METHOD FOR FUNCTIONALISING A CELLULOSE SUPPORT WITH METAL NANOPARTICLES AND ELECTROANALYTICAL SENSOR COMPRISING THE FUNCTIONALISED CELLULOSE SUPPORT

Abstract

The present invention relates to a method for functionalising a cellulose support with metal nanoparticles comprising the steps of: depositing on the cellulose support a single aqueous solution containing the metal precursor in the form of acid or salt in a concentration from 1 to 6 mM; and placing the cellulose support at a temperature from 65° C. to 80° C. for a time from 10 to 40 minutes. The present invention also relates to a method for producing an electroanalytical sensor comprising said functionalised cellulose support with electrocatalytic and concentration properties of the metal marker at the working electrode and to a method for producing the electroanalytical sensor.

Claims

1. A method for functionalising a cellulose support with metal nanoparticles comprising the steps of: depositing on a cellulose support a single aqueous solution of the metal precursor, in the form of acid or salt, in a concentration from 1 to 6 mM; and drying the cellulose support at a temperature from 65° C. to 80° C. for a time from 10 to 40 minutes.

2. A cellulose support functionalised with metal nanoparticles formed in situ, wherein the metal nanoparticles are made of gold.

3. A cellulose support functionalised with metal nanoparticles formed in situ obtained by the method according to claim 1 and with electrocatalytic and analyte concentration properties.

4. Use of the cellulose support according to claim 2 in the production of immunoenzymatic electroanalytical sensors or electroanalytical sensors for the detection of at least one metal selected from the group consisting of Cu, Fe, Zn, Pb, As, Cd and Hg in a biological fluid.

5. A method for producing an immunoenzymatic electroanalytical sensor or an electroanalytical sensor for the detection of at least a metal selected from the group consisting of Cu, Fe, Zn, Pb, As, Cd and Hg in a biological fluid comprising the steps of: providing a cellulose support; delimiting on the cellulose support a hydrophilic working area by depositing a hydrophobic material; depositing on the hydrophilic working area of the cellulose support, a single aqueous solution of the metal precursor, in the form of acid or salt, in a concentration from 1 to 6 mM; drying the cellulose support at a temperature from 65° C. to 80° C. for a time from 10 to 40 minutes so that metal nanoparticles are formed on the cellulose support; printing, on the hydrophilic working area of the cellulose support with metal nanoparticles, at least one working electrode, one reference electrode and a counter-electrode by screen-printing by depositing conductive inks in a sequence.

6. The method according to claim 5, wherein the aqueous solution is a HAuCl.sub.4 solution.

7. An immunoenzymatic electroanalytical sensor for detecting at least a metal selected from the group consisting of Cu, Fe, Zn, Pb, As, Cd and Hg in a biological fluid, comprising a cellulose support functionalised by metal nanoparticles formed in situ, on which a hydrophobic area delimits a hydrophilic working area, said hydrophilic working area comprising at least one working electrode, one reference electrode and one counter-electrode printed by screen-printing.

8. The sensor according to claim 7, wherein the metal nanoparticles are made of gold, the working electrode is made of gold, the reference electrode is made of silver/silver chloride and the counter-electrode is made of graphite.

9. The sensor according to claim 7, wherein the cellulose support is filter paper, the metal nanoparticles are made of gold, the marker is copper, the working electrode is made of gold, the reference electrode is made of silver/silver chloride and the counter-electrode is made of graphite.

10. A method for detecting at least at least a metal selected from the group consisting of Cu, Fe, Zn, Pb, As, Cd and Hg or a marker detectable by means of an immunoenzymatic sensor in a biological fluid comprising the steps of: providing a sensor according to claim 7; adding on said sensor an amount of biological fluid from 1 to 80 μl, wherein the biological fluid may be subjected to a concentration or dilution pre-treatment; applying a potential difference between the electrodes of the sensor; and detecting a current signal by means of a potentiostat, the signal being proportional to the amount of the at least one metal or marker in the biological fluid.

Description

BRIEF DESCRIPTION OF THE FIGURES

[0016] FIG. 1 represents a schematic view of a sensor according to the invention with reference to a preferred embodiment.

