CN114324514A - PET-based flexible electrode and preparation method and application thereof - Google Patents
PET-based flexible electrode and preparation method and application thereof Download PDFInfo
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- CN114324514A CN114324514A CN202111441662.9A CN202111441662A CN114324514A CN 114324514 A CN114324514 A CN 114324514A CN 202111441662 A CN202111441662 A CN 202111441662A CN 114324514 A CN114324514 A CN 114324514A
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Abstract
The invention provides a flexible electrode based on PET and a preparation method thereof, belonging to the technical field of electrochemical sensors. The PET-based flexible electrode comprises a PET substrate printed with carbon paste, and an MXene and MWCNT composite layer, a cortisol antibody layer and a bovine serum albumin layer are sequentially arranged on the PET substrate from bottom to top. The preparation method comprises the steps of firstly forming a flexible silk-screen printing carbon electrode on a PET substrate, then dropping a suspension of MXene and MWCNT on the surface of the silk-screen printing carbon electrode to form an MXene and MWCNT composite layer, then dropping a cortisol antibody on the surface of the MXene and MWCNT composite layer, finally adding bovine serum albumin to the working electrode, and obtaining the final flexible electrode through an incubation process. The electrode has the advantages of simple structure, simple manufacturing process, higher electrochemical performance, mechanical flexibility and biocompatibility, and can be widely applied to the fields of portable analysis equipment for clinical diagnosis, real-time monitoring of illness state, monitoring of human health and the like.
Description
Technical Field
The invention relates to the technical field of electrochemical sensors, in particular to a flexible electrode based on PET and a preparation method thereof.
Background
Cortisol is produced by the adrenal gland and has several important functions affecting glucose production, fat metabolism, inflammatory responses, the central nervous system and immune functions. Abnormal secretion of cortisol levels in the body suppresses the immune system, inhibits inflammation and reduces the concentration of fats and amino acids. Physiologically higher cortisol concentrations are associated with cushing's disease and lead to symptoms of fatigue, skeletal fragility and obesity; while lower cortisol concentrations can lead to edison's disease. Cortisol is also considered a biomarker of stress, and prolonged stress can have many negative consequences and adversely affect the immune, cardiovascular and central nervous systems. Thus, if the body is affected by chronic stress, the detection of cortisol can be a very useful indicator and aid in the early diagnosis of these diseases.
At present, flexible stretchable sensors based on physical signal monitoring are rapidly developed, and show great application prospects in human activity health monitoring and personalized treatment. The flexible electrochemical sensor is a powerful monitoring tool for acquiring abundant chemical information of signal molecules in organisms, and is widely applied to a health monitoring system due to the characteristics of good mechanical property, sensitivity, stability and the like. However, electrochemical sensors require higher conductivity and electrochemical inertness of the material than the currently rapidly developed physical sensors, resulting in relatively slow development of flexible electrochemical devices.
Disclosure of Invention
In order to solve the problems, the invention provides a flexible electrode based on PET and a preparation method thereof, wherein a flexible MXene and MWCNT composite layer, a cortisol antibody layer and a bovine serum albumin layer are sequentially formed on a PET substrate, the electrode has simple structure and simple manufacturing process, has higher electrochemical performance, mechanical flexibility and biocompatibility, and has great potential in the fields of wide application in clinical diagnosis portable analysis equipment, disease real-time monitoring, human health monitoring and the like.
In order to achieve the above purpose, the invention adopts a technical scheme that:
the flexible electrode based on the PET comprises a PET substrate printed with carbon paste, wherein an MXene and MWCNT composite layer, a cortisol antibody layer and a bovine serum albumin layer are sequentially arranged on the PET substrate from bottom to top.
Wherein the MXene and MWCNT composite layer is arranged on the surface of the PET substrate; a cortisol antibody layer disposed on the surface of the MXene and MWCNT composite layer; and a bovine serum albumin layer disposed on the surface of the cortisol antibody layer.
The preparation method of the PET-based flexible electrode comprises the following steps:
s10, fixing the PET substrate on a printing template, dripping carbon slurry on a screen, printing with a scraper, separating the PET substrate from the screen printing template, drying in a vacuum drying oven at 70 +/-5 ℃ for 240 +/-5 min to prepare a screen printing carbon electrode as a working electrode;
s20, dropping the suspension of MXene and MWCNT on the surface of the working electrode of S10, and placing the working electrode in a vacuum drying oven at 25-35 ℃ for 325-35min to form a MXene and MWCNT composite layer;
s30, dripping EDC on the surface of the MXene and MWCNT composite layer of S20, incubating at room temperature for 25-35min, dripping NHS on the surface of the MWCNT composite layer, incubating at room temperature for 25-35min, and finally dripping a cortisol antibody on the surface of the EDC-NHS, incubating at room temperature for 30 +/-5 min to obtain a cortisol antibody layer;
and S40, adding bovine serum albumin to the surface of the cortisol antibody layer, and incubating at room temperature for 25-35min to obtain the flexible electrode.
