• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    A molecule-selective sensor has a hollow body (1) in the interior of which are disposed a sensing electrode (4) and a reference electrode (5) immersed in an electrolyte (2). The end of the hollow body (1) is closed by a proteinaceous or other natural membrane (7) which has a surface layer (6) carrying or containing a chemically immobilized enzyme. <IMAGE>
    公开号:SU1034618A3
    申请号:SU792788705
    申请日:1979-06-18
    公开日:1983-08-07
    发明作者:Хаваш Йене；Надь Геза；Порьес Эмма；Пунгор Ерне
    申请人:"Раделкиш" Электрокемиаи Мюсердьярто Севеткезет (Инопредприятие)；
    IPC主号:
    专利说明:

    The invention relates to electrochemical sensors that are used for selectively determining the concentrations of compounds (for example, glucose B dissolved in liquids (for example, in blood. An electrochemical sensitive sensor is known which is used to determine compounds in liquids 13, the well-known sensor has a low mechanical strength. The closest technical solution to the present invention is an electrochemical sensor for determining the concentration of substances in thieves containing Kopnyt: filled with electricity, in which indicator and comparative electrodes are located, connected to a power source and a recording device, in which the filter is located, and on the end of the membrane there is a gel layer , which contains an enzyme in a chemically bound form. The mechanism of action of the known selective molecules with respect to molecules is described as follows. MoleumJML components (molecules of the so-called substrates, for example, glucose molecules and in some cases reagent molecules (oxygen molecules; diffuse into the layer that contains a selective enzyme, for example, glucose oxide) and which serves as a specific active catalyst, i.e. in the so-called reaction layer where the chemical reaction takes place. The signal output from the indicator electrode is an unambiguous function of the concentration or activity of the reagent involved in the fermentation reaction, If all factors can be considered constant, the local activity or concentration depends on the reaction rate, which is an unambiguous function of the substrate concentration. Therefore, in a steady state, by measuring the current or the emf value, the concentration can be directly determined compound in sample D 2. The disadvantage of simple sensors is their short lifespan (for example, several days, one or two weeks), which can be explained by the lack of but acceptable properties of the reaction layer. Besides; Taking into account the presence of the gel layer, in which the bound enzyme is contained, the sensitive element, except for the time of use, must be kept at a lower temperature (for example, from -1 to + 2 ° C) in order to preserve its enzymatic activity. The known sensors are easily damaged, do not have mechanical strength and have a long reaction time (for example, from 2 to 8 minutes). The purpose of the invention is to increase the mechanical strength and service life of the sensor. The goal is achieved by the fact that an electrochemical sensor for determining the concentration of substances in solutions, comprising a housing filled with electrolyte, in which the indicator and comparative electrodes are connected to a power source and a recording device, in the wall of which a filter is located, and at the end is a gas-permeable film which contains a gel layer containing an enzyme in chemically bound form, and between the body of the sensitive element and the indicator electrode is an insulating layer, to olnitelno comprises a membrane made of natural material pro- origin and containing in chemically immobilized form in the surface layer of one or more enzymes tityuv, wherein the membrane is in contact with the gas-permeable film. The membrane of natural origin is in contact with a protective net or fabric made of a permeable material. In the case there are several indicator electrodes. After immobilization, activated natural membranes in a dry state (in some cases at room temperature) can be stored for a very long time (from 0.5 to 1 year) without a noticeable change in the activity of the enzyme, since the enzyme is in its natural environment. The permeability of natural membranes with respect to ions, water, and gas molecules is ideal with respect to the measurement technique. Another beneficial property of natural membranes is that they are permeable to ions and gas molecules that are used as a reactant or reaction product, and impermeable to higher molecular weight compounds that can have a higher molecular weight. influencing the measurement results (for example, a substrate or other substances contained in a sample; so that the so-called hysteresis effect, which is often observed when replacing samples with different The proposed sensor is designed in such a way that when creating a reaction layer, a membrane ic is used with two reaction layers, or several membranes with one or two reaction layers superimposed on each other. each