fig1 includes , in a triaxial reference system x , y , z , a biosensor 1 . the biosensor 1 comprises a first structural layer 2 of photosensitive hydrogel ; a second structural layer 4 , of photosensitive hydrogel , which extends over the first structural layer 2 ; and a sensing region 6 , including a matrix of photosensitive hydrogel dispersed in which are bio - recognition elements , in particular enzymes such as gox ( glucose oxidase ) and lox ( lactate oxidase ). the second structural layer 4 has a through opening 8 in the sensing region 6 such that the sensing region 6 is , at least partially , exposed towards the outer environment through the through opening 8 . a working electrical terminal 10 is arranged in electrical contact with the sensing region 6 . whereas a counter - electrode electrical terminal 12 is arranged on the first layer 2 ( or , in part , in the first layer 2 ), alongside the sensing region 6 , and not in direct electrical contact with the sensing region 6 . a reference electrical terminal 14 extends over the first layer 2 ( or , in part , in the first layer 2 ), alongside the sensing region 6 , and not in direct electrical contact with the sensing region 6 . in particular , the sensing region 6 extends , in top plan view in the plane xy , between the counter - electrode electrical terminal 12 and the reference electrical terminal 14 . the working electrical terminal 10 , the counter - electrode electrical terminal 12 and the reference electrical terminal 14 are made of conductive material , such as , for example , an inert metal chosen from gold , silver , platinum , conductive polymers , and carbon . the reference electrode 14 may likewise be made of silver chloride , agcl . the biosensor 1 provides , in practice , an electrochemical cell with three electrodes . hydrogels , which are typical in the state of the art , are particularly attractive for manufacture of biochemical sensors since they are constituted by polymeric chains of hydrophilic molecules that form an excellent matrix for encapsulating functional enzymes , cells , and other biological material . in particular , the environmental conditions within the hydrogel are ideal for minimizing denaturation of the biological elements dispersed therein , favoring functionality thereof . the photosensitive hydrogel used for forming the first structural layer 2 , the second structural layer 4 , and the sensing region 6 includes hydrophilic polymers that comprise polymeric chains cross - linked with one another with both covalent bonds and non - covalent bonds . their monomers or pre - polymers are soluble in water , whereas the polymers are insoluble in water at physiological temperature , ph , and ionic force . the water content (% h 2 o ) is defined as % h 2 o = 100 . ( swollen - polymer weight / dry - polymer weight )/( swollen - polymer weight ). the polymers may have a molecular weight in the range of 500 - 200000 dalton , and their properties including viscosity , softening point , and degradation temperature are optimized according to the specific application . the first structural layer 2 , the second structural layer 4 , and the sensing region 6 may comprise : monomers , oligomers , or pre - polymers ( the molecular weight of pre - polymers controls the mechanical properties and viscosity ), or binders that regulate the mechanical properties of the mixture ( adhesion , etc . ); one or more solvents that further control the mechanical properties , such as for example the viscosity of the mixture ; and photo - active compounds ( pacs ) or photo - inhibitors ( phis ). according to one embodiment of the present disclosure , the hydrogel of the first structural layer 2 , of the second structural layer 4 , and of the sensing region 6 functions like a negative photoresist used in photolithographic processes , so that controlled ultraviolet ( uv ) irradiation of a portion of the second structural layer 4 and of the sensing region 6 causes polymerization of just the irradiated regions , enabling removal of the non - irradiated regions by development in water . in this case , thus , the hydrogel contains monomers or oligomers or precursor pre - polymers , and by exposure to incident uv radiation , for example , undergoes a reaction of photo - polymerization and / or photo - cross - linking . photo - cross - linking of the layers involved determines an increase of their molecular weight , which causes an advantageous reduction of the solubility of the layers in water . examples of hydrogels made up of simple monomers or mixtures of different monomers , which may be used according to the present disclosure , are : in the rest of the description , reference will