[0017] FIG. 2 represents the steps of the method according to the invention with reference to the production and use of the sensor according to the preferred embodiment of FIG. 1.

[0018] FIG. 3 shows graphs and images of the sensors relative to the concentration and volume optimisation experiments of the HAuCl.sub.4 solution used to functionalise a sensor according to the preferred embodiment of FIG. 1.

[0019] FIG. 4 shows graphs relative to the comparison of electrochemical performances of a sensor with paper functionalised with AuNP according to the preferred embodiment of FIG. 1 and a similar sensor with non-functionalised paper.

[0020] FIG. 5 shows graphs of the optimisation of the deposition potential, the deposition time, the scan rate and the conditioning potential for the sensor according to the preferred embodiment of FIG. 1.

[0021] FIG. 6 shows a graph comparing the performances of a sensor with AuNP-functionalised paper versus a non-functionalised sensor using samples containing increasing concentrations of copper ions. The relative calibration curve is shown in the box.

[0022] FIG. 7 shows the graph relative to a test of the sensor according to the preferred embodiment of FIG. 1 using two different concentrations of copper ions (200 ppb and 300 ppb).

[0023] FIG. 8 shows a graph showing the performances of a sensor according to the preferred embodiment of FIG. 1 in which the AuNPs have been functionalised in situ compared to an analogous sensor in which the AuNPs are pre-constituted and deposited on paper.

[0024] FIG. 9 shows graphs showing the different accuracy in the determination of H.sub.2O.sub.2 (hydrogen peroxide), a classic product of multiple enzymatic reactions, detectable by an immunoenzymatic sensor, using reduction potentials from −0.3V to −0.5V in case of functionalisation of paper with metal nanoparticles compared with non-functionalised paper support.

[0025] FIG. 10 shows scanning electron microscopy (SEM) images showing how the metal nanoparticles formed in situ are distributed. FIGS. 10A and 10B are relative to functionalised paper while FIG. 10C is relative to non-functionalised paper.

[0026] FIG. 11 shows a graph with the distribution of the dimensions of the metal nanoparticles formed in situ detected by dynamic light scattering (DLS) analysis.

[0027] FIG. 12 shows a graph comparing the performances of an immunoenzymatic sensor on paper functionalised (decorated) with AuNP and an immunoenzymatic sensor on non-functionalised paper.

DETAILED DESCRIPTION OF THE INVENTION

[0028] The method for functionalising a cellulose support with metal nanoparticles according to the present invention comprises the steps of: depositing on the cellulose support a single aqueous solution of the metal precursor, in the form of acid or salt, in a concentration from 1 to 6 mM; and placing the cellulose support at a temperature from 65° C. to 80° C. for a time from 10 to 40 minutes.

[0029] For the functionalisation of the metal nanoparticles, it is not necessary to add a reducing compound. Instead, the solution consists only in the metal precursor.

[0030] Preferably the aqueous solution of the metal precursor is a solution of tetrachloroauric acid (HAuCl.sub.4), preferably at a concentration of about 2.5 mM. Alternatively, use can be made of solutions of silver salts, preferably silver nitrate (AgNO.sub.3) and silver acetate (AgCH.sub.3COO); bismuth salts, preferably bismuth nitrate (Bi(NO.sub.3).sub.3); cobalt salts, preferably cobalt acetate (Co(CH.sub.3COO).sub.2) and cobalt sulphate (CoSO.sub.4); selenious acid (H.sub.2SO.sub.3); copper salts, preferably copper sulphate (CuSO.sub.4) and copper acetate (Cu(CH.sub.3COO).sub.2; hexachloroplatinic acid (H.sub.2PtCl.sub.6) and platinum salts, preferably potassium tetrachloroplatinate (K.sub.2PtCl.sub.4); palladium salts, preferably palladium dichloride (PdCl.sub.2) and sodium tetrachloropalladate (Na.sub.2PdCl.sub.4); nickel salts, preferably nickel chloride (NiCl.sub.2) and nickel nitrate (Ni(NO.sub.3).sub.2), to obtain respectively silver, bismuth, cobalt, selenium, copper, platinum, palladium and nickel nanoparticles.

