WO2023186363A1 - Biocapteurs pour l'identification d'espèces de nématodes - Google Patents

Biocapteurs pour l'identification d'espèces de nématodes Download PDF

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WO2023186363A1
WO2023186363A1 PCT/EP2023/051450 EP2023051450W WO2023186363A1 WO 2023186363 A1 WO2023186363 A1 WO 2023186363A1 EP 2023051450 W EP2023051450 W EP 2023051450W WO 2023186363 A1 WO2023186363 A1 WO 2023186363A1
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biosensor
electrodes
nematode
signal
electrochemical
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PCT/EP2023/051450
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English (en)
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Valtencir ZUCOLOTTO
Dirceu Ferreira JUNIOR
Isabella SAMPAIO DO NASCIMENTO
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Bayer Aktiengesellschaft
Universidade De São Paulo
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    • 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
    • G01N33/5308—Immunoassay; Biospecific binding assay; Materials therefor for analytes not provided for elsewhere, e.g. nucleic acids, uric acid, worms, mites
    • 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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2333/00—Assays involving biological materials from specific organisms or of a specific nature
    • G01N2333/435—Assays involving biological materials from specific organisms or of a specific nature from animals; from humans
    • G01N2333/43504—Assays involving biological materials from specific organisms or of a specific nature from animals; from humans from invertebrates
    • G01N2333/43526—Assays involving biological materials from specific organisms or of a specific nature from animals; from humans from invertebrates from worms
    • G01N2333/4353—Assays involving biological materials from specific organisms or of a specific nature from animals; from humans from invertebrates from worms from nematodes

Definitions

  • Plant-parasitic nematodes are parasites that in at least one phase of their life cycle use the roots of plants to acquire nutrients. Parasitism can cause stunted growth of plants, root necrosis, and leaf discoloration. Global agricultural losses caused by plant-parasitic nematodes amount to an estimated USD 157 billion annually, significantly impacting the worldwide economy.
  • the infected fields are mainly treated with crop rotation, where a nematode-resistant cultivar is planted, and with the use of nematicides.
  • these strategies are not directed to the treatment of one single species and can be ineffective when the nematode species present in the soil is resistant to the adopted strategy.
  • the extensive use of nematicides can not only make nematodes resistant but also cause several health problems for the population.
  • the identification and quantification of nematode species are essential for the adoption of the best strategy and for control to be carried out when the nematode population density is not yet high, avoiding the use of high doses of nematicides.
  • Identification of nematodes is currently performed using microscopy techniques, in which species differentiation is based on the morphometric characteristics of the specimens, or by molecular analysis using PCR (polymerase chain reaction) for DNA amplification and electrophoresis for the identification of the amplified sequences.
  • PCR polymerase chain reaction
  • electrophoresis for the identification of the amplified sequences.
  • point-of-care devices such as biosensors, appear as a new tool for the detection of agricultural pests, since the analysis of the sample can be performed in a simpler and faster way.
  • Biosensors are platforms on which biological molecules, such as enzymes, proteins, and DNA, form a biorecognition layer capable of selectively binding to the molecule to be detected.
  • the interaction between complementary molecules causes physicochemical changes that are converted to a signal measurable by a transducer, such as an electrode.
  • the signal is processed and converted into a physical parameter, e.g. electrical current, capacitance, or impedance.
  • Biosensors can be classified according to the analytical technique used to monitor interactions. Examples are electrochemical, optical, piezoelectric, and electrical biosensors. Electrical and electrochemical biosensors are interesting because they provide fast results, are cost-effective, and can be miniatured for point-of-care detection. These devices have been used in several areas, for example, in the detection of diseases, pesticides, and transgenic food.
  • the present invention provides a biosensor system comprising one or more electrodes capable of converting a physicochemical signal transduced from a biorecognition layer into an electronic signal; a biorecognition layer comprising biomolecules immobilized onto one or more electrodes capable of binding to the specific analyte of the nematode species.