be made to peg - da without this implying any loss of generality . fig2 - 11 show , in lateral view in the plane xz , successive steps of manufacture the biosensor 1 of fig1 , according to one aspect of the present disclosure . a substrate 20 is first prepared ( fig2 ), for example of glass , or silicon , or plastic material ( e . g ., polyethylene terephthalate , polyethylene terephthalate ( pet ), polyethylene naphthalate , polyethylene naphthalate ( pen ), polyether ether ketone , polyether ether ketone ( peek )). then ( fig3 ), a first photo - definible hydrogel layer 22 is formed on the substrate 20 , as described in what follows . a pre - polymeric mixture is prepared by adding a peg - da photo - initiator , in a percentage of 2 - 3 % v / v . any photo - initiator , with the capacity of absorbing uv radiation and undergoing photoreaction , producing reactive species , radicals that polymerize , and constituents of the pre - polymeric mixture is suited for the purpose . in particular , 2 - hydroxy - 2 - methyl - 1 - phenylpropan - 1 - one , also commercially known as darocur ™ is used as photo - initiator . the pre - polymeric solution thus formed is deposited , using the spin - coating technique , on the substrate 20 ( at 700 - 1000 rpm , for 8 - 15 s , in particular 800 rpm for 10 s ). the first photo - definible hydrogel layer 22 has a thickness comprised between 100 nm and 1000 nm , for example 200 nm . the deposition parameters may be adjusted according to the viscosity of the hydrogel - based solution used for obtaining a layer 22 having the desired thickness . the next step ( fig4 ) is the arrangement of ( commercially available ) conductive filaments that form the working electrical terminal 10 , the counter - electrode electrical terminal 12 , and the reference electrical terminal 14 . the aforesaid filaments have , for example , a diameter between 50 nm and 200 nm and are made of a material chosen from gold , silver , platinum , conductive polymers , and carbon . the filaments are arranged on the layer 22 prior to the cross - linking step . the filaments penetrate only partially into the layer 22 . in this way , they ( and in particular the working electrical terminal 10 ) are electrically accessible from above . then ( fig5 ), a cross - linking step is carried out , using a uv lamp 23 that generates uv radiation 25 , on selective portions of the first photo - definible hydrogel layer 22 . in particular , in order to obtain selective polymerization of the first photo - definible hydrogel layer 22 , a mask 24 is used provided with opaque regions 24 a , which are designed to block the incident uv radiation 25 , and transparent regions 24 b , which are transparent to the incident uv radiation 25 . in this way , only the portions of the first photo - definible hydrogel layer 22 that extend in the transparent regions 24 b undergo a process of cross - linking since the hydrogel behaves like a negative photoresist . according to one aspect of the present disclosure , the filaments , which form the working electrical terminal 10 , the counter - electrode electrical terminal 12 , and the reference electrical terminal 14 , extend partially inside the regions of the first photo - definible hydrogel layer 22 that are polymerized and partially outside so that , as illustrated in fig6 , after the polymerization step , the filaments will be electrically accessible from outside the first structural layer 2 formed . the polymerization step is carried out using the following exposure parameters : wavelength of uv radiation chosen according to the photo - initiator used , for example ( in the case of use of darocur ™), 365 nm ; exposure power comprised in the range between 12 mw / cm 2 and 20 mw / cm 2 , in particular 18 mw / cm 2 ; exposure time comprised between 5 s and 20 s , in particular 7 s . a subsequent step of bathing in deionized water enables removal in a few minutes of the portions of the first non - polymerized photo - definible hydrogel layer 22 , to form the first structural layer 2 , as illustrated in fig6 . then ( fig7 ), a second photo - definible hydrogel layer 26 ( provided with bio - recognition elements , for example enzymes ) is formed on the substrate 20 and the first structural layer 2 . the second photo - definible hydrogel layer 26 forms the sensing region 6 in subsequent manufacturing steps . in detail , the second photo - definible hydrogel layer 26 is formed starting from a pre - polymeric solution of hydrogel ( e . g ., peg - da ), a photo - initiator ( e . g ., darocur ™) at 3 % v / v , and an reduction - oxidation ( redox ) mediator at 1 % v / v . the redox mediator is a molecule able to mediate a reduction - oxidation reaction or , in other words , able to facilitate the flow of electrons , generated by the reduction - oxidation reaction , through the hydrogel matrix . the redox mediator is , for example , a derivative of ferrocene , such as vinylferrocene . an enzymatic solution is prepared by dissolving appropriate enzymes in a phosphate buffer ( pbs ), with ph ranging between 6 and 6 . 