[0031] It is possible to consider the use of particular precautions, such as a controlled atmosphere to avoid oxidation of the nanoparticles.

[0032] The cellulose support is preferably paper, more preferably filter paper.

[0033] The deposit surface is lower than 0.6 cm.sup.2. Preferably the deposit surface is from 0.2 cm.sup.2 to 0.6 cm.sup.2.

[0034] The cellulose support is preferably placed at a temperature of about 70° C. for about 30 minutes.

[0035] In virtue of to the aforesaid method, a cellulose support functionalised with metal nanoparticles is obtained. The particular treatment and the precursor solution according to the aforesaid method allow to obtain particular structural characteristics of the nanoparticles inserted in the cellulose structure, which give the functionalised support either an electrocatalytic function or a concentration function of the analytes.

[0036] As shown below in Example 11 (FIG. 10), the metal nanoparticles form aggregates on the cellulose support, defined as hot spots, which are very different from the aggregates formed by nanoparticles previously formed and then deposited on the support at a later time as well as also with respect to the aggregates formed by nanoparticles formed using a solution of metal precursor and subsequently a solution with a reducing compound. As further shown in Example 12 (FIG. 11), the metal nanoparticles have average dimensions equal to 196.2±20.7 nm with a polydispersity index equal to 0.13.

[0037] The larger dimensions of the nanoparticles obtained according to the invention allow a better conduction when used on an electrochemical sensor. The result is an increased sensitivity of the sensor, which can then be used for the detection of metals in biological liquids such as serum.

[0038] The functionalised cellulose support as described above can in fact be used in the production of single electroanalytical sensors or inserted in multiple sensor platforms for the detection of one or more markers (analytes) in a biological fluid.

[0039] The method for producing an electroanalytical sensor for detecting a marker in a biological fluid according to the present invention comprises the following steps.

[0040] A cellulose support is provided. Preferably, said support is formed of paper, preferably filter or office paper, more preferably filter paper, in particular filter paper with a weight in the range between 60-85 g/m.sup.2, more preferably 67 g/m.sup.2, Cordenons, Italy, or whatman cellulose filter paper can be used.

[0041] A hydrophilic working area is then delimited on the cellulose support, which is naturally hydrophilic, by depositing a hydrophobic material. The hydrophobic material can be wax and be printed on the substrate.

[0042] The hydrophilic working area thus delimited is the deposit area of the metal precursor; preferably it is lower than 0.6 cm.sup.2, more preferably it corresponds to a range from 0.2 cm.sup.2 to 0.6 cm.sup.2. A single aqueous solution of the metal precursor is then deposited on the hydrophilic working area of the cellulose support, in the form of acid or salt of a metal in a concentration from 1 to 6 mM. As already described above, the solution, containing only the precursor of the metal is preferably a solution of tetrachloroauric acid (HAuCl.sub.4) and the concentration of the acidic aqueous solution of the metal is preferably of about 2.5 mM.

[0043] The cellulose support is then placed at a temperature from 65° C. to 80° C., preferably 70° C., for a time from 10 to 40 minutes, preferably about 30 minutes, so that metal nanoparticles are formed on the cellulose support.

[0044] On the hydrophilic working area of the cellulose support, at least one working electrode, one reference electrode and one counter-electrode are then printed by screen-printing, by depositing conductive inks in succession.

[0045] Preferably, a gold-based ink is used for the working electrode, a silver/silver chloride-based ink is used for the reference electrode, and a graphite-based ink is used for the counter-electrode. It is possible to coat the working electrode with materials with a filter or barrier function, to reduce the risk of biofouling and further improve the performance of the sensor. With reference to FIG. 1, the working electrode is preferably printed in a central position with respect to the reference electrode and the counter-electrode. The working electrode can have an area of about 7 mm.sup.2.

[0046] The electroanalytical sensor for the detection of a marker in a biological fluid according to the invention therefore comprises a cellulose support functionalised with metal nanoparticles formed in situ, on which a hydrophobic area delimits a hydrophilic working area, said hydrophilic working area comprising at least one working electrode, one reference electrode and one counter-electrode printed by screen-printing.