  • the biorecognition layer can be formed by immobilizing biomolecules capable of selective binding to the analyte onto the electrodes. Covalent and non-covalent immobilization methods can be used.
  • thiolated molecules such as mercaptopropionic acid (MPA) and 11-mercaptoundecanoic acid (MU A) are typically used.
  • Crosslinking molecules such as carbodiimide (EDC) and N-Hydroxysuccinimide (NHS) also can be used to activate functional groups.
  • EDC carbodiimide
  • NHS N-Hydroxysuccinimide
  • the non-Faradaic impedance spectroscopy technique is used for capacitive measurements.
  • This technique consists of applying a potential difference between two metallic plates (electrodes), forming a capacitor. Biosensors operated by this technique are also called capacitive biosensors.
  • the non-Faradaic method is performed using only an electrolyte solution such as KC1 and PBS, without redox mediators.
  • the events on the recognition layer lead to changes in the dielectric constant of the medium (e) that directly affects the system capacitance, as described in this equation:
  • C eeoA/d
  • eo the vacuum dielectric constant (given by the value 8.85419 pF/m)
  • A the area of the plates
  • d the distance between them.
  • the geometry of the electrodes affects the detection capacity of these devices, since the greater the eoA/d factor, the greater the change in capacitance.
  • the electrode must have parallel plates very close to each other and a large geometric area.
  • interdigitated electrodes IDE
  • IDE interdigitated electrodes
  • several metallic plates called fingers are placed in parallel with each pair forming a capacitor.
  • the capacitors are associated in parallel and the total capacitance of the system (C t ) is given by the sum of the individual capacitances (Cl, C2, ...) as described by this equation:
  • a capacitive biosensor comprises one or more (preferably two) metallic electrodes which form the capacitor.
  • the electrodes are interdigitated.
  • several metallic plates called fingers are placed in parallel with each pair forming a capacitor.
  • the capacitive biosensor comprises interdigitated electrodes having at least 10 fingers. The fingers are separated by a distance of 1 to 100 pm.
  • the electronic signal which may be an electrical current, impedance, or capacitance is analyzed by the data processing device and provided to the user in a numerical or graphical representation, such as graphs or tables.
  • a numerical or graphical representation such as graphs or tables.
  • multivariate statistical methods can be used, such as multivariate analysis of variance, multivariate analysis of covariance, multivariate regression, principal component analysis, factor analysis, linear discriminant analysis, artificial neural networks. The results of such methods may be shown as score plots.
  • EIS electrochemical impedance spectroscopy
  • the electrochemical biosensor comprises three electrodes being a counter electrode, a working electrode, and the reference electrode. Biorecognition occurs on the surface of the working electrode, which is responsible for the transduction of the biochemical reaction.
  • the current generated by the system flows between the working electrode and the counter electrode.
  • the reference electrode is then used, which must be maintained at a known fixed potential.
  • the electrochemical biosensor may comprise more than one working electrode, one counter electrode, and reference electrodes.
  • the impedance is dependent on the events that occur on the surface of the working electrode and, for this reason, it can be monitored to determine the presence of the target molecule in the sample.
  • the excitation wave can be either an alternating potential or an alternating current, so that one of the parameters is controlled and the other is measured.
  • a sinusoidal potential results in a sinusoidal current that oscillates at the same frequency.
  • the components of the electrochemical system cause a phase and amplitude shift between these two waves.
  • the system impedance i.e., the resistance in an alternating current system, is calculated as the ratio between the sinusoidal potential and the response current.
  • the measurements are performed using redox mediators, so that the redox reactions between them are monitored.
  • the potassium ferricyanide (K 3 Fe(CN) 6 ) and potassium ferrocyanide (K 4 Fe(CN) 6 ) redox couple is the most used for this purpose.
  • This EIS method is so named because the current generated by electrochemical reactions obeys Ohm’s law, that is, it is directly proportional to the number of electrons involved in the redox reaction (n), the Faraday constant (F), the electrode surface area (A), and the flow of electroactive molecules (j):
  • the electrochemical impedance measurements can be represented by the Bode diagram, in which absolute values of impedance or phase angle are plotted as a function of frequency, or by the Nyquist diagram, in which real impedance values are given as a function of their respective imaginary values on a complex plane.