5 , and glutaraldehyde as agent for improving retention of the enzyme in the matrix . the enzymes are chosen , according to one embodiment , from between glucose oxidase ( gox ) and lactate oxidase ( lox ). the concentration of the enzymes in pbs is , for example , 20 mg / ml . the pre - polymeric solution and the enzymatic solution thus prepared are mixed together for a time comprised between 4 h and 5 h at a temperature comprised between 4 ° c . and 5 ° c . ( e . g ., 4 ° c .). the ratio between the pre - polymeric solution and the enzymatic solution is 10 : 1 v / v but may be varied according to the need . the mixture thus obtained ( known as “ sensing matrix ”) forms the second photo - definible hydrogel layer 26 , which is deposited on the substrate 20 and on the first structural layer 2 using the spin - coating technique , in a way similar to what has already been described with reference to the first photo - definible hydrogel layer 22 . the second photo - definible hydrogel layer 26 has a thickness comprised between 100 nm and 1000 nm , for example 200 nm . also in this case , the deposition parameters may be adjusted according to the viscosity of the solution used for the second photo - definible hydrogel layer 26 for obtaining a layer 26 ( and thus the sensing region 6 ) having the desired thickness . then ( fig8 ), a step of exposure to uv radiation is carried out to favor cross - linking of selective portions of the second photo - definible hydrogel layer 26 , using an appropriate mask 28 . exposure is obtained , for example , using the same uv lamp 23 used previously , which generates uv radiation 25 . in order to obtain selective polymerization of the second photo - definible hydrogel layer 26 , the mask 28 is used provided with opaque regions 28 a , which are designed to block the incident uv radiation 25 , and transparent regions 28 b , which are transparent to the incident uv radiation 25 . in this way , only the portions of the second photo - definible hydrogel layer 26 that extend in the transparent regions 28 b are subjected to a cross - linking process . according to one aspect of the present disclosure , the metal filament that forms the working electrical terminal 10 extends partially inside the regions of the second photo - definible hydrogel layer 26 , which is polymerized , and partially outside so that , after the polymerization step , the filament will be electrically accessible from outside the sensing region 6 thus formed . the polymerization step is carried out using the following exposure parameters : wavelength of the uv radiation chosen according to the photo - initiator used , for example , ( in the case of use of darocur ™) 365 nm ; exposure power comprised in the range between 12 mw / cm 2 and 20 mw / cm 2 , in particular 18 mw / cm 2 ; exposure time comprised between 5 s and 20s , in particular 7 s . next ( fig9 ), a step of bathing in deionized water is carried out , which enables removal in a few minutes of the portions of the second photo - definible hydrogel layer 26 that has not been polymerized , to form the sensing region 6 in an area corresponding to the working electrode 10 and in electrical contact therewith . next ( fig1 ), the second structural layer 4 is formed . for this purpose , a third photo - definible hydrogel layer 34 is formed on the substrate 20 , on the first structural layer 2 , and on the sensing region 6 . for this purpose , a pre - polymeric mixture is prepared by adding to polyethylene glycol diacrylate ( in what follows , peg - da ) a photo - initiator , in a percentage of 2 - 3 % v / v , as described with reference to the first photo - definible hydrogel layer 22 . in particular , 2 - hydroxy - 2 - methyl - 1 - phenylpropan - 1 - one , also known commercially as darocur ™, is used as photo - initiator . the pre - polymeric solution thus formed is deposited , using the spin - coating technique , on the substrate 20 , on the first structural layer 2 , and on the sensing region 6 . spin - coating is carried out between 700 rpm and 1000 rpm , for 8 - 15 s , in particular 800 rpm for 10 s . the third photo - definible hydrogel layer 34 thus formed has a thickness comprised between 100 nm and 1000 nm , for example 200 nm . the deposition parameters may be adjusted according to the viscosity