[0047] The in situ synthesised nanoparticles are metallic. The metal is preferably Au, Ag, Bi, Co, Se, Cu, Pt, Pd, Ni. More preferably, the metal nanoparticles are made of Au.

[0048] The deposit surface is lower than 0.6 cm.sup.2. Preferably the deposit surface is from 0.2 cm.sup.2 to 0.6 cm.sup.2.

[0049] The biological fluid is preferably blood, serum, urine or sweat or saliva or tear fluid or synovial fluid, more preferably blood.

[0050] The marker is preferably a metal selected from the group consisting of Cu, Fe, Zn, Pb, Hg, Cd, and As. More preferably the metal is Cu.

[0051] In a preferred embodiment, the working electrode is gold, the reference electrode is silver/silver chloride and the counter-electrode is graphite.

[0052] In a preferred embodiment, the sensor is immunoenzymatic and exploits the antigen-antibody interaction to bind the molecule of interest and then an enzymatic reaction to produce the signal to be measured. In particular, the sensor can detect serum proteins, transferrin, ferritin, haemoglobin, vitamins, antibodies, cytokines. The marker in case of immunoenzymatic sensor is preferably H.sub.2O.sub.2, ascorbic acid, nitrophenol, hydroquinone.

[0053] The method for detecting at least one marker in a biological fluid according to the present invention comprises the steps of providing a sensor as previously described; adding to said sensor a quantity of biological fluid from 1 to 80 μl, preferably from 20 to 40 μl, more preferably 30 μl, where said biological fluid has optionally undergone a pre-treatment by dilution or concentration; preferably the deposit of the solution takes place on a single side of the paper support, therefore either on the front side (the side on which the electrodes are printed) or on the rear side; more preferably it takes place on the front side; applying a potential difference between the sensor electrodes, in one or more passages, concentrating the marker at the working electrode; and detecting a current signal by means of a potentiostat which is proportional to the amount of marker in the biological fluid.

[0054] Preferably, a time-varying potential is applied which allows the oxidation of the analyte and a consequent current signal. More preferably, a potential fixed over time (DEPOSITION POTENTIAL) is applied at a determined value to reduce and concentrate the analyte on the working electrode and then a second time-varying potential is applied to allow the oxidation of the analyte and a consequent current signal.

[0055] In particular, the potentiostat detects a current which is proportional to the concentration of the marker in the biological fluid.

[0056] The electroanalytical sensor on a functionalised cellulose support described above can be used in a microfluidic platform coupled to other sensors printed on cellulose or other materials.

Example 1—Production of a Sensor for the Detection of Copper

[0057] With reference to FIG. 2, a hydrophobic wax pattern was printed on a sheet of filter paper (67 g/m.sup.2, Cordenons, Italy) by means of a solid ink printer (Xerox ColorQube 8580), necessary to delimit the area on which the gold nanoparticles will be synthesised and the electrodes printed. In order to create the hydrophobic barrier, the filter paper is placed in a stove at 100° C. for 2 minutes to allow the wax to melt in the paper.

[0058] 4 μL of a HAuCl.sub.4 solution at a concentration of 2.5 mM, prepared in ultrapure distilled water, by placing the support at 70° C. for 30 min, in order to synthesise the nanoparticles, were deposited on the area delimited by the hydrophobic barrier.

[0059] Subsequently, on this functionalised surface, the electrodes were printed by successive depositions of conductive inks, using the screen-printing technique. For this purpose, a gold-based ink (BQ331, DuPont, France) was used for the working electrode, a silver/silver chloride-based ink (Electrodag 477 SS, Acheson, Italy) for the reference and a graphite-based ink (Electrodag 421, Acheson, Italy) for the counter-electrode. Each ink requires a passage in the oven of respectively 20 minutes for the silver chloride and graphite ink, and of 40 minutes for the gold ink, at 70° C.

[0060] The gold working electrode (diameter=7 mm.sup.2) is printed in a central position with respect to the reference and working electrode.

