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    • 专利摘要:
    Wireless, portable and reusable biosensor. The present invention relates to a non-invasive biosensor device for the determination of analytes by visualizing a color change, and from a liquid sample. The present invention falls within the field of devices for health, control during sports, occupational safety and the food industry. (Machine-translation by Google Translate, not legally binding)
    公开号:ES2781376A1
    申请号:ES201930187
    申请日:2019-02-28
    公开日:2020-09-01
    发明作者:Campo García Francisco Javier Del；Brunet Antón Guimerá；Pellitero Miguel Aller；Michele Dei
    申请人:Consejo Superior de Investigaciones Cientificas CSIC；
    IPC主号:
    专利说明:

    [0002] Wireless, portable and reusable biosensor
    [0004] The present invention relates to a biosensor device for the non-invasive determination of analytes, by visualizing a color change, and from a liquid sample. The present invention falls within the scope of devices for health, control during sports, occupational safety and the food industry.
    [0006] BACKGROUND OF THE INVENTION
    [0008] Currently, in the field of portable chemical sensors and, more specifically, in the field of sweat measurements, we find that one of the trends is the development of skin patches. These sensors of a chemical nature have two distinct parts, the part with the sensor and the part with the control instrumentation. These parts generally have very different useful lives; While the control electronics can last for years without noticeable loss of performance, the sensor part deteriorates with use to a greater or lesser extent depending on its working conditions, in some cases allowing only one measurement to be carried out. .
    [0010] Because of this, current systems are designed so that instrumentation can be reused, while making the sensor part low cost and disposable. The paradigmatic example is that of personal glucometers, in which the sensor is located on a disposable plastic strip, the cost of which is a few cents of a euro. This strip is physically connected to the instrumentation when it is inserted into the reader. On the other hand, each strip allows only one measurement, and requires the extraction of a drop of blood by a capillary puncture, which is uncomfortable and can lead to infections.
    [0012] To improve the quality of life of patients suffering from diabetes, the industry seeks to develop non-invasive systems that allow the measurement of glycemia in other body fluids such as sweat. In this sense, the Abbott company has put recently on the market a device that allows the semi-continuous measurement of blood glucose in a minimally invasive way (in interstitial fluid). The system consists of 2 parts: a wireless reader and a 5cm diameter and 5mm thick capsule that incorporates the biosensor, its control electronics, a small memory, a radio frequency communication module, and a button battery that powers the set. Said capsule is placed in the arm, under the shoulder, where it is fixed by means of an adhesive, while the biosensor, which is located at the end of a 5mm long needle, remains inserted in the patient's arm. The biosensor has a useful life of 2 weeks, according to the manufacturer, after which the biosensor capsule is removed and replaced with a new one. Despite its advantages, the complexity of the biosensor part translates into a high cost of the product, per biosensor capsule.
    [0014] On the other hand, the works in the state of the art of groups stand out in which either the sensor part has to be physically connected to the instrumentation by means of cables, or the sensor part integrates an entire electronic circuitry that allows its control and the communication of data [M. Dei, J. Aymerich, M. Piotto, P. Bruschi, FJ del Campo, and F. Serra-Graells, "CMOS Interfaces for Internet-of-Wearables Electrochemical Sensors: Trends and Challenges," Electronics, vol. 8, no. 2, p. 150, Feb. 2019.] Furthermore, in these devices the need to carry out a continuous calibration in said devices to ensure the measurement is verified.
    [0016] That is why there is currently a need for a portable and disposable device capable of carrying out numerous measurements over time, thus capable of greatly reducing the environmental impact of this waste.
    [0018] DESCRIPTION OF THE INVENTION
    [0020] The present invention provides a non-invasive biosensor device for the determination of analytes from a liquid sample, such as sweat, food effluvia, etc., portable and wireless that can return to its initial state ready to perform a new measurement by means of the use of a pulse received without the need for cables, either through electromagnetic waves, more preferably radio frequencies, and without the need for complex electronics or instrumentation.
    [0021] The advantages of this device are:
    [0022] The possibility of reusing the sensor more than once, moving away from the devices of the state of the art, in which the sensor is disposable after a single use.
    [0023] It is not necessary to draw blood to deposit on the sensor, but a non-invasive measurement can be performed, for example, from the sweat of the subject. This takes it away from the current state of the art, in which it is performed using a device that performs a continuous measurement in an invasive way. The sensor life time can reach two weeks.
    [0024] A simplified calibration / possibility of self-calibration, with fewer steps and problems compared to the state of the art, since the sensors, of the state of the art, generally require a calibration at the beginning and after some measurements, but in the device of the The present invention by having information on color and its rate of change, it is possible to correct the concentration during measurements without the need for standards. Thus, by having the color information available at the end of the previous measurement, it is possible to know the charge that the sensor contains before each measurement. Knowing the charge and the rate of change, it is possible to calculate the analyte concentration in each measurement. In the case of the use of an optical measurement reader, said reader can carry out the necessary calculations to correct any pressure losses that may occur in the sensor. Consequently, the device does not require external patterns.
    [0025] The wireless device of the present invention does not need additional silicon components to function, and also avoids the connection of the sensors by cables to a measurement instrumentation. This facilitates both construction and use of the device. In fact, the device is designed to work with near field radio frequency. This has the advantage that the signal does not have to be encrypted for security reasons. In addition, the optical or colorimetric reader that will read the sensor should ideally be very close to it to facilitate reading and avoid measurement errors.
    [0026] Charge and discharge currents are not affected by capacitive currents during the measurement, as it is a coulometric (charge) measurement. This can be an advantage, especially in cases where the analyte is in very low concentrations. Also, if the measurement were electrochemical (voltammetric), the charge / discharge of the double layer could affect the measurement. However, as it is an optical measure, this problem does not occur since the color change is strictly associated with a faradaic (oxidation / reduction) process.
    [0027] Maximum use of two electrodes compared to three in the state of the art. In conventional electrochemical measurements based on the potential control of the working electrode, 3 electrodes are used. Applying these techniques with 2 electrodes means losing control of the potential of the working electrode (sensor), which could be counterproductive, because at that moment we stop knowing what potential is being measured, and therefore what processes are contributing to the current and which ones are not. In summary, it is rare to find amperometric sensors based on systems with only 2 electrodes because in them the auxiliary electrode must also fulfill the reference function, and the problem is that when current passes, its potential is modified. This causes the sensor potential to fluctuate, and makes the measurement less reliable. Therefore, from the point of view of an electrochemist, a 2-electrode amperometric system would not be very attractive. On the other hand, in a conventional amperometric measurement system, the direct connection of the antenna to the electrodes can result in the application of alternating potential differences of the order of several volts between the 2 electrodes of the system. However, in amperometric sensors, potentials of less than 1V are generally applied against the corresponding reference electrode. In fact, it seeks to apply the lowest possible potentials that guarantee a purely diffusive control of the measured current. This seeks to avoid interferences from other electroactive molecules capable of reacting at the electrode in that range of potentials. Furthermore, in some cases, the application of extreme work potentials can lead to irreversible damage to the sensor. In the case of Prussian Blue (in English Prussian Blue, with its initials PB), if an excessively high oxidation potential is applied, "Berlin Green" is produced in a semi-reversible process. This form of the complex, green in color, is unstable and reduces the lifetime of the blue form On the other hand, if an excessive reduction potential is applied, in the absence of K + ions in the medium, the structure of the material can be damaged.
    [0028] Problems associated with the lack of control of the electrochemical potential of the sensor are avoided, since the measurement carried out is not electrochemical but optical (colorimetric).
    [0030] The device of the present invention has application in a wide range of technical fields such as health, sports, occupational safety, the environment and the food industry. Initially, the presented invention aims to develop sensors or biosensors for non-invasive measurements, preferably in sweat, through the use of activity monitors, smart watches, and other "wearable" type devices, although it would also allow the manufacture of " smart labels "for food quality control.