of the hydrogel - based solution used for obtaining a layer 34 having the desired thickness . once again with reference to fig1 , a step of exposure to uv radiation is carried out to favor cross - linking of selective portions of the third photo - definible hydrogel layer 34 , using an appropriate mask 36 . exposure is obtained , for example , using the same uv lamp 23 used previously , which generates uv radiation 25 . in order to obtain selective polymerization of the third photo - definible hydrogel layer 34 , the mask 36 is provided with opaque regions 36 a , designed to block the incident uv radiation 25 , and transparent regions 36 b , transparent to the incident uv radiation 25 . in this way , only the portions of the third photo - definible hydrogel layer 34 that extend in the transparent regions 36 b are subjected to a cross - linking process . the step of polymerization of the third photo - definible hydrogel layer 34 is carried out using the following exposure parameters : wavelength of uv radiation chosen according to the photo - initiator used , for example , ( in the case of use of darocur ™) 365 nm ; exposure power comprised in the range between 12 mw / cm 2 and 20 mw / cm 2 , in particular 18mw / cm 2 ; exposure time comprised between 5 s and 20 s , in particular 7 s . a subsequent step of development in deionized water enables removal of the portions of the third non - polymerized photo - definible hydrogel layer 34 , to form the second structural layer 4 , as illustrated in fig1 . according to the present disclosure , the mask 36 is provided with an opaque region that covers , in use ( i . e ., when the mask 36 is arranged aligned to the third photo - definible hydrogel layer 34 ), the portion of the third photo - definible hydrogel layer 34 that extends over the sensing region 6 . in this way , the portion of the third photo - definible hydrogel layer 34 on the sensing region 6 does not undergo the cross - linking process and is removed during the step of development in deionized water . the through opening 8 is thus formed , through which the sensing region 6 is exposed , at least in part . the biosensor 1 of fig1 is thus formed . finally , by a peeling step , the substrate 20 is removed to obtain the biosensor 1 of fig1 . the step of peeling of the substrate 20 is optional . fig1 - 19 show steps for manufacturing a biosensor 1 ′ according to a further embodiment . with reference to fig1 , a substrate 40 is first prepared , for example , glass , or silicon , or plastic material ( e . g ., pet , pen , peek ). then , a first photo - definible hydrogel layer 42 is formed on the substrate 40 in a way similar to what has been described with reference to the layer 22 of fig3 , and not described any further herein . next ( fig1 ), a cross - linking step is carried out , using a uv lamp 23 which generates uv radiation 25 , on selective portions of the first photo - definible hydrogel layer 42 . in particular , in order to obtain selective polymerization of the first photo - definible hydrogel layer 42 , a mask 44 is used provided with opaque regions 44 a , which are designed to block the incident uv radiation 25 , and transparent regions 44 b , which are transparent to the incident uv radiation 25 . in this way , only the portions of the first photo - definible hydrogel layer 42 that extend in the transparent regions 44 b , undergo a cross - linking process . in particular , the first photo - definible hydrogel layer 42 is not irradiated in a region thereof that extends over a portion 40 ′ of the substrate 40 that , in subsequent manufacturing steps , will house the working electrical terminal 10 ′, the counter - electrode electrical terminal 12 ′, and the reference electrical terminal 14 ′. the portion 40 ′ of the substrate 40 may be chosen freely according to the geometrical shape that it is desired to bestow on the first structural layer 2 ( after the polymerization step ); for example , the portion 40 ′ of the substrate 40 extends along the periphery of the substrate 40 . next ( fig1 ), a bath in deionized water is carried out , which enables removal in a few minutes of the portions of the first non - polymerized photo - definible hydrogel layer 42 to form a first structural layer 2 ′. this is followed ( fig1 a ) by a step of deposition , by sputtering , of metal material , such as for example gold deposition by sputtering is assisted by a mask ( not illustrated ) designed to enable deposition of the metal material in specific regions of the substrate 40 and of the first structural layer 2 ′. metal strips are thus formed that extend from the surface of the first structural layer 2 ′ towards the portion 40 ′ of the substrate 