[0061] 5 μl of HCl 0.4 M are deposited on the hydrophilic area of the electrode (semi-circular area) and allowed to evaporate at room temperature in order to have a ready-to-use sensor without the need for the operator to add other reagents apart from the sample to analyse.

[0062] The measurement of the copper ions is carried out by depositing 30 μL of the solution under analysis (sweat samples) directly on the functionalised area, in direct contact with the printed electrodes and carrying out an analysis by means of linear sweep anodic stripping voltammetry (LS-ASV) in the potential range from −0.5 to 0.6 V.

Example 2

[0063] The volume and concentration of the HAuCl.sub.4, solution, and the synthesis time of the nanoparticles were optimised in order to reach the method and the sensor of Example 1. The optimisation steps were monitored by cyclic voltammetry with a scan rate of 0.05 V/s in the presence of 5 mM iron/ferrocyanide prepared in 0.1 M KCl.

[0064] The results are represented in FIG. 3. FIG. 3A shows the concentration and FIG. 3B shows the volume of the HAuCl.sub.4 solution that is deposited on the paper to synthesise the gold nanoparticles (AuNP). The study on the concentration was carried out in the range between 0 and 15 mM, while the study on the volume was assessed between 0 and 15 μl. The points shown are the intensity of the anodic peak obtained in the presence of 5 mM iron/ferrocyanide by cyclic voltammetry at a scan rate of 0.05 V/s. All experiments were repeated in triplicate. As regards the optimisation of the HAuCl.sub.4 concentration, it is evident how the colour of the synthesised nanoparticles changes when the concentration is greater than 2.5 mM. The colour of the AuNPs depends on the dimensions of the nanoparticles. The dark aspect represents the formation of aggregates which are not stable. This behaviour is also highlighted through the observation of the anodic current intensities: lower currents are recorded when the HAuCl.sub.4 concentration is greater than 2.5 mM, which has been chosen as the optimal concentration.

[0065] After optimising the concentration, the assessment of the effect of the volume was carried out. The effect of the volume is mainly a consequence of the diffusion of the aqueous solution in the test area. If the volume is too low, the drop does not cover the whole area, if the volume is too high there is an accumulation of the dissolved species on the periphery. The optimal volume was identified to be 4 μl. As evident from FIG. 3B the result is confirmed in terms of current intensity and colour/homogeneity of the AuNPs. Moreover, it is evident that a volume greater than or equal to 10 μl produces an accumulation effect of the species dissolved in the periphery.

[0066] The last optimisation step was on the heating time and formation of the nanoparticles (data not shown). The ideal compromise was found at 30 minutes at a temperature of 70° C.

Example 3

[0067] Following the optimisations described in Example 2, the electrochemical performances of the sensor with functionalised paper versus the sensor with non-functionalised paper was compared. The electrochemical efficiency was assessed in the presence of a 5 mM iron/ferrocyanide mixture by cyclic voltammetry experiments varying the scan rate from 0.02 to 1 V/s using unmodified paper (FIG. 4A) and modified with AuNP (FIG. 4B).

[0068] Both sensors follow the Randles-Sevcik equation (i.sub.p=(2.69×10.sup.5) n.sup.1.5ACD.sup.0.5v.sup.0.5) and the linear correlation between current and square root of the scan rate confirms the mass transfer diffusion of the analyte. Furthermore, this behaviour is consistent with the absence of trapping phenomena of the analyte on the working electrode.

[0069] As evident from the figures (FIGS. 4A and 4B), the presence of AuNP in the filter paper produces an increase in the current intensity (about twice) and an increase in the kinetics of transfer of the electrons to the solution/electrode interface (the peak-to-peak separation (ΔE) at 20 mV/s decreased from 210 to 140 mV when AuNP nanoparticles are present).

Example 4

[0070] For the development of the method and sensor described in Example 1, the electrochemical parameters for the detection of copper in relation to the anodic redissolution voltammetry were optimised. In particular, as shown in FIG. 5, the deposition potential, the deposition time, the scan rate and the conditioning potential were assessed. The initial conditions for the first parameter that have been optimised (deposition potential) are: t dep=200 s; scan rate=0.8 V/s; E cond=0 V. All the experiments were conducted in the presence of 200 ppb Cu (II) (prepared in a 0.1 M HCl solution).

