JPH0529690Y2 - - Google Patents
Info
- Publication number
- JPH0529690Y2 JPH0529690Y2 JP1985001388U JP138885U JPH0529690Y2 JP H0529690 Y2 JPH0529690 Y2 JP H0529690Y2 JP 1985001388 U JP1985001388 U JP 1985001388U JP 138885 U JP138885 U JP 138885U JP H0529690 Y2 JPH0529690 Y2 JP H0529690Y2
- Authority
- JP
- Japan
- Prior art keywords
- fluorescent material
- material layer
- organic fluorescent
- optical fiber
- fluorescence
- 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 - Lifetime
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- Investigating, Analyzing Materials By Fluorescence Or Luminescence (AREA)
- Investigating Or Analysing Biological Materials (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Description
【考案の詳細な説明】
〔産業上の利用分野〕
本考案は、血液中から生体組織を経て拡散して
くるO2ガスを皮膚表面にて測定する経皮酸素セ
ンサに関するものである。[Detailed Description of the Invention] [Industrial Application Field] The present invention relates to a transcutaneous oxygen sensor that measures O 2 gas that diffuses from blood through living tissue at the skin surface.
動脈血中のO2分布を測定するには直接動脈中
の血液を採取して測定する方法があるが、連続的
にO2分布を測定することはできず、しかも新生
児や重症患者には著しい負担となる。冒頭に述べ
た経皮酸素センサによれば、このような問題は解
消される。第５図はその構造例を示すもので、セ
ンサの基体１は互に係合するセル１ａとホルダ１
ｂとより構成されている。ホルダ１ｂの周囲には
温度センサ２及びヒータ３が埋込まれ、温度セン
サ２の検出信号を基に加温制御器４が所定の温度
に皮膚を加温するようにヒータ３へ給電する。ホ
ルダ１ｂの前面には、スペーサ５とで挟持される
ことにより半透膜６が配設され、その内部には電
解液７が収容されている。そしてこの電解液内へ
それぞれリード線の導出された陽極８ａ及び陰極
８ｂから成る電極８が浸漬されている。この経皮
酸素センサを測定部位の皮膚に当てると、加温に
より動脈が拡張し、血管から酸素ガスが拡散して
きて半透膜６を透過して電解液７へ溶込む。これ
により、電気分解が起り、電極８ａ，８ｂを通流
する電解電流値よりO2分布が測定される。
There is a method to measure O 2 distribution in arterial blood by directly collecting blood from the artery, but it is not possible to measure O 2 distribution continuously, and it is a significant burden on newborns and critically ill patients. becomes. According to the transcutaneous oxygen sensor mentioned at the beginning, this problem is solved. FIG. 5 shows an example of the structure, in which the base body 1 of the sensor includes a cell 1a and a holder 1 that engage with each other.
It is composed of b. A temperature sensor 2 and a heater 3 are embedded around the holder 1b, and based on a detection signal from the temperature sensor 2, a heating controller 4 supplies power to the heater 3 to heat the skin to a predetermined temperature. A semipermeable membrane 6 is disposed on the front surface of the holder 1b by being sandwiched between spacers 5, and an electrolytic solution 7 is housed inside the semipermeable membrane 6. Electrodes 8 consisting of an anode 8a and a cathode 8b, each having a lead wire led out, are immersed in this electrolyte. When this transcutaneous oxygen sensor is applied to the skin at the measurement site, the arteries expand due to heating, and oxygen gas diffuses from the blood vessels, passes through the semipermeable membrane 6, and dissolves into the electrolytic solution 7. As a result, electrolysis occurs, and the O 2 distribution is measured from the electrolytic current value flowing through the electrodes 8a and 8b.
しかしながら、この種の経皮酸素センサでは、
電解液を使用するためにその蒸発で長期保管が不
可能であり、また電解液及び電極等の劣化のため
にせいぜい６時間程度の連続使用しかできず、応
答時間も20秒以上であつた。また、電極が酸素を
消費するために、特に成人の場合では血液ガスと
の差が大きくなり、これを回避するために半透膜
に酸素透過度の低い膜を使用すると、応答時間が
さらに長くなつていた。検出信号も高インピーダ
ンスで、しかも微弱であるために電気メス、ハム
等の外部雑音に弱かつた。
However, with this type of transcutaneous oxygen sensor,
Since an electrolytic solution is used, long-term storage is impossible due to evaporation of the electrolytic solution, and due to deterioration of the electrolytic solution, electrodes, etc., continuous use is only possible for about 6 hours at most, and the response time is 20 seconds or more. In addition, since the electrode consumes oxygen, the difference with blood gas becomes large, especially in adults, and to avoid this, using a membrane with low oxygen permeability as a semipermeable membrane further lengthens the response time. I was getting used to it. The detection signal also has high impedance and is weak, making it vulnerable to external noise such as electric scalpels and hum.
