EXTENDED DETECTION RANGE BODY MONITORING DEVICE

Abstract

The present invention relates to a sensor for measuring a bodily analyte, the sensor comprising a microneedle array including at least two microneedles, each of the two microneedles comprising a coating covering at least part of the active surface of the microneedle, each of the coatings comprising a biomolecule adapted to react with a predetermined analyte, the coating being configured to allow electrochemical measurement of the analyte concentration in the interstitial fluid within a predetermined concentration range, the range of one of the two microneedles being different from the range of the other of the two microneedles. Figure for the abstract: Fig. 1

Description

Description Title of the invention: MONITORING DEVICE EXTENDED DETECTION RANGE BODY FIELD OF INVENTION

[0001] — The present invention relates to a device for measuring a bodily analyte. More Specifically, it concerns a body monitoring device through analysis of bodily fluid, typically interstitial. STATE OF THE ART

[0002] — Certain conditions such as diabetes require daily monitoring of physiological quantities of the human body, in particular concentrations of certain compounds (blood sugar in the example of glucose).

[0003] — For this purpose, it is common to prick a point on the skin so as to make a bead of a drop of blood, and to analyze this drop either reactively (for example with a strip), or electronically (for example, by at least one sensor analytical), in order to estimate the target quantity(ies).

[0004] — We now know of less invasive systems that simply analyze the Interstitial fluid, that is, the fluid that fills the space between the capillaries blood and cells. Indeed, interstitial fluid has a composition ionic similar to that of blood plasma.

[0005] — Such systems thus make it possible to monitor physiological parameters desired transcutaneously, without having to regularly pierce the skin.

[0006] In particular, a wrist-worn device called GlucoWatch has been proposed, implementing a phenomenon called iontophoresis (or ionophoresis) in which a An electric field helps to draw interstitial fluid through the skin to a sensor on the device's wall. This concept, however, was quickly abandoned. because only 6% of patients could tolerate the pain caused by the extraction electrical. Moreover, the measurement results were unreliable.