Example 5

[0071] Since the detection of copper ions is typically performed in a highly acidic environment, a comparison was made between a procedure in which the AuNP-functionalised sensor was first impregnated with HCl and then dried and then a solution of copper ions was applied, and a procedure in which the same sensor was not impregnated, but a solution of copper ions containing HCl was applied. In both cases the same sensitivity was obtained, demonstrating that it is possible to apply the HCl solution to the sensor beforehand and then provide the sensor ready for use without the operator having to add other reagents apart from the sample to be analysed.

Example 6

[0072] As shown in FIG. 6, a calibration curve was obtained by analysing distilled water with known concentrations of copper ions. The results obtained by means of a sensor constituted with AuNP-functionalised paper were compared with the results obtained using a non-functionalised sensor. In particular, copper ion concentrations from 10 to 400 μg/L were tested.

[0073] The results with functionalised paper are represented in FIG. 6 with solid lines, while the results with non-functionalised paper are represented by a dashed line. All the measurements were performed by impregnating the working area with 20 μl of copper ion solution in double distilled water using the parameters used in Example 4. The inner box of FIG. 6 shows the comparison between calibration curves obtained through non-functionalised and functionalised paper.

[0074] The use of functionalised paper highlighted a linear correlation between current intensity (deriving from the subtraction of the signal obtained in the absence of analyte, y) and the concentration of copper ions (expressed in μg/L, x) through the following equation: y=0.011x+0.252 with R.sup.2=0.995. The detection limit (3σ.sub.B/method sensitivity) calculated as the ratio between 3 times the standard deviation of the signal obtained in the absence of analyte (σ.sub.B) and the method sensitivity, defined as the slope of the linear section of the calibration curve resulted in 3 μg/L, and the limit of quantification was equal to 10 ppb. The response was linear in the range between 10 and 400 μg/L. As evident from the inner box of FIG. 6 it is evident that it is the presence of AuNP that allows the detection of copper ions.

Example 7

[0075] The performances of the sensor with functionalised paper were tested for the detection of copper ions in sweat samples. 20 μl of sweat obtained from volunteers who had done physical activity with different concentrations of copper (200 and 300 μg/L) were deposited on the working area of the sensor. As shown in FIG. 7, by adding known concentrations of copper ions (200 and 300 μg/L) and using the standard addition method, it was possible to quantify the presence of copper ions in sweat samples.

Example 8

[0076] The accuracy of the method was successfully assessed either by performing two-level recovery studies or by validating the results, comparing them with those obtained with the use of atomic absorption spectroscopy (AAS), as shown in the following Table 1.

TABLE-US-00001 TABLE 1 Recoveries Sweat Added sample concentration Recovery RSD #1 (μg/L) (%) (%) 100 98 4 250 82 9 Validation Detected copper ions Student's Sweat (μg/L) F-Test t-test sample AuNP Sp. Critical Sp. Critical #2 sensor AAS value value value value 384 ± 43 391 ± 10 18.49 19.00 0.137 2.776

[0077] The levels of copper ions that were detected in untreated sweat are in accordance with the physiological values (25-2100 μg/L), and the comparison with the reference method for the detection of copper ions (AAS) provided a good correlation within the degree of experimental uncertainty.

Example 9

[0078] In this example (FIG. 9) it was successfully demonstrated that the functionalisation of paper with metal nanoparticles increases the sensitivity in the detection of the products of immunoenzymatic type electrochemical sensors. Specifically, an increase in the capability of accurately detecting the immunoenzymatic sensor marker H.sub.2O.sub.2 (hydrogen peroxide) using an AuNP-functionalised paper and by applying a reduction potential preferably between −0.3V and −0.5V was demonstrated.

Example 10

[0079] In this example it was shown that the functionalisation of the filter paper with pre-constituted AuNPs or with metal precursors from which nanoparticles are generated in situ differs substantially.

