JPH0349387B2 - - Google Patents
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- Publication number
- JPH0349387B2 JPH0349387B2 JP60082303A JP8230385A JPH0349387B2 JP H0349387 B2 JPH0349387 B2 JP H0349387B2 JP 60082303 A JP60082303 A JP 60082303A JP 8230385 A JP8230385 A JP 8230385A JP H0349387 B2 JPH0349387 B2 JP H0349387B2
- Authority
- JP
- Japan
- Prior art keywords
- membrane
- diffusion
- reaction
- package
- equation
- 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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- 239000012528 membrane Substances 0.000 claims description 44
- 238000009792 diffusion process Methods 0.000 claims description 23
- 239000007788 liquid Substances 0.000 claims description 7
- 108090000790 Enzymes Proteins 0.000 claims description 4
- 102000004190 Enzymes Human genes 0.000 claims description 4
- 239000007795 chemical reaction product Substances 0.000 claims description 3
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 description 19
- 239000008103 glucose Substances 0.000 description 19
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 10
- 238000001514 detection method Methods 0.000 description 9
- 239000002609 medium Substances 0.000 description 9
- 238000004519 manufacturing process Methods 0.000 description 6
- 229910052697 platinum Inorganic materials 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- JVTAAEKCZFNVCJ-UHFFFAOYSA-N lactic acid Chemical compound CC(O)C(O)=O JVTAAEKCZFNVCJ-UHFFFAOYSA-N 0.000 description 4
- 239000001963 growth medium Substances 0.000 description 3
- 108010015776 Glucose oxidase Proteins 0.000 description 2
- 239000004366 Glucose oxidase Substances 0.000 description 2
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 2
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 2
- 238000004364 calculation method Methods 0.000 description 2
- 230000007613 environmental effect Effects 0.000 description 2
- 229940088598 enzyme Drugs 0.000 description 2
- 229940116332 glucose oxidase Drugs 0.000 description 2
- 235000019420 glucose oxidase Nutrition 0.000 description 2
- 238000009434 installation Methods 0.000 description 2
- 235000014655 lactic acid Nutrition 0.000 description 2
- 239000004310 lactic acid Substances 0.000 description 2
- 230000002503 metabolic effect Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 239000001301 oxygen Substances 0.000 description 2
- 229910052760 oxygen Inorganic materials 0.000 description 2
- 238000004806 packaging method and process Methods 0.000 description 2
- 229920000515 polycarbonate Polymers 0.000 description 2
- 239000004417 polycarbonate Substances 0.000 description 2
- 239000000047 product Substances 0.000 description 2
- 229910052709 silver Inorganic materials 0.000 description 2
- 239000004332 silver Substances 0.000 description 2
- 239000000758 substrate Substances 0.000 description 2
- 241000894006 Bacteria Species 0.000 description 1
- IAYPIBMASNFSPL-UHFFFAOYSA-N Ethylene oxide Chemical compound C1CO1 IAYPIBMASNFSPL-UHFFFAOYSA-N 0.000 description 1
- 108010093096 Immobilized Enzymes Proteins 0.000 description 1
- 239000013543 active substance Substances 0.000 description 1
- 210000004102 animal cell Anatomy 0.000 description 1
- 230000003197 catalytic effect Effects 0.000 description 1
- 229920002301 cellulose acetate Polymers 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 239000007789 gas Substances 0.000 description 1
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 1
- 244000005700 microbiome Species 0.000 description 1
- 229910017464 nitrogen compound Inorganic materials 0.000 description 1
- 150000002830 nitrogen compounds Chemical class 0.000 description 1
- 239000012466 permeate Substances 0.000 description 1
- 238000009790 rate-determining step (RDS) Methods 0.000 description 1
- 230000001954 sterilising effect Effects 0.000 description 1
- 238000004659 sterilization and disinfection Methods 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 235000000346 sugar Nutrition 0.000 description 1
- 150000008163 sugars Chemical class 0.000 description 1
Landscapes
- Apparatus Associated With Microorganisms And Enzymes (AREA)
Description
【発明の詳細な説明】
〔発明の利用分野〕
本発明は、固定化酵素を使用して、特定の物質
の反応生成を行なしめ、これにより被測定物の状
態を検出するバイオセンサーに関する。DETAILED DESCRIPTION OF THE INVENTION [Field of Application of the Invention] The present invention relates to a biosensor that uses an immobilized enzyme to react and produce a specific substance, thereby detecting the state of an object to be measured.
