WO2021112802A1 - Mesure de glucose sanguin réutilisable capacitative/impédimétrique avec des polymères à empreinte moléculaire - Google Patents

Mesure de glucose sanguin réutilisable capacitative/impédimétrique avec des polymères à empreinte moléculaire Download PDF

Info

Publication number
WO2021112802A1
WO2021112802A1 PCT/TR2020/051199 TR2020051199W WO2021112802A1 WO 2021112802 A1 WO2021112802 A1 WO 2021112802A1 TR 2020051199 W TR2020051199 W TR 2020051199W WO 2021112802 A1 WO2021112802 A1 WO 2021112802A1
Authority
WO
WIPO (PCT)
Prior art keywords
glucose
sensor
layer
graphene
electrodes
Prior art date
Application number
PCT/TR2020/051199
Other languages
English (en)
Inventor
Zihni Onur UYGUN
Original Assignee
Ege Universitesi
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Priority claimed from TR2020/07785A external-priority patent/TR202007785A2/tr
Application filed by Ege Universitesi filed Critical Ege Universitesi
Publication of WO2021112802A1 publication Critical patent/WO2021112802A1/fr

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • G01N33/54373—Apparatus specially adapted for solid-phase testing involving physiochemical end-point determination, e.g. wave-guides, FETS, gratings
    • G01N33/5438—Electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
    • G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/66—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood sugars, e.g. galactose
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2600/00—Assays involving molecular imprinted polymers/polymers created around a molecular template
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/02—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance
    • G01N27/026—Dielectric impedance spectroscopy