[0080] Specifically, the functionalisation of paper with pre-constituted AuNPs, directly added on paper, does not give a good functional result, because the paper does not acquire an electro-catalyst function. This is evident from tests carried out using the proposed sensor for the detection of copper ions. As shown in FIG. 8, the sensor for the detection of copper when printed on paper directly functionalised with pre-constituted AuNP does not work (the current peak is flat). Conversely, it works much better when the paper is functionalised starting from the metal precursor.

[0081] A possible explanation is that the in situ synthesis of the nanoparticles allows the metal precursor to be inserted in the cellulose network and the nanoparticles created in situ from the functional point of view are different from those deposited as such on paper.

Example 11

[0082] A more detailed structural analysis was performed using SEM (scanning electron microscopy) in order to study the morphological characteristics of AuNP-functionalised cellulose substrates. FIGS. 10A-B and 10C show SEM images of AuNP-functionalised paper and non-functionalised paper, respectively. In detail, the microscopy showed that the AuNPs were dispersed and adsorbed on the paper surface forming hot-spots (FIGS. 10A and 10B). No AuNPs were detected on the non-functionalised paper (FIG. 10C).

Example 12

[0083] A dynamic light scattering (DLS) analysis was performed in order to understand the dimensions distribution of the nanoparticles. DLS measurements revealed a monodisperse AuNP suspension (FIG. 11) with an average diameter of 196.2±20.7 nm and a satisfactory polydispersity index (PDI) of 0.13.

Example 13

[0084] A test was performed simulating a generic immunosensor (with activity comparable to any other more specific immunosensor) and alkaline phosphatase used as a label for assessing if paper functionalised with gold nanoparticles in situ modifies the signal detection through immunosensors. The response of the sensor printed on paper functionalised with gold nanoparticles created in situ was much better than that given by the sensor printed on the same undecorated paper. In particular, a dose of a generic antibody (20 μl) conjugated with the alkaline phosphatase enzyme (1 μg/mL), prepared in phosphate saline buffer solution (PBS) was placed on the electrochemical sensor printed on paper. Then the enzyme reagent was added: 70 μL of 1-naphthyl phosphate (5 mg/mL, prepared in DEA-MgCl2-KCl buffer pH 9.6). After 2 minutes of enzymatic reaction, the electroactive product (1-naphthol) derived from the reaction was measured in differential pulse voltammetry (DPV) with the following parameters: Ebegin=−0.2 V; Eend=0.4 V; Estep=0.016 V; Epulse=0.05 V; tpulse=0.06 s; scan rate=0.016 V/s. The measurement was repeated in triplicate, for each sensor (either decorated sensor or undecorated sensor). The results are indicated in FIG. 12.

[0085] Advantages

[0086] Significantly better sensor performances are obtained in virtue of the fact that the cellulose support, and not the inks for the electrode printing, is functionalised with metal nanoparticles in terms of either conductivity or concentration of the analyte to the electrode, in particular in the case in which the analyte to be measured is a metal. In fact, in the absence of such functionalisation, in the detection of analytes of biological fluids, the diffusion of the biological fluid sample inside the porous structure of the paper support generally prevents the analyte from accumulating at the working electrode. Vice versa, the functionalisation of the cellulose support with metal nanoparticles allows the detection of analytes, even at low concentrations (lower than 20 ppb), which cannot be highlighted with the sensor printed on non-functionalised cellulose. Furthermore, it is more advantageous to use a functionalised support rather than functionalising the electrodes: in particular, it is often difficult to mix an organic-based conductive ink with nanoparticles in aqueous solution. In the present method, instead, the metal nanoparticles are formed directly in the structure of the paper without the need to use additional reducing agents such as sodium borohydride, ascorbic acid or citrate. Also from the functional point of view, the metal nanoparticles synthesised in situ as per described optimised method have important advantages even regardless of the geometric shape and constituent material of the single electrodes: in fact, no equally satisfactory performances are obtained using pre-constituted metal nanoparticles.

[0087] Furthermore, the production of electroanalytical sensors, using the proposed method, does not involve the use of new technologies and therefore it can be easily implemented using processes and machinery already used for the industrial production of printed electrodes. Finally, cellulose supports functionalised with metal nanoparticles according to the method described, can also be used in microfluidic platforms for multiple sensors.