Further, in the step S20, the concentration of the MXene and MWCNT suspension is 1-15 mg/mL, and the mass ratio of the MXene to the MWCNT is 1: 1.
Further, in the step S30, the concentration of EDC is 0.1mM, the concentration of NHS is 0.15mM, and the concentration of cortisol antibody is 1-10 μ g/mL.
Further, in the step S40, the concentration of bovine serum albumin is 1 mg/mL.
An electrode system for detecting cortisol, comprising: the flexible PET-based electrode comprises a working electrode, a reference electrode and a counter electrode, wherein the working electrode is the PET-based flexible electrode, the reference electrode is an Ag/AgCl electrode, and the counter electrode is a carbon paste printed electrode.
Compared with the prior art, the technical scheme of the invention has the following advantages:
according to the flexible electrode based on the PET and the preparation method thereof, the flexible MXene and MWCNT composite layer, the cortisol antibody layer and the bovine serum albumin layer are sequentially formed on the PET substrate, the flexible electrode takes the PET as the substrate, and the MXene and MWCNT disordered network composite structure is the conducting layer and the sensing layer, so that the flexible electrode is simple in structure, simple in manufacturing process, high in electrochemical performance, mechanical flexibility and biocompatibility, and has great potential in the fields of wide application to portable analysis equipment for clinical diagnosis, real-time monitoring of disease conditions, monitoring of human health and the like.
Drawings
The technical solution and the advantageous effects of the present invention will become apparent from the following detailed description of the embodiments of the present invention with reference to the accompanying drawings.
FIG. 1 is a flowchart illustrating steps S20-S40 according to an embodiment of the present invention;
FIG. 2 is a cyclic voltammogram of electrodes prepared from suspensions of MXene and MWCNT at different ratios in 10mmol/L potassium ferricyanide in accordance with an embodiment of the present invention;
FIG. 3 is a cyclic voltammogram of electrodes prepared from suspensions of different concentrations of MXene and MWCNT in 10mmol/L potassium ferricyanide in accordance with an embodiment of the present invention;
FIG. 4 is a graph showing the relationship between the difference in current between electrodes prepared at different cortisol antibody concentrations and the difference in current before and after binding of antigen and antibody;
FIG. 5 is a graph showing the relationship between current difference before and after binding of an antigen antibody and an electrode prepared by adding a standard cortisol solution for different incubation times in accordance with one embodiment of the present invention;
FIG. 6 is a scanning electron microscope photograph of a PET-based flexible electrode according to an embodiment of the present invention;
FIG. 7 is a transmission electron microscope photograph of a PET-based flexible electrode according to an embodiment of the invention;
FIG. 8 shows an EDS spectrum of a PET-based flexible electrode according to an embodiment of the invention;
FIG. 9 is a graph showing the current response of a standard cortisol solution to which cortisol is added in different concentrations according to an embodiment of the present invention;
FIG. 10 is a linear relationship between the concentration of cortisol and the corresponding current signal when the analysis apparatus according to an embodiment of the present invention is applied to standard cortisol solution analysis;
FIG. 11 is a graph showing the response of electrodes with various interferents added to the electrodes to the resulting current for a PET-based flexible electrode in accordance with one embodiment of the present invention;
FIG. 12 is a graph showing the difference between different electrode test results for an analysis of PET-based flexible electrodes with the addition of standard cortisol solution in accordance with an embodiment of the present invention;
FIG. 13 shows an embodiment of the present invention applied to sweat cortisol measurement.
Detailed Description
The technical solutions in the embodiments of the present invention will be described clearly and completely with reference to the accompanying drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
Example 1
The present embodiment provides a PET-based flexible electrode, including: a PET substrate printed with carbon paste; an MXene and MWCNT composite layer disposed on a surface of the PET substrate; a cortisol antibody layer disposed on the surface of the MXene and MWCNT composite layer; and a bovine serum albumin layer disposed on the surface of the cortisol antibody layer.
The embodiment also provides a preparation method of the PET-based flexible electrode, as shown in fig. 1, comprising the following steps:
s10 first, fixing the PET substrate on the printing stencil; secondly, dripping carbon slurry on a silk screen, and then printing by using a scraper as a working electrode; an Ag/AgCl paste was also poured onto the template and printed as a reference electrode. Finally, the PET film is separated from the screen printing template and is placed in a vacuum drying oven to be dried at 70 +/-5 ℃ for 240 +/-5 min, and then the screen printing carbon electrode is prepared.