membrane is bound to another phase in immobilized form. In the case of the f-rnn of the hozidy electrode, the membrane surface contains f-glucosidase on the side of the test solution, and y-oxyoxidase on the side of the indicator electrode. The enzyme {-glucose and dase associated with the first membrane allows the reaction of hydrolysis of the measurable components between the p-glucose OM (e.g. amygdalin or salizin) and water, resulting in, among other things, glu: Goat. The enzyme-glucose oxidase bound to the second membrane catalyzes the reaction between glucose and oxygen. A signal proportional to the concentration of oxygen can be changed at the indicator electrode under the membrane. A signal proportional to a decrease in oxygen concentration is an unambiguous function of the concentration of a certain pro (Nl. With such an embodiment, on the one hand, a simplification with respect to the measurement technique can be made and, on the other hand, such compounds that, in the one-step reaction, do not form components, the amount of which can be measured, or which do not show changes in the concentration or activity of the determined components. The element can also be constructed in such a way that, with separated sections of the surface of the membrane of a natural structure that serves as a reaction zone, or with certain areas of the surface, enzymes of different varieties are associated in a statistically homogeneous distribution, and each of the areas I and the surface correspond to one or several indicator electrode With this construction, a selective sensor element can be obtained with multiple functions without increasing the size, as a result e what the determination of several components in the same test solution can be carried out in parallel, or with a parallel determination of the concentration of interfering components, the effect of which can be eliminated manually or automatically. In another embodiment of the invention, the sensing element is obtained by, for example, in the case of a sensing element for industrial purposes having large dimensions, to further increase the mechanical strength of the reaction zone, the membrane of the natural structure enters into contact with an inert polymeric mesh or fabric. In other embodiments of the invention, to achieve a very short reaction time on the surface layer of one side of the membrane of a natural structure, a reaction zone is created which contains the enzyme in immobilized form and on the surface layer of the other side of the membrane natural structure is created using the a1 shvka process a layer that is gas permeable or has ion exchange properties. A molecule-selective sensitive element is made in such a way that the membrane surface of the natural structure is treated at room temperature with a solution that contains an enzyme and a bifunctional reagent having groups suitable for forming chemical bonds, for example. glutaraldehyde. After completion of the reaction, the membrane will be placed in a water bath with distilled water, where the components remaining in water-soluble form are washed out. After completion of the washing operation, the membrane is in a state ready for measurement. After that, in some cases, a metal indicator electrode is made. in order to clean the surface of the indicator electrode, it is kept in nitric acid for several minutes, then washed and placed in a bath containing a reducing agent (for example, ascorbic acid, where oxygen and oxygen physically dissolved in the metal electrode are converted. The membrane is permeable for gas or for gas and dissolved substances, is placed on the body of the sensing element, after which the indicator electrode and the reference electrode are immersed in the sensing element in the body itelnogo member electrolyte solution so that the surface of the indicator electrode is in close proximity to the membrane. The electrodes are secured. The result is a finished -sensitive element to measurements state.
    The drawing shows a glucose selective element, a partial section.
    Example. In the cavity of the housing 1 of the sensing element, there is a buffer solution 2 containing chloride ions, in which a platinum indicator electrode 4 and silver, immersed in chamber 3, are immersed. (silver halide) reference electrode 5.
    The end of the body 1 of the sensing element is closed by a gas permeable gas polypropylene film b, which is in contact with the indicator electrode 4. The gas-permeable film b is in contact with the membrane 7 of natural origin made from pig intestines, and glucose oxidase (E.C.1.1. 3.4 is immobilized with glutaraldehyde Gas-permeable film b and membrane 7 of natural origin are attached to case 1 of the sensing element with a rubber ring 8.
    The other end of the body 1 of the sensing element is closed with a plastic cap 9. The indicator electrode 4 and the reference electrode 5 are connected via a cable 10 to a source of polarizing voltage, i-c. the entrance to the device for measuring the current.