微生物や動物細胞を培養するためには、環境条
件を適正なものに維持してゆく必要がある。
In order to cultivate microorganisms and animal cells, it is necessary to maintain appropriate environmental conditions.
培養制御に用いられてきた各種センサー類に
は、培地中の基質（糖、窒素化合物等）濃度や、
代謝生産物（各種生理活性物質、乳酸等）濃度を
直接しかも短時間で測定できものが少ない。した
がつて、培養の環境条件を適正なものに維持する
制御の指標としては、PH、溶存酸素濃度、温度の
ような間接的な指標を採用している。 Various sensors that have been used to control culture include the concentration of substrates (sugars, nitrogen compounds, etc.) in the culture medium,
There are few methods that can measure the concentration of metabolic products (various physiologically active substances, lactic acid, etc.) directly and in a short period of time. Therefore, indirect indicators such as pH, dissolved oxygen concentration, and temperature are used as control indicators to maintain appropriate environmental conditions for culture.
ところで、最近、培地中の基質濃度や代謝生産
物濃度等の直接的な指標を検出するものとして、
固定化酸素を使用したバイオセンサーが実用化さ
れ始めている。例えば、特開昭57−50883号公報
に開示されるような乳酸センサーもその一つであ
る。しかし、バイオセンサーの取付ける場合に、
この取付けが仲々難しく、特に培養装置にセンサ
ーを取付ける場合、雑菌を混入させないでセンサ
ーを取付けることが難しいという問題を残してい
る。また、バイオセンサーの故障等による取替え
の際にも、これを簡単に行なうことができない。 By the way, recently, as a method for detecting direct indicators such as substrate concentration and metabolic product concentration in the culture medium,
Biosensors using immobilized oxygen are beginning to be put into practical use. For example, a lactic acid sensor as disclosed in Japanese Patent Application Laid-Open No. 57-50883 is one such sensor. However, when installing a biosensor,
This installation is difficult, especially when attaching a sensor to a culture device, leaving the problem that it is difficult to attach the sensor without contaminating bacteria. Furthermore, when replacing the biosensor due to failure, etc., this cannot be done easily.
本発明の目的は、簡単に装置するに適したバイ
オセンサーを提供することである。
An object of the present invention is to provide a biosensor that is easy to install.
本発明は、細径棒状バツケージの先端部に凹部
を設け、この凹部内に、拡散膜と、固定化膜と、
選択透過膜と、一対の電極とからなる検出部を設
けたことを特徴とする。
The present invention provides a concave portion at the tip of a small-diameter rod-shaped bagage, and in this concave portion, a diffusion membrane, an immobilization membrane,
It is characterized in that it includes a detection section consisting of a selectively permeable membrane and a pair of electrodes.
すなわち、検出部が細径棒状パツケージ先端の
凹部に設けられており、装着は細径棒状パツケー
ジ先端をセンサー取付部位に挿入することのみで
良く、非常に簡単である。 That is, the detection part is provided in the recess at the tip of the thin rod-shaped package, and installation is very simple, as all that is required is to insert the tip of the thin rod-shaped package into the sensor attachment site.
以下、本発明を具体的な実施例により詳細に説
明する。
Hereinafter, the present invention will be explained in detail using specific examples.