  • the analysis of the Nyquist diagrams allows obtaining information about the components of the electrochemical system, such as the double-layer capacitance (Cai), charge-transfer resistance (Ret), solution resistance (Ro), and Warburg impedance (Z w ). All of these components form an electrical circuit in the electrochemical system that can be determined using theoretical models. An equivalent circuit is commonly found in electrochemical biosensors and modeled by John Randles.
  • the Nyquist plot is divided into three regions, according to the frequency of the excitation wave.
  • the capacitor impedance is very low, so that the system can be approximated as an open circuit, which impedance is given only by the resistance of the solution.
  • charge transfer processes are predominant.
  • R ct diameter
  • This parameter is dependent on the configuration of the biorecognition layer and, therefore, it is widely used to describe the processes that occur in it.
  • the system impedance is governed by the diffusion of electroactive species (Z w ) and the double-layer capacitance (C i), which behavior is represented in the spectrum by a straight line with a slope.
  • the invention further provides a diagnostic kit comprising (a) a biosensor and (b) a data processing device comprising means for receiving the electronic signal, analyzing the electronic signal, and generating an output of the electronic signal to a user.
  • nematode species may be detected simultaneously.
  • a method for the preparation of an analyte suitable for the use in the method for detecting simultaneously more than one nematode species comprising
  • step (b) extracting the proteins from nematodes and nematode eggs isolated in step (a) by homogenization.
  • the method for the preparation of an analyte suitable for use in the biosensor is executed in an agricultural field, greenhouse or glasshouse.
  • Figure 1 Score plot of the principal component analysis (PCA) obtained by the combination of two sensory sets - electrodes with organic film and electrodes with SAM - for discrimination of samples without incubation period. The 95% confidence ellipse is shown for each group of samples.
  • PCA principal component analysis
  • FIG. 2 Bar chart showing the percentage change in impedance of the biosensor constructed for the P. brachyurus species.
  • the biosensor was tested with a positive sample (containing the target proteins) and two negative samples (containing proteins from M. javanica or H. glycines species) .
  • a biosensor is a device that allows the identification and quantification of a molecule of interest, the analyte.
  • the biosensor is comprised of a by recognition layer which contains biomolecules such as DNA, enzymes, proteins, and/or antibodies which are suitable to bind selectively to the analyte.
  • the biosensor further comprises a transducer being one or more electrodes which is capable of converting the physicochemical change occurring in the biorecognition layer by the binding into an electronic signal.
  • a capacitive biosensor comprises one or more, preferably two metallic electrodes which form the capacitor.
  • the electrodes are interdigitated.
  • several metallic electrodes called fingers are placed in parallel with each pair forming a capacitor.
  • the biosensor comprises three or more electrodes. In a preferred embodiment the biosensor comprises two or more electrodes.
  • Electrodes in particular interdigitated electrodes, are usually manufactured using lithography and deposition techniques, e.g. sputtering, in which metals are deposited in the desired configuration on insulating substrates such as glass and silicon.
  • lithography and deposition techniques e.g. sputtering, in which metals are deposited in the desired configuration on insulating substrates such as glass and silicon.
  • the electrodes may be disposable gold electrodes on glass substrate. Such electrodes can be manufactured by photolithography.
  • Atomic force microscopy may be used for the morphological characterization of the working electrodes.
  • X-ray photoelectron spectroscopy technique may be used to analyse the chemical composition of the electrodes and to assess the effectiveness of electrochemical cleaning.
  • the biosensor comprises three electrodes being a counter electrode, a working electrode, and the reference electrode. Biorecognition occurs on the surface of the working electrode, which is therefore responsible for the transduction of the biochemical reaction.
  • the current generated by the system flows between the working electrode and the counter electrode, which must have a high surface area.
  • the reference electrode is then used, which must be maintained at a known fixed potential.