    The manufacture of a glucose-selective electrode is carried out in the following manner.
    A portion of commercially saline pig intestines are soaked for 10-15 minutes in distilled water. The swollen membrane, together with a gas-permeable film (such as polypropylene) with a thickness of 15 in the stretched state, is fixed at the end of the body of the sensing element (the polypropylene film must be on the side of the cavity of the body of the sensitive element). The membrane is dried for 20 minutes. Then, 60 mg of E.C. glucose oxidase are suspended in 0.5 ml of a buffer solution with a pH of 7.4. 1.1. 3. 4.) and add 25 µl of a 25% glutaraldehyde solution. 20 µl of the obtained homogeneous suspension with a uniform layer is applied to the surface of the membrane. After that, the membrane is dried for 20 minutes and then by washing with distilled water, the non-immobilized enzyme and excess glutaraldehyde are removed. The membrane prepared by the above method, containing the enzyme glucose oxidase in I1ir mobilized form, is in a state ready for measurement or storage.
    After manufacturing an activated membrane which is known in a known manner.
    mounted on a substrate, prepare a platinum indicator electrode. The surface of the indicator electrode is kept in a solution of nitric acid with a concentration of b mol / dm for 2-3 minutes. Then nitric acid is washed off with distilled water. After washing, the surface of the indicator electrode is kept
    0 in a freshly prepared 2% solution of ascorbic acid for 20-30 minutes. After this treatment, ascorbic acid is removed from the surface of the indicator electrode by distilled water. After washing, the indicator electrode is in a state ready for measurement (the treatment with nitric acid and ascor binic acid must be repeated
    when measuring every two to three weeks),
    After the preparatory operations, a glucose selective element is collected, which is then connected to a polarizing voltage source and to a device for measuring current strength.
    Determination of glucose concentration 0 in the sample can be carried out
    sensitive element by removing the calibration curve or additive method. The following is the preferred additive method, which is known as the multiple sample addition method.
    It has been established that between the decrease in the measured current strength (ui) and the glucose concentration in solution (c) there is the following relationship:
    l-l-l
    (L
    t
    V to
    Where
    maximum reaction rate;
    Michaelis constant for enzyme-substrate reaction
    R is a proportionality factor.
    From the measurement value of the decrease in current in two glucose-containing solutions with known concentrations, the values of N and K for given conditions and this sensitive element can be determined, from which the concentration of VI solution under study can be determined by reducing the current, according to formula:
    (And ± k11 ...
    C - 1.
     2 Taking equation 2 into account, the sample concentration is
    sr u ..
     jq
    (B)
    OH
    where aCh) sample volume / V is the total volume of the sample and standard solution.
    In the case of blood and urine, measurement by the multiple addition method is carried out as described below.
    6.6 ml of a buffer solution with a pH value of 7.4 was measured in a cell incubated at 37 ° C. In razvor immersed sensitive element. From the current value measured after the addition of 50 µl of glucose-containing solutions, which have a concentration of 2-Yutmol / dm, the values of V and K are calculated or automatically determined. After this, a known sample volume is introduced into the buffer solution and the change in current intensity is determined. (Depending on the glucose content of the blood sample to be tested, an appropriate sample volume is chosen. For samples with concentrations between 60 and 200 mg-%, the volume of samples should be 100 µl, for more dilute samples, 200 µl, and for more dilute samples 50 µl of concentrated samples. In the case of urine samples with concentrations of 0-1 g-%, 50 µl is added, with more concentrated samples it is diluted tenfold, and in the case of diluted samples (25-50 µl). From the measured value of the current decrease, the concentration to be determined is calculated by equation (2) manually or by computer.
    The values measured for the glucose-selective element for some samples are given in Table. one.
