56 through which a refrigerant 54 such as liquid nitrogen can be injected.
各出入口５５．５６は第５図に示すように例えば円弧形
状（この円弧より小ざな開口でも良い。）であり、それ
ぞれピン５７．５８の軸の回りで回動可能な蓋５９．６
０にて開閉できるようにしである。つまり、ｆ１５９．
６０は円板形状の一部を切欠いた切欠き又は孔が設けて
あり、第４図及び第５図に示す状態では出入口５５．５
６はＵ■いた状態になり、第６図に示すように’ｎ５’
９．６０を例えば１８０°回動した状態では閉じた状態
になる。 尚、先端部４４の後端には可撓性のチューブ
６１の前端が固着されている。このチューブ６１の内側
には例えば（図示しない）関節層を縦列して湾曲部が形
成されている。As shown in FIG. 5, each of the entrances and exits 55, 56 is, for example, in the shape of a circular arc (an opening smaller than this circular arc may also be used), and each lid 59, 56 is rotatable around the axis of a pin 57, 58.
It is designed so that it can be opened and closed at 0. In other words, f159.
Reference numeral 60 has a notch or hole formed by cutting out a part of the disk shape, and in the state shown in FIGS. 4 and 5, the entrance 55.5
6 is in the state of U■, and as shown in Figure 6, 'n5'
For example, when 9.60 is rotated by 180 degrees, it is in a closed state. Note that the front end of a flexible tube 61 is fixed to the rear end of the distal end portion 44 . A curved portion is formed inside the tube 61 by arranging articular layers (not shown) in tandem, for example.
このように構成された第２実施例の動作を以下に説明す
る。The operation of the second embodiment configured in this way will be described below.
先端部４４の１５９．６０を回動して、第５図に示ずよ
うに出入口５５．５６と６５９．６０の切欠きとを連通
させ、冷媒５４を注入し、その後１１５９．６０を回動
し、第６図に示すように出入口５５．５６を塞ぐ。しか
る後、内視鏡４１を通常の内視鏡検査のように、体腔内
に挿入した後、観察しながら先端部４４を測定部位へと
近接する位置へと移動操作をする。しかして測定部位か
らの磁束をピックアップ部１３のピックアップコイル２
１により取り込み、適宜処理を行ない、診断を行なう。Turn 159.60 of the tip 44 to communicate the inlet/outlet 55.56 with the notch 659.60 as shown in FIG. 5, inject the refrigerant 54, and then turn 1159.60. Then, as shown in FIG. 6, the entrances and exits 55 and 56 are closed. Thereafter, the endoscope 41 is inserted into the body cavity as in a normal endoscopy, and the distal end 44 is moved to a position close to the measurement site while observing. Therefore, the magnetic flux from the measurement site is transferred to the pickup coil 2 of the pickup section 13.
1, perform appropriate processing, and perform diagnosis.
この第２実施例によれば、目視により位置を確認しなが
ら磁気測定を行なうことができるので、より正確な測定
が可能となる。というのは、ただでさえ微弱な磁束なの
で測定位冒により１りられる知見が大きく異なってくる
からである。また、磁気による診断と同時に目視による
診断も行なえる。According to this second embodiment, magnetic measurement can be performed while visually confirming the position, so more accurate measurement is possible. This is because the magnetic flux is already weak, so the findings that can be obtained will vary greatly depending on the measurement position. In addition, visual diagnosis can be performed simultaneously with magnetic diagnosis.
従って、術とは診断を短時間で終了できると共に、患者
の苦痛も大幅に軽減される。Therefore, the surgery allows diagnosis to be completed in a short period of time, and the patient's pain is significantly reduced.
第７図は本発明の第３実施例の主要部を示す。FIG. 7 shows the main parts of a third embodiment of the present invention.
この実施例も第２実施例と同様に内視１４１’にピック
アップ部１３′を設けたものである。先端部４４′には
、例えば前端面に凹部を形成し、ピックアップ部１３′
が収納すると共に、半導体冷却素子７１を収納している
。この半導体冷却素子７１の反対側のピックアップ部１
３′の周囲は断熱材７２で覆われている。This embodiment is also similar to the second embodiment in that a pickup section 13' is provided in the endoscope 141'. For example, a recess is formed in the front end surface of the tip portion 44', and the pickup portion 13'
, and also houses a semiconductor cooling element 71. The pickup section 1 on the opposite side of this semiconductor cooling element 71
3' is covered with a heat insulating material 72.
上記半導体冷却素子７１は、リード線７３を介して冷却
用電力が供給される。尚、ピックアップ部１３′の前端
側は、断熱性のガラス等で覆われ、このガラスで覆われ
た前端側を磁気を検出しようと望む被検部位に近接でき
るようにしである。The semiconductor cooling element 71 is supplied with cooling power through a lead wire 73. The front end side of the pickup section 13' is covered with a heat insulating glass or the like, so that the front end side covered with this glass can be brought close to the test site where the magnetic field is to be detected.