[0007] — Transcutaneous probes in the form of a patch have been proposed as an alternative. a sticker that places a "microneedle-sensor" just under the skin, so as to put the sensor in permanent fluidic communication with the interstitial fluid, for a continuous monitoring. Some of these transcutaneous patch-type probes include- use wireless communication methods to transmit measurements on the interstitial fluid to a mobile terminal, for storage and / or processing of measures (verification of thresholds and variations, statistical analysis, etc.) triggering alerts if necessary, etc.). Examples include systems sugarBEAT"M or FreeStyle Libre. Document WO 2015 / 138989 describes a device comprising a sensor, the sensor comprising an array of electrodes configured to detect an analyte by implementing an electrochemical reaction in the user's skin. Such a device avoids the need to collect interstitial fluid, thus simplifying the device design. However, the device described in WO 2015 / 138989 may have a detection range for analyte concentration that is too narrow to detect several pathologies related to the concentration of the same analyte in the user's body. WO 2015 / 138989 proposes to resolve this problem by varying the geometry of the different microneedles described. However, this method is complex to implement because the microneedles are generally manufactured in parallel by micro-etching, which does not allow for the production of microneedles with different geometries in the same batch. Description of the invention One aim of the invention is to provide a solution for detecting the concentration of a body analyte over a wider concentration range than some of the known prior art systems allow, while simplifying the design of such a system. This objective is achieved within the framework of the present invention by means of a sensor for measuring a bodily analyte, having a first face intended to be placed against the skin of a user, the sensor comprising: - a network of microneedles adapted to be brought into contact with the user's interstitial fluid by insertion into the user's dermis, the microneedles being fixedly mounted on the first face, each microneedle comprising a metallic active surface arranged on the surface of the microneedle, - the network comprising at least two microneedles, each of the two microneedles comprising a coating covering at least part of the active surface of the microneedle, each of the coatings comprising a biomolecule adapted to react with a predetermined analyte, the coating being configured to allow an electrochemical measurement of a concentration of the analyte in the interstitial fluid within a predetermined concentration range, the range of one of the two microneedles being different from the range of the other of the two microneedles. The invention is advantageously complemented by the following features, taken individually or in any of their technically possible combinations: - the sensor comprises a plurality of microneedle arrays, the coating of one of the microneedles of one of the microneedle arrays comprising a type of biomolecule different from the type of biomolecule of a microneedle from another network, - the sensor comprises a plurality of microneedle arrays, the coating of a microneedle of one of the arrays comprising an arrangement of layers, each layer comprising a biochemical composition, the coating comprising a different arrangement and / or a different biochemical composition from another arrangement and / or a different biochemical composition of another coating of another microneedle of another array, - the coating of one of the microneedles has a different biomolecule density than the biomolecule density of another coating on the other microneedle, - a network comprises at least three microneedles, two of the at least three microneedles comprising coatings configured to allow electrochemical measurement of the concentration of the same analyte in the interstitial fluid within the same predetermined concentration range, - the sensor comprises a support base and several elementary support plates, several microneedles being fixedly mounted on each of the support plates, each support plate being fixedly mounted on the support base, and the coatings of the microneedles fixedly mounted on one of the support plates being configured to allow an electrochemical measurement of a concentration of the same analyte in the same first range, the coatings of the microneedles fixedly mounted on another of the support plates being configured to allow an electrochemical measurement of a concentration of the same analyte in the same second concentration range different from the first range, - the sensor comprises a support base and several support plates, several microneedles being fixedly mounted on each of the support plates, each support plate being fixedly mounted on the support base, and the coatings of the microneedles fixedly mounted on one of the support plates comprising the same first type of biomolecule, the coatings of the microneedles fixedly mounted on another of the support plates comprising the same second type of biomolecule, different from the first type of biomolecule, - One of the microneedles is monolithically formed with the support plate by micro-etching, - Each mounting plate is fixed to the support base using an electrically conductive adhesive to allow an electrical connection between the support base and the mounting plate, - the sensor comprises a plurality of electrodes, each electrode comprising the active surface of one of the microneedles, the electrode passing through a thickness of the support plate on which the microneedle is mounted, and comprising an electrical part tri-conductive on and / or in the support base. Another aspect of the invention is a device for measuring a body analyte, comprising a sensor according to an embodiment of the invention, and a housing configured to exploit an electrical signal emitted by the sensor representative of the concentration of the analyte(s) in the interstitial fluid. DESCRIPTION OF THE FIGURES Other features, purposes and advantages of the invention will become apparent from the following description, which is purely illustrative and not limiting, and which should be read in conjunction