    Table
    amount
    parallel
    measurements
    180
    11 11 11
    120
    90 From the table it can be seen that the spread of the values measured with the aid of the selective with respect to the glucosensitive element is much smaller than the spread of the values obtained by known methods, whose spread often exceeds 10%. Urea Acid Cholesterol U-Amino Acids T) -Amino Acids can also be made according to this example.
    The average value of the measured values, mg-%
    180
    121
    91
    That l l and c and 2 UreaPlatina E.S.1.7.3..3. Cholesterol oxidase Platinum E.G.1.1.3.6. Oxidase of U-amino acids. Same as ES.1.4.3.2. Oxidase D-amino acids .С.1.4.3.3. these elements are sensitive; selective with respect to molecules. In tab. Figure 2 shows the types of molecules in relation to which the sensitive element is selective, the enzymes immobilized on the natural membrane, which are in conjunction with a thin film permeable to gas, and the types of indicator electrodes.
    B "C" 1 "o" 3 1
    Oxalate oxidase E.C.1.2.3.4.
    xanthinoxylaa E.C.1.2.3.2.
    Bd phenoloxidase ol Y.C.1.10.3.1. Similarly, other elements that are more selective for molecules more sensitive to the molecules can be made and, moreover, in the quality of meMimmobilized
    Definable
    farm component

    OxyDi, It -amoxides of alanine .1.4.3.2. n
    yksIyaa L-amiocic acid
    S w% l "4r" i3 "
    Oisidase .i-amino acids of the acid E.G.1.4.3.2.
    F-serinehgidataza Y.S.4.2.1.14.
    homoserine dehydratase and ES4.2.1.15.
    Treoniidehydratase E.S.4.2.1.16.
    Histidage B.C.4.3.1.3.
    Neither tritreductase E.C.1.6.6.4.
    PRI mme R 2. Bifunctional selective with respect to the molecules of the sensitive element.
    In case 1 of the sensing element there is a buffer solution 2 containing chlorridions, in which
    Continuation of table 2
    : cn
    "." -
     1: a 6 l and c a 3
    HHAHitaTopHHft electrode
    Ammonium selective electrode
    Also
     P.
    - -
    ""
    two platinum indicator electrodes 4 are immersed, embedded separately in chambers 3. Polypropylene film 6 is gas permeable to gas with the surface of indicator electrodes 4, the wall of a fish air bubble, sheep intestines, etc. can be used for strengthening the membrane (see table. .3J, in the opening of the sensing element housing 1. The surface of the film 6 is covered with a piece of casing, namely a membrane of natural origin. With a part of the surface of the membrane 7 of natural origin that is in contact with one a dicator electrode or, respectively, on the opposite side of the membrane surface, is associated with D-amino acid oxidase in immobilized form, and on another portion of the membrane surface that is in contact with another indicator electrode or, respectively, on the same portion membrane surface on the opposite side, linked to the oxidation of b-amino acids in immobilized form. The remaining details of the structure of a bifunctional sensitive element selective to mo / molecules are similar to swarming sensitive element described in Example 1. Preparation of the reaction layer to contain tory amino acid oxidase, carried out on sledukvdim manner POLYPROM gas permeable film is secured pilenovoy wet membrane. Then the membrane is allowed to dry for 30 minutes at room temperature. Afterwards, a portion of the membrane surface is applied in an equal layer of 10 µl of this phosphate buffer solution, the pH value of which is 8.3 and in which every mg contains 5 mg of L-amino acid oxidase in suspended form (E. C.1.4.W.Z., sigma crystalline), after which 10 µl of a 25% glutaraldehyde solution is added. Immediately after that, another part of the membrane surface is applied with a uniform layer of 10 µl of such phosphate buffer solution, which contains
    Glucose oxidase E.C..1.1.3.4.
    Glucose oxidase E.C..1.1.3.4.
    Ureaz
    E.G.3.5.1.5.
    Alcohol oxidase E.C.1.1.3.1.9.
    Hexose oxidase
    E.C.1.1,3.5.
