An antibacterial and waterproof hydrogel biosensor based on conductive spandex fiber mesh and its preparation method

Abstract

The present invention discloses an antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh and a preparation method thereof. The preparation method comprises the following steps: 1) preparing graphene composite elastic spandex conductive fibers by solution dry spinning and weaving the fibers into a fiber mesh; 2) designing a rectangular mold and fixing the fiber mesh to hooks on the four sides of the mold groove as the first layer of the conductive fiber mesh structure; 3) preparing a sodium alginate / acrylamide mixed solution blended with nanosilver and pouring the solution into the mold for in-situ polymerization; 4) transferring the mold to a Ca 2+ A second gel matrix with a double network is formed in the coagulation bath. 5) After complete dialysis, the gel is immersed in a mixture of stearic acid / silicone emulsion / vegetable oil for hydrophobic modification, forming a third waterproof layer on its surface, ultimately yielding a hydrogel biosensor. This biosensor possesses conductive, stretchable, antibacterial, and waterproof properties, and can be used for biological strain monitoring.

Description

Technical Field

[0001] The present invention relates to a preparation technology of a conductive hydrogel and a biosensor, and in particular to an antibacterial-waterproof hydrogel biosensor based on a conductive spandex fiber mesh and a preparation method thereof. Background Art

[0002] The limb skeleton includes the upper and lower limbs, consisting of girdle bones connected to the trunk and free-moving, free-limb bones. The number and arrangement of bones in the upper and lower limbs are essentially the same. The upper limb bones are characterized by their lightness and flexibility, while the lower limb bones are thicker and more robust, supporting and moving the body, a function closely related to human upright gait. However, with the development of industry and transportation, the incidence of bone defects and injuries in daily life has increased year by year, and patients often experience a lengthy recovery period after orthopedic surgery.

[0003] During this recovery period, patients may also lack knowledge about postoperative rehabilitation, leading to incorrect, inadequate, or overtraining training. These situations not only fail to promote recovery but may even lead to unexpected consequences during bone repair. Therefore, real-time monitoring and assessment of the patient's recovery process would be of great assistance and effectively promote postoperative rehabilitation.

[0004] To address these issues, biostrain sensors are devices that convert their own strain information into biological signals. If these sensors can be applied to monitor patients' postoperative rehabilitation behaviors after fractures or bone injuries, they could provide guidance for these behaviors. Therefore, this paper proposes an antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh and a method for its preparation. These sensors are designed to address common issues encountered during the use of hydrogel biosensors and provide a novel strategy for assisting postoperative rehabilitation. Summary of the Invention

[0005] The present invention aims to address the ineffectiveness of conventional nerve damage repair materials by providing an antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh and its preparation method. This biosensor combines conductivity, stretchability, antibacterial properties, and waterproofing, and can be used for biological strain monitoring.

[0006] The present invention is implemented by the following technical solution, and the specific steps are as follows:

[0007] A method for preparing an antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh comprises the following steps:

[0008] 1) Graphene composite elastic spandex conductive fibers were prepared by solution dry spinning and woven into a fiber mesh;

[0009] 2) designing a rectangular parallelepiped mold, and fixing the fiber mesh in the rectangular parallelepiped mold as a first layer of conductive fiber mesh structure;

[0010] 3) preparing a sodium alginate / acrylamide mixed solution blended with nanosilver, and pouring the mixed solution into the rectangular parallelepiped mold after centrifugal degassing to perform in-situ polymerization;

[0011] 4) Transfer the rectangular parallelepiped mold to Ca 2+ Immersed in a coagulation bath to form a second layer of gel matrix structure with a double network;

[0012] 5) Demolding the rectangular parallelepiped from the mold, performing gel dialysis, and then immersing it in a stearic acid / organic silicone emulsion / vegetable oil mixed solution for hydrophobic modification to form a third waterproof layer structure on its surface. After drying, the hydrogel biosensor is finally obtained.

[0013] Furthermore, in the solution dry spinning process in step 1), graphene, polyurethane prepolymer, and a mixed diamine / diol solution are first prepared, and a chain terminator is added after the reaction to obtain a graphene-compounded spandex stock solution. The spandex stock solution is spun through a spinning head under pressure, and then twisted, oiled, and wound under hot air conditions to obtain spandex.