with the accompanying drawings on which: [fig.1] - Fig.1 schematically illustrates a top view of a sensor according to one embodiment of the invention, [fig.2] - Figure [fig.2] schematically illustrates a section of a microneedle comprising an active surface, [fig.3] - Figure [fig.3] schematically illustrates microneedles mounted fixed on a support plate according to one embodiment of the invention, [fig.4] - Figure [fig.4] schematically illustrates microneedles mounted fixed on a support plate according to one embodiment of the invention, [fig.5] - Figure [fig.5] schematically illustrates a top view of a sensor according to one embodiment of the invention, [fig.6] - Figure [fig.6] schematically illustrates a support base according to one embodiment of the invention, [fig.7] - Figure [fig.7] schematically illustrates a detail of a support base according to one embodiment of the invention, [fig.8] - the [fig.8] schematically illustrates a body monitoring device according to one embodiment of the invention. Throughout the figures, similar elements bear identical references. DEFINITIONS An "electrode" is defined as a conductive device for detecting variations in electrical potential in a living organism. An electrode comprises at least two ends, or terminals, between which an electrical potential or an electric current is transmitted. An electrode may preferably have at least three ends, at least two of which are intended to penetrate the body of a living organism. In this case, it should be noted that the electrode is a single unit, even though several ends are intended to penetrate the body of a living organism. DETAILED DESCRIPTION OF THE INVENTION With reference to [Fig. 1], a sensor 1 according to an embodiment of the invention is adapted for measuring a bodily analyte, and preferably for measuring the concentration in the interstitial fluid of the body analyte. Sensor 1 has a first face 4 intended to be placed against the user's skin, and preferably to be in contact with the user's skin. Figure 1 illustrates a top view of sensor 1. The sensor 1 comprises at least one array 2 of microneedles 3. The array 2 preferably comprises between 2 and 15 microneedles 3. The microneedles 3 are adapted to come into contact with the user's interstitial fluid by insertion into the user's dermis. In particular, the microneedle 3 has a wall that can be partially in contact with the interstitial fluid when the microneedle 3 is inserted into the user's dermis. The microneedles 3 are fixedly mounted on the first face 4. By "fixed," we mean that each microneedle 3 is attached to the first face 4. With reference to [Fig. 2], each microneedle 3 comprises a metallic active surface 5 arranged on the surface of the microneedle 3. In the embodiment of the invention schematically illustrated by [Fig. 2], the active surface 5 is arranged around and extending from the tip of the microneedle 3. The active surface 5 does not cover a portion of the microneedle surface surrounding a base of the microneedle. Thus, when the microneedle 3 is inserted into the dermis of a user, a portion of the dermis is not subject to measurement by the microneedle 3. Therefore, measurement noise can be avoided. The network 2 comprises at least two microneedles 3. Each of the two microneedles 3 includes coatings 6 covering at least part of the active surface 5 of the microneedle 3. Each of the coatings 6 includes a biomolecule adapted to react with a predetermined analyte. The predetermined analyte may be preferentially chosen from glucose and lactate. The coating 6 is configured to allow electrochemical measurement of the analyte concentration in the interstitial fluid within a predetermined analyte concentration range 17. The range 17 of one of the two microneedles 3 is different from the range 17 of the other microneedle 3. Thus, it is possible to measure the concentration of a body analyte in a user's interstitial fluid within a concentration range encompassing both ranges 17 of the two microneedles 3, using microneedles 3 with substantially identical geometries. Indeed, it may be necessary for the two microneedles 3 to have identical geometries in order to measure the analyte concentration at the same depth in the user's dermis. With reference to [Fig. 1], the same principle can be extended to three or more microneedles. [Fig. 1] schematically illustrates a network 2 in which three microneedles 3 have a coating 6 adapted to measure the analyte concentration in a first range 17, and three other microneedles 3 have a coating 6 adapted to measure the concentration of the analyte in a second range 17, and three other microneedles 3 include a coating 6 adapted to measure the concentration of the analyte in a third range 17. The array 2 can indeed comprise at least three microneedles 3, two of which have coatings 6 configured to allow electrochemical measurement of the concentration of the same analyte in the interstitial fluid within the same predetermined concentration range 17. Thus, for a constant geometry of microneedles 3, it is possible to increase the total active surface area 5 in contact with the interstitial fluid, thereby reducing measurement noise of the analyte concentration. With reference to [Fig. 1], the sensor can comprise a plurality of arrays 2 of microneedles 3, the coatings 6 of one of the microneedles 3 of one of the arrays 2 of microneedles 3 comprising a type of biomolecule different from the type of biomolecule of a microneedle 3 of another array 2. In [Fig. 1], the coatings 6 comprising a first type of biomolecules are schematically illustrated by circles, and the coatings 6 comprising a second type of biomolecules are schematically illustrated by squares. With reference to [Fig. 2], the coating 6 of a microneedle 3 may comprise an arrangement of layers 9, each layer 9 comprising a chemical or biochemical composition, the coating 6 comprising a different arrangement and / or a different biochemical composition from another arrangement and / or a different biochemical composition of another coating 6 of another microneedle 3. Thus, it is possible to vary the range 17 from one microneedle 3 to another microneedle 3 by modifying only the coating 6 of a microneedle 3. It is also possible in this way to modify the analyte that can be