S20 MXene and MWCNT suspension is dripped on the surface of the working electrode and placed in a vacuum drying oven at 30 +/-5 ℃ for 30 +/-5 min to form an MXene and MWCNT composite layer.
S30 dropping EDC on the surface of the MXene and MWCNT composite layer, incubating for 30 +/-5 min at room temperature, then dropping NHS on the surface of the MXene and MWCNT composite layer, incubating for 30 +/-5 min at room temperature, finally fixing the cortisol antibody on the surface of EDC-NHS, and incubating for 30 +/-5 min at room temperature to obtain a cortisol antibody layer.
And S40, adding bovine serum albumin to the surface of the cortisol antibody layer, and incubating at room temperature for 30 +/-5 min to obtain the final flexible electrode.
In the step S20, the concentration of the MXene and MWCNT suspension is 7.5mg/mL, and the ratio of the MXene and MWCNT suspension is 1: 1. The MXene and MWCNT composite layer and the PET substrate form a flexible working electrode, and the flexible working electrode has excellent electrochemical performance, high flexibility and convenient processing and treatment.
In the step S20, the concentration of the MXene and MWCNT suspension is 1-15 mg/mL, preferably 1mg/mL, 5mg/mL, 7.5mg/mL, 10mg/mL or 15mg/mL, wherein the optimal concentration is 7.5 mg/mL. MXene and MWCNT have large specific surface area, and carbon nanotubes have large aspect ratio, high mechanical strength, low rigidity and chemical inertness, so that the carbon nanotubes are ideal materials for preparing flexible sensors.
In the step S30, the EDC concentration is 0.1mM, and the NHS concentration is 0.15 mM; the concentration of the cortisol antibody is 1-10 mu g/mL, preferably 1 mu g/mL, 2.5 mu g/mL, 5 mu g/mL, 7.5 mu g/mL or 10 mu g/mL, wherein the optimal concentration is 5 mu g/mL. The electrochemical response is then maximized, providing excellent electrochemical performance for cortisol detection.
In step S40, the concentration of bovine serum albumin is 1mg/mL, and the electrochemical response is maximal at this time.
Performance testing
Respectively preparing MXene and MWCNT suspension with the mass ratio of 4:1, 2:1, 1:2 and 1:4, dripping onto the surface of a working electrode, and standing in a vacuum drying oven at 30 +/-5 ℃ for 30 +/-5 min to form an MXene and MWCNT composite layer. After the preparation, the cyclic voltammogram in 10mmol/L potassium ferricyanide was measured by an electrochemical workstation. As shown in fig. 2, the peak oxidation current was higher when the mass ratio of MXene and MWCNT was 1:1 than other mass ratios, and the MXene and MWCNT suspension at 1:1 was chosen as the optimal ratio for preparing the sensor.
MXene and MWCNT suspensions with the concentrations of 1mg/mL, 5mg/mL, 7.5mg/mL, 10mg/mL and 15mg/mL are respectively prepared to be dripped on the surface of a working electrode, and are placed in a vacuum drying oven at the temperature of 30 +/-5 ℃ for 30 +/-5 min to form an MXene and MWCNT composite layer. After the preparation, the cyclic voltammogram in 10mmol/L potassium ferricyanide was measured by an electrochemical workstation. As shown in fig. 3, the concentration of the suspension of MXene and MWCNT gave the highest response at 7.5mg/mL, with a negligible change in the redox peak current with further increase. Therefore, MXene and MWCNT suspension concentrations of 7.5mg/mL were chosen as the optimal concentrations for making flexible sensors, taking into account the mechanical, electrical and electrochemical properties.
As shown in fig. 4, when the antibody concentration of cortisol is higher than 5 μ g/mL, the current signal levels off, with no further significant binding between cortisol antibody and excess cortisol. Therefore, immunosensors were constructed using an optimal antibody concentration of 5. mu.g/mL. The current signal versus incubation time is shown in fig. 5, where the current signal rises rapidly from 5 to 20 minutes, and then drops slightly when the incubation time of cortisol is higher than 20 minutes. The incubation time with cortisol was therefore 20 minutes in the subsequent experiments.
FIGS. 6 to 7 show the cross-linked structure of MXene and MWCNT; the EDS energy spectrum shown in fig. 8 shows the distribution of fluorine, oxygen, titanium and carbon elements on the electrode surface.