第１図および第２図は本発明の一実施例を示す
図であり、センサー先端部の断面図を示す。第１
図および第２図において、１はセンサーのパツケ
ージであり、細径（0.5mm〜５mm）の棒状のパツ
ケージである。このパツケージ１の先端部には、
凹部が設けられ、この凹部内に後述する検出部３
０が設けられる。２は被測定液を拡散する拡散膜
である。３は被測定液選択透過膜の反応を促進さ
せる酵素を膜に固定化した固定化膜である。４は
被測定液選択透過膜であり、固定化膜で生成され
た反応生成物を選択的に透過させ、反応生成物を
電極に到達させる。５と６はリード線である。７
と８は一対の電極である。検出部３０は、２〜
４，７、および８で構成され、パツケージ１の先
端凹部内に設けられる。 FIGS. 1 and 2 are diagrams showing one embodiment of the present invention, and show cross-sectional views of the tip of the sensor. 1st
In the figure and FIG. 2, 1 is a sensor package, which is a rod-shaped package with a small diameter (0.5 mm to 5 mm). At the tip of this package 1,
A recess is provided, and a detection section 3, which will be described later, is placed inside this recess.
0 is set. 2 is a diffusion membrane that diffuses the liquid to be measured. 3 is an immobilized membrane in which an enzyme that promotes the reaction of the selectively permeable membrane for the liquid to be measured is immobilized on the membrane. Reference numeral 4 denotes a selectively permeable membrane for the liquid to be measured, which selectively permeates the reaction product produced in the immobilized membrane and allows the reaction product to reach the electrode. 5 and 6 are lead wires. 7
and 8 are a pair of electrodes. The detection unit 30 has 2 to
4, 7, and 8, and is provided in the recess at the tip of the package 1.
第３図は検出装置全体の構成を示している。第
３図において、１０は定電圧直流電源、９は電流
検出器、１１は増幅器である。１２は演算器であ
り、検出された電流の変化分により状態量を演算
する。１３は記録計であり、演算結果を記録す
る。１４はコネクタである。パツケージ１は、被
測定液にセンサー部３０が没するように挿入され
る。 FIG. 3 shows the overall configuration of the detection device. In FIG. 3, 10 is a constant voltage DC power supply, 9 is a current detector, and 11 is an amplifier. Reference numeral 12 denotes an arithmetic unit, which calculates a state quantity based on the detected change in current. 13 is a recorder, which records the calculation results. 14 is a connector. The package 1 is inserted so that the sensor section 30 is submerged in the liquid to be measured.
次に、上述の第１図〜第３図の如き構成におい
て、培地中のグルコース濃度を測定する場合を説
明する。グルコース濃度を測定する場合におい
て、検出部を構成する部材は次の通りである。陽
電極７は白金を使用した白金陽電極、陰電極８は
銀を使用した銀陰極とする。この両電極の表面に
接する選択透過膜４としてはセルロースアセテー
ト膜を使用し、固定化膜３としてはグルコースオ
キシターゼ膜を使用し、拡散膜２としてはポリカ
ーボネート膜を使用する。培地がパツケージ１の
先端凹部に浸入し、拡散膜２と接触する。これに
より、培地は拡散膜中に拡散し、固定化膜３と接
触する。この固定化膜３に接触した培地中のグル
コースは、酵素（グルコースオキシターゼ）の触
媒作用により、次の反応を生じる。 Next, a case will be described in which the glucose concentration in the medium is measured in the configuration shown in FIGS. 1 to 3 described above. In the case of measuring glucose concentration, the members constituting the detection section are as follows. The positive electrode 7 is a platinum positive electrode using platinum, and the negative electrode 8 is a silver cathode using silver. A cellulose acetate membrane is used as the permselective membrane 4 in contact with the surfaces of both electrodes, a glucose oxidase membrane is used as the immobilization membrane 3, and a polycarbonate membrane is used as the diffusion membrane 2. The medium enters the recess at the tip of the package 1 and comes into contact with the diffusion membrane 2. As a result, the medium diffuses into the diffusion membrane and comes into contact with the immobilization membrane 3. Glucose in the medium that has come into contact with this immobilized membrane 3 causes the following reaction due to the catalytic action of an enzyme (glucose oxidase).