[0014] Furthermore, during the preparation of the spandex stock solution, the graphene has a size of 2-4 microns and a concentration of 0.01-0.1 wt%; the polyurethane prepolymer is one of polyethers, polyesters, and aliphatic isocyanates, with a concentration of 20-35 wt%; the diamine is one of ethylenediamine, propylenediamine, and pentamethylenediamine; the diol is one of propylene glycol and butanediol, with a total concentration of 2-8 wt%; the reaction temperature is 60-90°C, and the reaction time is 45-60 min; the chain terminator is one of ethanolamine, diethanolamine, triethanolamine, and N,N-dimethylethanolamine, with a concentration of 0.1-1‰ of the diol;

[0015] During the spinning process, the aperture of the spinning head is about 50-100 microns, and the spinning speed is 50-100 m / s.

[0016] Furthermore, in step 2), a groove is formed in the rectangular mold, and several hooks are evenly fixed on the inner wall of the groove in the middle position in the depth direction of the groove to fix the fiber mesh. The spacing between adjacent hooks is 0.5-1 cm / piece, and the depth of the rectangular mold is 1-3 mm.

[0017] Furthermore, in step 3), the prepared mixed solution contains a crosslinker, an initiator, and a polymerization promoter. The size of the nanosilver is 20-50 nm, and the addition amount is 0.01-0.05 wt %. The viscosity of the sodium alginate at 10 g / L and 20° C. is 0.02-0.1 Pa·s, and the concentration is 3-4 wt %. The concentration of the acrylamide is 3-10 wt %. The concentration of the crosslinker N,N'-methylenebisacrylamide (MBAA) is 0.02-0.10 wt %. The initiator is one or more of ammonium persulfate, sodium persulfate, and potassium persulfate, with a concentration of 0.5-0.95 wt %. The polymerization promoter is tetramethylethylenediamine, with a concentration of 0.025-0.08 wt %.

[0018] The centrifugal degassing rate is 1000-2000 rpm, and the time is 3-8 min;

[0019] The in-situ polymerization temperature is 30-35° C. and the time is 4-12 hours.

[0020] Furthermore, in step 4), during the coagulation bath, the Ca 2+ Specifically, it is one or more of calcium chloride, calcium bicarbonate, and calcium gluconate, with a concentration of 5-20wt%, and the immersion time is 30min-4h.

[0021] Furthermore, in step 5), during the preparation of the stearic acid / organic silicone emulsion / vegetable oil mixed solution, the stearic acid concentration is 0.05-0.5 v / v%; the organosilicon is one or more of polydiethylsiloxane, dodecyltriethylsilane, polymethyltrifluoropropylsiloxane, polymethylvinylsiloxane, hexadecyltriethoxysilane, polydimethylsiloxane, hexadecyltrimethoxysilane, and methyltriethoxysilane, with a concentration of 1-5 v / v%; the vegetable oil is one or more of olive oil, soybean oil, and sesame oil, with a concentration of 0.5-2 v / v%; and the solvent is one of dichloromethane, acetone, and trichloroethane.

[0022] The drying is carried out using nitrogen drying, the time is 6-12 hours, and the temperature is 25-30°C.

[0023] An antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh is obtained by using any of the above-mentioned preparation methods.

[0024] Compared with the prior art, the present invention has the following advantages:

[0025] 1) The present invention uses spandex, graphene, nanosilver, stearic acid, silicone, etc. as raw materials, and combines solution dry spinning, nano-blending, in-situ casting, free radical polymerization, physical impregnation cross-linking and other combined processes to produce an antibacterial and waterproof hydrogel biosensor material based on a conductive spandex fiber mesh. The above raw material selection and process combination are original to the present invention.

[0026] 2) The present invention utilizes graphene doping and a solution dry spinning process to produce a conductive spandex composite fiber material, which is then woven into a fiber mesh. This mesh is then combined with a mold and in-situ casting to produce a conductive hydrogel material composited with the conductive fiber mesh. Due to the high elasticity of spandex fibers, their incorporation into a conductive hydrogel enhances the hydrogel's tensile properties and strength, while further improving its tear resistance. This ensures the integrity of the device is not compromised during use. Furthermore, the internally doped graphene exhibits excellent electrical conductivity, strengthening the fiber network while maintaining the material's high electrical conductivity. Furthermore, the stability of graphene overcomes issues such as oxidation during use, such as with conductive polymers, preventing conductivity degradation and ensuring the long-term application of the conductive hydrogel biosensor.