    [0032] The first aspect of the present invention is a wireless and portable biosensor device for displaying a color change from a first color to a second color, where said second color indicates the presence of an analyte in a liquid sample, and the first color indicates the absence of the analyte or a non-reading state, the device being characterized by comprising a layered structure comprising:
    [0033] • a transparent substrate comprising a face a and a face b, optionally the substrate comprises at least two holes that connect the two faces, a and b, of the substrate;
    [0034] • a conductive structure configured as the main structure of an antenna and at least one conductive track of the working and auxiliary electrodes, comprising conductive silver paste;
    [0035] • at least two transparent conductive structures configured to function as at least two transducers, one for the working electrode and the other for the auxiliary electrode;
    [0036] • at least one electrochromic structure, configured to function at least as a working electrode;
    [0037] • a transparent structure configured to deposit the sample on it and comprising
    [0038] ■ chitosan; Y
    [0039] ■ an oxidase enzyme.
    [0040] • a main dielectric structure and that is configured to isolate the conductive tracks from the conductive structure;
    [0041] • optionally a second dielectric structure located on the conductive structure and / or on the electrochromic one, exposing at least one area of said electrochromic layer, and wherein said dielectric structure layer comprises at least two holes;
    [0042] • at least one conductive track configured to connect with the conductive structure to close the circuit; Y
    [0043] • a diode;
    [0044] where the device works in direct current;
    [0045] where the antenna is configured so that, with a radio frequency between 10.56 MHz to 16.56 MHz, the measurement of the device is restarted until the state of no reading or absence of analyte in the sample; Y
    [0046] where the device is configured to reset to its state of non-reading or absence of analyte when receiving a signal of a certain radio frequency between 10.56 MHz to 16.56 MHz.
    [0048] In the present invention, by "substrate" or "transparent substrate" is understood to mean any transparent material with a thickness between 10 pm and 250 pm, preferably between 30 pm and 100 pm, more preferably selected from: polyethylene terephthalate (PET) and derivatives, polyurethane, polystyrene and derivatives, polyvinyl alcohol and derivatives, and cellulosic materials. In the present invention optionally the substrate comprises at least two holes or vias.
    [0050] In the present invention, "holes or pathways" are understood as the areas drilled with at least two small holes (60-120 pm in diameter) that allow connecting the conductive tracks to close the circuit, preferably through the substrate so that pass the silver paste from one face to the other of said substrate, forming an electrical contact between both faces, or through the second dielectric structure.
    [0052] In the present invention, "dielectric structure" or "dielectric" refers to all insulating materials or poor conductors that are used to protect the conductive tracks and prevent leakage currents or oxidation of the tracks when they come into contact with the liquid sample. where the analyte is found for its measurement. In the present invention it preferably refers to any photocurable resin, resin thermosetting and resin curable by drying or chemical reaction, more preferably it is a photocurable resin.
    [0054] In the present invention, a "transducer" is understood as a component of an electrode capable of transforming or converting a certain manifestation of input energy into another different from the output, but with very small values in relative terms with respect to a generator. The transparent conductive structure configured to function as a transducer is formed of a transparent conductive material that can be selected from at least one layer of PEDOT: PSS; at least a thin layer of size between 3 nm and 100 nm of a material selected from Au, Pt, graphene, carbon nanotubes, fullerenes; at least one layer comprising tin oxide; and any combination of the above; and is preferably PEDOT: PSS. In the present invention, the device comprises at least two transparent conductive structures configured to function as transducers, one for the working electrode and the other for the auxiliary electrode. In the absence of a conductive or electrochromic structure on said auxiliary electrode transducer, said transducer will act as an auxiliary electrode.
    [0056] In the present invention, "electrochromic structure" is understood to mean a material that, in reaction to an electric current, changes color. This structure is configured to function as a working electrode. In the present invention each electrochromic structure comprises a pigment, preferably Prussian Blue. More preferably it comprises:
    [0057] to. some microparticles, selected from mixed tin and indium oxide (ITO), of the core-covering type where the core is SiO2 and where the covering is an oxide of mixed antimony and tin, and a combination of the above; Y
    [0058] b. an ink comprising
    [0059] i. a pigment, preferably Prussian Blue; Y
    [0060] ii. a binder resin, preferably a Viton solution; and where the microparticle: ink ratio is 2.5: 1;
    [0061] and where the microparticles and the ink form a homogeneous particulate mixture with a particle size of said mixture of between 3 pm and 12 pm.
    [0062] For the elaboration of the electrochromic structure, a modification of the pigment, for example Prussian blue, can be carried out by means of a growth of said pigment on microparticles, thus generating an ink usable for the electrochromic structure of the device of the present invention. To carry out this growth of the pigment on the microparticles, it is carried out in a slightly acidic aqueous medium containing iron and ferro or ferricyanide salts. Subsequently, once the pigment has grown on the particles, they are filtered, washed, dried and ground to obtain the finest possible powder.
    [0064] This obtained powder is added to a binder resin in the form of a solution, all in a polar solvent, such as for example and not limited to 2-Butoxyethylacetate. In this way, a much greater contact is achieved between the pigment and the rest of the components, so that the electrical losses are reduced, as well as the voltage necessary for the use of the device of the present invention. The composition of the paste to make the electrochromic structure comprises:
    [0065] microparticles plus pigment, preferably Prussian Blue, in a percentage between 15% and 60% by weight;
    [0066] binder resin, preferably Viton, in a percentage of between 4% and 15% by weight; Y
    [0067] solvent in a percentage between 25% and 81% by weight.
    [0068] The preferred composition of the electrochromic structure used in the present invention comprises: 20% by weight of microparticles and pigment, 8% by weight of binder resin and 72% by weight of solvent.
    [0070] In the present invention, "antenna" is understood as the metallic structure with a spiral shape that acts as an interface between the nearby electromagnetic field and the currents that are induced in the same structure. The antenna transduces the signal of the electromagnetic oscillating field in alternating currents.
    [0072] In the present invention, "diode" is understood as any device capable of rectifying the alternating current of the radio frequency signal, the anode of the diode must be connected so that the electrons flow from the diode towards the electrochromic structure, and not vice versa. Otherwise the system would not work as planned. Therefore, it is not only important to rectify the current, but also its polarity. Furthermore, in the case that an alternating signal is applied to the reversible system comprising the pigment, the net circulating charge in the absence of said diode is zero. This means that there would be no noticeable color change on the working electrode (electrochromic structure). In the present invention the diode can be printed, or manufactured by a combination of microfabrication and printing processes, or a discrete component of silicon is used. In the present invention, "Schottky type diode" is understood to be that diode that has a metal-N junction, that is, in which the main metal is doped with an electron donor semiconductor, causing a high switching speed which allows to rectify very high frequency signals and eliminate excess current in high intensity circuits.
    [0074] In the present invention, "liquid sample" is understood as a sample that can be selected from a biological fluid or a food, liquid or solid, which may or may not be previously treated for the determination of the analyte that contains it.
    [0076] By "biological fluid" is meant in the present invention blood, sweat, saliva, tears and urine. In a preferred embodiment, the biological fluid is sweat.
    [0078] In a preferred embodiment of the wireless and portable biosensor device of the present invention the conductive structure, comprising conductive silver paste, is located directly on the face a of the substrate. In a more preferred embodiment of the device the transparent conductive structure, configured to function as a transducer, is located on the previous conductive structure, located on the face a of the substrate.
    [0080] In an even more preferred embodiment of the device it comprises a layered structure comprising:
    [0081] • a transparent substrate comprising a face a and a face b, and where the substrate comprises at least two holes that connect the two faces, a and b, of the substrate;
    [0082] • a first layer of conductive structure configured as the main structure of an antenna and conductive tracks of the working electrodes and auxiliary, which comprises conductive silver paste, and is located on at least a part of the face a of the substrate;
    [0083] • at least two second layers of transparent conductive structure, located on the first layer of conductive structure, and configured to function as at least two transducers, one for the working electrode and the other for the auxiliary electrode;
    [0084] • at least one third layer of electrochromic structure, located on at least some area of second layer of transparent conductive structure, and configured to function at least as a working electrode;
    [0085] • a fourth layer with a transparent structure adhered to the third layer with an electrochromic structure, and configured to deposit the sample to be determined on it and comprising:
    [0086] ■ chitosan; Y
    [0087] ■ an oxidase enzyme.