尚、ピックアップ部１３′において、ピックアップコイ
ル２１′はそのループ面が先端部４４′の前端面と平行
に配置して磁束をピックアップし易いように設定しであ
る。その他は上記第２実施例と同様の構造であり、同一
要素には同一符号に１１１！１を付りて示しである。In the pickup section 13', the pickup coil 21' is arranged so that its loop surface is parallel to the front end surface of the tip section 44' to facilitate pickup of magnetic flux. The rest of the structure is the same as that of the second embodiment, and the same elements are indicated by the same reference numerals with 111!1 added.
この第３実施例は半導体冷却素子７１によってピックア
ップ部１３′を冷却する構造であるので、ジョセフソン
効果を利用した超伝導リング２３としては、高温度で超
伝導になるセラミック系を用いている。Since this third embodiment has a structure in which the pickup section 13' is cooled by a semiconductor cooling element 71, a ceramic material that becomes superconductive at high temperatures is used as the superconducting ring 23 that utilizes the Josephson effect.
上述した各実施例では５ＱＵＩＤ磁束計として、ジョセ
フソン接合が１つのＲＦスクイドを用いたが、ジョセフ
ソン接合が２つとしたＤＣスクイドを用いても良い。In each of the embodiments described above, an RF SQUID with one Josephson junction was used as the 5QUID magnetometer, but a DC SQUID with two Josephson junctions may be used.
また、ピックアップ部が２次勾配型磁束計でなく、１次
勾配型磁束計を用いても良い。また冷媒は用いる超伝導
材料によって、液体へり１クム、液体窒素、液体濱素を
用いても良い。また近年、製作後項期間のみ高温で超伝
導となる材料が報告されているが、これらを用いた場合
、液体二酸化炭素、ドライアイス、アルコールとか塞材
等を冷媒に用いても良い。また、ピックアップコイルに
用１、、Ｎル材料ハＹ−Ｂａ−ＣｕＯのみでなく Ｂａ
−３ｒ−’／−Ｃｕ−０系でもＢａ−Ｙ−Ｃｕ−０−Ｆ
系でも［ｕ−Ｂａ−Ｃｕ系でも［ｕ−３ｒ−Ｃｕ系など
の材料を用いても良い。Furthermore, the pickup section may use a first-order gradient magnetometer instead of a second-order gradient magnetometer. Further, depending on the superconducting material used, the refrigerant may be liquid 1 cum, liquid nitrogen, or liquid hydrogen. Furthermore, in recent years, materials have been reported that become superconductive at high temperatures only during the post-production period, but when these are used, liquid carbon dioxide, dry ice, alcohol, or a plugging material may be used as a refrigerant. In addition, not only Y-Ba-CuO but also Ba
-3r-'/-Cu-0 system also Ba-Y-Cu-0-F
Materials such as [u-Ba-Cu system, [u-3r-Cu system] may be used.
またこの他、カテーテル内視鏡に処理用のヂ１！ンネル
を設けても良い。またスクイド素子のみでなく、超伝導
磁気抵抗素子を組み込んでも良い。In addition to this, there is also one for processing in catheter endoscopes! A channel may also be provided. In addition to the SQUID element, a superconducting magnetoresistive element may also be incorporated.
また、フラックスゲート磁束計、ホール素子磁束計等を
用いても良い。Alternatively, a fluxgate magnetometer, a Hall element magnetometer, or the like may be used.
また、内視鏡、カテーテルの本体はセラミック、プラス
チック、非磁性金属等の非磁性材料を用いて作成する。In addition, the bodies of endoscopes and catheters are made using non-magnetic materials such as ceramics, plastics, and non-magnetic metals.
これにより測定部以外からの磁気（特に内視鏡、カテー
テルの本体からの磁気）が測定結果に影響を与えること
がない。This prevents magnetism from sources other than the measuring section (particularly magnetism from the endoscope and catheter body) from affecting the measurement results.
尚、第２又は第３実施例において、ピックアップ部とか
その周囲の冷却室等を着脱自在の構造にすることもでき
る。Incidentally, in the second or third embodiment, the pickup section and the cooling chamber around it can also be constructed to be detachable.
［発明の効果］
以上述べたように本発明によれば体腔内に挿入可能な挿
入用具にジョセフソン接合を利用した磁束のピックアッ
プ手段を収納しているので、体腔内の深部の部位に対し
て近接して磁気を測定することができる。[Effects of the Invention] As described above, according to the present invention, the magnetic flux pickup means using Josephson junction is housed in the insertion tool that can be inserted into the body cavity. Magnetism can be measured in close proximity.