measured by a coating 6 by modifying only the coating 6 of a microneedle 3. The coating 6 of one of the microneedles 3 has a surface density of the biomolecule different from the surface density of the biomolecule of another coating 6 of another microneedle 3. Thus, it is possible to manufacture microneedles 3 comprising different ranges 17, by varying the surface density of the biomolecule in the coating 6 of each microneedle 3. The coating 6 may preferably include an outer layer 9 intended to be in direct contact with the interstitial fluid, configured to be biocompatible with the user's body. The range variations 17 presented by different coatings can be implemented preferentially by varying at least one parameter chosen from among the biochemical composition of a layer 9 of the coating, the thickness of a layer 9 for a constant biochemical composition between two coatings and the arrangement of the different layers 9 together in the same coating. The coating 6 can be configured to detect lactate, and in particular to measure the lactate concentration in the user's interstitial fluid. The sensor is preferably configured to allow an electrochemical measurement of a lactate concentration within an overall range, the overall range being defined as the union of the predetermined concentration ranges of each of the coatings 6 configured to measure a lactate concentration. In particular, the sensor can be configured to measure a lactate concentration within an overall range from 0.2 mM to 30 mM inclusive, and in particular from 0.5 mM to 20 mM inclusive.For this purpose, a first coating 6 can be configured to allow an electrochemical measurement of a lactate concentration in the interstitial fluid in a first concentration range 17 between 0.2 mM and 10 mM, preferably between 0.5 mM and 5 mM, and a second coating 6 of a microneedle different from that of the first coating 6 can be configured to allow an electrochemical measurement of a lactate concentration in the interstitial fluid in a second concentration range 17 between 0.2 mM and 30 mM, in particular between 5 mM and 30 mM, and preferably between 5 mM and 20 mM.Thus, the first and second concentration ranges improve the accuracy of lactate concentration measurement for two distinct physiological states of the user: a first normal state, corresponding to the first range, and a second hyperkalemic state corresponding to the second range or a part of the second range. Alternatively or in addition, a coating 6 can be configured to detect ketone bodies, and in particular to measure the concentration of ketone bodies in the user's interstitial fluid. The sensor 1 is preferably configured to allow electrochemical measurement of a ketone body concentration within an overall range, the overall range being defined as the union of the predetermined concentration ranges of each of the coatings 6 configured to measure a ketone body concentration. Specifically, the sensor 1 can be configured to measure a ketone body concentration within an overall range from 0.05 mM to 5 mM inclusive, and in particular from 0.1 mM to 4 mM inclusive.For this purpose, a first coating 6 can be configured to allow an electrochemical measurement of a concentration of ketone bodies in the interstitial fluid in a first concentration range 17 between 0.05 mM and 1 mM, preferably between 0.1 mM and 1 mM, and a second coating 6 of a microneedle different from that of the first coating 6 can be configured to allow an electrochemical measurement of a concentration of ketone bodies in the interstitial fluid in a second concentration range 17 between 0.05 mM and 5. mM, especially between 0.5 mM and 5 mM, and preferably between 11 mM and 4 mM. Thus, the first and second concentration ranges improve the accuracy of the measurement of ketone body concentration for two distinct physiological states of the user: a first normal state, corresponding to the first range, and a second state of ketoacidosis, corresponding to the second range or a part of the second range. Alternatively or in addition, a coating 6 can be configured to detect glucose, and in particular to measure a glucose concentration in the user's interstitial fluid. The sensor 1 is preferably configured to allow an electrochemical measurement of a glucose concentration within an overall range, the overall range being defined as the union of the predetermined concentration ranges of each of the coatings 6 configured to measure a glucose concentration. In particular, the sensor 1 can be configured to measure a glucose concentration within an overall range from 1 mM to 30 mM inclusive, and in particular from 1 mM to 20 mM inclusive. To this end, a first coating 6 can be configured to allow an electrochemical measurement of a glucose concentration in the interstitial fluid within a first concentration range 17 from 1 mM to 4 mM, preferably from 2.5 mM to 4 mM.A second re-coating 6 of a microneedle different from that of the first coating 6 can be configured to allow an electrochemical measurement of the concentration of glucose in the interstitial fluid in a second concentration range 17 between 3 mM and 15 mM, in particular between 4 mM and 10 mM, and a third re-coating 6 of a microneedle different from that of the first and second coatings 6 can be configured to allow an electrochemical measurement of the concentration of glucose in the interstitial fluid in a third concentration range 17 between 7.5 mM and 30 mM, in particular between 10 mM and 25 mM. Thus, the first range improves the accuracy of the glucose concentration measurement when the user is in a hypoglycemic state, and the second range improves the accuracy of the glucose concentration measurement when the user is in a euglycemic state.and the third range improves the accuracy of glucose concentration measurement when the user is in a state of hyperglycemia. With reference to [Fig. 3], [Fig. 4], and [Fig. 5], the sensor may preferably comprise a support base 10 and several elementary support plates 11. With reference to [Fig. 3], several of the microneedles 3 are fixedly mounted on a support plate 11. With reference to [Fig. 5], a plurality of support plates 11 may be fixedly mounted on the support base 10. The coatings 6 of the microneedles 3 fixedly mounted on one of the support