    [0088] • a fifth layer of the main dielectric structure located on the previous layers, exposing at least one area that corresponds to the sample deposit area of the fourth layer, and that is configured to isolate the conductive tracks of the main structure of the first layer;
    [0089] • a sixth layer of a conductive track comprising conductive silver paste, and is located on face b of the substrate and is configured to connect, through the holes in the substrate, with the conductive structure of the first layer and close the circuit; Y
    [0090] • a diode on the sixth layer;
    [0091] where the device works in direct current;
    [0092] where the antenna is configured so that, with a radio frequency between 10.56 MHz to 16.56 MHz, the measurement of the device is restarted until the state of no reading or absence of analyte in the sample; Y
    [0093] where the device is configured to reset to its state of non-reading or absence of analyte when receiving a signal of a certain radio frequency between 10.56 MHz to 16.56 MHz.
    [0095] In another preferred embodiment of the wireless and portable biosensor device of the present invention, in which the transparent conductive structure, configured to function as a transducer, is located directly on the substrate. In a The most preferred embodiment of the device, the conductive structure, which comprises conductive silver paste and is located directly on the transparent conductive structure. In an even more preferred embodiment of the device it comprises a layered structure comprising:
    [0096] • a transparent substrate comprising a face a and a face b and where the substrate comprises at least two holes that connect the two faces, a and b, of the substrate;
    [0097] • at least one first layer of transparent conductive structure located on the face a of the substrate and configured to function at least as two transducers, one of the working electrode and the other of the auxiliary electrode;
    [0098] • a second layer of conductive structure, configured as the main structure of an antenna and conductive tracks of the working and auxiliary electrodes, and comprising conductive silver paste, and is in contact with at least a part of the first layer of structure transparent conductor;
    [0099] • at least one third layer of electrochromic structure, located on at least some surface of the second layer of conductive structure, configured to function at least as a working electrode;
    [0100] • a fourth layer of transparent structure adhered to the third layer of electrochromic structure configured to deposit the sample on it and comprising
    [0101] ■ chitosan; Y
    [0102] ■ an oxidase enzyme.
    [0103] • a fifth layer of main dielectric structure located on the previous layers, exposing or not covering at least one area or surface that corresponds to the sample deposit area described in the fourth layer, and which is configured to isolate the conductive tracks of the second layer;
    [0104] • a sixth layer of a conductive track comprising conductive silver paste, and is located on face b of the substrate and is configured to connect, through the holes in the substrate, with the conductive structure of the first layer and close the circuit; Y;
    [0105] • a diode on the sixth layer;
    [0106] where the device works in direct current;
    [0107] where the antenna is configured so that, with a radio frequency of 10.56 MHz to 16.56 MHz, the measurement of the device is restarted until the state of no reading or absence of analyte in the sample; Y
    [0108] where the device is configured to reset to its state of non-reading or absence of analyte when receiving a signal of a certain radio frequency between 10.56 MHz to 16.56 MHz.
    [0110] In another even more preferred embodiment of the device it comprises a layered structure comprising:
    [0111] • a transparent substrate comprising a face a and a face b;
    [0112] • at least two first layers of transparent conductive structure located on one of the faces of the substrate and configured to function as at least two transducers, one for the working electrode and the other for the auxiliary electrode;
    [0113] • a second layer of conductive structure, configured as the main structure of an antenna and conductive tracks of the working and auxiliary electrodes, and comprising conductive silver paste, and is in contact with at least a part of the first layer of structure transparent conductor;
    [0114] • a third layer of dielectric structure configured to isolate the conductive tracks of the second layer;
    [0115] • at least a fourth layer of electrochromic structure, located on at least some area of the second layer of conductive structure, configured to function at least as a working electrode;
    [0116] • a fifth layer of a second dielectric structure located on the fourth layer of electrochromic structure, leaving at least one area exposed or not covered, corresponding to the sample deposit area, and wherein said dielectric structure comprises at least two holes;
    [0117] • a sixth layer with a transparent structure located, in the area exposed or not covered by the fifth layer, on the fourth layer with an electrochromic structure, configured to deposit the sample on it and comprising:
    [0118] ■ chitosan; Y
    [0119] ■ an oxidase enzyme.
    [0120] • a seventh layer of a conductive track, configured to connect with the second layer of conductive structure through the holes in the fifth layer of dielectric structure and close the circuit; Y
    [0121] • a diode on the seventh layer of conductive structure;
    [0122] where the antenna is configured so that, with a radio frequency of 10.56 MHz to 16.56 MHz, the measurement of the device is restarted until the state of no reading or absence of analyte in the sample; Y
    [0123] where the device is configured to reset to its state of non-reading or absence of analyte when receiving a signal of a certain radio frequency between 10.56 MHz to 16.56 MHz.
    [0125] In another more preferred embodiment of the device of the present invention, the diode is of the Schottky type and has dimensions between 0.8 mm and 1.6 mm.
    [0127] The oxidase enzyme to be used in the transparent structure of the device of the present invention will depend on the analyte to be determined in the liquid sample. For example, and without limiting us, the oxidase enzyme is selected from glucose oxidase, lactose oxidase, maltose oxidase, urate oxidase or ethanol oxidase, when the analyte is selected from glucose, lactose, maltose, uric acid, or ethanol, respectively. In a preferred embodiment the oxidase enzyme is glucose oxidase. In an even more preferred embodiment, the transparent structure comprising glucose oxidase, additionally comprises the enzyme mutarrotase, where said enzyme helps to improve the sensitivity of glucose detection by the device of the present invention.
    [0129] The device could further comprise a frame on the auxiliary electrode transducer. Thus, in a preferred embodiment the device further comprises a transparent conductive structure or an electrochromic structure, either located directly on the transparent conductive layer configured as a transducer of the auxiliary electrode and which are configured to function as an auxiliary electrode.
    [0131] By using a transparent conductive structure as an auxiliary electrode, the color change is visible from face b of the device, thus favoring the visualization of the measure.
    [0133] If the device of the invention comprises the additional electrochromic structure configured to function as an auxiliary electrode, this auxiliary electrode acts as a charge reserve layer to balance the reaction of the electrochrome and thus allows working with lower voltage. By using the same electrochromic material as the material for the auxiliary electrode as that used for the working electrode, the manufacturing of both electrodes is done in one step, and there is a lower energy cost for the activation of the device, since it will not be potential difference between working electrode and auxiliary electrode; and there will be no extra potential difference to apply to measure and reset the device.
    [0135] Another preferred embodiment of the wireless and portable biosensor device of the present invention where the electrochrome structure is deposited on the auxiliary electrode or in contact with both electrodes. This configuration reduces the working voltage of the device.
    [0137] Another aspect of the invention refers to a method for obtaining the device of the present invention, characterized in that it comprises the following steps: a. make holes in a transparent substrate that comprises a face a and a face b, preferably the substrate is made of PET between 30 pm -100 pm thick, using a technique selected from among CO2 laser, mechanical puncture and a combination of the above , in such a way that they connect the two faces of the substrate;
    [0138] b. print a conductive structure on the face a of the substrate using conductive silver paste to form the spiral structure of the antenna and the conductive tracks of the working and auxiliary electrodes, making at least one printed area coincide with the holes in the stage ( to); c. printing at least two transparent conductive structures on the printing made in step (b) using a transparent conductor, preferably PEDOT: PSS, to function as transducers, one of the working electrode and the other of the auxiliary electrode;
    [0139] d. printing an electrochromic structure on part of the conductive structure obtained in step (c);
    [0140] and. printing a conductive track on face b of the substrate, in such a way that the ends of the tracks coincide with the zones of tracks and make contact with the ends of the antenna and with the transducer of the auxiliary electrode;
    [0141] F. depositing a dielectric structure, preferably a layer of dielectric resin, on the face a of the material obtained after step (d), exposing at least one area that corresponds to the deposit area of the electrochromic structure sample;
    [0142] g. depositing a diode on the conductive track of face b of the substrate obtained in step (e), between one of the ends of the antenna and one of the electrodes that make up the sensor by means of silver paste or an anisotropic conductive adhesive; Y
    [0143] h. adhering a transparent structure comprising chitosan and an oxidase enzyme to the sample deposit zone that was exposed after depositing the dielectric structure in step (f).
