Microneedle patch-type device with integrated bioelectrode

Abstract

Integrated bioelectrode microneedle patch device The invention relates to a device for transdermal electrochemical measurements comprising at least one polymeric support having a surface dedicated to contact with a skin, at least one network of polymeric microneedles attached to said support and extending outwards from said surface of the support, and at least one porous and / or nano / micro structured bioelectrode, and comprising at least one biologically active species immobilized on the surface of a conductive material, characterized in that said microneedles and at least the contact surface of said support with said skin are formed of a cross-linked, biocompatible hydrogel, non-electronically conductive in the dry state and electrolytically conductive in contact with an aqueous fluid, and in that said bioelectrode is disposed in contact with the hydrogel and is devoid of direct contact with the skin.The invention also relates to a method for preparing said device and some of its uses. Figure for the abstract: Fig. 1.

Description

Title of the invention: Micro-needle patch type device with integrated bioelectrode Technical field

[0001] The present invention relates to the field of devices useful for the transdermal characterization of biomarkers and analytes in interstitial fluids. In particular, such a device is in the form of a micro-needle patch coupled to an electrode comprising at least one biologically active species, preferably an enzyme and called a bioelectrode. In order to limit repetitive, invasive and painful blood sampling, and to provide greater comfort to patients, the development of in / on-vivo transdermal devices has received considerable attention in recent decades for portable and rapid personal health monitoring. These devices rely on the detection or even quantification of biomarkers and analytes in interstitial fluids (ISF) as an adequate source of biological information to better understand and manage human health.ISF is a natural body fluid present between tissues and cells that includes electrolytes, nutrients, and many other biomarkers. ISF is also abundant in the human body (approximately 15–25% of human body weight), located just beneath the skin in weakly nerved areas such as the dermis or hypodermis, and is therefore easily accessible. The metabolite composition of ISF often closely correlates with that of blood. For example, for glucose biosensing, the glucose level in ISF is approximately 80–90% of the blood glucose concentration (approximately 5 mmol.1 *). Other biomarkers and analytes present in ISF at nmol.1-1 to mmol.L 1 concentrations and relevant for electrochemical biosensors may include, for example, lactate, alcohol, nitrate, alanine, cysteine, pyruvate, glycerol, Ca2+, Mg2+, K+, phosphate, urea, cholesterol, glutamate. .

[0002] Commercially available portable continuous glucose monitoring (CGM) devices have already revolutionized the monitoring and management of glucose levels in ISF. These electrochemical devices rely on the use of a needle to collect ISF from subcutaneous tissues. Enzymatic amperometric glucose biosensors are the most common type of commercially available biosensors due to advantages that include the high reactivity and high specificity of enzymes for both enzymatic and electroenzymatic reactions. Despite improved diabetes management, significant disadvantages of these portable devices include the needle length, which is typically between 5 and 7 mm and may cause discomfort to patients, and the sensor itself, which has limited lifetime, accuracy, and precision. There are also other technical constraints, such as the size and adhesive footprint of the device, the need to use expensive membranes or redox mediators (biocatalytic components for the biosensor), or limited biocompatibility and biodegradability.

[0003] Microneedle patches, also called MN, have become one of the most promising alternatives to replace the uncomfortable or invasive needles used in CGM devices. MN patches are arrays of micrometer-sized needles with heights generally between 20 and 2000 μm that are able to specifically penetrate the skin barrier to reach the dermis layer and access the dermal ISF. Located above the hypodermis, the dermis is weakly nerved and vascularized, which makes transdermal patches, MN, minimally invasive and less painful, due to their reduced dimensions, free of blood and, and less prone to causing infections. Nevertheless, the ability to offer such advantages requires careful considerations in the design of MN patches related to factors such as the materials used, their geometry and the way in which the microneedles are applied.

[0004] Like commercial needle-type CGMs, biosensors integrated in or on an MN patch are mainly based on electrochemical enzymatic biosensors, due in particular to their selectivity, specificity, low cost and simplicity of fabrication. MN patches are generally prepared by micromachining, lithography, etching, printing and micro-molding processes, and are fabricated using polymers and / or metals and / or ceramics. The different types of MNs are solid, hollow and porous MNs.

[0005] Solid MNs with integrated biosensor are constructed from a hard support, for example polycarbonate, [Ref 1] Damien K Ming et al BMJ Innov, 2022, 8, 87 - 94, poly(methyl methacrylate) (PMMA), and the bioelectrode, based on a thin conductive metal (for example Au, Pt) on which biocatalytic components (enzyme, redox mediator, etc., sometimes included in a porous polymer matrix) are deposited and sometimes coated with biocompatible polymer layers or membranes for reasons of biocompatibility and porosity. The bioelectrode is directly formed on the external surface of the MNs which therefore comprises the MN support (metal or rigid polymer such as polycarbonate) then a layer with the biocatalytic components (redox mediator and enzyme), and possibly a membrane or a biocompatible polymer layer. Such solid MNs have been used for the detection and / or monitoring of glucose and other metabolites.Unfortunately, direct contact between the sensor electrode and tissues and biological fluid promotes cytotoxicity and stability problems. In addition, delamination of the materials constituting the bio . electrode during insertion of the MN device into the skin may occur (i.e., mechanical damage to the electrode layer generating residual metal debris left in vivo).

[0006] For so-called hollow MNs, the enzymatic bioelectrode sensor is integrated either (i) inside the channel of a hollow needle of the MN patch [Ref 2] Hazhir Teymourian et al Anal. Chem., 2020, 92, 2, 2291 - 2300 or (ii) at the back of the device [Ref 3] US20090099427A1. Despite generally longer detection times than for the solid MNs-based biosensor, due to the driving force (e.g., capillary forces) required to establish contact between the biosensor and the ISF / biomarkers, this route can offer efficient fluid extraction and flexibility in terms of the type of bioelectrodes that can be incorporated. Nevertheless, leaching of biocatalytic components into the ISF is still a problem. There are also limitations in achieving effective penetration as the needles are less mechanically strong than solid MNs and have an ideal geometry for skin penetration.

[0007] MNs made of porous materials (e.g. based on poly(glycidyl methacrylate (PGMA) or silk) are a hybrid type between solid and hollow MNs. [Ref 4] Hiroyuki Kai et al, J. Phys. Energy, 2021, 3, 024006. MNs can be considered strong enough to guarantee efficient penetration into the skin, while providing a pore structure, possibly conductive because metallic [Ref 4], suitable for (i) depositing on the pores the enzymes and mediators constituting a bioelectrode and necessary for electrochemical detection and (ii) improving the contact of the ISF with the enzymes and mediators and the conductive surface constituting the bioelectrode of a sensor. The ISF can be guided towards the biosensor via capillary forces as is typically the case for hollow MNs.

[0008] Unfortunately, all of these integrated MN-enzymatic electrode biosensors (bioelectrodes) have the disadvantage of requiring expensive and time-consuming manufacturing processes and of being compatible only with complex and often limited electrode integration processes. However, for obvious reasons, these expensive and complex integration methods are an obstacle to their industrial production. Furthermore, all MN devices for which the electrode materials are deposited on the external surface of the MN are subject to non-benign toxicity problems related to the sensor, for example, in the case where the coating breaks or peels off during skin piercing and / or operation of the device, or simply due to direct contact between the coating and skin tissues and fluids.Although hollow or porous type MNs with the electrode on the back of the microneedles are more flexible in terms of the type of electrodes that can be integrated, and can offer improved safety, but on the other hand, they require increased latency and . constrained ISF extraction. In addition, a common problem is to obtain good adhesion of the electrode to the MN device. [Ref 7] SeungHyun Park et al Biosensors and Bioelectronics, 220, 2023, 1149121

[0009] Accordingly, there remains a need for a device useful for transdermal electrochemical measurement, coupling at least microneedles with at least one bioelectrode, and which is not complex to manufacture.

[0010] There also remains the need for the implementation of this device to be free from any risk of toxicity with regard to the subject being analyzed.

[0011] There also remains the need for such a device to be compatible with the implementation of a wide variety of bioelectrodes.

