JPH0244535B2 - - Google Patents
Info
- Publication number
- JPH0244535B2 JPH0244535B2 JP61268284A JP26828486A JPH0244535B2 JP H0244535 B2 JPH0244535 B2 JP H0244535B2 JP 61268284 A JP61268284 A JP 61268284A JP 26828486 A JP26828486 A JP 26828486A JP H0244535 B2 JPH0244535 B2 JP H0244535B2
- Authority
- JP
- Japan
- Prior art keywords
- membrane
- electrode
- heating body
- membrane holder
- oxygen concentration
- 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
Links
- 238000010438 heat treatment Methods 0.000 claims description 53
- 239000012528 membrane Substances 0.000 claims description 49
- 239000001301 oxygen Substances 0.000 claims description 25
- 229910052760 oxygen Inorganic materials 0.000 claims description 25
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 claims description 24
- 239000008280 blood Substances 0.000 claims description 19
- 210000004369 blood Anatomy 0.000 claims description 19
- 230000007547 defect Effects 0.000 claims description 7
- 239000011810 insulating material Substances 0.000 claims description 7
- 239000003792 electrolyte Substances 0.000 claims description 6
- 238000005259 measurement Methods 0.000 claims description 6
- 229910052751 metal Inorganic materials 0.000 claims description 5
- 239000002184 metal Substances 0.000 claims description 5
- 229920005597 polymer membrane Polymers 0.000 claims description 5
- 239000007789 gas Substances 0.000 claims description 2
- 230000002093 peripheral effect Effects 0.000 claims description 2
- 230000000149 penetrating effect Effects 0.000 claims 1
- 230000007246 mechanism Effects 0.000 description 5
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 206010033675 panniculitis Diseases 0.000 description 4
- 210000004304 subcutaneous tissue Anatomy 0.000 description 4
- 239000008151 electrolyte solution Substances 0.000 description 3
- 210000001519 tissue Anatomy 0.000 description 3
- 238000001514 detection method Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000012774 insulation material Substances 0.000 description 2
- 239000007788 liquid Substances 0.000 description 2
- 239000004033 plastic Substances 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 230000001681 protective effect Effects 0.000 description 2
- 238000006722 reduction reaction Methods 0.000 description 2
- 239000007787 solid Substances 0.000 description 2
- MYMOFIZGZYHOMD-UHFFFAOYSA-N Dioxygen Chemical compound O=O MYMOFIZGZYHOMD-UHFFFAOYSA-N 0.000 description 1
- 239000004593 Epoxy Substances 0.000 description 1
- 206010029113 Neovascularisation Diseases 0.000 description 1
- 229910021607 Silver chloride Inorganic materials 0.000 description 1
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 1
- 239000002390 adhesive tape Substances 0.000 description 1
- 210000001367 artery Anatomy 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 229910001882 dioxygen Inorganic materials 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 239000010931 gold Substances 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 150000002926 oxygen Chemical class 0.000 description 1
- 230000036284 oxygen consumption Effects 0.000 description 1
- 230000035699 permeability Effects 0.000 description 1
- 239000012466 permeate Substances 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- 230000010287 polarization Effects 0.000 description 1
- 229920000728 polyester Polymers 0.000 description 1
- 229920006254 polymer film Polymers 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 230000000241 respiratory effect Effects 0.000 description 1
- 230000029058 respiratory gaseous exchange Effects 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- HKZLPVFGJNLROG-UHFFFAOYSA-M silver monochloride Chemical compound [Cl-].[Ag+] HKZLPVFGJNLROG-UHFFFAOYSA-M 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
- 230000037303 wrinkles Effects 0.000 description 1
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は動脈血中の酸素濃度を経皮的に連続測
定する装置のセンサーの構造に関するもので、取
り分け、膜ホルダーの着脱が容易なセンサーに関
するものである。[Detailed Description of the Invention] [Field of Industrial Application] The present invention relates to the structure of a sensor for a device for transcutaneously and continuously measuring the oxygen concentration in arterial blood, and in particular to a sensor whose membrane holder is easy to attach and detach. It is something.