  • the biorecognition layer can be formed by immobilising biomolecules capable of selective binding to the analyte onto the electrodes.
  • biomolecules capable of selective binding to the analyte onto the electrodes.
  • biomolecules are fragments of DNA or RNA, antibodies, proteins, protein fragments, secondary metabolites, or saccharides.
  • Coupling through Protein A or G are examples for non-covalent immobilization.
  • Covalent immobilisation uses functional substrates such as carbodiimide (EDC) and N-Hydroxysuccinimide (NHS) or mercaptopropionic acid (MPA) and 11-mercaptoundecanoic acid (MU A) molecules.
  • APTES 3- Aminopropyltriethoxysilane
  • Iridium Tin Oxide electrodes may be used for Iridium Tin Oxide electrodes.
  • the electronic signal which may be an electrical current, impedance, or capacitance is analysed by the data processing device and provided to the user in a numerical or graphical representation, such as graphs or tables. Such graphs often show the capacitance in relation to the logarithm of the frequency.
  • multivariate statistical methods can be used, such as multivariate analysis of variance, multivariate analysis of covariance, multivariate regression, principal component analysis, factor analysis, linear discriminant analysis, artificial neural networks.
  • the results of such methods may be shown as score plots.
  • the analyte is one or more biomolecules, such as fragments of DNA, fragments of DNA or RNA, proteins, protein fragments, secondary metabolites, or saccharides which are detected by the biomolecules immobilised in the bio recognition layer.
  • the analyte are species-specific proteins from nematode species.
  • the biosensor comprises an electrode capable of converting a physicochemical signal transduced from a biorecognition layer into an electronic signal.
  • the biosensor may comprise more than one electrode, preferably one counter electrode, for working electrode, and two reference electrodes.
  • the biosensor may also comprise of interdigitated and electrodes having at least 10, preferably 20, more preferably 50, even more preferably 100, and most preferably 150 fingers. The fingers are separated by a distance of 1 to 100 microns, preferably 2 to 80 microns, more preferably 5 to 50 microns, even more preferably 10 to 25 microns, or most preferably 10 pm.
  • the interdigitated electrodes are manufactured using photolithography technique with sputtering metallization.
  • the biosensor further comprises a biorecognition layer comprising biomolecules immobilized onto the electrode capable of binding a component of an analyte specific for a nematode species.
  • the biomolecules may be a nucleic acid such as DNA or RNA or antibodies such as polyclonal or monoclonal antibodies.
  • the recognition of the analyte in the biorecognition layer occurs on the surface of the working electrode, which is therefore responsible for the transduction of the biochemical reaction.
  • the current generated by the system flows between electrodes, for example the working electrode and the counter electrode, which must have a high surface area.
  • the reference electrode is then used, which must be maintained at a known fixed potential.
  • amperometric measurements There are several electroanalytical techniques with different operating principles.
  • the amperometric, voltammetric, potentiometric and impedimetric measurements stand out.
  • amperometric measurements a fixed potential is applied to the reference electrode and the current generated by the redox reaction of the electroactive species between the working electrode and the counter electrode is measured.
  • the technique is called voltammetry.
  • potentiometric measurements it is measured the potential difference between the working and reference electrodes, resulting from charge accumulation on the surface of the working electrode.
  • impedimetric measurements consist of applying a fixed potential and measuring the impedance of the system.
  • the parameters obtained by these techniques are dependent on the events that occur on the surface of the working electrode and, for this reason, allow determining the presence of the target molecule in the sample.
  • Voltammetric measurements consist of applying a potential that varies over time.
  • the way in which the variation of the potential on the working electrode occurs in relation to the fixed potential of the reference electrode defines the type of voltammetry.
  • Square-wave voltammetry, differential-pulse voltammetry, and cyclic voltammetry are some examples of voltammetric techniques.