C6H12O6＋O2→H2O2＋C6H10O6 ……(1)
(1)式の反応によつて生成されたH2O2は選択透
過膜４中を拡散し、白金陽電極７表面に達する。
これにより、白金陽電極７表面で、H2O2は電気
化学的に酸化される。C 6 H 12 O 6 +O 2 →H 2 O 2 +C 6 H 10 O 6 ...(1) H 2 O 2 generated by the reaction of formula (1) diffuses in the selectively permeable membrane 4, It reaches the surface of the platinum positive electrode 7.
As a result, H 2 O 2 is electrochemically oxidized on the surface of the platinum positive electrode 7.
H2O2→2H+＋O2＋2e- ……(2)
(2)式によつて生成された2e-のため、電極間に
流れる電流が増大し、これは電流検出器によつて
検出される。この電流の変化と、グルコース濃度
との関係は、一義的な関係があるで、電流の変化
を入力することでグルコース濃度が演算できる。H 2 O 2 →2H + +O 2 +2e - ...(2) Due to the 2e - generated by equation (2), the current flowing between the electrodes increases, and this is detected by the current detector. Ru. There is a unique relationship between this change in current and the glucose concentration, and the glucose concentration can be calculated by inputting the change in current.
続いて、電流の変化とグルコース濃度との間の
関係を数式的に示す。まず、各膜での拡散、反応
速度を考える。拡散膜（ポリカーボネート膜）２
中のグルコースの拡散速度KV2は、拡散に関す
るフイツク（Fick）の法則より、
KV2＝D2C0／G−CG／y2 ……(3)
ここで、KV2：膜２中のグルコースの拡散速
度
D2：膜２の拡散定数
C0 G：膜２の培地側表面におけるグルコース濃度
（検出すべき状態量）
CG：膜２と３との境界面におけるグルコース濃
度
y2：膜２の厚さ
となる。一般に、拡散速度は、反応速度と比較す
れば非常に遅く、拡散→反応の系においては、拡
散が律速段階となつて全体の反応速度を決定して
しまう。また、(1)式の反応は、極めて敏速に進行
するため、膜２と３の境界面でのグルコースは、
ほぼ瞬間的に反応消費される。したがつて、(3)式
におけるCG≒０とできる。一方、培地のグルコ
ースの量は十分に多いので、消費されたことによ
る全体のグルコース濃度に与える影響はないと考
えて差し支えない。これらを考慮すると、(3)式
は、次のように近似できる。 Subsequently, the relationship between changes in current and glucose concentration is shown mathematically. First, consider the diffusion and reaction rates in each membrane. Diffusion membrane (polycarbonate membrane) 2
The diffusion rate of glucose in the membrane 2, KV 2 , is calculated from Fick's law regarding diffusion as follows: KV 2 = D 2 C 0 / G − C G /y 2 ...(3) where, KV 2 : Diffusion rate of glucose D 2 : Diffusion constant of membrane 2 C 0 G : Glucose concentration at the medium side surface of membrane 2 (state quantity to be detected) C G : Glucose concentration at the interface between membranes 2 and 3 y 2 : Membrane The thickness will be 2. Generally, the diffusion rate is very slow compared to the reaction rate, and in a diffusion->reaction system, diffusion becomes the rate-limiting step and determines the overall reaction rate. In addition, since the reaction of formula (1) proceeds extremely rapidly, the glucose at the interface between membranes 2 and 3 is
The reaction is consumed almost instantly. Therefore, C G in equation (3) can be approximately 0. On the other hand, since the amount of glucose in the medium is sufficiently large, it is safe to assume that consumption will not affect the overall glucose concentration. Considering these, equation (3) can be approximated as follows.