血液、特に動脈血中の酸素濃度（又は分圧）を
知ることは、新生児並びに人工呼吸を必要とする
重傷患者の呼吸管理を行なう上で極めて重要であ
る。動脈血液中の酸素濃度を測定する方法として
動脈中の血液を抜き取つて直接測定する方法とは
異なり、血液から皮下組織を通じて拡散して来る
酸素を皮膚の表面で捕促し、患者に苦痛を与える
ことなく、かつ経時的に連続測定可能とした経皮
血中酸素濃度測定法は既に知られている。
Knowing the oxygen concentration (or partial pressure) in blood, especially in arterial blood, is extremely important for respiratory management of newborns and severely injured patients requiring artificial respiration. Unlike the method of measuring oxygen concentration in arterial blood, which involves drawing blood from the artery and directly measuring it, this method traps oxygen that diffuses from the blood through the subcutaneous tissue on the surface of the skin, causing pain to the patient. A transcutaneous blood oxygen concentration measurement method is already known that allows continuous measurement over time.
第２図及び第３図は、従来使用されている代表
的な経皮血中酸素濃度測定用センサーの構造を示
したものである。 FIGS. 2 and 3 show the structure of a typical sensor for measuring transcutaneous blood oxygen concentration that has been conventionally used.
第２図の１は金、白金等の貫金属よりなる陰
極、２はガラス、エポキシ等の絶縁材、３は銀／
塩化銀よりなる陽極、４は加熱ヒーター、５は温
度検出素子、６は４弗化樹脂、ポリエステル等の
酸素ガス透過性の高分子フイルムよりなる電極
膜、７はKCl等の電解質溶液からなる電解液、８
は電極膜を固定するための“０”リング等の固着
機構、９は外周保護外皮である。次に経皮測定の
原理を第２図に示したセンサーにより説明する。 In Figure 2, 1 is a cathode made of solid metal such as gold or platinum, 2 is an insulating material such as glass or epoxy, and 3 is silver/
An anode made of silver chloride, 4 a heater, 5 a temperature detection element, 6 an electrode membrane made of an oxygen gas permeable polymer film such as tetrafluoride resin or polyester, and 7 an electrolyte made of an electrolyte solution such as KCl. liquid, 8
9 is a fixing mechanism such as a "0" ring for fixing the electrode film, and 9 is a protective outer skin. Next, the principle of transcutaneous measurement will be explained using the sensor shown in FIG.
第２図に示したセンサーと皮膚との間に、水、
食塩水等を主体とした接触液を介在させ、中央部
に孔のあいたデイスク状の両面粘着テープを用い
てセンサーを皮膚面に密着させ、定温加熱部の温
度を43〜44℃に設定すると、これと接した部分の
皮膚が加熱されて皮下組織が動脈化される。その
ため組織内の酸素濃度は、動脈血中に含まれるも
のと実質的に等しいものとなり、この酸素が皮膚
組織を拡散して膜を透過し、さらに電解液中を拡
散して陰極に到達する。この際、陰極と陽極との
間に酸素の還元反応に必要な分極電圧を加えてお
くと、陰極部で酸素の還元反応が起り、電極間に
酸素の量に比例した電解電流が流れる。 Between the sensor shown in Figure 2 and the skin, water,
When the sensor is brought into close contact with the skin using a disc-shaped double-sided adhesive tape with a hole in the center, and the temperature of the constant-temperature heating part is set at 43 to 44 degrees Celsius, a contact liquid mainly composed of saline solution is used. The skin in contact with this is heated and the subcutaneous tissue becomes arterialized. The oxygen concentration in the tissue is therefore substantially equal to that contained in arterial blood, and this oxygen diffuses through the skin tissue, permeates the membrane, and further diffuses through the electrolyte to reach the cathode. At this time, if a polarization voltage necessary for the oxygen reduction reaction is applied between the cathode and the anode, the oxygen reduction reaction occurs at the cathode, and an electrolytic current proportional to the amount of oxygen flows between the electrodes.
従つて、この電流を測定することにより皮下組
織、したがつて、動脈血内の酸素濃度を近似的に
測定出来ることになる。 Therefore, by measuring this current, it is possible to approximately measure the oxygen concentration in the subcutaneous tissue and therefore in the arterial blood.