[0012] There also remains a need for such a device to provide good adhesion of this bioelectrode and in particular for it not to be subject to a detachment phenomenon.

[0013] There also remains a need for this bioelectrode to have rapid contact with the ISF to be characterized without having contact with the skin.

[0014] The present invention aims precisely to meet these needs. Summary of the invention

[0015] Thus, according to one of its aspects, the present invention relates to a device useful for transdermal electrochemical measurements, said device comprising at least one polymeric support 1 having a surface dedicated to contact with a skin 2, at least one network of polymeric micro-needles 3 integral with said support 1 and protruding outwards from said surface of the support 1 dedicated to contact with said skin 2, and at least one porous bioelectrode 10, where appropriate nano- or micro-structured, and comprising at least one biologically active species, in particular an enzyme, immobilized on the surface of a conductive material, characterized in that said micro-needles 3 and at least the contact surface of said support 1 with said skin 2 are formed of a crosslinked, biocompatible hydrogel, non-electronically conductive in the dry state and electrolytically conductive in contact with an aqueous fluid,and in that said bioelectrode 10 is arranged in contact with the hydrogel dedicated to swelling in contact with said aqueous fluid and is devoid of direct contact with the skin 2.,

[0016] For the purposes of the invention, a porous bioelectrode is a bioelectrode capable of being, at least on the surface and where appropriate in depth, interpenetrated by the hydrogel.

[0017] Thus, according to a particular embodiment, a bioelectrode can be formed from a conductive material which is porous, in particular selected from the group consisting of platinum, platinum-iridium, gold, palladium, iridium, their alloys, graphite, carbon, indium tin oxide, ruthenium dioxide, carbon nanotubes or conductive polymers.

[0018] According to another embodiment, a bioelectrode may comprise on the surface of its conductive material, and in contact with the immobilized biological species(s), one or more porous polymeric materials selected for example from poly(ethylene oxide), polymers comprising heterocyclic nitrogen groups such as for example poly(vinylpyridine) or poly(vinylimidazole), perfluorinated ionomer polymers such as for example Nafion, poly(urethane), redox polymers (i.e. polymers having multiple redox centers based on transition metals such as osmium, a polysaccharide biopolymer such as for example cellulose acetate, dextran or chitosan, a conductive polymer based on poly(aniline) or poly(3,4-ethylenedioxythiophene) derivatives), or one of their combinations. The conductive material of the bioelectrode 10 may therefore, in this second embodiment, be or not, natively porous.

[0019] Unexpectedly, the inventors have thus found that the coupling of a bioelectrode, porous and where appropriate nano-structured or micro-structured, to a support comprising at least one network of micro-needles can be carried out under conditions making it possible to satisfy the aforementioned expectations provided that this support is formed in particular of a hydrogel in accordance with the invention, namely capable of evolving from a state which is non-conductive with respect to electrons when it is in the dry state to an electrolytically conductive state when it is swollen by an aqueous fluid.A porous aspect of the bioelectrode also has the advantage of allowing the penetration of said hydrogel into the pores of the bioelectrode and thus promoting intimate contact of the surface of the bioelectrode on which at least one biologically active species is immobilized, preferably an enzyme, where appropriate in combination with an electrochemical mediator, with the interstitial fluid which has soaked the hydrogel. This intimate contact promotes physical adhesion between the bioelectrode and the polymer constituting the substrate or the needles of the MN patch, and also promotes the performance of the biologically active species and the bioelectrode.

[0020] More precisely, and as is apparent from the examples below, the micro-needles 3 of the device according to the invention advantageously possess, in the dry state, the mechanical resistance necessary for the perforation of a body tissue, in particular at depths of between 200 and 2000 μm in the case of human skin, to access its interstitial fluid, ISF, effectively. When the crosslinked and dry hydrogel, constituting these micro-needles 3, is in contact with this ISF fluid, it swells and the fluid to be analyzed will diffuse therein by osmotic pressure difference and / or capillarity. Thus, from an electrical point of view, the micro-needles 3 as well as the part of the support 1 secured to its micro-needles 3, can be considered, when they are impregnated with ISF, as becoming an extension of the tissues with the ISF and then provide an electrolyte function. The bioelectrode comprising the species biologically active species placed in contact with this ISF-swollen hydrogel allows, under these conditions, to carry out a measurement or operation faithful to that which would be carried out if it were inserted directly into the skin but advantageously in a minimally invasive manner. In addition, the integration method described in the invention makes it possible to take advantage of the porosity of the bioelectrode 10. By interpenetrating at the level of the bioelectrode 10, the hydrogel maximizes the contact surface between the active species(s) of the bioelectrode 10 and the interstitial fluid carried by the hydrogel during its swelling.

[0021] According to an alternative embodiment, the or at least one bioelectrode 10 is integrated into the crosslinked hydrogel constituting the support 1 which is in direct contact with the rear of the micro-needles 3.

[0022] According to another embodiment variant, the or at least one bioelectrode 10 is integrated into the crosslinked hydrogel constituting micro-needle(s) 3.

[0023] In particular, the bioelectrode 10 is at least partially interpenetrated with crosslinked hydrogel.

[0024] According to yet another embodiment variant, the device according to the invention comprises at least one additional electrode, distinct or not from a bioelectrode. In particular, the device according to the invention may comprise at least one additional electrode distinct from a bioelectrode, notably chosen from a reference electrode, a counter-electrode, a hybrid reference electrode and a counter-electrode.

[0025] In such an embodiment, the device according to the invention may comprise at least one of the electrodes, in particular a porous bioelectrode 10, in the crosslinked hydrogel constituting the support 1 in direct contact with the rear of the micro-needles 3 and at least one or even several other electrodes in the crosslinked hydrogel constituting the micro-needle(s) 3.

[0026] The device according to the invention is therefore advantageous in several ways.

[0027] Its constituent crosslinked hydrogel is compatible with the integration of any bioelectrode 10 for the detection of analytes, ions and / or biomarkers. This hydrogel also provides an enzymatic bioelectrode with a suitable aqueous environment, to operate under satisfactory conditions and in particular allows its lifetime / stability to be extended.

[0028] Only its crosslinked hydrogel component is in direct contact with the biological tissue being analyzed, and therefore the risk of delamination of the coating and / or constituent material of the bioelectrode (for example, mediator, enzyme, AgCl layer, etc.), during insertion of the micro-needles into the tissue is eliminated.

[0029] The risk of detachment of component(s) from the bioelectrode 10 is also eliminated given the integration of the latter in depth of the crosslinked hydrogel of the device according to the invention.

[0030] Positioning the bioelectrode 10 near the rear of the tips of the microneedles 3 and / or within the microneedles 3 themselves also limits the distance that the analyte, ion, proton and / or biomarker must travel and / or any mass transport limitations that could affect detection performance including reducing latency.

[0031] According to a particular variant, the device comprises at least one bioelectrode 10 comprising an enzyme, in particular an oxidoreductase.

[0032] In particular, the bioelectrode 10 is of the electrochemical glucose biosensor type, in particular of the 2nd generation type, which combines the enzyme flavin adenine dinucleotide-dependent glucose dehydrogenase (FAD GDH) with a redox mediator, 1,10-phenantholine-5,6-dione (PLQ), physically adsorbed at the level of a porous electrode made of multi-walled carbon nanotubes (MWCNT), in particular as described in the document WO2018 115710A1.

[0033] According to a particular variant, the device according to the invention is in the form of a transdermal micro-needle patch, MN. In particular, the polymeric microneedles (3) are not hollow.

[0034] According to a preferred variant, the support 1 and micro-needle 3 assembly is made up of said crosslinked hydrogel, biocompatible and non-conductive in the dry state.

[0035] In particular, the crosslinked hydrogel is free of metallic constituent and electronically conductive polymer.

[0036] According to another preferred variant, the hydrogel is devoid of biologically active species other than that(s) immobilized on said bioelectrode(s) 10.