一方、特開昭58−154641によれば、励起光によ
り照射された蛍光物質の光放射の減少を測定する
ことにより、患者の身体内へ挿入して組織内の酸
素濃度を測定する酸素濃度測定装置が開示されて
いる。これにより、使用時間を長くでき、外部雑
音に対する影響を受け難く、ドリフトも少なくで
きる組織内の酸素測定が可能になる。しかしなが
ら、この装置は、経皮酸素の測定を意図したもの
ではなかつた。 On the other hand, according to Japanese Patent Application Laid-Open No. 58-154641, oxygen concentration measurement is performed by inserting it into the patient's body and measuring the oxygen concentration in the tissue by measuring the decrease in light emission of a fluorescent substance irradiated with excitation light. An apparatus is disclosed. This makes it possible to measure oxygen in tissues, which can be used for a longer period of time, is less susceptible to external noise, and has less drift. However, this device was not intended for measuring transcutaneous oxygen.
本考案は、このような有機系蛍光物質の蛍光強
度が、電子親和力が大である酸素ガスにより著し
く低減する消光作用を経皮酸素測定にも応用でき
ることを確認して、前述の欠点を解消する経皮酸
素センサを提供することを目的とする。 The present invention eliminates the above-mentioned drawbacks by confirming that the quenching effect, in which the fluorescence intensity of organic fluorescent substances is significantly reduced by oxygen gas, which has a high electron affinity, can also be applied to transcutaneous oxygen measurements. The purpose is to provide a transcutaneous oxygen sensor.
本考案は、この目的を達成するために、動脈拡
張用ヒータを備えた基体の前面に、透明板に蛍光
物質を形成した有機系蛍光物質層を着脱自在に設
けると共に、基体内に有機系蛍光物質層の背面に
対してほぼ45°の反射面を有する反射体を設け、
さらに基体の側面から反射面に対してほぼ45°で
先端面が対面した光フアイバを有機系蛍光物質層
に沿つた方向に導出し、この光フアイバの後端
に、有機系蛍光物質層を励起する光源及びこの励
起により生じた蛍光を検出する蛍光検出部を接続
したことを特徴とする。有機系蛍光物質層として
は、多孔性ガラスに蛍光物質を吸着させたもの、
透明基板上の溶媒に蛍光物質を溶解させたもの、
透明基板上のマトリツクスポリマに蛍光物質を分
散させたもの等が考えられる。
In order to achieve this objective, the present invention has removably provided an organic fluorescent material layer in which a fluorescent material is formed on a transparent plate on the front surface of a base body equipped with an artery dilation heater, and an organic fluorescent material layer within the base body. A reflector having a reflective surface at an angle of approximately 45° to the back surface of the material layer is provided,
Furthermore, an optical fiber whose tip face faces the reflective surface at approximately 45 degrees is guided from the side of the substrate in a direction along the organic fluorescent material layer, and the organic fluorescent material layer is excited at the rear end of this optical fiber. The present invention is characterized in that a light source for excitation and a fluorescence detection section for detecting fluorescence generated by this excitation are connected. The organic fluorescent material layer includes porous glass with fluorescent material adsorbed,
A fluorescent substance dissolved in a solvent on a transparent substrate,
A possible example is one in which a fluorescent substance is dispersed in a matrix polymer on a transparent substrate.
有機系蛍光物質が、皮膚に沿つて導出された光
フアイバを通して到達した光源からの励起光によ
り背後から励起されると、蛍光が発せられ、光フ
アイバを逆方向に伝達されて蛍光検出部で検出可
能となる。この状態で皮膚から拡散してきた酸素
ガスは、有機系蛍光物質まで到達し、蛍光物質へ
消光反応を惹起させる。したがつて、蛍光検出部
では、酸素ガスの増量に対応して減少する光量の
蛍光が検出される。
When an organic fluorescent substance is excited from behind by excitation light from a light source that reaches through an optical fiber guided along the skin, fluorescence is emitted, which is transmitted in the opposite direction through the optical fiber and detected by a fluorescence detection unit. It becomes possible. The oxygen gas that has diffused from the skin in this state reaches the organic fluorescent material and causes a quenching reaction in the fluorescent material. Therefore, the fluorescence detection section detects fluorescence with a decreasing amount of light corresponding to an increase in the amount of oxygen gas.