Definitions

  • the present invention relates to a sensor that can be used to measure blood glucose using molecular imprinting technology.
  • the invention generally relates to a fast and precise, single frequency based impedimetric/capacitive electrochemical sensor that determines the amount of sugar (glucose, analyte) in liquid samples.
  • This electrochemical sensor contains molecularly imprinted polymers (MIPs) for use in real-time measurements of sugar molecules in liquid samples. The robust and strong structure of the molecularly imprinted polymers allows the sensor to be reused
  • the glucose molecule or dextrose is found in the blood in a chair conformation.
  • its state in the chair conformation namely the a-D-Glucose form
  • this is the form that circulates freely in the blood and is phosphatized when it enters the cell, and it is the primary energy source of the body. Its sensitive and rapid measurement is extremely important in people suffering from diabetes.
  • Glucose measurement strips and devices known in the art are disposable electrodes where glucose oxidase (GO x ) or glucose dehydrogenase (GDH) bio-recognizing enzyme systems are placed on the surface, which recognize glucose in the blood sample and enable it to be degraded enzymatically.
  • the measurement is carried out by transmitting the electrons given by the bioelectroactive molecules formed by glucose, which undergoes a biochemical change, to the measuring device as an electrochemical signal.
  • the use of enzyme systems in strips has limitations such as sensitivity -specificity problems and the systems allowing single use. For example, since the GO x system works in an oxygen dependent manner, its sensitivity is affected by the oxygen level in the blood. In contrast, although GDH has high sensitivity, it is not as specific as GO x , as it can interfere with other substances. In addition, the interaction of enzyme systems with humidity and temperature in the environment can affect the accuracy of the measurements.
  • Today's blood glucose analyzers which are the biosensor class, are analysis systems developed by immobilization of a biological sensor, that is, an enzyme, receptor, antibody, DNA or protein molecule, on a physicochemical transducer that has affinity only for the analyte molecule.
  • the signals resulting from the interaction between the biological sensor and the analyte molecule are transmitted to the analysis system by the "transducer" and the measurement is performed by analyzing the concentration-dependent response of this signal.
  • Biosensors can be catalytic or affinity based, depending on the biosensor on them.
  • catalytic-based biosensor systems an enzyme enzymatically degrades the analyte molecule and measurement is performed on the resulting secondary molecules or with tertiary molecules that can make these secondary molecules measurable.
  • affinity-based biosensors analysis is performed by measuring the degree of antigen-antibody, DNA-DNA, protein- ligand binding.
  • Affinity-based biosensors are more advantageous than catalytic ones in that they do not require any additional molecules other than the receptor-ligand pairs given.
  • Both types of biosensors can be designed based on electrochemical, optical and piezoelectricity according to the "transducer" type. If the signals emerging as a result of these physicochemical changes are electrochemical, "transducer" type electrical signals can be sensors. For example, if electroactive products are formed as an enzyme converts a substrate or the conductivity changes due to the charge distribution of the electrode surface, it is advantageous to measure the analyte electrochemically. On the other hand, if the resulting product is a product that absorbs or emits optically light, then an optical biosensor should be used. If there is a change in pressure, velocity, and strain, it is more appropriate to design a piezoelectric biosensor that converts these changes into electrical charges.
  • electrochemical biosensor systems are the least susceptible to interference, yet the most practical and cost-effective systems that can provide measurement in almost any type of substance.
  • the low cost and ease of use of electrochemical biosensor systems cause them to be preferred more in scientific studies.
  • Biosensor systems developed on the basis of bioaffmity are biosensor systems based on the binding kinetics of biomolecule and analyte.
  • Immune system biomolecules, single-stranded DNA, artificial single-stranded DNA (Aptamer) or cell surface receptors can be used as bio recognition agents in bioaffinity-based biosensors.
  • highly specific analyzes can be made in the field of health with biosensors.
  • Electrochemically developed affinity biosensors are usually based on measurement by signals from a secondary antibody molecule or a secondary marker molecule specific to the analyte molecule. Generally, electrochemical measurement can be performed as the secondary molecule changes the electric current in a measurable way.
  • biosensor systems seem to be very advantageous and sensitive measurement systems due to the specificity of biological sensors to analyte, the use of biological receptors as a sensor molecule limits the analysis when the environmental conditions of the biosensor are considered.
  • Optimum working conditions are required for the efficient operation of biological molecules. These are physical properties such as pH, temperature, pressure, light, ion strength, polarity of the liquid being measured. Even small changes in these properties can affect a measurement. For example, acetyl choline esterase enzyme activity is extremely sensitive to pH changes.
  • Another example is the regeneration of antigen-antibody based biosensors. Disruption of antigen-antibody interactions in this process is achieved by changing the ionic strength, but in the meantime, the molecules can be damaged.
  • Another example is the effects of low ambient temperature. In this case, the activity of the used enzyme may not be observed/observed low. As in these examples, a number of interactions restrict the use of biosensor systems and pose a major obstacle to practical applications.
  • biosensor instead of the term biosensor, the term sensor is more appropriate, because synthetic sensors are produced instead of biosensors.