  • Cyclic voltammetry provides information on the redox potential of electroactive species and the current generated by electrochemical reactions. For that, a triangular wave is applied that linearly sweeps a potential range. When reaching a stipulated potential, the sweep direction is reversed, varying the potential until the cycle is completed. During scanning towards the most positive potential, the electroactive species is oxidized to an E p a potential, with anodic current I pa . In the opposite direction, the species is reduced in an E pc potential, with a cathodic current I pc The graph generated by the voltammetry measurements is called voltammogram.
  • the redox currents (I p ) are proportional to the scanning speed of the potential (v), the electroactive area of the electrode (A), the number of electrons involved in the reaction (n), the concentration of the electroactive species (C) and the diffusion coefficient (D), as described by the Randles-Sevcik equation:
  • the variation in the redox potential and the current generated can be indicative of the presence of the analyte and its concentration, enabling the use of this technique both as a qualitative and quantitative method.
  • Samples of the three selected species containing eggs and juveniles were collected from soils. Samples in an aqueous solution were centrifuged in a first stage for 10 min at 2000 rpm, so that the nematodes and soil residues were deposited at the botom of the centrifugation tube. The supernatants were removed and a 40 g/75 ml sucrose solution was added; the samples were homogenized and centrifuged for 10 min at 650 g rotation. After this second centrifugation, the nematodes (eggs and juveniles) were suspended in the supernatant while the residues formed precipitates, due to the sucrose density being higher than the density of nematodes.
  • the supernatants containing the nematodes were collected and filtered through a 500 mesh size sieve (0.025 mm mesh opening). In this procedure, the nematodes are retained in the mesh to be collected by inverting the sieve and rinsing with an appropriate volume of water. Finally, the solutions were analyzed using an optical microscope with a 40X magnifying glass to check whether the final samples contained a significant number of nematodes and if the soil residues had been removed.
  • the proteins were extracted.
  • the samples containing nematodes were processed in a Turrax-type homogenizer for 15 s, three times. Then, to break the cell membranes and extract the proteins, the samples were sonicated in a tip sonicator for 1 h with 20% amplitude. As the sample is heated during this process, they were immersed in ice, which was changed every 20 min of sonication.
  • the proteins in the homogenate were quantified using the Bradford colorimetric method, which uses the Coomassie brilliant blue BG-250 dye. Samples of the extracted proteins were used to immunize rabbits for aiming the production of polyclonal antibodies.
  • the immunized serum containing the antibodies was used for the construction of the biorecognition layer of the immunosensors.
  • the extracted proteins were used as positive and negative controls in the detection stage.
  • the electrochemical and interdigitated electrodes were fabricated using the photolithography technique with sputering metallization.
  • the substrates BK7 glass
  • a photosensitive film called photoresist
  • the substrates were exposed to ultraviolet light through an optical mask containing the configuration desired for the device.
  • a positive photoresist was used, in which the regions exposed to light were removed by the revealing chemical solution (aqueous potassium hydroxide solution).
  • the substrates were cleaned with oxygen plasma for removing organic residues.
  • Metallization was performed in a vacuum chamber and the thickness was measured by a quartz crystal.
  • a 15 nm chrome layer was first deposited for adhesion on the substrate, then a 120 nm thick gold layer was deposited.
  • a 15 nm titanium film was used as the adhesion layer.
  • the electrochemical electrodes were cleaned with O2 plasma using 35 W power and 5 seem gas flow rate (cm 3 /min).
  • Electrodes functionalization were characterized as for morphology, by atomic force microscopy. Roughness was determined in 4 different electrodes for reproducibility analysis. For interdigitated electrodes, the roughness per area and mean square roughness obtained were 1.24 ⁇ 0.04 nm and 1.58 ⁇ 0.05 nm, respectively. Also, the results revealed that electrodes fabricated by this methodology present similar roughness, with a standard deviation of about 3%. This characteristic is essential for a better organization of the self-assembled monolayer and for the analysis of electrical conductivity to be reproducible. Example 5. Electrodes functionalization
  • the capacitive biosensor was constructed by the formation of a self-assembled layer: clean interdigitated electrodes were modified with 1 mM 3-mercaptoproprionic acid (MPA) at room temperature and humid atmosphere for 15 h; then, the electrodes were washed with Milli-Q water and incubated for 1 h with an aqueous solution containing 2 mM l-ethyl-3-(3-dimethylaminopropyl)carbodiimide (EDC) and 5 mMN- hydroxysuccinimide (NHS), to activate the carboxylic group from MPA molecules.