plates 11 may be configured to allow An electrochemical measurement of the concentration of the same analyte in a first range 17. The coatings 6 of the microneedles 3, fixedly mounted on another of the support plates 11, are configured to allow an electrochemical measurement of the concentration of the same analyte in a second concentration range, different from the first range 17. Thus, it is possible to simplify the manufacture of a sensor comprising microneedles 3 adapted to measure different concentration ranges. Indeed, it is particularly difficult to coat the same set of microneedles 3, for example, made from a silicon wafer, with different coatings 6. It is therefore possible to assemble on the same sensor 1 sets of microneedles 3 that have previously been coated with different coatings 6, by mounting different support plates 11 on the support base 10, and thus allow the measurement of different ranges 17.In this embodiment, the network 2 is formed by the set of microneedles 3 fixedly mounted on the two support plates 11. The sensor 1 may include a support base 10 and several support plates 11. Several microneedles 3 may be fixedly mounted on each of the support plates 11, each support plate 11 being fixedly mounted on the support base 10. The coatings 6 of the microneedles 3 fixedly mounted on one of the support plates 11 comprise a first type of biomolecule, and the coatings 6 of the microneedles 3 fixedly mounted on another of the support plates 11 comprise a second type of biomolecule, different from the first type of biomolecule. It is thus possible to assemble on the same sensor 1 sets of microneedles 3 that have previously been coated with different coatings 6, by mounting different support plates 11 on the support base 10, and thus allow the measurement of both different ranges 17 for the same analyte and different analytes. Referring to [Fig. 3] and [Fig. 4], the microneedles 3 are preferentially formed monolithically with the support stage 11 by micro-etching. This allows for the fabrication of microneedles 3 with substantially identical geometries, while detecting wide ranges of analyte concentrations. Each support plate 11 can preferably be fixed to the support plate 10 by means of an electrically conductive adhesive 12, thus enabling an electrical connection between the support base 10 and the support plate 11. This simplifies both the mounting of a plate 11 onto the base 10 and the electrical transmission of a signal representing the concentration of the body analyte. Furthermore, the use of the electrically conductive adhesive allows the plate 11 to be fixed to the base 10 while avoiding exposing the sensor 1 to temperatures exceeding 30°C, and preferably exceeding 50°C. Such temperatures are likely to damage the biomolecules of the coating 6, and thus to prevent the measurement of the analyte concentration. With reference to [Fig. 3], [Fig. 4], and [Fig. 5], the sensor 1 may comprise a plurality of electrodes 13, each electrode 13 comprising the active surface 5 of one of the microneedles 3. Each electrode 13 may pass through a thickness of the support plate on which the microneedle 3 is mounted and includes an electrically conductive portion on and / or within the support base 10. Thus, an electrical signal representative of a concentration of the body analyte can be transmitted to the support base 10 while simplifying the fabrication of the sensor 1, which includes microneedles adapted to measure different concentration ranges 17. With reference to [Fig. 6] and [Fig. 7], the electrically conductive portion(s) of the support base 10 may include conductive areas 21 of the support base 10. The conductive areas 21 may be fabricated by localized deposition of a metallic layer. With reference to [fig.[4], the support plate 11 may include conductive areas 22, arranged on the face of the support plate opposite the face on which the microneedles 3 are mounted. The conductive areas 21 of the base 10 and the conductive areas 22 of the plate 11 are preferably arranged so as to be opposite each other when the plate 11 is mounted on the base 10, allowing an electrical connection to be established, preferably by means of electrically conductive adhesive. Preferably, the sensor includes a plurality of dots of electrically conductive adhesive, each dot of adhesive being deposited between an electrically conductive area 21 of the base 10 and an electrically conductive area of ​​the plate 11. The base 10 may also include conductive tracks 23, allowing one or more conductive areas 21 of the base 10 to be connected to a processing unit. With reference to [Fig. 6] and [Fig. 7], the LO base and the support plate(s) 11 preferably include complementary shape elements designed to secure the support plates 11 to the support base 10. A complementary shape element may preferably be a cavity formed in the support base 10, with a geometry complementary to the contour of one or more support plates 11. Alternatively, or in addition, the complementary shape element may preferably be bosses arranged on the support base 10 and adapted to receive at least one support plate 11, for example, so as to surround and / or hold it. Thus, during the mounting of the support plates 11 onto the base 10, the support plate 11 and the microneedles can be held in a controlled position until the support plate(s) 11 are fixed to the base 10.Furthermore, each of the support plates 11 can thus be fixed in a perfectly controlled position. With reference to [Fig. 8], one aspect of the invention is a device 15 for measuring a body analyte. The device 15 comprises a housing 16 in the shape of a case watch with a strap 20 adapted to fit around an individual's wrist. The case 16 houses a processing unit configured to exploit the electrical signal delivered by each microneedle 3 and provide information representative of an analyte concentration, typically a blood glucose level. The device 15 preferably includes a capsule 19 comprising at least one sensor 1 of the aforementioned type, and preferably a plurality of sensors 1. The device 15 may also include a patch 18 to which the capsule 19 is attached, the patch 18 itself being provided with an adhesive enabling the entire patch and capsule 19 assembly to adhere to the skin of an individual.