40 . fig1 b shows , in top plan view in the plane xy , the substrate 40 provided with the first structural layer 2 ′ and with the working electrical terminal 10 ′, the counter - electrode electrical terminal 12 ′, and the reference electrical terminal 14 ′ thus formed . they may be made also of metals such as silver , platinum , or of conductive polymers , or carbon . then ( fig1 ), a sensing region 6 ′ is obtained , similar to the sensing region 6 of the biosensor 1 . for this purpose , a second photo - definible hydrogel layer 46 is formed ( provided with bio - recognition elements , e . g . enzymes ) on the substrate 40 , the first structural layer 2 ′, and the working electrical terminal 10 ′, of the counter - electrode electrical terminal 12 ′, and the reference electrical terminal 14 ′. the second photo - definible hydrogel layer 46 forms , in subsequent manufacturing steps , the sensing region 6 ′. the second photo - definible hydrogel layer 46 is formed as described previously with reference to the second photo - definible hydrogel layer 26 , starting from a pre - polymeric solution of hydrogel ( e . g ., peg - da ), a photo - initiator ( e . g ., 2 - hydroxy - 2 - methyl - 1 - phenylpropan - 1 - one ) at 3 % v / v , and a redox mediator ( e . g ., a derivative of ferrocene , such as vinylferrocene ) at 1 % v / v . an enzymatic solution is prepared by dissolving appropriate enzymes in a pbs phosphate buffer with ph levels ranging between 6 and 6 . 5 and glutaraldehyde as agent for improving retention of the enzyme in the matrix . the enzymes are chosen , according to one embodiment , between glucose oxidase ( gox ) and lactate oxidase ( lox ). the concentration of the enzymes in pbs is , for example , 20 mg / ml . the pre - polymeric solution and the enzymatic solution thus prepared are mixed together for a time comprised between 4 h and 5 h at a temperature comprised between 4 ° c . and 5 ° c . ( e . g ., 4 ° c .). the ratio between the pre - polymeric solution and the enzymatic solution is 10 : 1 v / v , but may be varied according to the need . the mixture thus obtained ( known as “ sensing matrix ”) is deposited using the spin - coating technique and forms the second photo - definible hydrogel layer 46 , in a way similar to what has already been described with reference to the second photo - definible hydrogel layer 26 . the second photo - definible hydrogel layer 46 has a thickness comprised between 100 nm and 1000 nm , for example 200 nm . also in this case , the deposition parameters may be adjusted according to the viscosity of the solution used for the second photo - definible hydrogel layer 46 for obtaining a layer 46 ( and thus the sensing region 6 ′) having the desired thickness . next ( fig1 , a step of exposure to uv radiation is carried out to favor cross - linking of selective portions of the second photo - definible hydrogel layer 46 , using an appropriate mask ( not illustrated ). exposure is obtained , for example , used the same uv lamp 23 previously used , which generates uv radiation 25 . in order to obtain selective polymerization of the second photo - definible hydrogel layer 46 , a mask is used provided with opaque regions , designed to block the incident uv radiation 25 , and regions transparent to the incident uv radiation 25 . in this way , only the portions of the second photo - definible hydrogel layer 46 aligned , along z , to the transparent regions are subjected to a cross - linking process since the hydrogel behaves like a negative photoresist . the polymerization step is carried out using the exposure parameters already previously indicated for polymerization of the second photo - definible hydrogel layer 26 . a subsequent step of bathing in deionized water enables removal in a few minutes of the portions of the second photo - definible hydrogel layer 46 that has not been polymerized , to form the sensing region 6 ′, as illustrated in fig1 . after the step of removal of the hydrogel that has not been polymerized , only the metal path that forms the working electrical terminal 10 ′ extends in direct contact with the sensing region 6 ′. the metal paths that form the counter - electrode electrical terminal 12 ′ and reference electrical terminal 14 ′ are not in direct contact with the sensing region 6 ′, but extend alongside it . next ( fig1 ), a second structural layer 4 ′ is formed , similar to the second structural layer 4 of the biosensor 1 . the steps for producing the second structural layer 4 ′ are similar to those described previously for the second structural layer 4 ( see the description of fig1 and 11 ) and are not referred to any further herein . in particular , the process for