  • EDC mM l-ethyl-3-(3-dimethylaminopropyl)carbodiimide
  • NHS mMN- hydroxysuccinimide
  • Modified interdigitated electrodes were subjected to 20 consecutive measurements of electrical capacitance to evaluate reproducibility in the frequency range from 10 2 Hz to 10 6 Hz.
  • the capacitance values have shown to be reproducible for almost all frequencies, with a very small variation for the 0.6 xlO 6 to IxlO 6 Hz range.
  • electrodes modified with immunized serum of M. incognita species were incubated in a solution containing 30 pg/mL of protein of M. javanica species (negative) for 1 h and in a solution containing the same concentration of protein of M. incognita species (positive) also for 1 h.
  • Electrical impedance spectra were collected before and after the described incubations. The measurements were performed in a buffer solution and a 5 -minute delay was adopted before the measurements for the organization of the electric double layer.
  • each variable is represented as a vector whose intensity and direction determine its influence on the principal components 1 and 2. It is observed that the electrodes submitted to cleaning with KOH show a small intensity in the y-direction and a large intensity in the x-direction, indicating that this variable has a greater influence on the principal component 1 (PCI).
  • PCI principal component 1
  • the vector that represents electrodes cleaned with etOH has a small intensity on the x-axis and a large intensity on the y-axis; thus, its greatest influence is on PC2. Since PCI is the component that most discriminates the samples, the cleaning protocol using KOHwas chosen to perform the other studies.
  • the loading plot for this set of variables shows that there is a negligible contribution from the sets of clean electrodes and with organic film (FO) to the PCI, responsible for the major differentiation of the samples. Therefore, the discrimination of the samples is due to the specific interaction between the antibodies present in the SAM and its target proteins.
  • the goal of the biosensor developed here is to detect plant-parasitic nematodes in a simple and fast manner, with the possibility to be performed in the field. Thus, it was studied the possibility of detection without the incubation with the sample. For this, FO and AC electrodes were subjected to capacitance measurements in a buffer solution, after waiting 10 min for the organization of the double electric layer. In a later step, a solution containing non-specific proteins (negative samples) at 30 pg/mL was added to the electrodes; after 10 min of waiting required for the sample to interact with the sensory unit and for the organization of the double electrical layer, electrical impedance measurements were performed in the same solution containing the proteins.
  • the procedure was repeated in a solution containing the target proteins (positive) at 30 pg/mL.
  • the capacitance values were analyzed by the principal component analysis to assess whether the detection performed without an incubation time is also capable of discriminating the samples.
  • the score plot obtained, shown in Figure 1 demonstrates not only the biosensor’s ability to differentiate samples based on measurements taken without the incubation period, but also shows a higher PCI score compared to the results of experiments performed with 1 h of incubation. Adding the principal components 1 and 2, discrimination of 100% of the samples is obtained.
  • the loading plot obtained by the combination of two sensory sets - electrodes with organic film and electrodes with SAM - also showed that PCI depends almost exclusively on the electrodes that have antibodies, while PC2 is dominated by the values generated from the electrodes modified with organic film.
  • at least two sensory sets are necessary, i.e., two distinct variables.
  • the ideal model found in this study is the combination of capacitance measurements on FO and AC electrodes, which together can identify all samples.
  • Electrochemical measurements are performed in a miniaturized electronic device.
  • An electrolyte solution containing 5 mM Ferri/iron in 0.1 M KC1 is added to the electrode, covering the entire surface.
  • the electrodes are subjected to cyclic voltammetry measurement in the potential range from -0.5 to 0.6 V, at a sweep speed of 50 mV s’ 1 . This step is performed only to pre-activate the electrodes.