[0027] 3) The hydrogel biosensor in the present invention is equipped with triple reinforcement: the first is spandex fiber mesh reinforcement, the second is nano-silver nano-reinforcement, and the third is double network structure reinforcement. First, a three-layer sandwich (a fiber mesh is sandwiched between the upper and lower layers of hydrogel) fiber network reinforcement structure is formed by combining the casting method inside the hydrogel to ensure the elasticity, strength and tear resistance of the hydrogel; secondly, combined with nano-silver reinforcement technology, nano-silver adsorbs the sodium alginate and polyacrylamide molecular chains to form physical entanglement points, making the polymer matrix network denser, thereby achieving the purpose of reinforcement; finally, the sodium alginate and polyacrylamide inside the hydrogel matrix are in the Ca 2+ The physical and chemical crosslinking of the hydrogel matrix with MBAA creates a dual network structure, reinforcing the hydrogel matrix. The synergistic effect of these multiple reinforcements ensures that the conductive hydrogel of the present invention possesses excellent mechanical properties, ensuring that it will not break or become damaged by high-frequency, high-frequency stretching during real-time monitoring of a patient's recovery, thus ensuring the stability of the biosensor.

[0028] 4) The hydrogel biosensor of the present invention is equipped with a first layer of conductive fiber mesh structure + a second layer of gel matrix structure + a third layer of waterproof layer structure from the inside out, so that it can meet various needs during use. The first layer of conductive fiber mesh structure ensures the strength, elasticity and conductivity of the hydrogel biosensor; the second layer of gel matrix structure ensures the strength and stability of the material; the third layer of waterproof layer ensures that the biosensor will not swell or lose strength due to water and sweat absorption during use, thereby ensuring the stability and accuracy of the biosensor's transmission of patient rehabilitation movement signals. It is through the synergy between the above-mentioned composite structures that the hydrogel biosensor of the present invention can meet the complex needs of patients' postoperative rehabilitation monitoring.

[0029] 5) The hydrogel biosensor of the present invention is conductive, stretchable, antibacterial, and waterproof. The graphene doped in the spandex fiber and the nanosilver nanocomposite in the polymer matrix ensure the hydrogel's excellent conductivity. The internal spandex fiber mesh and cross-linked acrylamide ensure the hydrogel's elasticity and resilience. Combined with the hydrogel's conductive properties, when the hydrogel biosensor stretches with the patient's limb movement during recovery, its resistance changes, causing the transmitted electrical signal to change synchronously, resulting in a real-time strain-resistance curve. This resistance change can reflect the patient's movement amplitude, thus enabling real-time monitoring of the patient's movement behavior. Since patients sweat and come into contact with external objects during postoperative recovery, bacteria can grow on the hydrogel. This can also cause the hydrogel to absorb sweat or other liquids, leading to contamination or damage. Therefore, the present invention further incorporates nanosilver and hydrophobic materials such as stearic acid and silicone to ensure that the hydrogel will not grow bacteria or swell and damage due to water / liquid absorption during use. It is through the coordination of the above functions that the hydrogel biosensor of the present invention can meet complex usage requirements and provide scientific guidance for patients' postoperative recovery. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] Figure 1 The figure is a schematic diagram of the preparation process of the antibacterial-waterproof hydrogel biosensor based on the conductive spandex fiber mesh of the present invention.

[0031] Figure 2 The contact angle results of the antibacterial-waterproof hydrogel biosensor based on the conductive spandex fiber mesh according to the embodiment of the present invention are shown (A is Example 1 and B is Example 2);

[0032] Figure 3 These are the inhibition zone results of the antibacterial-waterproof hydrogel biosensor based on the conductive spandex fiber mesh according to the embodiments of the present invention (A is Example 1 and B is Example 3). DETAILED DESCRIPTION

[0033] The present invention is further described below with reference to specific examples and accompanying drawings.