しかしながら、前記第２図に示した従来使用さ
れているセンサーでは、下記のごとき欠点を有す
る。即ち、この型のセンサーは陰極を皮膚加熱体
として利用しているため、必然的に大きな断面が
必要となる。そのため陰極部での酸素の反応量が
多く、電解液の消耗が著しく速い。 However, the conventionally used sensor shown in FIG. 2 has the following drawbacks. That is, since this type of sensor uses a cathode as a skin heating element, it necessarily requires a large cross section. Therefore, the amount of oxygen reacted at the cathode is large, and the electrolyte is consumed extremely quickly.
従つて電解液の交換を頻繁に行なう必要があ
り、その都度電極膜の交換が必要となる。又酸素
消費が多いため皮膚組織内に酸素の濃度勾配が生
し、実測される値は動脈血中に含まれる酸素濃度
よりはるかに低い値となる。これを避けるため酸
素透過性の悪い膜を使用すると、実測値は動脈血
中の酸素濃度に近い値が得られるようになるが、
応答速度が遅くなるという欠点が生ずる。その他
第２図に示したセンサーの欠点としては膜交換を
行なう時、フイルム状の電極膜を電極の端部に
“０”リング又はこれに代る固着機構で固着する
という方式をとつているため、膜を一定条件で装
着することが難かしく、又膜交換には熟練を要す
るため膜の装着の良否により特性のバラツキが生
ずるという問題がある。 Therefore, it is necessary to frequently replace the electrolytic solution, and the electrode membrane must be replaced each time. Furthermore, due to high oxygen consumption, an oxygen concentration gradient occurs within the skin tissue, and the actual measured value is much lower than the oxygen concentration contained in arterial blood. To avoid this, if a membrane with poor oxygen permeability is used, the actual measured value will be close to the oxygen concentration in arterial blood.
This has the disadvantage that the response speed becomes slow. Another disadvantage of the sensor shown in Figure 2 is that when replacing the membrane, the film-like electrode membrane is fixed to the end of the electrode using a "0" ring or an alternative fixing mechanism. However, since it is difficult to attach the membrane under constant conditions and skill is required to replace the membrane, there are problems in that characteristics vary depending on whether the membrane is properly attached or not.
第３図は前記第２図に示したセンサーの欠点を
改良したもので、改良点と特徴は下記のごとくで
ある。即ち第３図に示したセンサーの構造は、電
極を直接加熱せず、別に加熱体１７を設ける構造
としたため、これによつて陰極１０は、酸素と適
度な反応量が得られるように適宜断面積を変える
ことが可能となつた。第３図に示した陰極１０は
リング状の断面を有するものの例を示したが、こ
れによつて第２図のセンサーに見られた巨大陰極
なるが故に生ずる欠点を解消することが出来るよ
うになつた。又、電極膜を交換する時に生ずるト
ラブルも第３図に示した構造をとることによつて
解決出来た。即ち第３図に示したセンサーは、全
体の構造として陰陽両電極が内蔵された上蓋部１
３、電極膜をあらかじめ貼り付けた膜ホルダー１
４、発熱体１８及び感熱体１９の埋め込まれた加
熱体１７の３つの独立した部分より構成され、膜
ホルダー部が上蓋部と加熱体の間に容易に装着出
来る構成となつているため、装着時に膜にシワを
作つたりすることなく、しかも何等熟練を要せず
膜交換を行なうことが出来るので、膜交換時のト
ラブルが解消された。なお、皮膚の動脈化は、電
極部からの加熱ではなく、別に設けた加熱体によ
り、高精度でかつ広域にわたつて加熱されるた
め、有効に皮下組織の動脈化が行なわれるという
メリツトがある。 FIG. 3 shows an improved version of the sensor shown in FIG. 2, and the improvements and features are as follows. That is, in the structure of the sensor shown in FIG. 3, the electrode is not directly heated, but a separate heating element 17 is provided, so that the cathode 10 can be appropriately disconnected so as to obtain an appropriate amount of reaction with oxygen. It became possible to change the area. The cathode 10 shown in FIG. 3 is an example having a ring-shaped cross section, but this makes it possible to eliminate the drawbacks caused by the large cathode seen in the sensor of FIG. 2. Summer. Further, the trouble that occurs when replacing the electrode membrane can be solved by adopting the structure shown in FIG. That is, the sensor shown in Fig. 3 has an overall structure including an upper lid part 1 in which both negative and negative electrodes are built-in.