[0037] According to another preferred variant, said biologically active species is an enzyme, in particular an oxidoreductase, and participates in an electrocatalytic reaction with an exchange of electrons between the enzyme and the conductive material.

[0038] According to another of its aspects, the present invention relates to a method for preparing a device according to the invention, in particular by micromolding, and comprising at least the crosslinking of at least one polymer, preferably a biopolymer, to form said crosslinked hydrogel characterized in that at least said or one porous and where appropriate nano- or micro-nanostructured bioelectrode 10 is integrated by bringing into contact with said polymer before or simultaneously with its crosslinking.

[0039] In particular, said bioelectrode 10 or even the ancillary electrodes are arranged in contact with the aqueous formulation containing at least said non-crosslinked polymer and are subjected to mechanical pressure there to position them in depth near the base of the micro-needles 3 and / or in depth of micro-needle(s) 3, prior to or simultaneously with the crosslinking.

[0040] According to yet another of its aspects, the present invention relates to the use of a device according to the invention for transdermal electrochemical measurements, in particular for the characterization of at least one analyte in an interstitial fluid.

[0041] Thus, the invention relates in particular to a method for detecting and / or measuring at least one analyte in an interstitial liquid of a patient, in particular in a non-invasive manner, comprising at least bringing the micro-needles 3 of a device according to the invention into contact with said interstitial liquid of said patient under conditions conducive to the swelling of said crosslinked hydrogel constituting the micro-needles 3 by this liquid and to the diffusion of this liquid by osmotic pressure difference and / or capillarity to the bioelectrode(s) 10 of said device.

[0042] Other characteristics, variants and advantages of the objects of the invention will become more apparent upon reading the description, examples and figures which follow, given for illustrative and non-limiting purposes of the invention.

[0043] In the rest of the text, the expressions “between ... and ...”, “ranging from ... to ...” and “varying from ... to ...” are equivalent and are intended to mean that the limits are included, unless otherwise stated. Brief description of the drawings

[0044] [Fig-1] represents an example of a device diagram according to the invention.

[0045] [Fig.2] represents cyclic voltammograms recorded at a scan rate = 1 mV.s-1 in phosphate buffer (PB) (0.1 M, pH = 7.4) with a dextran-methacrylate (Dex-MA) microneedle biosensor with a crosslinked degree of substitution (DS = 9%) comprising an electrode based on MWCNTs coated with immobilized PLQ and FADGDH (MN-BS) in the absence (dotted line) of glucose and in the presence (solid line) of 0.1 M glucose.

[0046] [Fig.3] illustrates continuous blood glucose monitoring by chronoamperometry at -0.1 V vs. pseudo-reference Ag / AgCl with a cross-linked Dex-MA microneedle biosensor (DS = 37%) comprising an electrode based on MWCNTs coated with PLQ and FADGDH immobilized (MN-BS) in artificial skin containing 5 mmol.L-1 of glucose, n = 1.

[0047] [Fig.4] reports a selectivity test by chronoamperometry in PB at -0.1 V vs pseudo-reference Ag / AgCl and with agitation of 300 rpm with a biosensor based on MWCNT without hydrogel coating and with hydrogel coating in the presence of 5 mmol.L-1 of glucose (1), then successive additions of 2) 0.2 mmol.L-1 of acetaminophen, 3) 1 mmol.L-1 of cholesterol, 4) 8 mmol.L-1 of urea, 5) 2 mmol.L-1 of lactate, 6) 0.3 mmol.L-1 of galactose, 7) 0.5 mmol.L-1 of uric acid UA, 8) 0.1 mmol.L-1 ascorbic. Detailed description

[0048] As is clear from the above, the invention aims to provide devices which are invasive devices that can intervene transdermally, continuously or not, for the transdermal detection of biomarkers in interstitial fluids.

[0049] More particularly, this device comprises at least one polymeric support 1, at least one porous bioelectrode 10 and micro-needles 3 arranged on one of the faces of the support 1. These micro-needles 3 penetrate into a biological tissue up to the interstitial liquid thereof and in which it is precisely sought to electrochemically characterize at least one chemical or biological species.

[0050] In the device according to the invention, the micro-needles 3 are solid. In other words, they are not hollow but made of crosslinked hydrogel in accordance with the invention and, where appropriate, a bioelectrode 10 integrated into this hydrogel but without possible direct contact with the tissue being analyzed.

[0051] They generally have a length varying from 200 to 3000 pm.

[0052] In an alternative embodiment, the device according to the invention may comprise several networks of micro-needles 3 and / or several bioelectrodes 10 and / or distinct electrodes.

[0053] In particular, the device according to the invention is in the form of a micro-needle patch, MN, in particular as illustrated in [Fig.l].

[0054] The device in [Fig.l] is formed of a body made of a crosslinked hydrogel which is, when not in use, in a dry state. The body comprises a support 1 and microneedles 3 which project from a face 4 of the support 1 in contact with the skin 2 of a patient and which have penetrated into the dermis 6 of the patient's skin, through the stratum corneum 7 and the epidermis 8.

[0055] The device further comprises a bioelectrode 10. This bioelectrode 10 is porous, which means that the hydrogel can interpenetrate the structure of the electrode (as shown in [Fig.l]).

[0056] The interstitial fluid present in the dermis comprising the biomarkers diffuses thanks to the hydrogel towards the bioelectrode 10 through the microneedles 3 then into the support 1, and finally into the pores of the porous bioelectrode 10, forming a crosslinked hydrogel filled with electrolyte (interstitial fluid).

[0057] An electrical connection 9 of the bioelectrode may be made by a wire made of an electrically conductive material (for example a copper silver plated wire) adhering to the back of the bioelectrode with a conductive paste (such as carbon paste). Crosslinked hydrogel

[0058] For the purposes of the invention, a crosslinked hydrogel is a hydrophilic and insoluble three-dimensional polymer. Its crosslinking is obtained by physical or chemical, preferably chemical, bonds existing between polymer chains.

[0059] In the dry state, the crosslinked hydrogel has the hardness necessary for the penetration of the micro-needles 3 that it composes but on the other hand is not capable of ensuring circulation electrons. In other words, it is not an electronic conductor. It is therefore devoid of any metallic constituent and organic conductive polymer such as, for example, PEDOT, poly(pyrrole) or poly(aniline).

[0060] Furthermore, this crosslinked and dry hydrogel is capable of swelling upon contact with a fluid, in particular an aqueous fluid such as water or a biological fluid. It can therefore absorb and retain a large quantity of a fluid. This hydrogel swelling rate (SR) is generally defined by the ratio between the weight of the swollen hydrogel and the weight of this same hydrogel in the corresponding dry state. More precisely, the fluid diffuses inside the crosslinked hydrogel by phenomena of capillarity and / or osmotic pressure difference between the fluid and the hydrogel. Thus impregnated, the crosslinked hydrogel makes it possible to bring the aqueous fluid to be characterized into contact with, in particular, the bioelectrode that it incorporates. In particular, the hydrogel, by at least partially penetrating the porous bioelectrode, increases the contact surface between the fluid and the bioelectrode.In other words, the swelling of the hydrogel by the interstitial liquid causes the device according to the invention, insulating in the dry state, to become an electrolytic matrix (ionic conductor), and makes it possible to make the electrical bridge between the tissue where the micro-needles 3 are inserted and the bioelectrode(s) and, possibly electrodes, which it contains. In contrast to devices of the prior art, the crosslinked and swollen hydrogel according to the invention also acts as a filter isolating the bioelectrode(s) / electrodes, which it incorporates, from any possible contact with the biological tissue. The structural network of the crosslinked gel is such that in the swollen state it makes any migration of possible small fragments of the bioelectrode(s) / electrodes towards this tissue almost impossible. Any risk of toxicity due to the bioelectrodes / electrodes is therefore excluded.

[0061] The crosslinked hydrogel according to the invention is also biocompatible.

[0062] For the purposes of the invention, a biocompatible hydrogel is a hydrogel which, due to its chemical nature, is not likely to cause an undesirable effect on the biological tissue being analyzed.