KV2＝D2C0／G／y2 (3)′
固定化膜３中のH2O2の生成反応速度SV3は、
拡散が律速である場合には、上述のKV2に比例
するので、
SV3＝ｋ・D2C0／G／y2 ……(4)
となる。 KV 2 = D 2 C 0 / G /y 2 (3)′ The production reaction rate SV 3 of H 2 O 2 in the immobilized membrane 3 is
When diffusion is rate-determining, it is proportional to the above-mentioned KV 2 , so SV 3 =k·D 2 C 0 / G /y 2 (4).
生成されたH2O2が選択透過膜４中を拡散する
拡散速度KV4は、同様にフイツクの法則により、
KV4＝D4C34／y4 ……(5)
ここで、KV4：膜４中のH2O2の拡散速度
D4：膜４の拡散定数
y4：膜４の厚さ
C34：膜３と４の境界面におけるH2O2濃度
となる。また、白金陽電極７表面における(2)式の
反応において、e-の生成反応速度は、拡散が律速
であるときには、膜４の拡散速度KV4に比例す
ると考えて差支えない。したがつて、(2)式の生成
反応速度ｄ〔e-〕／dtは、
ｄ〔e-〕／dt＝k′・D4C34／y4 ……(6)
ただし、k′：生成反応速度定数
膜３と４の境界面におけるH2O2の濃度C34の変
化速度dC34／dtを考えると、膜３中で反応して生
成するH2O2の生成速度SV3から、膜４へ拡散す
るH2O2の拡散速度KV4の差になる。 Similarly, the diffusion rate KV 4 at which the generated H 2 O 2 diffuses through the permselective membrane 4 is determined by Fick's law as follows: KV 4 = D 4 C 34 /y 4 ...(5) Here, KV 4 : Diffusion rate of H 2 O 2 in the film 4 D 4 : Diffusion constant of the film 4 y 4 : Thickness of the film 4 C 34 : H 2 O 2 concentration at the interface between the films 3 and 4. Furthermore, in the reaction of equation (2) on the surface of the platinum positive electrode 7, it can be considered that the production reaction rate of e - is proportional to the diffusion rate KV 4 of the membrane 4 when diffusion is rate-determining. Therefore, the production reaction rate d[e - ]/dt in equation (2) is d[e - ]/dt=k'・D 4 C 34 /y 4 ...(6) where, k': production Reaction rate constant Considering the rate of change of the concentration C 34 of H 2 O 2 at the interface between membranes 3 and 4, dC 34 /dt, from the production rate SV 3 of H 2 O 2 reacting and generated in membrane 3, This is the difference in the diffusion rate KV 4 of H 2 O 2 diffusing into the membrane 4.
したがつて、
dC34／dt＝SV3−KV4＝ｋ・D2C0／G／y2−D4C34／y4 (7)
この(7)式において、時間ｔ＝０のときC34＝０
の初期条件を考えて、C34を解くと次式となる。 Therefore, dC 34 /dt=SV 3 −KV 4 =k・D 2 C 0 / G /y 2 −D 4 C 34 /y 4 (7) In this equation (7), when time t=0 C34 =0
Considering the initial conditions of and solving C 34 , we get the following equation.