producing the second structural layer 4 ′ evisions formation of a through opening 8 ′ in the sensing region 6 ′. the sensing region 6 ′ is exposed , at least in part , through the through opening 8 ′. fig1 shows , in perspective view , the biosensor 1 ′ produced according to the steps of fig1 - 18 . as may be noted from fig1 , in this embodiment the substrate 40 is not removed , in so far as it functions as support for the working electrical terminal 10 ′, the counter - electrode electrical terminal 12 ′, and the reference electrical terminal 14 ′. to favor adherence of the substrate 40 to the first structural layer 2 ′, it is possible to insert an adhesive layer , for example an organosilane - based adhesive layer , between the substrate 40 and the first structural layer 2 ′, prior to the step of deposition of the first hydrogel layer 42 of fig1 . functionalization of the substrate 40 with silane molecules is obtained according to a procedure , for example described in u . s . pat . no . 9 , 244 , 067 to di matteo et al . in particular , the substrate is treated by an oxygen - plasma treatment ( a common plasma - etching system is used for this purpose ). a silane solution ( 2 % v / v ) is likewise prepared with 3 -( trimethoxysilyl ) propyl methacrylate in isopropyl alcohol , correcting the ph with acetic acid , to bring it to a value of 4 . 5 - 5 . the solution then undergoes gentle stirring , and then it is necessary to wait a few minutes ( i . e ., at least 30 minutes ) before using it . this enables hydrolysis of the siloxane groups . the substrate 40 is then dipped in the silane solution , washed in isopropyl alcohol and then heated to 120 ° c . for 60 minutes . the substrate 40 is thus functionalized with silane molecules that expose methacrylic groups , to which the hydrogel 42 will subsequently bind during its polymerization , to form the state 2 ′. the silanes are chosen according to the type of hydrogel that is deposited on the substrate . in the case of peg - da - based hydrogel , the silanes may be chosen in the family of acrylate or methacrylate silanes , cyclic azosilanes , silanes with amine terminations , dipodal silanes , and carboxylate silanes . the biosensor 1 , 1 ′ may be used by laying it directly on the skin of the patient to be monitored , so that the sensing region 6 , 6 ′ faces the skin through the through opening 8 , 8 ′. the through opening 8 , 8 ′ formed through the second structural hydrogel layer 4 , 4 ′ provides , in use , a closed chamber that does not prevent natural transpiration of the skin , but considerably limits exchange of air with the external environment , causing a rapid increase of the local temperature of the skin up to values of approximately 35 - 40 ° c . the vapor that is generated within the through opening 8 , 8 ′ saturates the environment and favors formation of sweat , which , coming into contact with the sensing region 6 , 6 ′, enables the biological analysis to be carried out . from the sweat produced glucose or lactate may in fact be monitored , thanks to the enzymes gox or lox present in the sensing matrix . monitoring the current present between the working electrical terminal 10 , 10 ′ and the counter - electrode electrical terminal 12 , 12 ′ enables information to be obtained , in typical manner , on the analyte concentration monitored . the present applicant has found that the hydrogel matrix used according to the present disclosure to create the sensing region 6 , 6 ′ provides a linear response in the range of concentrations of 10 μm to 4 mm for glucose , and 1 μm to 4 mm for lactate , i . e ., in ranges compatible with the concentrations typically present in human sweat . in use , the biosensor 1 functions as amperometric sensor . as is known , an amperometric sensor is based upon the measurement of the current between the working electrical terminal 10 and the counter - electrode electrical terminal 12 , a current that is induced by the redox reaction between the analyte and the enzyme that is obtained on the working electrical terminal 10 . the current is proportional to the concentration of the analyte to be monitored . for this purpose , a constant potential ( determined by the redox potential of the mediator , previously evaluated via cyclic voltammetric measurements ) is applied to the electrochemical cell , and the response of the current is monitored . this potential enables operation in optimal conditions for monitoring of the current . in particular , the working electrode 10 is fixed at a potential , for example of 0 . 25 v , with respect to the reference electrical terminal 14 . the value of 0 . 