第１図〜第３図は、本考案の一実施例による経
皮酸素センサを示す。
1 to 3 show a transcutaneous oxygen sensor according to an embodiment of the present invention.
第３図は経皮酸素センサを示すもので、基体１
１の凹部１１ａの前面段階部１１ｂに有機系蛍光
物質層（以下、単に蛍光層とする）１５が嵌入さ
れ、側面に温度センサ２及びヒータ３が埋込ま
れ、さらに光フアイバ２０が取付けられて構成さ
れている。温度センサ１２及びヒータ１３は付属
の加温制御器と共に前述の如く皮膚を一定温度
（42〜44℃程度）に保持する。蛍光層１５は、例
えばガラス板１５ａにピレン、コロネン、ペリレ
ン等の有機系蛍光物質１５ｂを塗布して形成す
る。そして粘着テープ、弾性等を利用して段階部
１１ｂに着脱可能に成つており、装着状態でガラ
ス板１５ａが凹部１１ａに対して気密にする。 Figure 3 shows a transcutaneous oxygen sensor, with base 1
An organic fluorescent substance layer (hereinafter simply referred to as a fluorescent layer) 15 is fitted into the front step portion 11b of the recess 11a of the recess 1, a temperature sensor 2 and a heater 3 are embedded in the side surface, and an optical fiber 20 is attached. It is configured. The temperature sensor 12 and heater 13, together with the attached heating controller, maintain the skin at a constant temperature (approximately 42 to 44°C) as described above. The fluorescent layer 15 is formed, for example, by coating a glass plate 15a with an organic fluorescent material 15b such as pyrene, coronene, or perylene. The glass plate 15a can be attached to and removed from the stepped portion 11b using adhesive tape, elasticity, etc., and the glass plate 15a is airtight with respect to the recessed portion 11a in the attached state.
基体１１の側面から導出された光フアイバ２０
は、第１図に示すように、励起光用及び蛍光用光
フアイバ２０ａ，２０ｂに分岐しており、共通部
フアイバ２０ｃでは両者２０ａ，２０ｂの素子が
同心円状（第２図ａ）又はランダム（第２図ｂ）
に混合されている。また、基体１１の凹部１１ａ
には、蛍光層１５の背面に対してほぼ45°の反射
面を有するミラー４３が設けられている。共通部
フアイバ２０ｃの先端面２０ｄは、ミラー４３の
反射面にほぼ45°で対面している。 Optical fiber 20 led out from the side of base 11
As shown in Fig. 1, the optical fibers 20a and 20b are branched into excitation light and fluorescence optical fibers 20a and 20b, and in the common fiber 20c, the elements of both 20a and 20b are arranged concentrically (Fig. 2a) or randomly (Fig. 2a). Figure 2 b)
is mixed with. In addition, the recess 11a of the base 11
A mirror 43 having a reflective surface at an angle of approximately 45° to the back surface of the fluorescent layer 15 is provided. The distal end surface 20d of the common fiber 20c faces the reflective surface of the mirror 43 at approximately 45 degrees.
励起光用光フアイバ２０ａの後端は、励起光
（波長300〜400nm）を透光するフイルタ３１を通
して励起用光源、例えば水銀ランプ３２に接続す
る。蛍光用光フアイバ２０ｂの後端には、蛍光
（波長400〜500nm）を透光するフイルタ３３を通
して光検出器、例えばフオトマルチプライヤー３
４と、その検出信号の増幅器３５と、その増幅信
号を励起用光源３２の駆動交流電源に対して同期
検波する検波器３６と、その検波出力をO2分圧
対蛍光量の非直線に対して直線化するリニアライ
ザ３７とが接続する。 The rear end of the excitation light optical fiber 20a is connected to an excitation light source, such as a mercury lamp 32, through a filter 31 that transmits excitation light (wavelength: 300 to 400 nm). At the rear end of the fluorescence optical fiber 20b, a photodetector such as a photomultiplier 3 is inserted through a filter 33 that transmits fluorescence (wavelength: 400 to 500 nm).
4, an amplifier 35 for the detection signal, a detector 36 for synchronously detecting the amplified signal with respect to the driving AC power supply of the excitation light source 32, and a detector 36 for synchronously detecting the amplified signal with respect to the driving AC power supply of the excitation light source 32, and for detecting the detection output against the non-linearity of O 2 partial pressure versus fluorescence amount. A linearizer 37 is connected to the straight line.