3. Membrane holder 1 with electrode membrane pasted in advance
4. It is composed of three independent parts: the heating element 17 in which the heating element 18 and the heat sensitive element 19 are embedded, and the membrane holder part is structured so that it can be easily installed between the upper lid part and the heating element, making it easy to install. Since the membrane can be replaced without causing wrinkles on the membrane and without requiring any skill, troubles during membrane replacement are eliminated. Note that arterialization of the skin is not performed by heating from the electrode section, but is heated over a wide area with high precision by a separately provided heating element, which has the advantage of effectively arterializing the subcutaneous tissue. .
前記のごとく、第３図に示したセンサーは、第
２図に示したセンサーの持つ欠点を解決したが、
なお下記に示す欠点を有することが判つた。 As mentioned above, the sensor shown in Fig. 3 solves the drawbacks of the sensor shown in Fig. 2, but
However, it was found that it had the following drawbacks.
即ち、電極部を内蔵した上蓋部１３と、加熱機
構を有する加熱体１７とを独立した部分として分
離したため、上蓋部と加熱体の両方から、それぞ
れリード線２０及び２１を取り出す必要があり、
そのため上蓋部と加熱体はネジ等の回転機構によ
り両者を固着することが出来ず、ビス２２を用い
て両者を固着するという方式が用いられている。
前記のビスによる固着方式は、各ビスの締めつけ
が均一でない場合には、上蓋部と加熱体が歪んだ
状態で固着されこの場合には電極の端面と電極膜
面が同様に歪んだ状態で被合されることになり、
電極の安定性が悪くなる。その他ビスの取りはず
しが面倒で着脱時に紛失する等のトラブルが発生
しがちである。
That is, since the upper lid part 13 containing the electrode part and the heating body 17 having a heating mechanism are separated as independent parts, it is necessary to take out the lead wires 20 and 21 from both the upper lid part and the heating body, respectively.
Therefore, it is not possible to fix the upper lid part and the heating body using a rotating mechanism such as a screw, and a method is used in which the two are fixed together using screws 22.
In the fixing method using screws, if the screws are not tightened uniformly, the top cover and the heating element will be fixed in a distorted state, and in this case, the end face of the electrode and the electrode membrane surface will be covered in a similarly distorted state. will be combined,
Electrode stability deteriorates. In addition, it is troublesome to remove screws, which tends to cause problems such as losing them when installing and removing them.
本発明は、従来のセンサーの上部欠点を解決す
るとともに高分子膜の交換を容易にするために為
されたものである。 The present invention has been made to solve the problems of the upper part of the conventional sensor and to facilitate the replacement of the polymer membrane.
本発明の要旨とするところは、電極支持体によ
り支持され、貫金属からなる陰極と該陰極の外周
に絶縁材を介して同心円状に配置した陽極部から
なる電極部と、
該電極部の外方に着脱できるように設けられ、
端面に高分子膜を装着し得る膜ホルダーと、
該膜ホルダーの外方に設けられ、かつ、前記電
極部と前記電極支持体を介して一体をなす加熱体
と、
該発熱体の外周と熱的に接続しするリング状の
接続部と、該接続部の端面より内方に延びて前記
膜ホルダーの端面と前記加熱体の端面とを覆い、
中央に開口部を有する平板部とからなる皮膚加熱
体と、
前記電極部の端面に電解液を保持するように前
記膜ホルダーの端面と前記平板部によつて周辺部
分が挟持されるガス透過性の高分子膜と、からな
る血中酸素濃度測定センサーにおいて、
前記加熱体の端面に一又は二以上の凹状欠損部
を有し、前記膜ホルダーの端面が前記凹状欠損部
の底面より出ていることを特徴とする経皮的血中
酸素濃度測定センサーにある。
The gist of the present invention is to provide an electrode part supported by an electrode support body and consisting of a cathode made of a solid metal and an anode part arranged concentrically around the outer periphery of the cathode with an insulating material interposed therebetween; It is designed so that it can be attached and detached on both sides.
a membrane holder to which a polymer membrane can be mounted on an end surface; a heating element provided outside the membrane holder and integrated with the electrode part and the electrode support; and an outer periphery of the heating element and a heat exchanger. a ring-shaped connecting portion that connects the membrane holder to the end surface of the heating body;
a skin heating body consisting of a flat plate part having an opening in the center; and a gas permeable body whose peripheral part is sandwiched between the end face of the membrane holder and the flat plate part so as to hold an electrolyte on the end face of the electrode part. A blood oxygen concentration measuring sensor consisting of a polymer membrane having one or more concave defects on the end surface of the heating body, and the end surface of the membrane holder protruding from the bottom surface of the concave defect. A transcutaneous blood oxygen concentration measurement sensor is characterized by the following.