第１図ないし第３図は本発明の第１実施例に係り、第１
図は第１実論例の電気系の構成図、第２図は第１実施例
の概略の外観図、第３図はカテーテルの先端部の構造を
示す断面図、第４図は本発明の第２実施例の先端側の構
造を示す概略断面図、第５図は第４図の底面図、第６図
は冷却室の出入口を閉じた状態での第４図の底面図、第
７図は本発明の第３実施例の先端側を示す概略断面図で
ある。
１・・・生体磁気計測用体腔内挿入用具２・・・カテー
テル ３・・・接続コード４・・・ＲＦ発振器
５・・・ＲＦアンプ６・・・ロックインアンプ
７・・・プロセッサ８・・・モニタ １１・
・・冷却室１３・・・ピックアップ部 １４・・・冷媒
２１・・・ピックアップコイル
２２・・・ジョセフソン接合
２３・・・リング
第２図
第３図
第６図
第７図Figures 1 to 3 relate to the first embodiment of the present invention.
The figure is a configuration diagram of the electrical system of the first practical example, FIG. 2 is a schematic external view of the first embodiment, FIG. A schematic sectional view showing the structure on the tip side of the second embodiment, FIG. 5 is a bottom view of FIG. 4, FIG. 6 is a bottom view of FIG. 4 with the entrance and exit of the cooling chamber closed, and FIG. 7 FIG. 3 is a schematic sectional view showing the distal end side of a third embodiment of the present invention. 1... Intrabody cavity insertion tool for biomagnetic measurement 2... Catheter 3... Connection cord 4... RF oscillator
5...RF amplifier 6...Lock-in amplifier
7...Processor 8...Monitor 11.
...Cooling chamber 13...Pickup section 14...Refrigerant 21...Pickup coil 22...Josephson junction 23...Ring Fig. 2 Fig. 3 Fig. 6 Fig. 7
Claims (1)
効果を利用した磁気計測手段を設けたことを特徴とする
生体磁気計測用体腔内挿入用具。1. A body cavity insertion device for biomagnetism measurement, characterized in that a magnetic measurement means utilizing the Josephson effect is provided at the tip of the body cavity insertion device inserted into a body cavity.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62311299A JP2519275B2 (en) | 1987-12-08 | 1987-12-08 | Tool for inserting into body cavity for biomagnetic measurement |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62311299A JP2519275B2 (en) | 1987-12-08 | 1987-12-08 | Tool for inserting into body cavity for biomagnetic measurement |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH01151438A true JPH01151438A (en) | 1989-06-14 |
| JP2519275B2 JP2519275B2 (en) | 1996-07-31 |
Family
ID=18015460
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP62311299A Expired - Fee Related JP2519275B2 (en) | 1987-12-08 | 1987-12-08 | Tool for inserting into body cavity for biomagnetic measurement |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2519275B2 (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2006122203A1 (en) * | 2005-05-11 | 2006-11-16 | The University Of Houston System | An intraluminal magneto sensor system and method of use |
| US8380279B2 (en) | 2005-05-11 | 2013-02-19 | The University Of Houston System | Intraluminal multifunctional sensor system and method of use |
| JPWO2016021633A1 (en) * | 2014-08-05 | 2017-08-03 | 国立大学法人 東京医科歯科大学 | Biomagnetic measurement device |
| WO2021070094A1 (en) * | 2019-10-07 | 2021-04-15 | Asahi Intecc Co., Ltd. | Intracardiac catheter device and methods of use thereof |
-
1987
- 1987-12-08 JP JP62311299A patent/JP2519275B2/en not_active Expired - Fee Related
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2006122203A1 (en) * | 2005-05-11 | 2006-11-16 | The University Of Houston System | An intraluminal magneto sensor system and method of use |
| US8212554B2 (en) | 2005-05-11 | 2012-07-03 | The University Of Houston System | Intraluminal magneto sensor system and method of use |
| US8380279B2 (en) | 2005-05-11 | 2013-02-19 | The University Of Houston System | Intraluminal multifunctional sensor system and method of use |
| JPWO2016021633A1 (en) * | 2014-08-05 | 2017-08-03 | 国立大学法人 東京医科歯科大学 | Biomagnetic measurement device |
| US10952631B2 (en) | 2014-08-05 | 2021-03-23 | National University Corporation Tokyo Medical And Dental University | Biomagnetism measurement device |
| WO2021070094A1 (en) * | 2019-10-07 | 2021-04-15 | Asahi Intecc Co., Ltd. | Intracardiac catheter device and methods of use thereof |
| CN114554959A (en) * | 2019-10-07 | 2022-05-27 | 朝日英达科株式会社 | Intracardiac catheter apparatus and methods of use |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2519275B2 (en) | 1996-07-31 |
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