  • the production and application of these artificial receptors is carried out by polymerizing monomers with special functional groups in such a way that they surround the analyte molecule according to its three-dimensional properties. Thus, it is possible to design specialized cavities for certain molecules to enter on these polymers.
  • This artificial receptor creation technology is called molecular imprinting or molecular imprinting technology (MIT).
  • MIT molecular imprinting
  • MIP molecular imprinted polymers
  • MIT in brief, is the technology of producing monomers on this mould, which will surround the molecule in accordance with the three- dimensional structure of a mould molecule in complicated and complex solutions.
  • the chemical structure of the monomers of the artificial polymeric receptor to be formed is chosen according to the functional group or groups that will interact with the target molecule to be bound. For example, if there are amine groups or groups that can form a positive charge on the analyte, that is, the target molecule, the monomer molecule must functionally contain negatively charged groups in order for the target molecule to surround/attract.
  • the "fingerprint" of the target molecule is created on the polymer structure and an artificial receptor containing the cavities that only the target molecule can enter, is obtained Afterwards, these durable polymers, on which specific cavities are formed, can selectively recognize and bind the target molecule.
  • MIT is a relatively new technology that can perform different tasks such as molecular recognition, catalysis, chromatographic separation, chemical identification in different solvents. These polymers are not easily affected by the physical conditions in which bio receptors are affected and they are more closed to interference. However, their production is also less costly than biologically derived receptors. All these advantages show that the use of MIP instead of biological molecules is a more appropriate choice in sensor systems.
  • MIPs Molecular imprinted polymers
  • the invention relates to an impedimetric/capacitive electrochemical sensor modified with molecular imprinted polymers (MIPs) that can quickly detect the amount of sugar (glucose, analyte) in liquid samples, such as blood, plasma, urine, etc. based on a single frequency.
  • sugar glucose
  • MIPs molecular imprinted polymers
  • glucose is bound to a unique cavity located on the sensor surface. Since the glucose molecule entering into the glucose-specific cavity with this sensor will only generate a binding-separation signal and there is no electrochemical reaction, it is highly selective since the impedimetric/capacitive method is used as the method only to measure the binding.
  • an electrochemical sensor has been developed that is not affected by environmental conditions, can be used multiple times and does not interfere with substances other than sugar.
  • the interaction of the bioreceptor-analyte molecule can be determined by measurement of surface capacitance or impedance without the use of secondary molecules. Since impedance and capacitance allow examining the surface characteristics of the electrodes electrically, binding of only the bioreceptor-analyte is sufficient for the measurement.
  • new generation sensors have been designed by diol formation to contain artificial recognition agents to be used for glucose measurement, that is, molecularly imprinted polymers and boronic acid derivatives that can interact with hydroxyl groups on glucose entering these imprinted cavities.
  • artificial recognition agents to be used for glucose measurement that is, molecularly imprinted polymers and boronic acid derivatives that can interact with hydroxyl groups on glucose entering these imprinted cavities.
  • These polymers were synthesized electrochemically (in situ) using molecular imprinting technology and placed on the sensor that contains strips, that is, glucose-imprinted polymers.
  • the new generation strips were developed using an artificial receptor that would directly bind to the target molecule glucose on an affinity basis, not an indirect recognition agent (enzyme).
  • EIS can measure the thickness of the electrode surface or the charge distribution (capacitance), it is a sensitive method to determine even small changes that change the electrical charge distribution on the electrode surface.
  • electrode surface capacitance can be measured using a potentiostat without any biochemical reaction.
  • Single frequency impedance is called a non-electrochemical method by measuring glucose binding at a frequency that does not change in terms of time-dependent resistance, i.e. impedance.
  • the binding characteristic of glucose to the strip surface is observed, and surface impedance and capacitance are used as the measurement method.
  • a glucose sensor modified with glucose binding MIPs formed on the graphene layer between a platinum electrode (electron source) and a gold electrode (electron acceptor) has been developed. With the frequency potential applied between these electrodes, the glucose amount can be determined by impedimetric and capacitive measurement.
  • glucose concentrations in different samples can be determined by measuring the increase in the impedance of the strip/electrode and the decrease in capacitance in unit of time, caused by the glucose specifically bound to these polymers in the new generation strips, which are designed as modified with MIP on the sensor surface and contain glucose-imprinted polymers.
  • the change in the electrical charge distribution of the surface of the inventive sensor electrodes reduces the surface capacitance (C) together with the impedance, it is important to monitor glucose binding not only by impedance measurements but also by capacitance measurements.
  • the developed glucose measurement basis is in chrono-impedimetric and chrono- capacitive properties.
  • a strip modified with glucose binding MIPs formed on the graphene layer between a platinum electrode (electron source) and a gold electrode (electron acceptor) has been developed.
  • the glucose amount can be determined by impedimetric and capacitive measurement.
  • FIG. 1 Side view and parts of the glucose sensor
  • Figure 2 Top view of the glucose sensor
  • Figure 3 Side integrated view of the glucose sensor Definitions of Elements/Pieces/Parts Forming the Invention