    [0145] In a preferred embodiment of the method for obtaining the device of the present invention described, which comprises
    [0146] additionally a step (c ') subsequent to step (c) of printing a layer on the transducer of the auxiliary electrode selected from a transparent conductive structure or an electrochromic structure.
    [0148] Another aspect of the present invention refers to an alternative method for obtaining the device of the present invention, characterized in that it comprises the following steps:
    [0149] to. printing on the face a of the transparent substrate, preferably by screen printing, a first conductive structure, using conductive silver paste, to form the conductive tracks that constitute the spiral structure of the antenna and the conductive tracks of the working and auxiliary electrode;
    [0150] b. on the first conductive structure obtained in step (a), deposit at least two second transparent conductive structures using a transparent conductor to function as transducers one of the working electrode and the other of the auxiliary electrode, preferably selected from • at least one layer of PEDOT: PSS;
    [0151] • at least one thin layer with a size between 3 and 10 nm of a material selected from Au, Pt, graphene, carbon nanotubes, fullerenes;
    [0152] • at least one layer comprising tin oxide;
    [0153] • and any combination of the above;
    [0154] c. printing the third structure of electrochromic material on the second transparent conductive structure obtained in step (b);
    [0155] d. depositing a fourth dielectric structure, preferably a layer of dielectric resin, on the face a of the material obtained after step (c), exposing at least one area that corresponds to the sample deposit area of the third structure;
    [0156] and. print at least one conductive track on the dielectric material structure deposited in step (d), so that the ends of the tracks coincide with the inner ends of the antenna and with the contact of the auxiliary electrode deposited in step (a) ;
    [0157] F. depositing a new structure of dielectric material, defining the working areas of the electrodes, the contacts for the diode and other possible electronic or measurement components, and the area in which the sample to be analyzed will be confined.
    [0158] g. mount a diode on the conductive tracks in the area suitable for it using silver paste or an anisotropic conductive adhesive; and h. adhering a transparent structure comprising chitosan and an oxidase enzyme in the zone of deposit of the sample of the structure free of dielectric structure of step (f).
    [0160] In a preferred embodiment of the method for obtaining the device of the present invention described, it comprises
    [0161] additionally a step (c ') subsequent to step (c) of printing a layer on the transducer of the auxiliary electrode selected from a transparent conductive structure or an electrochromic structure.
    [0162] Another aspect of the invention refers to another alternative method for obtaining the device of the present invention, characterized in that it comprises the following steps
    [0163] to. make holes in a transparent substrate that comprises a face a and a face b, preferably the substrate is PET between 30-100pm thick, using a technique selected from among CO 2 laser, mechanical puncture and a combination of the above, of such that they connect the two faces of the substrate;
    [0164] b. print on the face a of the substrate at least two transparent conductive structures using a transparent conductor to function as transducers, one of the working electrode and the other of the auxiliary electrode, preferably selected from among
    [0165] • at least one layer of PEDOT: PSS;
    [0166] • at least one thin layer of size between 3 nm and 100 nm of a material selected from Au, Pt, graphene, carbon nanotubes, fullerenes;
    [0167] • at least one layer comprising tin oxide;
    [0168] • and any combination of the above;
    [0169] c. screen printing a second conductive structure on the printing made in step (b) using conductive silver paste to form the conductive tracks that constitute the spiral structure of the antenna and the conductive tracks of the working and auxiliary electrodes, making at least one printed area coincides with the holes in step (a);
    [0170] d. printing the electrochromic material on the second conductive structure obtained in step (c);
    [0171] and. printing a series of conductive tracks on the second face b of the substrate, in such a way that the ends of the tracks coincide with the zones of tracks and make contact with the ends of the antenna and with the contact of the transducer of the auxiliary electrode;
    [0172] F. depositing a fifth dielectric structure, preferably a dielectric resin layer, on the face a of the material obtained after step (e) exposing at least one area that corresponds to the deposit area of the sample of the fourth electrochromic structure;
    [0173] g. mounting a diode on the conductive tracks of face b of the substrate obtained in step (e), in the area suitable for this by means of silver paste or an anisotropic conductive adhesive; Y
    [0174] h. adhering a transparent structure comprising chitosan and an oxidase enzyme in the zone of deposit of the sample of the structure free of dielectric structure of step (f).
    [0176] In a preferred embodiment of the method for obtaining the device of the present invention described, it comprises
    [0177] additionally a step (d ') subsequent to step (d) of printing a layer on the transducer of the auxiliary electrode selected from a transparent conductive structure or an electrochromic structure.
    [0179] Another aspect of the present invention refers to another alternative method for obtaining the device of the present invention, characterized in that it comprises the following steps
    [0180] to. printing on the face a of the transparent substrate, preferably by screen printing a first conductive structure, using conductive silver paste, to form the conductive tracks that constitute the spiral structure of the antenna and the conductive tracks of the working and auxiliary electrode;
    [0181] b. print on the first conductive structure obtained in step (a), at least two second transparent conductive structures using a transparent conductor to function as transducers, one of the working electrode and the other of the auxiliary electrode, preferably selected from • at least one layer of PEDOT: PSS;
    [0182] • at least one thin layer with a size between 3 and 10 nm of a material selected from Au, Pt, graphene, carbon nanotubes, fullerenes;
    [0183] • at least one layer comprising tin oxide;
    [0184] • and any combination of the above;
    [0185] c. printing the third structure of electrochromic material on the second transparent conductive structure obtained in step (b);
    [0186] d. depositing a fourth dielectric structure, preferably a layer of dielectric resin, on the face a of the material obtained after step (c), exposing at least one area that corresponds to the sample deposit area of the third structure;
    [0187] and. print a series of conductive tracks on the structure of dielectric material deposited in step (d), so that the ends of the tracks coincide with the inner ends of the antenna and with the contact of the auxiliary electrode deposited in step (a) ;
    [0188] F. depositing a new structure of dielectric material, defining the working areas of the electrodes, the contacts for the diode and other possible electronic or measurement components, and the area in which the sample to be analyzed will be confined;
    [0189] g. mount a diode on the conductive tracks in the area suitable for it using silver paste or an anisotropic conductive adhesive; and h. adhere a transparent structure comprising chitosan and an oxidase enzyme in the deposit zone of the sample of fourth structure free of dielectric structure.
    [0191] In a preferred embodiment of the method for obtaining the device of the present invention described, it comprises
    [0192] additionally a step (c ') subsequent to step (c) of printing a layer on the transducer of the auxiliary electrode selected from a transparent conductive structure or an electrochromic structure.
    [0194] Another aspect of the present invention refers to another alternative method for obtaining the device of the present invention, characterized in that it comprises the following steps
    [0195] to. print on the face a of the substrate at least two second transparent conductive structures using a transparent conductor to function as transducers, one of the working electrode and the other of the auxiliary electrode, preferably selected from among
    [0196] • at least one layer of PEDOT: PSS;
    [0197] • at least one thin layer with a size between 3 and 10 nm of a material selected from Au, Pt, graphene, carbon nanotubes, fullerenes;
    [0198] • at least one layer comprising tin oxide;
    [0199] • and any combination of the above;
    [0200] b. printing, preferably by screen printing, a second conductive structure on the printing made in step (a) using conductive silver paste to form the conductive tracks that constitute the spiral structure of the antenna and the conductive tracks of the working and auxiliary electrode;
    [0201] c. printing the electrochromic material on the second conductive structure obtained in step (b);
    [0202] d. printing a series of conductive tracks on the second face b of the substrate, in such a way that the ends of the tracks coincide with the zones of tracks and make contact with the ends of the antenna and with the contact of the auxiliary electrode;
    [0203] and. depositing a fifth dielectric structure, preferably a layer of dielectric resin, on the face a of the material obtained after step (d) exposing at least one area that corresponds to the deposit area of the fourth structure sample;
    [0204] F. mounting a diode on the conductive tracks of face b of the substrate obtained in step (d), in the area suitable for this using silver paste or an anisotropic conductive adhesive; Y
    [0205] g. adhering a transparent structure comprising chitosan and an oxidase enzyme in the deposit zone of the fourth structure sample free of dielectric structure;
    [0207] In a preferred embodiment of the method for obtaining the device of the present invention described, it comprises
    [0208] additionally a step (c ') subsequent to step (c) of printing a layer on the transducer of the auxiliary electrode selected from a transparent conductive structure or an electrochromic structure.