C34＝ｋ・D2・y4・C0／G／D4・y2｛１−exp（−D4／y4
・ｔ）｝
……(8)
(8)式より、
Lim
ｔ→∞C34＝ｋ・D2・y4／D4・y2C0 G ……(9)
となる。膜３と４の境界面でのH2O2濃度C34は、
時間の経過とともに、(9)式の右辺の定常値とな
り、このとき(2)式の反応は平衡に達する。この(2)
式の反応速度ｄ〔e-〕／dtは、(6)式に示す通りで
あり、(6)式にこの定常値C34を代入すると、
ｄ〔e-〕／dt＝k′・ｋD2／y2・C0 G ……(10)
となる。(10)式において、k′、ｋ、D2、y2は定数で
あり、結局、培地のグルコース濃度C0 Gは、(2)式
におけるe-の反応生成速度ｄ〔e-〕／dtに比例す
る。C0 G＝０のとき、電極７，８間に流れる電流
をI0とし、C0 G≠０のとき流れる電流をＩとする
と、
Ｉ−I0＝ｄ〔e-〕／dt・Ｋ ……(11)
Ｋ：定数
となる。(10)式と(11)式から、目的とする培地のグル
コース濃度C0 Gは、
＝C0 G＝y2／D2・k′・ｋ・Ｋ（Ｉ−I0）
ただし、
Ｚ＝y2／D2・k′・ｋ・Ｋ（定数）
となる。このように、グルコース濃度C0 Gは、電
流の変化分を検出すれば求めることができる。C 34 =k・D 2・y 4・C 0 / G /D 4・y 2 {1−exp(−D 4 /y 4
・t)} ...(8) From equation (8), Lim t→∞C 34 =k・D 2・y 4 /D 4・y 2 C 0 G ...(9). The H 2 O 2 concentration C 34 at the interface between membranes 3 and 4 is
As time passes, the right-hand side of equation (9) becomes a steady value, and at this time the reaction of equation (2) reaches equilibrium. This (2)
The reaction rate d[e - ]/dt in the equation is as shown in equation (6), and by substituting this steady value C 34 into equation (6), d[e - ]/dt=k′・kD 2 /y 2・C 0 G ……(10). In equation (10), k', k, D 2 and y 2 are constants, and after all, the glucose concentration C 0 G in the medium is the reaction production rate of e - in equation (2) d[e - ]/dt is proportional to. When C 0 G = 0, the current flowing between electrodes 7 and 8 is I 0 , and when C 0 G ≠ 0, I is the current flowing, then I-I 0 = d[e - ]/dt・K... ...(11) K: Becomes a constant. From equations (10) and (11), the target glucose concentration C 0 G of the medium is: = C 0 G = y 2 /D 2・k′・k・K (I−I 0 ) However, Z= y 2 /D 2・k′・k・K (constant). In this way, the glucose concentration C 0 G can be determined by detecting the amount of change in current.
したがつて、第３図において、電流検出器９が
グルコース濃度C0 Gに対応した電流Ｉを検出する
ことによつて、演算器１２がこれを入力し、予め
記憶しているI0との差（Ｉ−I0）を求め、この差
に比例したグルコース濃度C0 Gを演算する。この
演算により得られたグルコース濃度C0 Gは、記録
計１３に記録される。 Therefore, in FIG. 3, when the current detector 9 detects the current I corresponding to the glucose concentration C 0 G , the arithmetic unit 12 inputs this and compares it with the pre-stored I 0 . The difference (I-I 0 ) is determined, and the glucose concentration C 0 G proportional to this difference is calculated. The glucose concentration C 0 G obtained by this calculation is recorded on the recorder 13.
第１図〜第３図で示したパツケージ１内に組込
まれたバイオセンサーの培養槽への装置は、第４
図、第５図に示すように行なわれる。まず、パツ
ケージ１全体を、エチレンオキサイドガスや紫外
線等により殺菌後、弾性体１５を有する包装部材
１９等により包装しておく、培養槽１８内の培地
を加熱殺菌し、冷却する。センサー取付部分の弾
性体栓１７と弾性体１５の表面を殺菌後密着させ
る。パツケージ１を押し込み弾性体１５、栓１７
を貫通させ、パツケージ先端が培地に浸ることを
可能とする。パツケージ１の挿入後、包装部材１
９を取り除き、コネクタ１４、ケーブル２０を介
して、外部機器２１を接続する。なお、１６はロ
ツクナツトである。 The device for connecting the biosensor installed in the package 1 shown in FIGS. 1 to 3 to the culture tank is
This is carried out as shown in FIG. First, the entire package 1 is sterilized using ethylene oxide gas, ultraviolet rays, etc., and then the culture medium in the culture tank 18, which is packaged with a packaging member 19 having an elastic body 15, is heat sterilized and cooled. After sterilization, the elastic plug 17 of the sensor attachment portion and the surface of the elastic body 15 are brought into close contact with each other. Push in the package 1, elastic body 15, plug 17
pierce through, allowing the tip of the package to be immersed in the medium. After inserting the package 1, the packaging member 1
9 is removed, and an external device 21 is connected via the connector 14 and cable 20. Note that 16 is a lock nut.