Example 2
The three-electrode detection system is formed by taking the PET flexible electrode as a working electrode, an Ag/AgCl electrode as a reference electrode and a carbon paste printing electrode as a counter electrode, and the detection of the cortisol in the human sweat can be realized by using the three-electrode detection system.
Several common substances in sweat have been studied, including glucose (Glu), Lactic Acid (LA), Ascorbic Acid (AA), sodium chloride (NaCl), Urea (UA), and potassium chloride (KCl). As shown in fig. 11, cortisol was the only substance that elicited a dramatic current response, while other studied substances consistently exhibited lower corresponding current changes. Relative resistance (R/R) of electrodes0) Is not provided withA significant change occurred.
As shown in fig. 12, eight separate prepared working electrodes were prepared and measured under the same conditions to ensure reproducibility of the working electrode test results. It can be seen from the figure that the prepared working electrode has acceptable reproducibility of cortisol detection.
The cortisol standard solutions with different concentrations are prepared by using a phosphoric acid buffer solution with the pH value of 7.4 and the concentration of 0.1mol/L, as shown in fig. 9-10, the response current is correspondingly reduced along with the increase of the cortisol concentration, and the better electrochemical sensing capability is reflected. The response current showed a linear relationship with cortisol concentration between 0.1fg and 1ng, with a correlation coefficient of 0.998 and a detection limit of 0.03 fg/mL.
Detection of Cortisol in actual sweat samples
To verify the feasibility of the invented electrode as a flexible sensor, actual sweat was dropped onto the electrode surface. Differential pulse voltammetry was chosen to monitor the concentration of cortisol at the electrode surface. The prepared electrodes were incubated with cortisol for 20 minutes to provide sufficient time for antigen-antibody interaction. To assess the accuracy of the measurement results, a chemiluminescence immunoassay method, namely the CLIA method, was used for validation. As shown in fig. 13, the present working electrode measurement method has good agreement with the CLIA method.
The above description is only an exemplary embodiment of the present invention, and not intended to limit the scope of the present invention, and all equivalent structures or equivalent processes that are transformed by the content of the present specification and the attached drawings, or directly or indirectly applied to other related technical fields, are included in the scope of the present invention.
Claims (8)
1. A PET-based flexible electrode, characterized by: the composite coating comprises a PET substrate printed with carbon paste, and an MXene and MWCNT composite layer, a cortisol antibody layer and a bovine serum albumin layer are sequentially arranged on the PET substrate from bottom to top.
2. A method for preparing a flexible PET-based electrode according to claim 1, wherein: the method comprises the following steps:
s10, fixing the PET substrate on a printing template, dripping carbon slurry on a screen, printing with a scraper, separating the PET substrate from the screen printing template, placing the PET substrate in a vacuum drying box, drying at 65-75 ℃ for 235-75 min, and preparing a screen printing carbon electrode as a working electrode;
s20, dropping the suspension of MXene and MWCNT on the surface of the working electrode of S10, and placing the working electrode in a vacuum drying oven at 25-35 ℃ for 25-35min to form a MXene and MWCNT composite layer;
s30, dripping EDC on the surface of the MXene and MWCNT composite layer of S20, incubating for 25-35min, dripping NHS on the surface of the composite layer, incubating for 25-35min, and dripping cortisol antibody on the surface of EDC-NHS, incubating for 25-35min to obtain a cortisol antibody layer;
and S40, adding bovine serum albumin to the surface of the cortisol antibody layer, and incubating for 25-35min to obtain the flexible electrode.
3. The method of claim 2, wherein: in the step S10, the PET substrate has a thickness of 0.15 mm.
4. The method of claim 2, wherein: in the step S20, the concentration of the MXene and MWCNT suspension is 1-15 mg/mL, and the mass ratio of the MXene to the MWCNT is 1: 1.
5. The method of claim 2, wherein: in the step S30, the concentration of EDC is 0.1mM, the concentration of NHS is 0.15mM, and the concentration of cortisol antibody is 1-10 mug/mL.
6. The method of claim 2, wherein: in the step S40, the concentration of the bovine serum albumin is 1 mg/mL.
7. Use of the flexible PET-based electrode according to claim 1 for the detection of cortisol.
8. An electrode system for the detection of cortisol, comprising: the method comprises the following steps: the PET-based flexible electrode of claim 1, the reference electrode being an Ag/AgCl electrode, and the counter electrode being a carbon paste printed electrode.
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| CN116930289A (en) * | 2023-09-19 | 2023-10-24 | 江阴市人民医院 | Preparation method of high-sensitivity aptamer sensor for troponin cTnI detection |
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