    [0210] In the present invention, "printing or printing" is understood to be any layer or structure that can be manufactured by techniques such as screen printing, ink-jet, or offset, or by a combination of techniques from the aforementioned fields, as well as microfabrication.
    [0212] Another aspect of the invention is a patch or label comprising the device of the present invention.
    [0214] Another aspect of the present invention relates to the use of the patch or label of the present invention for the qualitative and / or quantitative detection of an analyte in a liquid sample.
    [0216] The liquid sample can be selected from a biological fluid or a food. In a preferred embodiment, the biological fluid is sweat.
    [0218] The analyte to be determined can be selected from glucose, lactose, maltose, uric acid or ethanol, among others, more preferably the analyte to be determined is glucose.
    [0220] Another aspect of the invention refers to a system characterized in that it comprises:
    [0221] to. the device of the present invention; Y
    [0222] b. means of emission of a signal in a radio frequency between 10.56 MHz to 16.56 MHz configured to restart the measurement of the device until the state of no reading or absence of analyte.
    [0224] In a more preferred embodiment of the system of the present invention, the signal emission means are selected from mobile devices with Near Field Communication (NFC) capabilities, Near Field Communication readers ( NFC), smart phone devices or smart watches.
    [0226] Another aspect of the present invention refers to a method for the qualitative and / or quantitative detection of an analyte in a liquid sample comprising:
    [0227] (i) contacting the liquid sample with the transparent structure configured to deposit the sample on it; Y
    [0228] (ii) detection of the analyte by color change.
    [0229] A preferred embodiment of the method of the present invention comprises an additional step, subsequent to step (ii), which comprises step (iii) of restarting the device by sending a signal at a certain radio frequency between 10.56 MHz to 16.56 MHz. In this way, we prepare the device for the detection of another sample according to steps (i) and (ii).
    [0231] Throughout the description and claims the word "comprise" and its variants are not intended to exclude other technical characteristics, additives, components or steps. For those skilled in the art, other objects, advantages and characteristics of the invention will emerge partly from the description and partly from the practice of the invention. The following examples and figures are provided by way of illustration, and are not intended to be limiting of the present invention.
    [0232] BRIEF DESCRIPTION OF THE FIGURES
    [0234] FIG. 1 Diagram of the assembly of one of the embodiments and of the parts of the device of the present invention.
    [0236] FIG. 2 Diagram of the assembly of another of the embodiments and of the parts of the device of the present invention.
    [0238] FIG. 3 Diagram of the assembly of another of the embodiments and of the parts of the device of the present invention.
    [0240] FIG.4 Scheme of the biosensor device of the present invention.
    [0242] FIG. 5 Cyclic voltammograms obtained in support electrolyte for the different types of electrodes.
    [0244] FIG. 6 Cyclic voltammetry in support electrolyte and derived voltabsorptogram for SiO2-ATO electrodes.
    [0246] FIG. 7 Cyclic voltammetry in support electrolyte and derived voltabsorptogram for ITO electrodes.
    [0247] FIG. 8 Evolution of absorbance when alternating the potential from -0.1 to 0.4 V vs Ag / Ag + in 60s intervals in a 0.25 mM H2O2 solution in support electrolyte.
    [0249] FIG. 9 Temporal evolution of the absorbance spectra for an ITO / PB electrode in a 0.25mM H2O2 solution in support electrolyte.
    [0251] FIG. 10 Temporal evolution of absorbance measured at 700nm for different concentrations of hydrogen peroxide in an ITO electrode.
    [0253] FIG. 11 Representation of the absorbance measured at 700nm at a fixed time of 100s for an ITO / PB electrode (triangles) and another of SiO2-ATO / PB (circles).
    [0255] FIG. 12 Amperometric calibration curves of the glucose biosensor obtained in an ITO / PB electrode (triangles) and another of SiO2-ATO / PB (circles).
    [0257] FIG. 13 Spectroscopic calibration curves of the glucose biosensor obtained in an ITO / PB electrode (triangles) and another of SiO2-ATO / PB (circles).
    [0259] EXAMPLES
    [0261] The invention will be illustrated below by means of tests carried out by the inventors, which demonstrate the effectiveness of the product of the invention.
    [0263] Example 1.
    [0264] Obtaining the glucose biosensor device comprising PEDOT: PSS as a transparent structure located on the substrate.
    [0265] As can be seen in figures 1:
    [0266] (a) First, in a transparent PET substrate between 30 pm -100 pm thick (1) a series of through holes (2) are made in certain areas, corresponding to the paths that will serve to facilitate contact. between the two faces of the substrate. The routes are made using a CO2 laser.
    [0267] On said substrate, the main structure of the antenna and the conductive tracks (3) for the working and auxiliary electrode are screen-printed. In our In this case, conductive silver paste is used and the printing is by screen printing.
    [0269] (b) Next, the transducers for the working (sensor) and auxiliary (4) electrodes are printed. The material of these transducers will be a transparent conductor, preferably PEDOT: PSS.
    [0271] (c) Next, the electrochromic material (5) comprising SIO2-ATO or ITO is printed, at least on the central transducer and, additionally, also on the auxiliary electrode.
    [0273] (d) The next step consists of printing a series of conductive tracks on the opposite face of the substrate, so that the ends of the tracks (6) coincide with the track areas and make contact with the ends of the antenna and with the auxiliary electrode contact, which are located on the front face;
    [0275] (e) done this, the substrate is turned over;
    [0277] (f) and the antenna and conductive tracks are protected with a structure of dielectric material (7), Loctite © EDAG-PF 455BC. This structure, in turn, defines the working areas of the electrodes and the area in which the sample to be analyzed will be confined. The reason to print the dielectric after having completed the printing of the conductive material on both sides, is to avoid blocking the track areas in case the first printing (a) was not perfect. In this case a photocurable resin is used.
    [0279] (g) The diode (8) is mounted on the front face. To fix it we will use a silver paste or an anisotropic conductive adhesive. In our case, we preferably use Loctite 3880 silver conductive paste for mounting discrete components.
    [0281] In particular, a Schottky-type diode from the Panasonic brand, reference DB2S20500L. Its dimensions are 0.8mm x 1.6mm x 0.6mm (x, y, z).
    [0283] (h) Finally, a transparent structure (9) comprising chitosan and an oxidase enzyme in the sample deposit zone and that is free of dielectric structure and defined by it. Finally obtaining the biosensor device (10).
    [0285] Although the sample is placed on the face of the sensor, the fact of having transparent electrodes on a transparent substrate means that the color change can also be read from the rear face of the device.
    [0287] Example 2.
    [0288] Obtaining the glucose biosensor device that comprises ITO as a transparent structure located on the face of the substrate.
    [0290] As can be seen in figure 2:
    [0291] (a) In the first place, in a transparent ITO-PET substrate with a total thickness of between 30 pm -100 pm (1) a series of through holes (2) are made in certain areas, corresponding to the paths that will serve to facilitate electrical contact between the two faces of the substrate. The pathways are made using a CO 2 laser.
    [0293] (b) Next, an etching must be made to define the areas of the working and auxiliary electrodes, in the ITO. This engraving is carried out as follows: first, the ITO-PET sheet is pre-cut and a series of registration marks are made to facilitate the alignment of the subsequent printing stages. Also, marks are made to align a vinyl mask, which defines the areas to be recorded. Once the electrode areas are protected, the substrate is treated in a dilute aqua regia (HCl-HNO3) bath that removes ITO from areas where it is not needed. Subsequently, the substrate is rinsed with deionized water, and dried. The process continues.