  • the invention relates to an electrochemical sensor modified with molecular imprinted polymers (MIPs) that can quickly detect the amount of sugar (glucose, analyte) in liquid samples, such as blood, plasma, urine, etc. based on a single frequency
  • MIPs molecular imprinted polymers
  • Figure 1 shows the side view and parts of the inventive sensor.
  • the inventive sensor that detects the glucose amount in liquid samples includes the insulating support layer (1) used as the top layer coating and increasing the durability of the sensor surface, the plastic insulating layer (2) containing the electrodes (4, 6), the MIP (3) with glucose selective cavities, the gold electrode (4), which interacts electrically with the platinum electrode (6) through the graphene connection layer (5), the graphene connection layer (5) which is located on the plastic insulating layer (2) between the gold and platinum electrodes (4,6) and conducts the electric current between these two electrodes, the platinum electrode (6) that interacts electrically with the gold electrode (4) through the graphene connection layer (5), molecular glucose imprinted polymer layer (7) specific to glucose, which is the analyte desired to be determined, placed on the graphene connection layer (5), the sample chamber (8), which can receive at least 50 pL of sample, which is defined to bring the sample in which the sugar amount is to be determined to contact the sensor, copper conductive wires (9) used for the external connection of gold (4) and platinum (6) electrodes
  • Two types of monomers are used in the production of molecular imprinted polymers.
  • AAPBA acrylamidophenyl boronic acid
  • a solvent with a pH of 7 and containing 50 mM of dihydrogen phosphate is dissolved in a solvent with a pH of 7 and containing 50 mM of dihydrogen phosphate.
  • a glucose (Glc) is added into this mixture and 0.01-0.5 mg, preferably 0.5 mg of pyrrole is added to this mixture as secondary monomer and it is waited at room temperature ( ⁇ 25 °C) for a maximum of 4 hours until the sensor is prepared.
  • the liquid samples whose glucose amount is to be determined are dropped into the sample chamber (8) by the sensor of the invention.
  • a maximum potential of 200 mV is applied to the sensor with a frequency in the range of 100-150 Hz.
  • the binding of glucose in the liquid sample to the glucose selective MIP cavities on the graphene layer increases impedance and decreases capacitance. Converting the rate of increase in impedance to ratio of glucose confirms the selectivity of glucose by showing a decrease in the decrease in capacitance due to glucose binding.
  • the amount of sugar in liquid samples can be detected with the sensor of the invention.
  • Capacitance measurement is used here as a control mechanism.
  • the increase in capacitance is independent of the glucose concentration, but if there is binding to the cavities, in other words, if glucose is bound to the cavities, the change in capacitance correlates with the glucose concentration.
  • glucose binding to the cavities an increaseis observed over time and then, no increase is observed. However, if it accumulates on the surface, this increase continues, so when both the impedance increase and the capacitance increase are correlated with each other, the correct amount of glucose is measured.
  • the interacting boronic acid and imino groups are polymerized after self-arrangement around glucose, and the cavities are thus formed in accordance with the three-dimensional structure of glucose. Since this hollow glucose is suitable for its three-dimensional structure, only glucose can enter these cavities. This can be thought as a key-lock match.
  • glucose concentrations in different samples can be determined by measuring the impedance/capacitance changes of strip/electrode and the decrease in capacitance in unit of time, caused by the glucose specifically bound to these polymers in the new generation strips, which are designed as modified with MIT on its surface and contain glucose-imprinted polymers. Since the change in the electrical charge distribution of the surface of the electrodes changes the surface capacitance (C) together with the impedance, it is important to monitor glucose binding not only by impedance measurements but also by capacitance measurements. In addition, since these measurements will follow the correlated changes in unit of time, the developed glucose measurement basis is in chronoimpedimetric and chrono-capacitive properties.
  • the binding characteristic of glucose to the surface is observed, and surface impedance and capacitance are used as the measurement method.
  • Impedance (Z or R) or electrochemical impedance spectroscopy (EIS) is an effective measurement technique used in examining the electrolyte-electrode interface, in measuring mass transfer rates and investigating electrode reactions. With this measurement, non-electroactive large mass proteins and antigens can be measured at very low detection ranges and very low detection limits.
  • This algorithm was calculated to be 1 millimeter square of graphene coated MIP area and derived as follows: with binding of glucose to the surface, an increase in capacitance and impedance is observed, this increase continues for 3 seconds, after this second there is no increase in capacitance, but increase in impedance continues and an increase is achieved in impedance with glucose concentration. If the capacitance increases and the impedance does not change after 3 seconds, it means that non-glucose molecules accumulate on the surface. This time increases as the graphene-coated area increases. In order for the sensor to be used again after the measurement, the electrode is put into ethanol-water mixture and kept for 5 minutes. The sensor can be reused after the Glc has been removed (washing)
  • the measuring range of glucose in a liquid sample is in the range of 20 mg/dL and 800 mg/dL with this sensor.
  • a very thin cellulose membrane that protects the MIP at the point where this liquid sample contacts.
  • This membrane has the ability to hold the shaped elements originating from blood and it was made of nitrocellulose material of 10 pm thickness that allows the passage of molecules that are below 1000 Daltons.
  • the sensor of the invention is a lateral flow sensor. It is designed as a 3.5mm headphone jack that can be connected to a device, mobile phone, analyzer or a platform by means of copper conductive wires (9) connected separately to the gold (4) and platinum (6) electrodes of this sensor.