Claims

Demands

1. Sensor (1) for measuring a body analyte, having a first face (4) intended to be placed against the skin of a util- reader, the sensor comprising: - a network (2) of microneedles (3) adapted to be brought into contact with the user's interstitial fluid by insertion into the dermis of the user, the microneedles (3) being fixedly mounted on the first face (4), each microneedle (3) comprising an active surface (5) me- Talc arranged on the surface of the microneedle (3), - the network (2) comprising at least two microneedles (3), each of the two microneedles (3) comprising a coating (6) covering the less in part the active surface (5) of the microneedle (3), each of the coatings (6) comprising a biomolecule adapted to react with a predetermined analyte, the coating (6) being configured for to allow an electrochemical measurement of the analyte concentration in the interstitial fluid within a predetermined concentration range (17) completed, the range (17) of one of the two microneedles (3) being different from the range (17) of the other of the two microneedles (3).

2. Sensor (1) according to claim 1, comprising a plurality of networks (2) of microneedles (3), the coatings (6) of one of the mi- cross-needles (3) of one of the microneedle arrays (3) comprising a type of biomolecule different from the type of biomolecule of a mi- cross-needle (3) of another network (2).

3. Sensor (1) according to claim 1 or 2, comprising a plurality of microneedle arrays (2), microneedle coating (6) (3) of one of the networks (2) comprising an arrangement of layers (9), each layer (9) comprising a biochemical composition, the re- garment including a different arrangement and / or composition biochemical different from another arrangement and / or another com- biochemical position of another coating (6) of another mi- cross-needle (3) of another network (2).

4. Sensor (1) according to any one of claims 1 to 3, wherein the re- garment (6) of one of the microneedles (3) has a density of the Dbiomolecule different from a density of the biomolecule of another re- garment (6) of the other microneedle (3).

5. Sensor (1) according to any one of claims | to 4, wherein a network (2) comprises at least three microneedles (3), and in which two of the at least three microneedles (3) include coatings (6) configured to allow an electrochemical measurement of a concentration of the same analyte in the interstitial fluid in the same range (17) of predetermined concentration.

6. Sensor (1) according to any one of claims | to 5, comprising a base support (10), and several elementary support plates (11), in which: - several of the microneedles (3) are fixedly mounted on each of the support plates (11), - each support plate (11) is fixedly mounted on the support base (10), And - the coatings (6) of the microneedles (3) fixedly mounted on one of the support plates (11) are configured to allow electro- measurement chemical concentration of the same analyte in the same first range (17), - the coatings (6) of the microneedles (3) fixedly mounted on another support plates (11) are configured to allow measurement electrochemical analysis of a concentration of the same analyte in the same second concentration range, different from the first range (17).

7. Sensor (1) according to any one of claims 2 to 6, comprising a base support (10), and several support plates (11), in which: - several of the microneedles (3) are fixedly mounted on each of the support plates (11), - each support plate (11) is fixedly mounted on the support base (10), And - the coatings (6) of the microneedles (3) fixedly mounted on one of the support plates (11) include the same first type of bio- molecule, - the coatings (6) of the microneedles (3) fixedly mounted on another support plates (11) include the same second type of bio- molecule, different from the first type of biomolecule.

8. Sensor (1) according to claim 6 or 7, wherein one of the mi- croaiguilles (3) is formed monolithically with the plate support (11) by microgravure.

9. Sensor (1) according to any one of claims 6 to 8, wherein each The support plate (11) is fixedly mounted on the support base (10) by a electrically conductive glue (12) so as to allow a electrical connection between the support base (10) and the support plate {11).

10. Sensor (1) according to any one of claims 6 to 9, comprising a plurality of electrodes, each electrode: - comprising the active surface (5) of one of the microneedles (3), - passing through a thickness of the support plate on which the mid- croaiguille (3) is mounted, - comprising an electrically conductive part on and / or in the support base (10).

11. Device (15) for measuring a body analyte, comprising: - a sensor (1) according to any one of claims 1 to 10, - a housing (16) configured to exploit an electrical signal emitted by the sensor (1) representative of the concentration of the analyte(s) in the interstitial fluid.