[0063] The biocompatible aspect of the hydrogel is an advantage because it is the only one in direct contact with the tissues as a component of the microneedles 3 penetrating the skin of a subject. Thus, the hydrogel constituting the microneedles 3 and the support 1 acts as a screen between the tissue and the bioelectrode 10 and any additional electrodes associated with it in the device according to the invention. In addition, if the hydrogel, although crosslinked, remains bioresorbable in the long term, the hydrogel components of the polymer microneedles 3 will not pose any risk in the event of breakage of a microneedle in the skin 2 during use of the device, since they can be resorbed over time without damage to the tissues.

[0064] Finally, given its biocompatibility, the hydrogel can play a beneficial role with regard to the stability of bioelectrode(s) 10 associated in the device according to the invention. It constitutes a biocompatible environment which is particularly advantageous for enzymes, allows their denaturation to be reduced and can allow favorable mass transport.

[0065] As already specified, the crosslinked hydrogel according to the invention advantageously has good swelling properties (swelling in 24 hours greater than 10%, preferably 20%, more preferably more than 50%) and in the dry state good mechanical hardness for piercing the skin (Young's modulus greater than 10 kPa).

[0066] As detailed below, the precursor polymer of this hydrogel must also be in the "liquid" state for the integration of at least one bioelectrode 10 or even additional electrodes and make possible its penetration at least partially into the structure of said bioelectrode. The polymer solution can also be solid at room temperature but liquid at a temperature compatible with the biologically active species(s), in particular the enzyme(s), associated with the bioelectrode (for example <60 degrees or possibly <80 degrees for engineered thermostable enzymes). This is the case, for example, of gelatin gels.

[0067] The crosslinked hydrogel according to the invention can be obtained by crosslinking any type of polymer which, once crosslinked, forms in contact with an aqueous fluid an insoluble and infusible hydrogel.

[0068] In particular, the crosslinked hydrogel according to the invention can be obtained by crosslinking one or more biopolymers with, where appropriate, one or more synthetic polymers, where appropriate chemically modified to be crosslinkable, or one of their mixtures.

[0069] For the purposes of the invention, the term "biopolymer" designates a polymer derived from renewable natural resources (a material also known as "natural". The biopolymers considered according to the invention have the advantage of possessing, in addition to very good compatibility with human skin, biodegradability as such or even in vivo.

[0070] This term “biopolymer” thus covers natural polymers such as, for example, a protein or a polysaccharide, but also derivatives of natural polymers such as, for example, those which derive from a chemical modification of these natural polymers to make them crosslinkable or compatible with a specific crosslinking method.

[0071] This chemical modification most often consists of introducing into the structure of the polymers to be modified crosslinkable units in particular chosen from thiol, divinylsulfonyl, maleimide, azide, alkynyl, alkenyl, acrylate, methacrylate, aldehyde, norbornenyl, oxy-amine units, and in particular from acrylates, methacrylates.

[0072] As an illustration of synthetic polymers suitable for forming a hydrogel crosslinked suitable for the invention may in particular be cited raw poly(ethylene glycol) (PEG) or modified by different chemical functions such as for example poly(ethylene glycol) diacrylic (PEGDA), poly(ethylene glycol) dimethacrylic (PEGDMA), poly(vinyl pyrrolidone) (PVP), poly(methyl vinyl ether / maleic acid-PEG, PVA-MA, -PLA, -PLLA, -PGA, -PLGA and their derivatives.

[0073] By way of illustration of biopolymers suitable for forming a crosslinked hydrogel in accordance with the invention, mention may in particular be made of polyhydroxy acids, such as, for example, polyglycolic acid (PGA) and polylactic acid (PLA), also known as polylactide; polysaccharides, such as, for example, cellulose, chitin and starch and proteins or peptides, such as, for example, collagen, gelatin, elastins, fibroins, corn zein, silk from various species of silkworms, keratin and their derivatives.

[0074] According to a preferred embodiment variant, the crosslinked and biocompatible hydrogel considered according to the invention is obtained by crosslinking at least one biopolymer chosen from polymers of the chitosan, dextran, alginates, collagen, gelatin, agarose, chitin, polyhydroxyalkanoates, pullan, starch, amylose, amylopectin, cellulose type in particular carboxymethylcellulose, and hydroxypropylcellulose, hyaluronic acid, gellan gum, xanthan gum such as for example the derivatives of these polymers resulting from their chemical modification to make them crosslinkable or compatible for a specific crosslinking mode and their combinations.

[0075] According to a particular embodiment, this biopolymer is or derives from at least one polymer chosen from alginates, hyaluronic acid, carboxymethylcellulose, chitosan, dextran and their derivatives.

[0076] In particular, the hydrogel is a crosslinked dextran hydrogel.

[0077] For the purposes of the invention, the term dextran covers dextrans which have or have not been chemically modified to be crosslinked.

[0078] Thus, it may be of interest to crosslink a chemically modified dextran polymer with acrylate and / or methacrylate units which are well known to be photopolymerizable.

[0079] These functional groups which make crosslinking by irradiation possible, are introduced with a given degree of substitution, DS. Conventionally, the DS corresponds to the number of polymerizable functions introduced on 100 monomer units. This DS can be determined by 1H NMR.

[0080] Thus, according to a particular embodiment, the device according to the invention comprises a hydrogel deriving from the crosslinking of a dextran polymer, modified by units chosen from acrylate, methacrylate, alkenyl, and alkynyl, preferably a dextran polymer modified by methacrylate units, Dex-MA, and DS varying from 5 to 65%. Electrodes and their integration mode

[0081] Another specific feature of the device of the invention is based on the method of integrating the porous bioelectrode(s) required according to the invention or even other additional electrode(s).

[0082] As specified above, the electrodes are arranged so as not to have direct contact with the tissue whose ISF is the subject of the analysis.

[0083] Generally, they are fully integrated into the crosslinked hydrogel to be swollen by this ISF, with the exception of their end dedicated to the external electrical connection. Generally this connection is located on the upper face or one of the lateral faces of the device.

[0084] In contrast to conventional devices, the bioelectrode(s) and possibly additional electrode(s) are also not, within the scope of the present invention, in communication with a channel to which the microneedles would be connected.

[0085] As already specified above, they are on the other hand arranged either near and / or within solid micro-needles of the device.

[0086] According to a particular embodiment, they are integrated into the thickness of the support located at the rear of the micro-needles.

[0087] This mode of integration is notably illustrated in [Fig.l]. Bioelectrodes

[0088] Bioelectrodes are electrodes widely described in the literature and those skilled in the art are able, thanks to their general knowledge, to access bioelectrodes satisfying the specificities of the invention. The term “bioelectrode” very often refers to an electrode comprising one or more enzymes.

[0089] In particular, a bioelectrode according to the invention may comprise a conductive material chosen from electrodes based on Pt, Au, Ag, Pd, Ni, Ir, graphitic carbon, amorphous carbon, graphene, graphene oxide, diamond, boron-doped diamond, nanotubes, doped semiconductor fibers e.g. doped silicon, metal oxides, e.g. indium-tin oxide, conductive polymer electrodes e.g. a PEDOT material, and conductive fibers.

[0090] A bioelectrode can be nano-structured or micro-structured. It can thus be a nano- or micro-electrode.

[0091] Its general shape may be planar or non-planar. A planar bioelectrode may be an electrode printed on a porous or non-porous substrate. This substrate may comprise a sheet of carbon paper or fabric or a printed sheet or pad or electrode, e.g., a screen-printed electrode.

[0092] A non-planar shaped bioelectrode comprises a Pt wire or a carbon fiber wire or a wound electrode.

[0093] For example, the bioelectrodes suitable for the invention may be chosen from bioelectrodes based on Pt, Au, Ag, Pd, Ni, Ir, graphitic carbon, amorphous carbon, graphene, graphene oxide, diamond, boron-doped diamond, nanotubes, doped semiconducting fibers e.g. doped silicon, metal oxides, e.g. indium-tin oxide, conductive polymer electrodes e.g. PEDOT and conductive fibers.