Abstract

La présente invention concerne un capteur qui peut être utilisé pour mesurer le glucose sanguin à l'aide d'une technologie d'impression moléculaire. La présente invention concerne de manière générale des capteurs électrochimiques capacitifs/impédimétriques monofréquences uniques et rapides utilisés afin de déterminer la quantité de sucre (glucose, analyte) dans des échantillons liquides.
PCT/TR2020/051199 2019-12-04 2020-12-01 Mesure de glucose sanguin réutilisable capacitative/impédimétrique avec des polymères à empreinte moléculaire WO2021112802A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
TR2019/19281 2019-12-04
TR201919281 2019-12-04
TR2020/07785A TR202007785A2 (tr) 2019-12-04 2020-05-18 Moleküler baskilanmiş poli̇merler i̇le i̇mpedi̇metri̇k/kapasi̇ti̇f tekrar kullanilabi̇li̇r kan şekeri̇ ölçümü
TR2020/07785 2020-05-18

Publications (1)

Publication Number Publication Date
WO2021112802A1 true WO2021112802A1 (fr) 2021-06-10

Family

ID=76221815

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/TR2020/051199 WO2021112802A1 (fr) 2019-12-04 2020-12-01 Mesure de glucose sanguin réutilisable capacitative/impédimétrique avec des polymères à empreinte moléculaire

Country Status (1)

Country Link
WO (1) WO2021112802A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN115266889A (zh) * 2022-08-01 2022-11-01 江南大学 一种用于检测葡萄糖浓度的GaN传感器及检测方法

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5704354A (en) * 1994-06-23 1998-01-06 Siemens Aktiengesellschaft Electrocatalytic glucose sensor
WO2016090189A1 (fr) * 2014-12-03 2016-06-09 The Regents Of The University Of California Capteurs chimiques et biocapteurs non invasifs et portables
WO2016200104A1 (fr) * 2015-06-12 2016-12-15 서울대학교산학협력단 Capteur biologique et son procédé de formation et système de régulation de glucose, procédé de formation de système de régulation de glucose, et procédé de régulation de glucose par ce dernier
KR20180006835A (ko) * 2016-07-11 2018-01-19 삼성전자주식회사 바이오 센서 및 그의 제작 방법