測定に際しては、両面テープを利用して加温さ
れた基体１１の前面周囲を皮膚に貼着し、励起用
光源３２により光フアイバ２０ａ，２０ｃ、ミラ
ー４３及びガラス板１５ａを通して蛍光物質１５
ｂを励起する。動脈血化した毛細血管内からは酸
素ガスが拡散してきて、蛍光物質１５ｂまで到達
する。経皮O2分圧に対応する発光量の蛍光は、
光フアイバ２０ｃ，２０ｂを通して光検出器３４
で電気信号に変換され、増幅・検波・直線化され
てO2分圧値を指示する。この際、フイルタ３３
の存在により蛍光のみが検出されるために高精度
の測定が可能であり、またフイルタ３１の存在に
より、光源側へ侵入した蛍光が吸収されるため
に、多重反射による蛍光が検出側に伝達されるこ
とがなく、一層精度が向上する。蛍光層１５の厚
みは、酸素ガスが素早く透過して１秒以下の応答
時間を与える程度にしても十分な検出感度が得ら
れる。数日間の連続使用により蛍光物質の劣化し
た場合には、蛍光層１５を基体１１から外し、新
しいものと交換する。 For measurement, the heated front surface of the substrate 11 is attached to the skin using double-sided tape, and the fluorescent substance 15 is applied using the excitation light source 32 through the optical fibers 20a, 20c, the mirror 43, and the glass plate 15a.
Excite b. Oxygen gas diffuses from within the capillaries that have become arterial blood and reaches the fluorescent material 15b. The amount of fluorescence corresponding to the transcutaneous O2 partial pressure is
A photodetector 34 is passed through the optical fibers 20c and 20b.
It is converted into an electrical signal, amplified, detected, and linearized to indicate the O 2 partial pressure value. At this time, the filter 33
Due to the presence of the filter 31, only the fluorescence is detected, making it possible to perform highly accurate measurements.Furthermore, the presence of the filter 31 absorbs the fluorescence that has entered the light source side, so that the fluorescence due to multiple reflections is not transmitted to the detection side. The accuracy is further improved. Sufficient detection sensitivity can be obtained even if the thickness of the fluorescent layer 15 is set to such a value that oxygen gas passes through it quickly and provides a response time of 1 second or less. If the fluorescent material deteriorates after several days of continuous use, the fluorescent layer 15 is removed from the base 11 and replaced with a new one.
第４図は、同様に基体前面と皮膚との密着を容
易にするために基体５１からそれぞれ光フアイバ
２０を側方へ導出した別の実施例を示すもので、
ミラー４３に代えて基体５１内にプリズム５３が
収納されている。他の部分は第１図と同様な構成
にする。 FIG. 4 shows another embodiment in which optical fibers 20 are led out to the sides from the base 51 in order to facilitate close contact between the front surface of the base and the skin.
A prism 53 is housed in the base body 51 instead of the mirror 43. The other parts have the same structure as in FIG.
以上、本考案によれば、蛍光物質自体の劣化が
少ないために、通常の用途では数日間の連続使用
が可能になる。蛍光物質への酸素透過時間も含め
た蛍光現象の応答が速く、生体の急激な変動にも
追従可能である。酸素ガスを全く消費しないため
に、その拡散が悪い成人でも血液ガス値との差が
少なくなる。光学的測定であるために外部雑音に
対しては全く影響を受けず、蛍光量は温度に対し
安定なのでドリフトが少なくなる。さらに、基体
の側面から光フアイバが導出され、皮膚へセンサ
を密着させるのも容易となり、蛍光物質は基板交
換式に容易に交換できる。
As described above, according to the present invention, since the fluorescent material itself has little deterioration, continuous use for several days is possible in normal applications. The response of the fluorescence phenomenon, including the oxygen permeation time to the fluorescent material, is fast, and it is possible to follow rapid changes in living organisms. Since oxygen gas is not consumed at all, the difference with blood gas values is reduced even in adults with poor oxygen diffusion. Since it is an optical measurement, it is completely unaffected by external noise, and the amount of fluorescence is stable with respect to temperature, which reduces drift. Furthermore, the optical fiber is led out from the side surface of the base, making it easy to bring the sensor into close contact with the skin, and the fluorescent material can be easily replaced by replacing the substrate.