[0094] When the conductive material of the bioelectrode according to the invention is non-porous, it is surface-modified by a polymeric or inorganic porous material. This material may in particular be chosen from crosslinked hydrogels or polymers such as, for example, Nafion, a cellulose acetate, a sulfonated poly(ether ketone), glutaraldehyde, a poly(ethylene glycol) diglycidyl ether, poly(dimethyl siloxane), chitosan, a dextran, an alginate, redox polymers based on transition metal compounds and complexes, poly(ethylene oxide), polymers comprising heterocyclic nitrogen groups such as poly(vinylpyridine) or poly(vinylimidazole), poly(urethane), conductive polymers based on poly(aniline) derivatives or poly(3,4-ethylenedioxythiophene), and combinations or copolymers thereof.

[0095] It should be noted that such a material is also advantageous for improving the performance of the bioelectrode in terms of stability or capacity for detecting interfering molecules or species. It is therefore possible to consider it in association with a porous conductive material.

[0096] According to another variant, the bioelectrodes 10 considered according to the invention are formed from a nano-structured or micro-structured conductive material.

[0097] These may thus be 3D porous bioelectrodes such as “papers” made of carbon nanotubes and 2D micro / nanostructured bioelectrodes.

[0098] In particular, the bioelectrode is based on carbon nanotubes and in particular based on multi-walled carbon nanotubes (MWCNT).

[0099] At least one biologically active species, in particular an enzyme, is immobilized on the surface of the conductive material.

[0100] Advantageously, the bioelectrode comprises at least one enzyme, where appropriate combined with a molecule which facilitates the transfer of electrons between the enzyme and the electrode 10, such as for example an electrochemical mediator or a 'promoter' type molecule which improves the orientation and / or the transfer of electrons between the electrode and the enzyme.

[0101] On the other hand, the hydrogel of said device is advantageously devoid of biologically active species or mediator, other than that(s) immobilized on said bioelectrode(s).

[0102] Thus, the device can integrate a bioelectrode on which is or are im- mobilized, generally by adsorption, one or more enzymes chosen in particular from oxidases, e.g. glucose oxidase, pyruvate oxidase, xanthine oxidase, lactate oxidase, dehydrogenases e.g. lactate dehydrogenase, reductases e.g. nitrate and nitrite reductase and metalloenzymes, e.g. bilirubin oxidase or laccase, etc.

[0103] A bioelectrode may thus comprise a working electrode, WE. The term "working electrode" herein designates an electrode at which a candidate compound (analyte, biomolecule, active agent) is electro-oxidized or electro-reduced with or without the intervention of a redox mediator or 'promoter' molecule. The term "redox mediator" designates an electron transfer agent that transfers electrons between a compound and an electrode directly or indirectly. The term "promoter" designates an agent that facilitates the orientation of enzymes on the surface and / or the transfer of electrons between the active site of the enzyme and the electrode.

[0104] In a particular embodiment, the device according to the invention comprises an enzymatic bioelectrode.

[0105] The bioelectrode can also be modified with a biological catalyst (or not) to improve its performance, e.g. selectivity, specificity, activity.

[0106] According to yet another variant, the device can integrate a bioelectrode on which is immobilized a non-enzymatic catalyst such as for example conductive nanoparticles, e.g. Au, Pt, Ir. and / or other nanostructured materials, e.g. carbon nanotubes, quantum dots, mesoporous and doped carbon, and / or redox molecules such as organic molecules or organometallic species.

[0107] According to yet another variant, the bioelectrode according to the invention can also be modified by a biorecognition element, e.g. stretavadin, extravaidine, aptamers, etc.

[0108] Such bioelectrodes are particularly interesting for detecting and / or measuring a chemical or biological analyte such as, for example, proteins, amino acids, viruses, hormones, drugs, drugs (for example, cannabinoids, amphetamines, cocaine and opioids) and nicotine metabolites (for example, cotinine), and in particular an analyte chosen from glucose, lactate, alcohol, nitrate, alanine, cysteine, pyruvate, glycerol, Ca2+', Mg2+, K+ ions, phosphate, urea, cholesterol, glutamate, hydrogen peroxide, hydrogen, etc. This type of bioelectrode is often metal or carbon based and is used for the electro-oxidation or electro-reduction of the candidate compound and often with one or more catalytic or electrocatalytic elements such as noble metals, nanoparticles, and enzymes.In particular, these may be WE electrodes with recognition elements (often called 'receptors') to facilitate specific and selective detection. and often with a polymeric element to facilitate properties such as mechanical, recognition and / or signal transmission properties.

[0109] Thus and as already specified above, a device according to the invention advantageously comprises at least one enzymatic bioelectrode and in particular dedicated to interacting with glucose and which associates the enzyme FAD-GDH with the redox mediator phe-nanthroline quinone (PLQ) physically adsorbed at the level of a multi-walled carbon nanotube (MWCNT) electrode, in particular as described in document WO2018 115710A1.

[0110] In another example, a device according to the invention may comprise at least one bioelectrode with an immobilized enzyme and at least one immobilized redox species selected from a compound of osmium, ruthenium, iron and cobalt, coupled to a polymer selected from poly(vinylpyridine), poly(aniline), poly(thiophene), poly(acetylene), poly(pyrrole), a biopolymer based on poly(saccharides), or from aromatic molecules selected from the group formed by 9,10-phenanthrenequinone, l,10-phenanthroline-5,6-dione, 9,10-anthraquinone, phenanthrene, l,10-phenanthroline, 5-methyl-l,10-phenanthroline, phenazines, phenathiozines, tetrathiofulvalene, or inorganic complexes from a composed of osmium, ruthenium, iron and cobalt, or polyoxometalates. The immobilized redox species will be used to enhance the electrocatalytic or bioelectrocatalytic reaction.

[0111] Of course, a device according to the invention can integrate several bioelectrodes which are respectively capable of interacting with biological species also called biomarkers, distinct such as for example lactate and glucose. The integration of several bioelectrodes with different sensors in the same device has the advantage of making possible for example the simultaneous and real-time monitoring of several biomarkers in the interstitial fluids.

[0112] In another embodiment, a second bioelectrode dedicated to the same target can be used for a duplicate measurement or as a calibration electrode.

[0113] In a variant, the device according to the invention comprises at least one additional electrode, distinct from the bioelectrode, notably chosen from a reference electrode, a counter-electrode, and a hybrid reference and counter-electrode. The sensor then operates so that a current is generated between the working electrode represented by the bioelectrode and the counter-electrode or the hybrid electrode.

[0114] Thus, the device according to the invention may further comprise a counter-electrode, CE. Such electrodes are particularly interesting for establishing a circuit with a working electrode on which the current is applied or measured. The electrodes of Pt, Ag, AgCl, or other metals (Ti, Au, Pd, tin), metal oxides (IrO2), Carbon electrodes (glassy carbon), conductive polymer electrodes (PEDOT), are auxiliary electrodes typically used in electrochemistry.

[0115] The device according to the invention may also comprise at least one reference electrode, RE. Such electrodes are particularly interesting for measuring or controlling the potential of an indicator or the working electrode. Saturated calomel electrodes or silver chloride electrodes are reference electrodes typically used in electrochemistry.

[0116] The device according to the invention may also comprise an electrochemical detection device, attached to said electrode(s) via electrical connections preferably surrounded by insulation. This detection device thus makes it possible to carry out measurements by potentiometry, cyclic voltammetry (CV), fast sweep cyclic voltammetry (FSCV), square wave voltammetry (SWV), pulsed voltammetry or chronoamperometry.

[0117] Method for preparing a device according to the invention

[0118] As specified above, the invention also relates to a method for preparing a device according to the invention, in particular by micromolding, comprising at least one step of crosslinking at least one polymer, in particular a biopolymer, to form said crosslinked hydrogel characterized in that said bioelectrode of said device is integrated by contacting with said polymer before or simultaneously with its crosslinking.

[0119] In particular, when the bioelectrode or even the ancillary electrodes are brought into contact, the polymer is in the form of a formulation, in particular aqueous, liquid or semi-liquid, i.e. of viscous appearance and preferably having a viscosity varying from 1 to 100 Pa.s 1 to 1 Hz with a shear stress of 0.2%.