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5704354A (en) * 1994-06-23 1998-01-06 Siemens Aktiengesellschaft Electrocatalytic glucose sensor
WO2016090189A1 (fr) * 2014-12-03 2016-06-09 The Regents Of The University Of California Capteurs chimiques et biocapteurs non invasifs et portables
WO2016200104A1 (fr) * 2015-06-12 2016-12-15 서울대학교산학협력단 Capteur biologique et son procédé de formation et système de régulation de glucose, procédé de formation de système de régulation de glucose, et procédé de régulation de glucose par ce dernier
KR20180006835A (ko) * 2016-07-11 2018-01-19 삼성전자주식회사 바이오 센서 및 그의 제작 방법

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN115266889A (zh) * 2022-08-01 2022-11-01 江南大学 一种用于检测葡萄糖浓度的GaN传感器及检测方法

Similar Documents

Publication Publication Date Title
Pundir et al. Determination of urea with special emphasis on biosensors: A review
Liu et al. Electrochemical microfluidic chip based on molecular imprinting technique applied for therapeutic drug monitoring
Xie et al. Electrochemical sensor for 2, 4-dichlorophenoxy acetic acid using molecularly imprinted polypyrrole membrane as recognition element
Wang et al. Electrochemical sensor for simultaneous determination of uric acid, xanthine and hypoxanthine based on poly (bromocresol purple) modified glassy carbon electrode
Hillberg et al. Molecular imprinted polymer sensors: implications for therapeutics
Kawano et al. Rapid detection of a cocaine-binding aptamer using biological nanopores on a chip
Aghaei et al. A novel capacitive biosensor for cholesterol assay that uses an electropolymerized molecularly imprinted polymer
Peng et al. Development of a new atropine sulfate bulk acoustic wave sensor based on a molecularly imprinted electrosynthesized copolymer of aniline with o-phenylenediamine
Moreira et al. Electrochemical biosensor based on biomimetic material for myoglobin detection
Chen et al. Detection of uric acid based on multi-walled carbon nanotubes polymerized with a layer of molecularly imprinted PMAA
US20040126814A1 (en) Sensor having molecularly imprinted polymers
Reddy et al. Artificial molecular recognition material based biosensor for creatinine by electrochemical impedance analysis
Dabrowski et al. Early diagnosis of fungal infections using piezomicrogravimetric and electric chemosensors based on polymers molecularly imprinted with D-arabitol
Yücebaş et al. Molecular imprinted polymer based electrochemical sensor for selective detection of paraben
US20100173421A1 (en) Sensor
Kitade et al. Potentiometric immunosensor using artificial antibody based on molecularly imprinted polymers
Li et al. A novel sensitive and selective electrochemical sensor based on molecularly imprinted polymer on a nanoporous gold leaf modified electrode for warfarin sodium determination
WO1997039343A1 (fr) Biodetecteurs
Soylemez et al. Development of a novel biosensor based on a conducting polymer
Mihailescu et al. Platform with biomimetic electrochemical sensors for adiponectin and leptin detection in human serum
EP1960774B1 (fr) Capteur
Xu et al. Ion channel mimetic chronopotentiometric polymeric membrane ion sensor for surface-confined protein detection
WO2021112802A1 (fr) Mesure de glucose sanguin réutilisable capacitative/impédimétrique avec des polymères à empreinte moléculaire
Prasad et al. Barbituric acid sensor based on molecularly imprinted polymer‐modified hanging mercury drop electrode
EP1671125A1 (fr) Detection sans marqueur de biomolecules

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 20895843

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

32PN Ep: public notification in the ep bulletin as address of the adressee cannot be established

Free format text: NOTING OF LOSS OF RIGHTS PURSUANT TO RULE 112(1) EPC (EPO FORM 1205A DATED 06/09/2022)

122 Ep: pct application non-entry in european phase

Ref document number: 20895843

Country of ref document: EP

Kind code of ref document: A1