    [0295] If the ITO-coated PET sheet is protected by plastic, the process can be simplified as follows: using a cutting tool, the electrode areas are outlined and registration marks are made on the substrate. Next, the protector is removed from the areas from which the ITO is to be removed, which is recorded in a diluted aqua regia bath as described in the paragraph previous. With the ITO removed, the substrate is rinsed with deionized water, and dried. The remaining protector is removed, exposing the ITO electrode transducers, and the process continues.
    [0297] (c) On said substrate, the main structure of the antenna and the conductive tracks for the working and auxiliary electrodes (3) are printed by screen printing. In our case, conductive silver paste is used and the printing is by screen printing.
    [0298] The process continues with steps (d) - (h) of example 1, until obtaining the biosensor device 10 '.
    [0300] Example 3
    [0301] Obtaining the glucose biosensor device comprising PEDOT: PSS as a transparent conductive layer located on the face of the substrate.
    [0303] As can be seen in figure 3:
    [0304] (a) First, on a transparent PET substrate between 30 qm -100 qm thick (1), the main structure of the antenna and the conductive tracks for the working and auxiliary electrode (2) are printed by screen printing. . In our case, conductive silver paste (Loctite EDAG PM-406V1) is used and the printing is by screen printing.
    [0306] (b) Next, the transducers for the working (sensor) and auxiliary (3) electrodes are printed. The material of these transducers will be a transparent conductor, in this case it is PEDOT: PSS.
    [0308] (c) Next, the electrochromic structure comprising SiO2-ATO (5) is printed on the transducers.
    [0310] (d) Subsequently, a structure of dielectric material is deposited so that it partially protects the antenna, exposing at least the inner end of it (11).
    [0312] (e) The next step consists of printing a series of conductive tracks on the dielectric material structure deposited in the previous step, so that the ends of the tracks (6) coincide with the inner ends of the antenna and with the contact of the auxiliary electrode deposited in step (a);
    [0314] (f) Next, a new structure of dielectric material (12) is deposited, in our case, Loctite © EDAG-PF 455BC). This structure, in turn, defines the working areas of the electrodes, the contacts for the diode and other possible electronic or measurement components, and the area in which the sample to be analyzed will be confined. The mission of this structure is to protect the conductive tracks from degradation by the environment, as well as to avoid possible measurement errors caused by spillage of the sample beyond the area of the electrochromic and auxiliary electrodes.
    [0316] (g) Finally, a diode (8) is mounted, in our case it is the reference DB2S20500L, from Panasonic.
    [0318] (h) Finally, a transparent structure (9) that comprises chitosan and an oxidase enzyme is adhered to the sample deposit zone and that is free of dielectric structure and defined by it. Finished biosensor device shown (10 ")
    [0320] The sensor device of the present invention according to examples 1 to 3 is schematized in Figure 4, and they show a color change in the presence of the analyte to be determined. The concentration of said analyte is calculated from the rate of color change and its intensity.
    [0322] Example 4
    [0323] Electrochemical performance of the electrodes whose electrochromic structure comprises SiO2-ATO or ITO and its comparison with the electrodes already present in the state of the art that comprise in their electrochromic structure a commercial graphite paste (DropSens electrodes with reference DRP-710), or with commercial modified screen-printed carbon electrodes (screen-printed electrodes using Gwent graphite paste reference C2070424P2).
    [0325] Figure 5 shows the cyclic voltammograms recorded on the support electrolyte for all electrodes (SiO2-ATO, ITO, commercial graphite paste, commercial modified screen-printed carbon electrodes). The most striking difference in the voltammetry of the different Prussian Blue-modified pastes is the much higher current observed for the blue pastes presented here compared to those obtained from commercial materials.
    [0327] Blue electrodes show superior electrochemical behavior based on their peak-to-peak separation compared to commercial graphite-based materials (Table 1)
    [0329] Table 1: Data obtained from voltammetry experiments
    [0334] This is due to better contact between Prussian Blue and the conductive material of the particles. Furthermore, the ITO-modified nanoparticles show the smallest peak-to-peak separation, ca. 30 mV to 5 mVs-1, probably due to the better conductivity offered by ITO nanoparticles compared to SiO2-ATO microparticles. However, the much higher loading of Prussian Blue than the state of the art, arising from the available massive surface area of the nanoparticles, combined with the thickness of the printed layer on the screen, produces much wider peaks in comparison. with the other materials.
    [0336] Example 5.
    [0337] Spectro-electrochemical performance of the electrodes whose electrochromic structure comprises SiO2-ATO or ITO and its comparison with the electrodes already present in the state of the art that comprise in its electrochromic structure a commercial graphite paste, or with commercial modified screen-printed carbon electrodes, in the detection of H 2 O 2 , simulating the conditions of a biosensor based on the reaction of an oxidase where it occurs said hydrogen peroxide and its optical quantification.
    [0339] The black color of the graphite in the commercial Prussian blue modified electrodes prevents the observation of any spectro-electrochemical change.
    [0341] On the other hand, the cyclic voltammograms, with a scanning speed of 5 mVs-1, of the electrodes whose electrochromic structure comprises SiO2-ATO (Figure 6) or ITO (Figure 7) presented here, the color change associated with the process is observed. redox of Prussian Blue, clearly. In addition, it is observed together with the derivative of their respective voltabsorptograms with an evolution of absorbance when alternating the potential -0.1 to 0.4 V vs Ag / Ag + in intervals of 60s in a 0.25 mM H2O2 solution in the support electrolyte. Figure 8 shows the change in absorbance as reducing and oxidizing potentials are applied. The data shows that electrodes whose electrochromic structure comprises ITO show a greater contrast between the oxidized and reduced states than electrodes whose electrochromic structure comprises SiO2-ATO / Prussian Blue.
    [0343] For the optical quantification of hydrogen peroxide, the measurement was carried out as follows. First, Prussian Blue was lowered to Prussian White by applying a potential of -0.1 V vs. Ag / Ag +. Once a stable background colorimetric signal was observed, after approximately 60 seconds of electrode polarization, the potentiostat was turned off, leaving the electrochemical cell in an open circuit. Then, the hydrogen peroxide present in the solution chemically oxidized the Prussian white back to Prussian Blue, and the corresponding color change was monitored by UV-Vis reflectance (Fig. 9). The maximum color contrast depends on the color of the underlying conductive particles, which were white (SiO2-ATO) or pale yellow (ITO) respectively. These were found to be 675 nm for SiO2-ATO / Prussian Blue electrodes and 700 nm for ITO / Prussian Blue. Figure 10 shows diagrams of absorbance versus time at these wavelengths, as a means of monitoring peroxide reduction. hydrogen on the surface PW / Prussian Blue. As the data shows, the higher the H2O2 concentration, the faster the electrode fully recovers its blue color. Figure 11 shows the relationship between peroxide concentration and reflectance measured at 700 nm, 100 seconds after electrode depolarization. Similar to coulometric sensors, whose sensitivity and detection limit can be adjusted by choosing a suitable integration time, here the sensor performance can be adjusted to the sample concentration simply by adjusting the integration time of the spectrophotometer and / or the sampling time after electrode depolarization (in our case 300 ms and 100 s, respectively). This provides control over the sensitivity, linear range, and limit of detection of the method (see Table 2).
    [0345] Table 2: Spectroscopic determination of H2O2 at different sampling times.
    [0347]
    [0350] As the table shows, the analytical parameters of the sensor can be controlled through the sampling time of the optical measurements. Increasing the sampling time allows to improve the sensitivity of the measurement, and detect lower analyte concentrations. On the other hand, the dynamic range of the sensor is narrowed, since the photodetector saturates at lower concentrations as a direct consequence of the longer sampling time.
    [0352] Example 6
    [0353] The devices of example 1 and 2 are used for the determination of glucose in sweat. The enzymatic oxidation of glucose produces hydrogen peroxide which, in the electrodes modified with SiO2-ATO and Prussian Blue, allows the quantification of glucose electrochemically and spectroscopic.