[0034] Comparative Example 1:

[0035] 1) Design a rectangular mold (with a groove in the center, 5 cm long, 1.5 cm wide, and 1.5 mm deep). Prepare a mixed solution of sodium alginate (viscosity 0.02-0.1 Pa·s (10 g / L, 20°C, concentration 3 wt%) and acrylamide (concentration 5 wt%, initiator ammonium persulfate, concentration 0.5 wt%, crosslinker MBAA, concentration 0.05 wt%, and polymerization accelerator tetramethylethylenediamine, concentration 0.03 wt%) blended with silver nanoparticles (approximately 30 nm, addition amount 0.05 wt%). Degassing was performed by low-speed centrifugation (1000 rpm, time 5 min). The solution was then poured into the rectangular mold and in-situ polymerized (in-situ polymerization temperature 35°C, time 6 h).

[0036] 2) Transfer the rectangular mold to a 10 wt% calcium chloride coagulation bath and immerse for 2 h to form a gel matrix structure with a double network;

[0037] 3) After complete dialysis, the gel was immersed in a mixed solution of 0.25 v / v% stearic acid / 3 v / v% polydiethylsiloxane / 0.5 v / v% olive oil (solvent: dichloromethane) for hydrophobic modification to form a waterproof layer structure on its surface. After completion, it was dried in nitrogen at 25°C for 8 h to finally obtain a hydrogel biosensor.

[0038] The material inhibition zone is about 1.14cm 2 The contact angle is about 148°. The tensile strength of the hydrogel was tested using a universal testing machine. When its elongation at break was about 626%, the maximum tensile strength was about 724 kPa. It broke after 5 cycles of stretching at 500% strain. When applied to biological strain sensors, the resistance change rate was linearly related to the strain, and it would not grow bacteria or absorb sweat during use.

[0039] Example 1:

[0040] 1) preparing graphene-composite elastic spandex conductive fibers by solution dry spinning (first, preparing a 0.05 wt% graphene with a size of 2-4 microns, a 25 wt% polyether polyurethane prepolymer, and a 5 wt% mixed ethylenediamine / propylene glycol solution; after the reaction, adding a chain terminator ethanolamine at a concentration of 0.5‰ of the propylene glycol to obtain a graphene-composite spandex stock solution; spinning the stock solution through a spinning head under pressure; twisting, oiling, and winding under hot air conditions to obtain spandex; wherein the spinning head aperture is approximately 50 microns and the spinning rate is 100 m / s) and weaving the fibers into a fiber web;

[0041] 2) Design a rectangular mold (a groove structure is set in the middle of the rectangular mold. A small hook is set at the middle position of the depth direction of the four sides of the groove, which is 0.75mm away from the bottom of the groove, to fix the fiber mesh. Multiple hooks are set along the length and width of the rectangular mold, with a spacing of 0.5cm / piece. The groove of the rectangular mold is 5cm long, 1.5cm wide and 1.5mm deep. Figure 1 The middle mold is only a schematic diagram), and the fiber mesh is fixed to the hooks on the four sides of the groove of the rectangular mold as the first layer of conductive fiber mesh structure;

[0042] 3) A mixed solution of sodium alginate (viscosity 0.02-0.1 Pa·s (10 g / L, 20°C, concentration 3 wt%) and acrylamide (concentration 5 wt%, initiator ammonium persulfate, concentration 0.5 wt%, crosslinker MBAA, concentration 0.05 wt%, and polymerization accelerator tetramethylethylenediamine, concentration 0.03 wt%) blended with silver nanoparticles (size approximately 30 nm, addition amount 0.05 wt%) was prepared. The mixed solution was centrifuged at low speed (1000 rpm, time 5 min) for degassing and then cast into a rectangular mold for in situ polymerization (in situ polymerization temperature 35°C, time 6 h).

[0043] 4) Transfer the rectangular mold to a 10 wt% calcium chloride coagulation bath and immerse for 2 h to form a second layer of gel matrix structure with a double network;

[0044] 5) After complete dialysis, the gel was immersed in a mixed solution of 0.25 v / v% stearic acid / 3 v / v% polydiethylsiloxane / 0.5 v / v% olive oil (solvent: dichloromethane) for hydrophobic modification to form a third waterproof layer structure on its surface. After completion, it was dried in nitrogen at 25°C for 8 h to obtain an antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh.