25 v is the peak anode potential , measured by the present applicant , of the mediator in vinylferrocene immobilized in the hydrogel matrix . the counter - electrode terminal is an auxiliary electrode and functions as drain of the current generated during the redox reaction on the working electrical terminal 10 ( the counter - electrode 12 “ collects ” the electrons generated by the enzyme - analyte reaction ). the three - electrode configuration may provide the presence of a stable potential between the working electrical terminal 10 and the reference electrical terminal 14 . however , other configurations , in particular a configuration with two electrodes ( in which the reference electrode coincides with the counter - electrode ) may likewise be used according to a further aspect of the present disclosure . a potentiostat ( not illustrated in the figures ) may be operatively coupled to the working electrical terminal 10 , to the counter - electrode electrical terminal 12 , and to the reference electrical terminal 14 , and is configured to control the voltage through the working terminal / counter - electrode terminal pair and to adjust it to maintain the difference of potential imposed between the working terminal 10 and the reference terminal 14 . the reference electrical terminal measures and controls the potential of the working electrical terminal 10 , while the counter - electrode electrical terminal 12 allows passage of all the other for balancing the current that is still observed on the working electrical terminal 10 . with this arrangement , the current generated by the redox reaction is made to pass between the working terminal 10 and the counter - electrode terminal 12 . this current , which may be measured , indicates a concentration of electroactive species present in the analyte . the biosensor 1 ′ functions in a way similar to the biosensor 1 , according to what has been described above . the advantages that may be obtained with the invention described are evident from the foregoing description . in particular , the first structural layer 2 and the second structural layer 4 operate as a capsule that supports , protects , and contains the sensing region 6 and , at the same time , function as insulating layer between the electrodes . thus , further supporting and containment layers are not necessary , rendering the biosensor 1 simple and inexpensive to produce . the manufacturing process evisions use of devices and technologies widely employed in the field of microfabrication of micro - electromechanical devices , and in particular the shape of the layers 2 , 2 ′, 4 , 4 ′ is defined through simple photolithographic steps . the biosensor 1 , 1 ′ may thus be integrated within more complex electronic devices or mems , exploiting the same manufacturing technology . use of the hydrogel enables a biosensor to be obtained that does not cause discomfort during use ( being of flexible material ) and that has the appearance , for example , of a small plaster . it is thus simple to use , self - contained , and aesthetically discreet . the biosensor in question further works at low potentials . it may further be integrated in a discreet way in medical devices or in other wearable devices , such as a bracelet . since the analysis is conducted on the basis of the patient &# 39 ; s sweat , use of the biosensor 1 , 1 ′ does not cause any pain . finally , it is clear that numerous modifications and variations may be made to what has been described and illustrated herein , all of which fall within the scope of the inventive idea , as defined in the annexed claims . for example , the electrical terminals 10 , 10 ′, 12 , 12 ′, 14 , 14 ′ may be obtained using other technologies , for example by ink - jet deposition . furthermore , the bio - recognition elements trapped in the bioactive region 6 may be different from the enzymes gox and lox ; for example , they may be chosen from enzymes of another type , or else from : antibodies , nucleic acids , and cell receptors .
a biosensor is for sensing analytes in a fluid . the biosensor may include a first structural layer having a first hydrogel , a second structural layer having a second hydrogel , and a bioactive region extending between the first structural layer and the second structural layer and having a third hydrogel . the biosensor may include a first electrode coupled to the bioactive region , and a second electrode coupled to the first structural layer and being spaced apart from the bioactive region . the second structural layer may have a through opening adjacent the bioactive region , and the bioactive region may be configured to be in fluid communication with an environment external to the biosensor for receiving the fluid comprising the analytes .