    [0354] Figure 12 shows the Michaelis-Menten amperometric graphs for glucose using the two electrochromic devices manufactured as indicated in Examples 1 and 2. The dynamic range of both biosensors is between 0.1 mM and 1 mM glucose, and that reaches a saturation greater than 2.5 mM. The analytical performance of our blue biosensors in terms of detection limit and sensitivity, ca. 60 pM and 810-3 mAb -2M-1 (see Table 3), is comparable to that of other reported amperometric biosensors.
    [0356] Table 3: Amperometric and spectroscopic determination of glucose for the two types of electrode
    [0358]
    [0361] Figure 13 shows the spectroscopic calibration charts of the glucose biosensor for the two different devices. As has been seen, no substantial differences are observed when the amperometric or spectroscopic detection method is used, since a similar dynamic range is reached in all cases, reaching a plateau in both cases at concentrations above 2.5 mM. A slight gain is achieved in the detection limit since it decreases to approximately 15 pM probably due to the effect of the high background currents present in amperometric detection that disappear when a spectroscopic detection method is used, but, ultimately, the yields Both types of electrochromic electrodes are comparable, regardless of the device used.
    权利要求:
    Claims (31)
    [1]
    1. A wireless and portable biosensor device for the visualization of a color change from a first color to a second color, where said second color indicates the presence of an analyte in a liquid sample, and the first color indicates the absence of the analyte or a non-reading state, the device being characterized in that it comprises a layered structure comprising:
    • a transparent substrate comprising a face a and a face b, optionally the substrate comprises at least two holes that connect the two faces, a and b, of the substrate;
    • a conductive structure configured as the main structure of an antenna and at least one conductive track of the working and auxiliary electrodes, comprising conductive silver paste;
    • at least two transparent conductive structures configured to function as at least two transducers, one for the working electrode and the other for the auxiliary electrode;
    • at least one electrochromic structure, configured to function at least as a working electrode;
    • a transparent structure configured to deposit the sample on it and comprising
    ■ chitosan; Y
    ■ an oxidase enzyme.
    • a main dielectric structure and that is configured to isolate the conductive tracks from the conductive structure;
    • optionally a second dielectric structure located on the conductive structure and / or on the electrochromic one, exposing at least one area of said electrochromic layer, and wherein said dielectric structure layer comprises at least two holes;
    • at least one conductive track configured to connect with the conductive structure to close the circuit; Y
    • a diode;
    where the device works in direct current;
    where the antenna is configured so that, with a radio frequency between 10.56 MHz to 16.56 MHz, the measurement of the device is restarted until the state of no reading or absence of analyte in the sample; Y
    where the device is configured to reset to its state of non-reading or absence of analyte when receiving a signal of a certain radio frequency between 10.56 MHz to 16.56 MHz.
    [2]
    2. The device according to claim 1, wherein the conductive structure, comprising conductive silver paste, is located directly on the face a of the substrate.
    [3]
    The device according to claim 2, wherein the transparent conductive structure is located on the conductive structure located on the face a of the substrate.
    [4]
    The device according to claim 3, the device being characterized in that it comprises a laminated structure comprising:
    • a transparent substrate comprising a face a and a face b, and where the substrate comprises at least two holes that connect the two faces, a and b, of the substrate;
    • a first layer of conductive structure configured as the main structure of an antenna and conductive tracks of the working and auxiliary electrodes, comprising conductive silver paste, and located on at least a part of the face a of the substrate;
    • at least a second layer of two transparent conductive structures, located on the first conductive structure layer, and configured to function as at least two transducers, one for the working electrode and the other for the auxiliary electrode;
    • at least one third layer of electrochromic structure, located over at least some area of second layer of conductive structure, and configured to function at least as a working electrode;
    • a fourth layer with a transparent structure attached to the third layer with an electrochromic structure, and configured to deposit the sample to be determined on it and comprising:
    ■ chitosan; Y
    ■ an oxidase enzyme.
    • a fifth layer of the main dielectric structure located on the previous layers, exposing at least one area that corresponds to the sample deposit area of the fourth layer, and that is configured to isolate the conductive tracks of the main structure of the first layer;
    • a sixth layer of a conductive track comprising conductive silver paste, and is located on face b of the substrate and is configured to connect, through the holes in the substrate, with the conductive structure of the first layer and close the circuit; Y
    • a diode on the sixth layer.
    [5]
    5. The device according to claim 1, wherein the transparent conductive structures, configured to function as two transducers, one for the working electrode and the other for the auxiliary electrode, are located directly on the face a of the substrate.
    [6]
    6. The device according to claim 5, wherein the conductive structure, comprising conductive silver paste, is located on the transparent conductive structure.
    [7]
    The device according to claim 6, the device being characterized in that it comprises a layered structure comprising:
    • a transparent substrate comprising a face a and a face b and where the substrate comprises at least two holes that connect the two faces, a and b, of the substrate;
    • at least a first layer of transparent conductive structures located on the face a of the substrate and configured to function as two transducers, one for the working electrode and the other for the auxiliary electrode;
    • a second layer of conductive structure, configured as the main structure of an antenna and conductive tracks of the working and auxiliary electrodes, and comprising conductive silver paste, and is in contact with at least a part of the first layer of structure transparent conductor; • at least one third layer of electrochromic structure, located on at least some surface of the second layer of conductive structure, configured to function at least as a working electrode;
    • a fourth layer of transparent structure adhered to the third layer of electrochromic structure configured to deposit the sample on it and comprising
    ■ chitosan; Y
    ■ an oxidase enzyme.
    • a fifth layer of main dielectric structure located on the previous layers, exposing or not covering at least one area or surface that corresponds to the sample deposit area described in the fourth layer, and which is configured to isolate the conductive tracks of the second layer;
    • a sixth layer of a conductive track comprising conductive silver paste, and is located on face b of the substrate and is configured to connect, through the holes in the substrate, with the conductive structure of the first layer and close the circuit; Y;
    • a diode on the sixth layer.
    [8]
    The device according to claim 6, the device being characterized in that it comprises a laminated structure comprising:
    • a transparent substrate comprising a face a and a face b;
    • at least a first layer of transparent conductive structures located on one of the faces of the substrate and configured to function as two transducers, one for the working electrode and the other for the auxiliary electrode;
    • a second layer of conductive structure, configured as the main structure of an antenna and some conductive tracks of the working and auxiliary electrodes, and comprising conductive silver paste, and is in contact with at least a part of the first layer of structures transparent conductive;
    • a third layer of dielectric structure configured to isolate the conductive tracks of the second layer;
    • at least a fourth layer of electrochromic structure, located on at least some area of the second layer of conductive structure, configured to function at least as a working electrode;
    • a fifth layer of a second dielectric structure located on the fourth layer of electrochromic structure, leaving at least one area exposed or not covered, corresponding to the sample deposit area, and wherein said dielectric structure comprises at least two holes;
    • a sixth layer with a transparent structure located, in the area exposed or not covered by the fifth layer, on the fourth layer with an electrochromic structure, configured to deposit the sample on it and comprising:
    ■ chitosan; Y
    ■ an oxidase enzyme.
    • a seventh layer of a conductive track, configured to connect with the second layer of conductive structure through the holes in the fifth layer of dielectric structure and close the circuit; Y
    • a diode on the seventh layer of conductive structure.
    [9]
    9. The device according to any of claims 1 to 8, wherein the diode is of the Schottky type and has dimensions of between 0.8 mm and 1.6 mm.
    [10]
    10. The device according to any one of claims 1 to 9, wherein the oxidase enzyme is selected from glucose oxidase, lactose oxidase, maltose oxidase, urate oxidase or ethanol oxidase.
    [11]
    The device according to any one of claims 1 to 10, wherein the oxidase enzyme is glucose oxidase.
    [12]
    12. The device according to claim 11, wherein it further comprises mutarrotase enzyme.
    [13]
    The device according to any one of claims 1 to 12, wherein the device comprises an additional structure on the transducer of the auxiliary electrode configured to function as an auxiliary electrode.