第１図は本発明の経皮的血中酸素濃度測定セン
サーの判断図であつて、図中２６は、陰陽両極２
３，２４，２５、及び加熱体２７等を支持固定す
るための電極支持体で、プラスチツクゴム等の電
気及び熱絶縁材よりなる。２７は端部にネジ３１
を有する金属よりなる加熱体で、加熱ヒーター２
８及び温度検出素子２９が内臓されている。３２
は端部にあらかしめ電極膜３３を貼り付けた膜ホ
ルダーで、この膜面と電極端面の間に電解液が保
持される。３４はネジ３１′によつて加熱体２７
に固着される金属よりなる皮膚加熱体で、接続部
３４−１と平板部３４−２とから構成されてい
る。平板部３４−２の中央に開孔部３６が設けら
れている。万一火傷を起こした場合に火傷部が大
きくならないように側面部及び底面の外周部に、
プラスチツク又はゴム等からなる熱絶縁材３５が
貼り付けてもよい。 FIG. 1 is a judgment diagram of the transcutaneous blood oxygen concentration measurement sensor of the present invention, in which 26 is the negative and positive polarity 2.
3, 24, 25, heating element 27, etc., and is made of electrical and thermal insulating material such as plastic rubber. 27 has a screw 31 at the end
Heating heater 2 is a heating body made of metal having
8 and a temperature detection element 29 are built-in. 32
is a membrane holder with a roughened electrode membrane 33 attached to its end, and an electrolytic solution is held between this membrane surface and the electrode end surface. 34 is connected to the heating body 27 by a screw 31'.
The skin heating body is made of metal and is fixed to the body, and is composed of a connecting part 34-1 and a flat plate part 34-2. An opening 36 is provided in the center of the flat plate portion 34-2. In order to prevent the burn area from getting bigger in the event of a burn, there are
A thermal insulation material 35 made of plastic, rubber, etc. may be applied.
３７は加熱体２７の端面に設けられた凹状欠損
部で、膜ホルダー３２の端部が凹状欠損部３７の
底面３８より出ている。 Reference numeral 37 denotes a concave cutout provided on the end surface of the heating body 27 , and the end of the membrane holder 32 protrudes from the bottom surface 38 of the concave cutout 37 .
第４図ａは本発明の経皮的血中酸素濃度測定セ
ンサーの皮膚加熱体３４を外した状態の側面図、
第４図ｂはその平面図である。 FIG. 4a is a side view of the transcutaneous blood oxygen concentration measurement sensor of the present invention with the skin heating element 34 removed;
FIG. 4b is a plan view thereof.
本発明によるセンサーは、加熱体２７と皮膚加
熱体３４がネジ部３１，３１′で接合され、膜ホ
ルダ３２が皮膚加熱体により電極側に圧着される
構造となつている。
The sensor according to the present invention has a structure in which the heating body 27 and the skin heating body 34 are joined by threaded portions 31 and 31', and the membrane holder 32 is pressed onto the electrode side by the skin heating body.
前記の構造をとることにより、陰陽両極からの
信号線、ヒーター線、感熱素子からのリード線、
等が電極側に集結することが出来るため、第２図
に示したセンサーに見られるごとく、リード線を
電極側２０と加熱体側２１とに分離する必要がな
くなり１本のコード３０でセンサーと繋ぐことが
出来るようになつた。 By adopting the above structure, signal wires from both negative and negative poles, heater wires, lead wires from the heat-sensitive element,
etc. can be gathered on the electrode side, so there is no need to separate the lead wires into the electrode side 20 and the heating body side 21, as seen in the sensor shown in Fig. 2, and the lead wires can be connected to the sensor with a single cord 30. Now I can do it.
この結果、従来上蓋と加熱部とをビス２２によ
り固定したことにより生ずる欠点を一帰すること
が出来るようになつた。 As a result, it has become possible to completely eliminate the drawbacks caused by conventionally fixing the upper lid and the heating section with the screws 22.