〔発明の効果〕
以上説明したように本発明によれば、細径棒状
パツケージの先端部に設けた凹部に検出部を組込
んでいるので、装置はパツケージを押し込むこと
のみによつて実現でき、極めて簡単にこれを行な
うことができる。[Effects of the Invention] As explained above, according to the present invention, since the detection part is incorporated into the recess provided at the tip of the small diameter rod-shaped package, the device can be realized only by pushing the package. You can do this very easily.
第１図および第２図は本発明の一実施例を示す
図、第３図は検出装置の全体構成図、第４図と第
５図はセンサーの装着例を示す図である。
１……パツケージ、２……拡散膜、３……固定
化膜、４……選択透過膜、５，６……リード線、
７……電極（陽電極）、８……電極（陰電極）、９
……電流検出器、１０……直流定電圧電源、１１
……増幅器、１２……演算器、１３……記録計、
３０……検出部。
FIGS. 1 and 2 are diagrams showing an embodiment of the present invention, FIG. 3 is a diagram showing the overall configuration of a detection device, and FIGS. 4 and 5 are diagrams showing an example of mounting a sensor. 1... Package, 2... Diffusion membrane, 3... Immobilization membrane, 4... Selective perms membrane, 5, 6... Lead wire,
7... Electrode (positive electrode), 8... Electrode (negative electrode), 9
... Current detector, 10 ... DC constant voltage power supply, 11
...Amplifier, 12...Arithmetic unit, 13...Recorder,
30...detection section.
Claims (1)
該凹部内には、被測定液を拡散する拡散膜と、該
拡散膜によつて拡散された被測定液の反応を促進
させる酵素を固定化した固定化膜と、該固定化膜
で生成された反応生成物の選択的に透過させる選
択透過膜と、一対の電極とからなる検出部を設
け、該電極間に流れる電流の変化により前記被測
定液の状態量を検出することを特徴とするバイオ
センサー。1 A recess is provided at the tip of the small diameter rod-shaped package,
Inside the recess, there is a diffusion membrane that diffuses the liquid to be measured, an immobilization membrane on which an enzyme is immobilized that promotes the reaction of the liquid to be measured diffused by the diffusion membrane, and an enzyme generated by the immobilization membrane. The present invention is characterized in that it includes a detecting section consisting of a permselective membrane that selectively allows a reaction product to pass through, and a pair of electrodes, and detects the state quantity of the liquid to be measured based on a change in the current flowing between the electrodes. biosensor.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60082303A JPS61241650A (en) | 1985-04-19 | 1985-04-19 | biosensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60082303A JPS61241650A (en) | 1985-04-19 | 1985-04-19 | biosensor |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS61241650A JPS61241650A (en) | 1986-10-27 |
| JPH0349387B2 true JPH0349387B2 (en) | 1991-07-29 |
Family
ID=13770781
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP60082303A Granted JPS61241650A (en) | 1985-04-19 | 1985-04-19 | biosensor |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS61241650A (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH01156453U (en) * | 1988-04-21 | 1989-10-27 |
-
1985
- 1985-04-19 JP JP60082303A patent/JPS61241650A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS61241650A (en) | 1986-10-27 |
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