    [14]
    The device according to claim 13, wherein the additional structure is selected from a transparent conductive structure or an electrochromic structure.
    [15]
    The device according to claim 14, wherein the additional structure is an electrochromic structure.
    [16]
    16. The device according to any of claims 1 to 15, wherein each electrochromic structure comprises
    to. microparticles, selected from among
    i. mixed oxide of tin and indium;
    ii. of the core-covering type where the core is SiO 2 and where the covering is a mixed oxide of antimony and tin; Y
    iii. any combination of the above;
    b. an ink comprising
    i. pigment, preferably Prussian Blue;
    ii. a binder resin, preferably a Viton solution; and where the microparticle: ink ratio is 2.5: 1;
    and where the microparticles and the paint form a homogeneous particulate mixture with a particle size of said mixture of between 3 pm and 12 pm.
    [17]
    17. Procedure for obtaining the device of claim 4, characterized in that it comprises the following steps
    to. making holes in a transparent substrate comprising a face a and a face b by means of a technique selected from among CO2 laser, mechanical puncture and a combination of the previous ones, in such a way that they connect the two faces of the substrate;
    b. print a conductive structure on the face a of the substrate using conductive silver paste to form the spiral structure of the antenna and the conductive tracks of the working and auxiliary electrodes, making at least one printed area coincide with the holes in the stage ( to);
    c. print at least two transparent conductive structures on the impression made in step (b) using a transparent conductor, to function as transducers, one of the working electrode and the other of the auxiliary electrode;
    d. printing an electrochromic structure on part of the conductive structure obtained in step (c);
    and. printing a conductive track on face b of the substrate, in such a way that the ends of the tracks coincide with the areas of the holes and make contact with the ends of the antenna and with the transducer of the auxiliary electrode;
    F. depositing a dielectric structure on the face a of the material obtained after step (d), exposing at least one area of the electrochromic structure that corresponds to the sample deposit area; g. depositing a diode on the conductive track of face b of the substrate obtained in step (e), between one of the ends of the antenna and one of the electrodes that make up the sensor, using silver paste or an anisotropic conductive adhesive; Y
    h. adhering a transparent structure comprising chitosan and an oxidase enzyme to the sample deposit zone that was exposed after depositing the dielectric structure in step (f).
    [18]
    18. Method for obtaining the device according to claim 17, wherein it comprises
    additionally a step (c ') subsequent to step (c) of printing a layer on the transducer of the auxiliary electrode configured to function as an auxiliary electrode and selected from a transparent conductive structure or an electrochromic structure.
    [19]
    19. Procedure for obtaining the device of claim 7, characterized in that it comprises the following steps
    to. making holes in a transparent substrate comprising a face a and a face b by means of a technique selected from among CO2 laser, mechanical puncture and a combination of the previous ones, in such a way that they connect the two faces of the substrate;
    b. printing on the face a of the substrate at least two transparent conductive structures using a transparent conductor to function as transducers, one of the working electrode and the other of the auxiliary electrode, c. printing a second conductive structure on the printing made in step (b) using conductive silver paste to form the conductive tracks that constitute the spiral structure of the antenna and the conductive tracks of the working electrodes;
    d. printing an electrochromic structure on the second conductive structure obtained in step (c);
    and. printing a conductive track on face b of the substrate, in such a way that the ends of the tracks coincide with the areas of the holes and make contact with the ends of the antenna;
    F. depositing a dielectric structure on the face a of the material obtained after step (e) exposing at least one area that corresponds to the area for depositing the sample of the electrochromic structure and g. mounting a diode on the conductive tracks of face b of the substrate obtained in step (e), between one of the ends of the antenna and one of the electrodes that make up the sensor, using silver paste or an anisotropic conductive adhesive; Y
    h. adhering a transparent structure comprising chitosan and an oxidase enzyme in the zone of deposit of the sample of the structure free of dielectric structure of step (f).
    [20]
    20. Method for obtaining the device according to claim 19, wherein it comprises
    additionally a step (d ') subsequent to step (d) of printing a layer on the transducer of the auxiliary electrode selected from a transparent conductive structure or an electrochromic structure.
    [21]
    21. Procedure for obtaining the device of claim 8, characterized in that it comprises the following steps
    to. print on the face a of the transparent substrate a conductive structure, using conductive silver paste, to form the tracks conductors that constitute the structure of the antenna and the conductive tracks of the working and auxiliary electrode;
    b. printing on the conductive structure of step (a), at least two second transparent conductive structures using a transparent conductor to function as transducers, one of the working electrode and the other of the auxiliary electrode;
    c. printing an electrochromic structure on the transparent structure obtained in step (b);
    d. depositing a dielectric structure on the face a of the material obtained after step (c) exposing at least one area that corresponds to the area for depositing the sample;
    and. printing at least one conductive track on the dielectric structure of step (d), so that the ends of the tracks coincide with the inner ends of the antenna and with the contact of the auxiliary electrode; F. depositing another dielectric structure, leaving the working areas of the electrodes, the contacts for the diode, and the area of the sample to be analyzed; g. mounting a diode on the conductive tracks using silver paste or an anisotropic conductive adhesive; Y
    h. adhering a transparent structure comprising chitosan and an oxidase enzyme in the zone of deposit of the sample of the structure free of dielectric structure of step (f).
    [22]
    22. Method for obtaining the device according to claim 21, wherein it comprises
    additionally a step (c ') subsequent to step (c) of printing a layer on the transducer of the auxiliary electrode selected from a transparent conductive structure or an electrochromic structure.
    [23]
    23. A patch or label comprising the device according to any one of claims 1 to 16.
    [24]
    24. Use of the patch according to claim 23 or the device according to any of claims 1 to 16, for the qualitative and / or quantitative detection of an analyte in a liquid sample.
    [25]
    25. Use according to claim 24, wherein the liquid sample is selected from a biological fluid or a food.
    [26]
    26. Use according to claim 25, wherein the biological fluid is sweat.
    [27]
    27. Use according to any of claims 23 to 26, wherein the analyte to be determined is glucose.
    [28]
    28. A system characterized by comprising
    to. the wireless and portable biosensor device described in any one of claims 1 to 16; Y
    b. means of emission of a signal in a radio frequency between 10.56 MHz to 16.56 MHz configured to restart the measurement of the device until the state of no reading or absence of analyte.
    [29]
    29. The system according to claim 28, wherein the means of emission of the radio frequency signal are selected from among mobile devices with Near Field Communication capability, Near Field Communication readers, smart phone devices, smart watches.
    [30]
    30. Method for the qualitative and / or quantitative detection of an analyte in a liquid sample comprising:
    (i) contacting the liquid sample and the transparent structure of the device described in any of claims 1 to 16; Y
    (ii) detection of the analyte by color change.
    [31]
    31. Method according to claim 30, wherein it comprises a step subsequent to step (ii) of restarting the device by sending a signal at a certain radio frequency between 10.56 MHz to 16.56 MHz, for the detection of another sample according to the steps ( i) and (ii).
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    同族专利:
    公开号 | 公开日
    EP3933395A1|2022-01-05|
    ES2781376B2|2021-01-27|
    WO2020174117A1|2020-09-03|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    WO2015112638A1|2014-01-21|2015-07-30|The Regents Of The University Of California|Salivary biosensors and biofuel cells|
    US20170081626A1|2014-03-25|2017-03-23|Universite Grenoble Alpes|Implantable biocompatible reactor|
    WO2017098076A1|2015-12-10|2017-06-15|Consejo Superior De Investigaciones Científicas |Electrochromic biosensor|
    法律状态:
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    ES201930187A|ES2781376B2|2019-02-28|2019-02-28|Wireless, portable and reusable biosensor|ES201930187A| ES2781376B2|2019-02-28|2019-02-28|Wireless, portable and reusable biosensor|
    PCT/ES2020/070144| WO2020174117A1|2019-02-28|2020-02-28|Reusable, portable, wireless biosensor|
    EP20762607.8A| EP3933395A1|2019-02-28|2020-02-28|Reusable, portable, wireless biosensor|
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