ところが、第３図の従来のセンサーにおいては
上蓋部１３から加熱体１７を外すと膜ホルダー１
４は露出されるので膜ホルダー１４の着脱は容易
であつたが、本発明においては加熱体２７と皮膚
加熱体３４に分離されているため皮膚加熱体３４
を外しても膜ホルダー３２は加熱体２７の内部に
収納された状態になつている。本発明において
は、加熱体２７の端部に凹状欠損部３７を設ける
ことによつて、電極部に装着した電極膜を交換す
る時に、溝を通して指又はピンセツト等で膜ホル
ダーを掴み出すことが出来るので、膜ホルダーの
着脱が容易に行なえること及び膜ホルダーを加熱
部内部に収納可能なごとく装着出来るため、膜ホ
ルダーを使用することによつてセンサーの高さが
高くなるということを避けることが出来る。 However, in the conventional sensor shown in FIG. 3, when the heating element 17 is removed from the upper lid part 13, the membrane holder 1
Since the membrane holder 4 is exposed, it was easy to attach and detach the membrane holder 14, but in the present invention, since the heating body 27 and the skin heating body 34 are separated, the skin heating body 34
Even if the membrane holder 32 is removed, the membrane holder 32 remains housed inside the heating body 27. In the present invention, by providing the concave cutout 37 at the end of the heating body 27, when replacing the electrode membrane attached to the electrode part, the membrane holder can be grasped and pulled out with fingers or tweezers through the groove. Therefore, the membrane holder can be easily attached and detached, and the membrane holder can be installed so that it can be stored inside the heating section, so it is possible to avoid increasing the height of the sensor by using the membrane holder. I can do it.
以上の通り、凹状欠損部３７は加熱体２７と皮
膚加熱体３２が分離された構造のセンサーにおい
て始めて有効に作用する。 As described above, the concave defect 37 only works effectively in a sensor in which the heating body 27 and the skin heating body 32 are separated.
以上述べてきたように、本発明によれば、陰陽
両極からの信号線、ヒーター線、感熟素子からの
リード線等が電極側に集結することができるの
で、一本のコードでセンサーと機器を繋ぐことが
できて、取扱いが非常に容易になるとともに、膜
ホルダーの着脱も容易であり、実用上極めて有用
である。
As described above, according to the present invention, the signal line from the negative and positive poles, the heater line, the lead wire from the sensitive element, etc. can be gathered on the electrode side, so that a single cord can connect the sensor and the device. This makes it extremely easy to handle, and the membrane holder can be easily attached and detached, making it extremely useful in practice.
第１図ａは本発明の経皮的血中酸素濃度測定セ
ンサー、ｂ，ｃ，ｄはそれぞれ本発明によるセン
サーの分解された部分である電極支持体、膜ホル
ダー及び皮膚加熱体の断面図である。第２図ａ，
ｂはそれぞれ従来のセンサーの断面図及び平面
図、第３図ａ，ｂ，ｃ及びｄはそれぞれ従来の他
のセンサーの全体、各部の断面図である。第４図
ａは本発明のセンサーの皮膚加熱体を外した状態
の側面図、ｂはその平面図である。
１……陰極、２……絶縁材、３……陰極、４…
…加熱ヒーター、６……電極膜、７……電解液、
８……固着機構、９……外周保護外皮、１０……
陰極、１１……絶縁材、１２……陽極、１３……
上蓋部、１４……膜ホルダー、１５……電極膜、
１６……“０”リング、１７……加熱体、１８…
…発熱体、１９……感熱体、２０……信号側リー
ド線、２１……加熱側リード線、２２……ビス、
２３……陰極、２４……陽極、２５……絶縁材、
２６……電極支持体、２７……加熱体、２８……
発熱体、２９……感熱体、３０……リード線、３
１……ネジ、３１′……ネジ、３２……膜ホルダ
ー、３３……電極膜、３４……皮膚加熱体、３４
−１……接続部、３４−２……平板部、３５……
熱絶縁材、３６……開孔部、３７……凹状欠損
部、３８……凹状欠損部の底面。
FIG. 1a is a transcutaneous blood oxygen concentration measuring sensor of the present invention, and b, c, and d are cross-sectional views of an electrode support, a membrane holder, and a skin heating body, which are disassembled parts of the sensor according to the present invention, respectively. be. Figure 2a,
3b is a sectional view and a plan view of a conventional sensor, respectively, and FIGS. 3a, b, c, and d are sectional views of the whole and each part of another conventional sensor, respectively. FIG. 4a is a side view of the sensor of the present invention with the skin heating element removed, and FIG. 4b is a plan view thereof. 1... Cathode, 2... Insulating material, 3... Cathode, 4...