第１図は本考案の実施例による経皮酸素センサ
の光フアイバ部分の構成を示す図、第２図はその
光フアイバの先端断面図、第３図は光フアイバに
接続する経皮酸素センサの断面図、第４図は別の
実施例の要部断面図並びに第５図は従来の経皮酸
素センサの断面図である。
２……温度センサ、３……ヒータ、１１，５１
……基体、１５……有機系蛍光物質層、１５ａ…
…ガラス板、１５ｂ……有機系蛍光物質、２０…
…光フアイバ、４３……ミラー、５３……プリズ
ム。
Fig. 1 is a diagram showing the configuration of the optical fiber part of a transcutaneous oxygen sensor according to an embodiment of the present invention, Fig. 2 is a sectional view of the tip of the optical fiber, and Fig. 3 is a diagram showing the structure of the transcutaneous oxygen sensor connected to the optical fiber. 4 is a sectional view of a main part of another embodiment, and FIG. 5 is a sectional view of a conventional transcutaneous oxygen sensor. 2... Temperature sensor, 3... Heater, 11, 51
...Substrate, 15...Organic fluorescent material layer, 15a...
...Glass plate, 15b...Organic fluorescent material, 20...
...Optical fiber, 43...Mirror, 53...Prism.
Claims (1)
板に蛍光物質を形成した有機系蛍光物質層を着脱
自在に設けると共に、前記基体内に前記有機系蛍
光物質層の背面に対してほぼ45°の反射面を有す
る反射体を設け、さらに前記基体の側面から前記
反射面に対してほぼ45°で先端面が対面した光フ
アイバを前記有機系蛍光物質層に沿つた方向に導
出し、 この光フアイバの後端に、前記有機系蛍光物質
層を励起する光源及びこの励起により生じた蛍光
を検出する蛍光検出部を接続したことを特徴とす
る経皮酸素センサ。[Claims for Utility Model Registration] An organic fluorescent material layer, which is a transparent plate with a fluorescent material formed thereon, is removably provided on the front surface of a base body provided with an artery dilation heater, and the organic fluorescent material layer is provided within the base body. A reflector having a reflective surface at an angle of approximately 45° to the back surface of the substrate is provided, and an optical fiber whose tip face faces the reflective surface at an angle of approximately 45° is placed along the organic fluorescent material layer from the side surface of the substrate. A transcutaneous oxygen sensor, characterized in that a light source that excites the organic fluorescent material layer and a fluorescence detection section that detects fluorescence generated by the excitation are connected to the rear end of the optical fiber.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1985001388U JPH0529690Y2 (en) | 1985-01-11 | 1985-01-11 |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1985001388U JPH0529690Y2 (en) | 1985-01-11 | 1985-01-11 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS61118057U JPS61118057U (en) | 1986-07-25 |
| JPH0529690Y2 true JPH0529690Y2 (en) | 1993-07-29 |
Family
ID=30474088
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1985001388U Expired - Lifetime JPH0529690Y2 (en) | 1985-01-11 | 1985-01-11 |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0529690Y2 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2014002388A1 (en) * | 2012-06-29 | 2014-01-03 | セイコーエプソン株式会社 | Substance detection device and wristwatch type body fat burning measurement device |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP2773266B1 (en) * | 2011-10-31 | 2022-11-30 | Sentec Ag | A device for application of a sensor to a measurement site, a kit of an application device and sensor and use of an application device for optical measurements of physiological parameters |
| JP7376891B2 (en) * | 2019-10-30 | 2023-11-09 | 国立大学法人九州大学 | Biological information measuring device and biological information measuring program |
| EP4208076A4 (en) * | 2020-09-01 | 2024-10-02 | The General Hospital Corporation | SYSTEMS AND METHODS FOR MONITORING AN ANALYTE OR PARAMETER FOR A PATIENT |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE3148830A1 (en) * | 1981-12-10 | 1983-06-23 | Wolfgang Prof. Dr.Dr. 6500 Mainz Barnikol | "DEVICE FOR DETERMINING THE OXYGEN CONCENTRATION IN GASES, LIQUIDS AND TISSUES" |
-
1985
- 1985-01-11 JP JP1985001388U patent/JPH0529690Y2/ja not_active Expired - Lifetime
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2014002388A1 (en) * | 2012-06-29 | 2014-01-03 | セイコーエプソン株式会社 | Substance detection device and wristwatch type body fat burning measurement device |
| JP2014010046A (en) * | 2012-06-29 | 2014-01-20 | Seiko Epson Corp | Substance detection device and wrist watch type body fat burning measurement device |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS61118057U (en) | 1986-07-25 |
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