[0120] This liquid formulation, preferably aqueous, contains said polymer and preferably at least one crosslinking agent.

[0121] The electrode(s) to be integrated are arranged on the surface of this liquid formulation and are subjected to mechanical pressure to position them in depth near the base of the microneedles or within the hydrogel constituting the microneedles, prior to or simultaneously with crosslinking. Indeed, at this viscosity, the electrode(s) with their contact point can be inserted easily with moderate force (light pressure of the thumb for example) in a precise and / or reproducible manner. They can be inserted so that the contact recovery wires (or other electrical contacts) preferentially exit the patch from the top and / or the side of the support secured to the microneedles.

[0122] In addition, the liquid aspect of the polymer formulation at the time of insertion of the porous bioelectrode allows the polymer to penetrate into the structure of the electrode and thus obtain a large contact surface with the hydrogel which will carry the fluid. interstitial.

[0123] After insertion of the electrode(s), crosslinking is carried out or continued until a crosslinked and dry hydrogel is obtained. To do this, the crosslinking operation is generally followed by a drying operation.

[0124] The crosslinking may be chemical crosslinking. In which case, a crosslinker is also present in the liquid formulation containing the polymer(s) and preferably the biopolymer(s) to be crosslinked. This often slow crosslinking method is conducive to the integration of the electrode(s) during crosslinking.

[0125] Crosslinking may also be triggered using a physical stimulus such as heat, gas exposure, or irradiation (e.g., light, UV radiation, X-rays, gamma radiation, microwave irradiation).

[0126] According to a particular embodiment, the crosslinking is carried out photochemically.

[0127] Advantageously, the devices according to the invention can be prepared by a micromolding technique using a silicone mold, itself obtained from a master model produced by micromachining.

[0128] The liquid formulation, preferably aqueous, containing the biopolymer and preferably at least one crosslinking agent is poured into the mold obtained from this master model. This mold makes it possible to obtain, after evaporation of the water or solvent from the solution, and crosslinking, the dry crosslinked hydrogel device which can be removed from the mold. Use

[0129] A device according to the invention is advantageously useful for transdermal electrochemical measurements, in particular for the characterization of at least one analyte in an interstitial liquid.

[0130] For the purposes of the invention, the term analyte covers any chemical or biological species such as a drug, a bioactive agent, a metabolite or even an endogenous biochemical product.

[0131] Any analyte present in the skin interstitial fluid can be characterized using the device according to the invention. Examples include, but are not limited to, glucose, sodium, potassium, alcohol, lactate (important for athletes), cortisol, urea, drugs (e.g., cannabinoids, amphetamines, cocaine, and opioids) and nicotine metabolites (e.g., cotinine), as well as medicinal substances that a patient may be taking for one or more medical conditions.

[0132] Thus, the present invention also aims at a method for detecting and / or measuring at least one analyte in an interstitial liquid, in particular in a non-invasive manner, comprising at least bringing the micro-needles of a device according to the invention into contact with said interstitial liquid under conditions conducive to swelling of said hydrogel constituting the micro-needles by this liquid and diffusion of this liquid by osmotic pressure difference and / or capillarity to the bioelectrode of said device.

[0133] The following examples and figures are presented for illustrative purposes and do not limit the scope of the invention. Materials

[0134] Dextran T70 (Dex T70, Mw = 70,000 g / mol) and Dextran T20 (Dex T20, Mw = 20,000 g / mol) from Pharmacosmos,

[0135] Methacrylic anhydride (94%),

[0136] Lithium phenyl-2,4,6-trimethylbenzoylphosphinate (LAP, > 95%),

[0137] Phosphate buffer (PBS 10X): 1370 mM NaCl, 27 mM KC1, 100 mM Na2HPO4, 18 mM KH2PO4; pH = 7.4),

[0138] NaH2PO4 (> 99%),

[0139] D-glucose (> 99%),

[0140] l,10-phenantholine-5,6-dione (PLQ, 97%),

[0141] N,N-dimethylformamide (DMF, 99.9%), porcine gelatin (gel strength 300, Type A), agar, bovine serum albumin (BSA, > 95%) from Sigma-Aldrich,

[0142] MWCNTs, (0 = 9.5 nm, 1.5 pm length, > 95% purity) from Nanocyl,

[0143] PTFE filters from Millipore (JHWP, 0.45 pm pore size, 0 (filter) = 46 mm), polydimethylsiloxane and its crosslinking agent (PDMS, Sylgard 184) from Dow,

[0144] Flavin adenine dinucleotide-dependent glucose dehydrogenase (FAD GDH) enzyme from Sekisui

[0145] Phosphate buffers (PB 0.lM Na2HPO4; pH = 7.4) and PBS (PBS1X: 137 mM NaCl, 2.7 mM KC1, 1 mM Na2HPO4, 1.8 mM KH2PO4; pH = 7.4)

[0146] Artificial interstitial fluid (ISF): It was prepared by dissolving 22 g.L1 of BSA in PBS buffer and adjusting the pH to 7.4. Glucose solutions in PB, PBS and 1TSF were prepared IM by solubilizing the adequate amount of glucose in PB, PBS or ISF and adjusting the pH to 7.4.

[0147] Artificial dermis (AD): It was prepared as follows: several solutions of gelatin (4% or 24% (w / w)) and agar (1% (w / w)) were mixed in 40 mL of artificial ISF in the presence and absence of glucose (5 mmol.L *) in a 100 mL flask, and heated at 80°C for 30 minutes with stirring. Then, the solution (AD 4 or AD24, comprising 4 or 24% gelatin respectively) was poured into Petri dishes and allowed to cool overnight before use.

[0148] Skin phantom: it is composed of a thin Teflon membrane (Millipore PTFE filter, JHWP, pore size 0.45 qm, 0 (filter) = 47 mm) to mimic the upper layer of the epidermis (mimics the dry stratum corneum), and the artificial dermis described above prepared in PBS with 22 gL-1 of BSA in the presence or absence of glucose 5 mmol.L 1 to mimic the lower layer of the dermis.

[0149] Electrochemical measurements were performed using a Biological VMP3 multipotentiostat with EC-lab software or a Princeton Applied research PARSTAT MC (PMC 1000 / DC) running Versa Studio software with a three-electrode system consisting of

[0150] - a pseudo-reference electrode made of homemade Ag / AgCl wire (sat. KC1),

[0151] - a platinum wire as a counter electrode and

[0152] - a modified glassy carbon electrode or an MWCNT-based electrode modified or the integrated MN-BS device described herein as a working electrode.

[0153] Amperometric measurements were performed in a Faraday cage at room temperature using a Princeton Applied research PARSTAT MC potentiostat (PMC 1000 / DC) running Versa Studio software with a three-electrode system, consisting of an Ag / AgCl wire as a pseudo-reference electrode, a platinum wire as a counter electrode, and the selected working electrode. Example 1 Preparation of chemically modified dextran

[0154] Methacrylated dextrans were synthesized according to the method described in application FR 2 114 492.

[0155] The detailed protocol is as follows: Dextran (5 g) was dissolved in 100 mL of distilled water, DW, in a beaker. After complete dissolution, different equivalents of methacrylic anhydride from 0.0625 to 0.5 equivalents relative to the hydroxyl functions of dextran were added dropwise into the polymer solution to obtain the desired degree of substitution (DS) for the polymer, i.e. 9, 18, 37 or 62%. Then, the pH was adjusted using NaOH (3 mol.1-1) to be around 9 - 11 during the whole reaction. The solution was stirred at room temperature for 1 h. Finally, the modified Dextran was dialyzed against distilled water for 1 week (membrane 12-14 kDa) and lyophilized. The white solid was stored at -20°C before use.