...Heating heater, 6... Electrode film, 7... Electrolyte,
8...Fixing mechanism, 9...Outer protective cover, 10...
Cathode, 11... Insulating material, 12... Anode, 13...
Upper lid part, 14... Membrane holder, 15... Electrode membrane,
16..."0" ring, 17... heating element, 18...
... Heating element, 19 ... Heat sensitive element, 20 ... Signal side lead wire, 21 ... Heating side lead wire, 22 ... Screw,
23... cathode, 24... anode, 25... insulating material,
26... Electrode support, 27... Heating body, 28...
Heating element, 29... Heat sensitive element, 30... Lead wire, 3
1... Screw, 31'... Screw, 32... Membrane holder, 33... Electrode membrane, 34... Skin heating element, 34
-1... Connection part, 34-2... Flat plate part, 35...
Thermal insulation material, 36... Opening portion, 37... Concave defect, 38... Bottom surface of the concave defect.
Claims (1)
陰極と該陰極の外周に絶縁材を介して同心円状に
配置した陽極部からなる電極部と、 該電極部の外方に着脱できるように設けられ、
端面に高分子膜を装着し得る膜ホルダーと、 該膜ホルダーの外方に設けられ、かつ、前記電
極部と前記電極支持体を介して一体をなす加熱体
と、 該加熱体の外周と熱的に接続しするリング状の
接続部と、該接続部の端面より内方に延びて前記
膜ホルダーの端面と前記加熱体の端面とを覆い、
中央に開口部を有する平板部とからなる皮膚加熱
体と、 前記電極部の端面に電解液を保持するように前
記膜ホルダーの端面と前記平板部によつて周辺部
分が挟持されるガス透過性の高分子膜と、 からなる血中酸素濃度測定センサーにおいて、 前記加熱体の端面に一又は二以上の凹状欠損部
を有し、前記膜ホルダーの端面が前記凹状欠損部
の底面より出ていることを特徴とする経皮的血中
酸素濃度測定センサー。[Scope of Claims] 1. An electrode part supported by an electrode support and consisting of a cathode made of a penetrating metal and an anode part arranged concentrically around the outer periphery of the cathode with an insulating material interposed therebetween; Designed to be removable,
a membrane holder to which a polymer membrane can be mounted on an end face; a heating body provided outside the membrane holder and integrated with the electrode portion through the electrode support; and an outer periphery of the heating body and a heat exchanger. a ring-shaped connecting portion that connects the membrane holder to the end surface of the heating body;
a skin heating body consisting of a flat plate part having an opening in the center; and a gas permeable body whose peripheral part is sandwiched between the end face of the membrane holder and the flat plate part so as to hold an electrolyte on the end face of the electrode part. A blood oxygen concentration measuring sensor consisting of a polymer membrane, and one or more concave defects on the end surface of the heating body, and the end surface of the membrane holder protrudes from the bottom surface of the concave defect. A transcutaneous blood oxygen concentration measurement sensor characterized by:
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61268284A JPS62122634A (en) | 1986-11-10 | 1986-11-10 | Sensor for percutaneous measurement of concentration of oxygen in blood |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61268284A JPS62122634A (en) | 1986-11-10 | 1986-11-10 | Sensor for percutaneous measurement of concentration of oxygen in blood |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS62122634A JPS62122634A (en) | 1987-06-03 |
| JPH0244535B2 true JPH0244535B2 (en) | 1990-10-04 |
Family
ID=17456400
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP61268284A Granted JPS62122634A (en) | 1986-11-10 | 1986-11-10 | Sensor for percutaneous measurement of concentration of oxygen in blood |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS62122634A (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DK3232928T3 (en) * | 2014-12-15 | 2023-07-03 | Radiometer Basel Ag | APPARATUS AND METHOD FOR NON-INVASIVE DETERMINATION OF THE CONCENTRATION OF AN ANALYTE |
-
1986
- 1986-11-10 JP JP61268284A patent/JPS62122634A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS62122634A (en) | 1987-06-03 |
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