    Creatinase
    Mr. E.C.3.5.3.3,
    Ureaz
    E.C.3.5.1.5. 10 mg oxidase) j-amino acids (BC1.4.3,2., Sigma (V) in suspended form, after which 10 µl of a 25% solution of glutaral acid dehydrate are added. The remaining steps for the manufacture of the sensing element are similar to those described in Example 1 Selective determination of the L and L amino acid isomers is carried out in parallel with the use of a bifunctional selective with respect to the molecules of the sensitive element. The measurement is carried out in an ice-free manner. The selective sensitive element is first calibrated with a solution containing and then a solution containing the 1-form of the amino acid to be determined (for example, phenylalanine). When calibrating, the sensitive element from the mixed phosphate buffer solution (pH 8) is placed in a standard solution that mixes at a constant rate the pH and the decrease in the intensity of the current (U) measured by the polarizing voltage — 0.6 V is measured. If the value of ui is a function of the concentration of the standard solution, then a calibration curve can be constructed using which, after measuring l, the ratio of optical isometers of various amino acids can be determined. Application made in co. In keeping with this example of a complex sensing element, it is extremely useful in studying the effectiveness of the resolvation process. To determine the ratio of the izomers, the additive method described in Example 1 can be applied. By analogy, other bifunctional selective elements with respect to molecules can be made (see cm. Table 4). Table 4. .
    Glucose oxidase
    Glucose B.C.1.1.3.4. Froze A multi-functional molecule-selective sensing element that can be used to parallelly determine various amino acids. The structure of the multifunctional sensing element is similar to that of the bifunctional sensing element described in Example 2. The difference lies in the fact that this sensing element does not contain a gas-permeable film b and that, moreover, to the electrolyte solution 2, which is in the sensing element case 1 immersed three selectively to the hydrogen ions of the glass electrodes 4, which are in contact with the natural passage membrane 7, on which three well-separated surface areas form three personal reaktsionnyz layer which contain three selective amino acid decarboxylase (L-lysine decarboxylase, L -tyrosine dekarbo silazu, L-phenylalanine decarboxylase) in an immobilized form.
    Continued table. four
    Glucosidea E.G.3.2.1.1.21.
    Glucose Oxidase E.C.1.1.3.4 The preparation of the reaction layers is carried out by analogy with that described in Example 2. With the help of selectively sensitive molecules, the content of L-tyrosine, LI-lysine and L-phenylalanine in samples containing amino acids. The determination can be carried out using three calibration curves corresponding to three amino acids, showing the dependence of concentration on potential. Similar versions of a multifunctional sensitive element selective in relation to molecules can also be made. Separate reaction layers in the immobilized state contain the following enzymes: L decarboxylase, arginine, li li-glutamic acid decarboxylase, U glutamine decarboxylase, L-histidine decarboxylase, urease. The proposed device allows to obtain electrodes with high mechanical strength and long service life.
    权利要求:
    Claims (3)
    [1]
    . 1. ELECTROCHEMICAL SENSOR FOR DETERMINING THE CONCENTRATION OF SUBSTANCES IN SOLUTIONS, containing a housing filled with an electrolyte, in which indicator and comparative electrodes are located, connected to a power source and a recording device, a filter is located in the wall, and a gas-permeable film on which the gel is placed at the end a layer containing an enzyme in a chemically bonded form, and between the case of the sensing element and the indicator electrode there is an insulating layer, which consists in that, in order to increase I mechanical strength and service life, the sensor further comprises a membrane made from a substance of natural origin and containing in chemically immobilized form in the surface layer of one or more enzyme species, wherein the membrane is in contact with the gas-permeable film.
    [2]
    2. The sensor according to π. 1, characterized in that the membrane of natural origin is in contact with a protective mesh or fabric made of inert material.
    [3]
    3. The sensor according to paragraphs. 1 and 2, characterized in that in the housing. There are several indicator electrodes.