[0156] A PBS solution containing 20% ​​(w / w) Dex-MA with a DS of 9, 18, 37 or 62% and 1% (w / w) LAP as photoinitiator was prepared in a 10 ml vial. 100 μl of solution was poured into a 6 mm diameter cylindrical Teflon mold (without microneedle cavity) and the solution was allowed to air dry for 24 h. The polymer was crosslinked by first irradiating the back of the patch at 405 nm for 1 min (P = 75 mW / cm2), followed by demolding the dry polymer cylinder. 4 dry photocrosslinked dextran-methacylate materials (DS of 9, 18, 37 or 62%) were thus obtained.

[0157] These 4 materials were characterized by a swelling test.

[0158] To do this, the 4 dried photo-crosslinked Dex-MA materials were weighed (weight W0). The samples were placed in a vial containing PBS (IX) at room temperature (21-24°C). They were removed every hour and their surface was quickly wiped with a paper towel to remove excess water. Then, the samples were immediately weighed (Wt) and placed back in PBS for the next measurement points. This operation was repeated until no further weight changes were detected. The swelling ratio (SR) was calculated according to SR = (Wt -W0) / W0. Three experiments were performed in parallel for each material.

[0159] Table 1 below reports the average values ​​of the swelling rates thus determined.

[0160] [Tables 1] Dex-MA Sample Swelling Rate (%) DS=62% 43.9 + 2.2 DS=37% 55.2 + 2.0 DS=18% 84.2+1.5 DS=9% 98.0 + 2.5

[0161] The maximum swelling rate for each formulation was reached in approximately 1-2 hours. An increase in SR is correlated with a decrease in DS.

[0162] The hardness of each of these 4 materials was also characterized by a compression test.

[0163] These compression tests were carried out using a TAXT.Plus texturometer (Stable Micro Systems, UK).

[0164] The compression speed was set at 0.5 mm.s-1 with a maximum compression force of up to 50 N. The compression modulus values, E, were calculated as the slope of the curve of applied force versus displacement. Table 2 reports these values.

[0165] [Tables2] Sample Compression modulus (MPa) Dex-MA DS=62% 159 + 7 Dex-MA DS=37% 167 + 10 Dex-MA DS=18% 161 + 9 Dex-MA DS=9% 155 + 7

[0166] No alteration of the mechanical properties of the materials is observed. It is advantageous to note that the compression moduli of the photo-crosslinked dried DexMA materials are well above 10 kPa, the threshold value for piercing the skin. Example 2

[0167] Preparation of a micro-needle patch, MN coupled to a working bioelectrode according to the invention.

[0168] a) Preparation of a working bioelectrode (WE) in carbon nanotubes with coating of electrochemical mediator (PLO) and enzyme (FADGDH).

[0169] 66 mg of MWCNT were dispersed in 66 ml of DMF on a 100 ml flask, and placed in a water bath under sonication for 1h30. The suspension was filtered through a PTFE filter using a vacuum pump, washed with distilled water and left for 2h under a hood. After filtration, the resulting carbon nanotube "paper" was left to dry at room temperature against another PTFE filter for 24h. The carbon nanotube "paper" was gently detached from the filter paper and cut into individual electrodes of 0 = 4 or 6 mm. Then, the MWCNTs were respectively modified by a first addition of 9 and 20 μl of a PLQ solution (5 mM) in acetone / H2O mixture (volume ratio of 1:1), and left to dry for 10 minutes. Respectively 13.5 and 30 μl of a solution of FADGDH in PB phosphate buffer (10 mg.mL-1) were deposited on the surface of the modified electrode, and left to dry for a few hours.Finally, electrical contact was made using a metal wire attached to the back of the bioelectrode with carbon paste and left to dry for 2 hours. The back of the electrode was insulated with silicone paste and left to dry for a few hours before use.

[0170] b) Preparation of the polydimethylsiloxane mold. PDMS. for the MN patch

[0171] A master mold was fabricated from aluminum by micro-milling. The aluminum mold consisted of a 7 mm cylindrical array with 5x5 (25) pencil-shaped microneedles with respective heights of 800, 1000, and 1200 pm, a base width of 400 pm, and an edge-to-edge distance between the needles of 400 pm. A reverse mold was prepared by casting a mixture of PDMS and its curing agent (ratio of 10:1) onto the master mold, under vacuum to remove air bubbles, and then cured at 100 °C for 2 h. Finally, the master and reverse molds were cooled in air for a few hours, and the PDMS mold was gently detached from the aluminum mold.

[0172] c) Preparation of the MN patch with integration of the working electrode

[0173] A PBS solution containing 20% ​​(w / w) Dex-MA with a DS of 9, 18, 37 or 62% and 1% (w / w) LAP as photoinitiator was prepared in a 10 ml vial. 100 μl of solution was poured into a PDMS mold. The mold was placed in an aluminum holder connected to a vacuum pump, and a reduced pressure (1-10 mbar) was applied for 2 h to fill the mold tips. The working electrode, WE, prepared in a) was then embedded in the MN patch by inserting the electrode inside the polymer solution such that the electrode surface was close to the back of the tips, and the back of the electrode was exposed to allow electrical connection 9. The MN patch with the embedded electrode, WE, was then allowed to dry for 24 h. The polymer was crosslinked by first irradiating the back of the patch at 405 nm for 1 min (P = 75 mW / cm2), followed by demolding the device and a final irradiation at 405 nm for 1 min on the needle face of the patch. Finally, the electrical connection was made by bonding an Ag / Cu wire with carbon paste to the back of the electrode. Example 3

[0174] Efficiency test of MN device with integrated MWCNT-based working electrode for electrooxidation and glucose detection

[0175] The MN device considered is a crosslinked Dex-MA microneedle patch (DS = 9%) integrating a working electrode based on MWCNT with immobilized PLQ and FADGDH and prepared according to example 2c).

[0176] The cyclic voltammograms, shown in [Fig.2] were recorded in the absence and presence of glucose in a phosphate buffer solution prepared at 0.1 M, pH = 7.4 (PB) in air, in a 3-electrode cell using the MN device as the working electrode, a platinum wire as the counter electrode, and a chlorinated silver wire (Ag / AgCl) as the reference electrode. In the absence of glucose (dotted line), the redox signal of the PLQ is observed with a redox activity typical of quinone (dominant low potential redox couple around E1 / 2 = -0.24 V vs. Ag / AgCl pseudo-reference). In the presence of 0.1 M glucose (solid line), a strong increase in current is observed with a low attractive trigger potential of about -0.3 V compared to the Ag / AgCl pseudo-reference.

[0177] It appears that the process of integrating the bioelectrode into the hydrogel matrix did not significantly disrupt the bioelectrocatalytic oxidation of glucose. This same efficiency of bioelectrocatalytic oxidation was verified with Dex-MA microneedle patches of DS of 18, 37 and 62%. Example 4

[0178] Application of a device according to the invention for continuous measurement of blood sugar in a two-layer artificial skin phantom

[0179] Continuous glucose monitoring was performed with the integrated cross-linked MN Dex-MA electrode (DS = 37%) prepared according to Example 2 in a bi-layer artificial skin phantom as detailed above in the Materials and Methods chapter.

[0180] The amperometric measurements were carried out as also described in the Materials and Methods chapter. The counter electrodes and reference electrodes were here inserted directly into the skin phantom (no integration with the MN patch). The needles of the MN device made of crosslinked Dex-MA (DS = 37%) integrating a bioelectrode-type working electrode based on MWCNTs coated with PLQ and FADGDH as prepared according to Example 2c) pierced the bilayer artificial skin phantom (24%) using a penetration force of 10 N, and a constant force of approximately 1 to 2 N to maintain the needles inside the artificial dermis.

[0181] Immediately after insertion and concomitant application of -0.1 V, the recorded current increased to about 3 pA ([Fig.3]). In the absence of glucose, the current did not exceed 0.1 pA. The maximum catalytic current was reached at about 4 h. A decrease in current, typical of these 2nd generation glucose enzymatic electrodes, was then obtained until about 22 h where the electrode performance decreased to less than 2% of the maximum catalytic current. Example 5

[0182] Device for glucose detection with a MWCNT-based bioelectrode without hydrogel versus a device according to the invention with crosslinked hydrogel (DexMA 37%): Characterization in the presence of different interfering species in artificial ISF.