  • electrochemical impedance measurements are performed at open circuit potential in the frequency range 10’ 1 Hz to 10 3 Hz, with an AC amplitude of 10 mV.
  • these measurements were performed before and after the incubation with the sample for 30 min.
  • the percentage change in R ct resulting from the incubation was calculated for all samples tested. The results showed a much greater variation for the positive samples (containing the target proteins), as seen in Figure 2, indicating the selectivity of the biosensor.
  • Example 11 Electrochemical impedance response as a function of the analyte concentration

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Abstract

La présente invention concerne un système de biocapteur comprenant une ou plusieurs électrodes permettant de convertir un signal physicochimique transduit d'une couche de bioreconnaissance en un signal électronique ; une couche de bioreconnaissance comprenant des biomolécules immobilisées sur une ou plusieurs électrodes permettant de se lier à l'analyte spécifique de l'espèce de nématode ainsi qu'un procédé de détection simultanée de plus d'une espèce de nématode.
PCT/EP2023/051450 2022-03-30 2023-01-20 Biocapteurs pour l'identification d'espèces de nématodes WO2023186363A1 (fr)

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Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008032066A1 (fr) * 2006-09-16 2008-03-20 University Of Leeds Procédés et dispositifs de détection de changements structurels dans une molécule par mesure de l'impédance électrochimique
WO2014015187A1 (fr) * 2012-07-18 2014-01-23 Biological Dynamics, Inc. Manipulation de microparticules dans des régions diélectrophorétiques de faible champ
WO2016176203A1 (fr) * 2015-04-29 2016-11-03 Dots Technology Corp. Compositions et procédés pour la détection d'allergènes
US20170052174A1 (en) * 2015-08-17 2017-02-23 Sandia Corporation Shear horizontal surface acoustic wave (sh-saw) resonators and arrays thereof
WO2018015884A1 (fr) * 2016-07-21 2018-01-25 King Abdullah University Of Science And Technology Électrode de graphène sur puce, procédés de production et procédés d'utilisation
WO2020240570A1 (fr) * 2019-05-28 2020-12-03 Ramot At Tel-Aviv University Ltd. Systèmes et procédés de détection d'un organisme pathogène
WO2021021944A1 (fr) * 2019-07-31 2021-02-04 Axbio Inc. Systèmes et méthodes d'évaluation d'une molécule cible

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008032066A1 (fr) * 2006-09-16 2008-03-20 University Of Leeds Procédés et dispositifs de détection de changements structurels dans une molécule par mesure de l'impédance électrochimique
WO2014015187A1 (fr) * 2012-07-18 2014-01-23 Biological Dynamics, Inc. Manipulation de microparticules dans des régions diélectrophorétiques de faible champ
WO2016176203A1 (fr) * 2015-04-29 2016-11-03 Dots Technology Corp. Compositions et procédés pour la détection d'allergènes
US20170052174A1 (en) * 2015-08-17 2017-02-23 Sandia Corporation Shear horizontal surface acoustic wave (sh-saw) resonators and arrays thereof
WO2018015884A1 (fr) * 2016-07-21 2018-01-25 King Abdullah University Of Science And Technology Électrode de graphène sur puce, procédés de production et procédés d'utilisation
WO2020240570A1 (fr) * 2019-05-28 2020-12-03 Ramot At Tel-Aviv University Ltd. Systèmes et procédés de détection d'un organisme pathogène
WO2021021944A1 (fr) * 2019-07-31 2021-02-04 Axbio Inc. Systèmes et méthodes d'évaluation d'une molécule cible

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
MATTOS GABRIEL J ET AL: "Serological diagnosis of strongyloidiasis in immunocompetent and immunosuppressed patients based on an electrochemical immunoassay using a flexible device allied to PLS-DA and ROC statistical tools", SENSORS AND ACTUATORS B: CHEMICAL, ELSEVIER BV, NL, vol. 354, 9 December 2021 (2021-12-09), XP086917027, ISSN: 0925-4005, [retrieved on 20211209], DOI: 10.1016/J.SNB.2021.131213 *

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