    类似技术:
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    Preininger et al.1994|Optical fiber sensor for biological oxygen demand
    Tor et al.1986|New enzyme membrane for enzyme electrodes
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    Tsuchida et al.1981|Immobilization of D-glucose oxidase onto a hydrogen peroxide permselective membrane and application for an enzyme electrode
    Guilbault1976|[41] Enzyme electrodes and solid surface fluorescence methods
    US4350763A|1982-09-21|Method for determining biochemical oxygen demand
    Qiong et al.1998|Silk fibroin/cellulose acetate membrane electrodes incorporating xanthine oxidase for the determination of fish freshness
    SU1034618A3|1983-08-07|Electrochemical transducer for determining concentration of substances in solutions
    Toyota et al.1985|Determination of total protein in serum using a tyrosinase enzyme electrode
    CA1109374A|1981-09-22|Stabilization of activated galactose oxidase enzyme
    Campanella et al.1988|Enzyme sensor for the determination of choline-containing phospholipids in some biological fluids
    Santoni et al.1997|Enzyme electrode for glucose determination in whole blood
    Meier et al.1991|Rapid measurement of penicillin contained in complex media using enzyme-loaded glass electrodes
    Moody et al.1988|Factors concerning the design and calibration of an amperometric enzyme electrode system for the flow injection analysis of cholesterol
    Campanella et al.1989|Enzyme-entrapping membranes for enzyme sensors
    Sittampalam et al.1982|Amperometric determination of glucose at parts per million levels with immobilized glucose oxidase: An undergraduate experiment
    Filipović-Kovačević et al.2002|Amperometric biosensor for monitoring respiration activity of Saccharomyces cerevisiae in the presence of cobalt and zinc
    同族专利:
    公开号 | 公开日
    DE2926167A1|1980-01-31|
    GB2054859A|1981-02-18|
    US4354913A|1982-10-19|
    DE2926167C2|1981-12-03|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    US3539455A|1965-10-08|1970-11-10|Leland C Clark Jr|Membrane polarographic electrode system and method with electrochemical compensation|
    US3843446A|1971-04-20|1974-10-22|Research Corp|Preparation of enzymatically active membranes|
    US3896008A|1971-10-28|1975-07-22|Owens Illinois Inc|Electrochemical potentiometric method for selectively determining alkaline phosphatase content in aqueous fluids|
    GB1442303A|1972-09-08|1976-07-14|Radiometer As|Cell for electro-chemical analysis|
    CA1056746A|1974-09-06|1979-06-19|Chung J. Lai|Biologically active membrane material|
    US4092219A|1975-08-13|1978-05-30|Lin Min|Preparation of enzyme-membrane complexes|
    US4069106A|1977-01-13|1978-01-17|The United States Of America As Represented By The Secretary Of Agriculture|Immobilization of enzymes on keratin|
    US4216065A|1979-06-18|1980-08-05|University Of Delaware|Bio-selective electrode probes using tissue slices|JPS60114760A|1983-11-28|1985-06-21|Hitachi Ltd|Maltose sensor|
    US4605626A|1985-05-01|1986-08-12|Rohrback Technology Corporation|Electrochemical system with rotating electrode/sparger assembly|
    EP0214336A1|1985-09-13|1987-03-18|Phillips Petroleum Company|Determination of alcohol content in water immiscible organic systems|
    DE9116462U1|1991-06-10|1992-11-19|Degussa Ag, 6000 Frankfurt, De|
    US7529574B2|2003-08-14|2009-05-05|Isense Corporation|Method of constructing a biosensor|
    ES2334486B1|2008-07-11|2010-12-30|Biolan Microbiosensores, S.L.|BIOSENSOR SUPPORT.|
    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    HURA000683|HU179570B|1978-06-21|1978-06-21|Molecule selective sensor and method for making this|
    GB7925303A|GB2054859A|1978-06-21|1979-07-20|Molecule-selective sensor and a process for its preparation|
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