[0183] The amperometric measurement with the glucose electrode considered in the previous example can be carried out at different potentials, the applied potential having an impact on factors such as the contribution of electrochemical interferences as well as bioelectrocatalysis which affects the performance of the sensor.

[0184] [Fig. 4] shows a chronoamperogram recorded at -0.1 V which shows, first, a glucose sensor signal (oxidation current) after addition of 5 mmolL 1 of physiologically relevant glucose. Successive additions of potential interferents were then made. The current remained virtually unchanged with the addition of acetaminophen, cholesterol, urea, lactate, galactose and uric acid (UA) (2-7). Uric acid and acetaminophen are known to be oxidized at potentials that interfere with glucose sensors and are therefore known as common electrochemical interferents. In contrast, the signal from the glucose electrode (oxidation current) changes significantly with the addition of ascorbic acid (AA) (8) corresponding to the electrochemical oxidation of the compound at the working potential of -0.1 V relative to the pseudo reference Ag / AgCl.Nevertheless, this current only implies an interference rate of 6.8%, which is very acceptable. Finally, a second addition of 5 mmol of Ll glucose was made (1) which again resulted in an increase in current, showing the robustness of the MWCNT-based biosensor device to the presence of interfering species. However, this current is lower than the current from the first glucose addition.

[0185] The same experiment was carried out on devices having a coating based on Dex-MA DS = 37% crosslinked in accordance with the invention. Similar to the devices without hydrogel, an increase in current is obtained upon the first addition of glucose, followed by a practically unchanged current with the addition of acetaminophen, cholesterol, urea, lactate, galactose and uric acid (UA) (2-7), an oxidation of ascorbic acid is observed upon its addition due to its oxidation at this working potential, involving an interference rate of only 4.9%, which shows the beneficial effect of the hydrogel with respect to the interfering species. Finally, a final increase in current is observed following the last addition of glucose, an increase whose value is very close to that obtained upon the first addition, showing the protective and stabilizing effect of the hydrogel with respect to the interfering species with respect to the device. Example 6

[0186] Characterization of the stability of an MN patch with an integrated bioelectrode according to the invention versus an electrode immobilized on the back of the patch.

[0187] A PBS solution containing 20% ​​(w / w) Dex-MA with a DS of 37% and 1% (w / w) LAP as photoinitiator was prepared in a 10 ml vial. The solution was cast into the PDMS mold prepared in Example 1. The mold was placed in an aluminum holder connected to a vacuum pump, and reduced pressure (1-10 mbar) was applied for 24 h to fill the mold tips and dry the polymer. The dry polymer was then crosslinked under UV-vis at 405 nm for 1 min (P = 75 mW / cm2). The MWCNT-based electrode (prepared in Example 2) was then integrated by depositing a polymer layer containing 20% ​​(w / w) Dex-MA with a DS of 37% and 1% (w / w) LAP on the electrode and bonding the electrode to the back of the patch. The resulting MN patch was then exposed again to UV-vis at 405 nm for 1 min to crosslink the bonding layer.

[0188] This device not in accordance with the invention and that in accordance with the invention prepared using a Dex-MA of DS of 37%, in example 2, were then analyzed by chro-noamperometry at -0.1V by immersing the hydrogel part of the device in a solution of PB under stirring for 1 h min, followed by an addition of 5 mM of glucose. However, after 24 h, no catalytic current was observed with the MN patch not in accordance with the invention. A partial detachment of the electrode was also observed.

Claims

Claims

1. Device useful for transdermal electrochemical measurements, said device comprising at least one polymeric support (1) having a surface dedicated to contact with a skin (2), at least one network of polymeric micro-needles (3) integral with said support (1) and protruding outwards from said surface of the support (1) dedicated to contact with said skin (2), and at least one bioelectrode (10), porous and comprising at least one biologically active species, in particular an enzyme, immobilized on the surface of a conductive material, characterized in that said micro-needles (3) and at least the contact surface of said support (1) with said skin (2) are formed of a crosslinked hydrogel, biocompatible, non-electronically conductive in the dry state and electrolytically conductive in contact with an aqueous fluid,and in that said bioelectrode (10) is arranged in contact with the hydrogel dedicated to swelling in contact with said aqueous fluid and is devoid of direct contact with the skin (2).,

2. Device according to the preceding claim in which said or at least one bioelectrode (10) is integrated into the crosslinked hydrogel constituting the support (1) which is in direct contact with the rear of the microneedles (3).

3. A device according to any preceding claim wherein the bioelectrode (10) is at least partially interpenetrated with crosslinked hydrogel.

4. Device according to any one of the preceding claims, characterized in that said hydrogel is free of metallic constituent and electronically conductive polymer.

5. Device according to any one of the preceding claims, characterized in that said hydrogel is devoid of biologically active species other than that(s) immobilized on said bioelectrode(s) (10).

6. Device according to any one of the preceding claims, characterized in that said polymeric microneedles (3) are not hollow.

7. A device according to any preceding claim wherein said biologically active species is an enzyme, optionally combined with a molecule which facilitates the transfer of electrons between the enzyme and said electrode 10.

8. Device according to any one of the preceding claims in which the bioelectrode (10) is formed from a nano-structured or micro-structured conductive material and in particular is based on carbon nanotubes and more particularly is based on multi-walled carbon nanotubes (MWCNT).

9. Device according to any one of the preceding claims, characterized in that it comprises at least one enzymatic bioelectrode and, in particular, dedicated to interacting with glucose and which associates the enzyme FAD-GDH with the redox mediator phenanthroline quinone (PLQ) physically adsorbed at the level of a multi-walled carbon nanotube (MWCNT) electrode.

10. Device according to any one of the preceding claims in which said hydrogel is obtained by crosslinking one or more biopolymers with, where appropriate, one or more synthetic polymers, where appropriate chemically modified to be crosslinkable, or one of their mixtures.

11. Device according to the preceding claim wherein said biopolymer is selected from polyhydroxy acids, such as for example polyglycolic acid (PGA) and polylactic acid (PLA), also known as polylactide; polysaccharides, such as for example cellulose, chitin and starch and proteins or peptides, such as for example collagen, gelatin, elastins, fibroins, corn zein, silk from various species of silkworms and keratin and their derivatives.

12. Device according to the preceding claim in which said biopolymer is or derives from at least one polymer chosen from alginates, hyaluronic acid, carboxymethylcellulose, chitosan, dextran, and their derivatives, and in particular dextran.

13. Device according to any one of the preceding claims in which said hydrogel derives from the crosslinking of at least one dextran polymer modified by units chosen from acrylate, methacrylate, alkenyl and alkynyl and in particular a dextran polymer modified by methacrylate units, Dex-MA, and DS varying from 5 to 65%.

14. Device according to any one of the preceding claims in the form of a micro-needle transdermal patch, MN.

15. Device according to any one of the preceding claims comprising at least one additional electrode, separate or not from a bio- electrode, in particular chosen from a reference electrode, a counter electrode, or a hybrid reference and counter electrode.

16. A device according to any preceding claim comprising an electrochemical sensing device attached to said electrode(s) via electrical connections.

17. Method for preparing a device according to any one of the preceding claims by micromolding and comprising at least one step of crosslinking at least one biopolymer to form said crosslinked hydrogel characterized in that at least said or one porous bioelectrode of said device is integrated by contacting with said biopolymer before or simultaneously with its crosslinking.

18. Use of a device according to any one of claims 1 to 16 for transdermal electrochemical measurements, in particular for the characterization of at least one analyte in an interstitial fluid.

19. Method for detecting and / or measuring at least one analyte in an interstitial liquid, in particular in a non-invasive manner, comprising at least bringing the micro-needles (3) of a device according to any one of claims 1 to 16 into contact with said interstitial liquid under conditions conducive to the swelling of said hydrogel constituting the micro-needles (3) by this liquid and to the diffusion of this liquid by osmotic pressure difference and / or capillarity to the bio-electrode(s) (10) of said device.

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