[0045] Compared with comparative example 1, this embodiment adds a conductive spandex fiber mesh structure. The antibacterial zone of the material is about 1.27cm 2 ,like Figure 3As shown in Example A, the contact angle is about 143°. Figure 2 As shown in Example A, the tensile strength of the hydrogel was tested using a universal testing machine. When its elongation at break was approximately 1258%, the maximum tensile strength was approximately 1.42 MPa. It was cyclically stretched 50 times under 500% strain without breaking. When applied to a biological strain sensor, the resistance change rate was linearly related to the strain, and it did not grow bacteria or absorb sweat during use.

[0046] Example 2:

[0047] 1) preparing graphene-composite elastic spandex conductive fibers by solution dry spinning (first, preparing a 0.05 wt% graphene with a size of 2-4 microns, a 25 wt% polyether polyurethane prepolymer, and a 5 wt% mixed ethylenediamine / propylene glycol solution; after the reaction, adding a chain terminator ethanolamine at a concentration of 0.5‰ of the propylene glycol to obtain a graphene-composite spandex stock solution; spinning the stock solution through a spinning head under pressure; twisting, oiling, and winding under hot air conditions to obtain spandex; wherein the spinning head aperture is approximately 50 microns and the spinning rate is 100 m / s) and weaving the fibers into a fiber web;

[0048] 2) Design a rectangular mold (a groove structure is set in the middle of the rectangular mold. Small hooks are set in the middle of the longitudinal direction (depth direction) on the four sides of the groove to fix the fiber mesh. Several hooks are set along the length and width of the mold, with a spacing of 0.5 cm per hook. The mold groove is 5 cm long, 1.5 cm wide, and 1.5 mm deep). The fiber mesh is fixed to the hooks on the four sides of the groove of the rectangular mold as the first layer of conductive fiber mesh structure;

[0049] 3) A mixed solution of sodium alginate (viscosity 0.02-0.1 Pa·s (10 g / L, 20°C, concentration 3 wt%) and acrylamide (concentration 5 wt%, initiator ammonium persulfate, concentration 0.5 wt%, crosslinker MBAA, concentration 0.05 wt%, and polymerization accelerator tetramethylethylenediamine, concentration 0.03 wt%) blended with silver nanoparticles (size approximately 30 nm, addition amount 0.05 wt%) was prepared. The mixed solution was centrifuged at low speed (1000 rpm, time 5 min) for degassing and then cast into a rectangular mold for in situ polymerization (in situ polymerization temperature 35°C, time 6 h).

[0050] 4) The rectangular mold was transferred to a 10 wt% calcium chloride coagulation bath and immersed for 2 h to form a second layer of gel matrix structure with a double network. After dialysis and drying, the desired hydrogel biosensor was finally obtained.

[0051] Compared with Example 1, this embodiment reduces the design of the third waterproof layer. The material antibacterial zone is about 2.98cm 2 ; The contact angle is about 22°, such as Figure 2 As shown in the negative control in Figure B; the tensile strength of the hydrogel was tested using a universal testing machine. When its elongation at break was about 1344%, the maximum tensile strength was about 1.28 MPa; it did not break after 50 cycles of stretching at 500% strain; when it was applied to a biological strain sensor, there was a linear relationship between its resistance change rate and strain, and it would not grow bacteria during use, but it would absorb sweat and partially swell. After swelling, the resistance change rate and strain curve changed, affecting the monitoring results.

[0052] Example 3:

[0053] 1) preparing graphene-composite elastic spandex conductive fibers by solution dry spinning (first, preparing a 0.05 wt% graphene with a size of 2-4 microns, a 25 wt% polyether polyurethane prepolymer, and a 5 wt% mixed ethylenediamine / propylene glycol solution; after the reaction, adding a chain terminator ethanolamine at a concentration of 0.5‰ of the propylene glycol to obtain a graphene-composite spandex stock solution; spinning the stock solution through a spinning head under pressure; twisting, oiling, and winding under hot air conditions to obtain spandex; wherein the spinning head aperture is approximately 50 microns and the spinning rate is 100 m / s) and weaving the fibers into a fiber web;

[0054] 2) Design a rectangular mold (a groove structure is set in the middle of the rectangular mold. Small hooks are set in the middle of the longitudinal direction (depth direction) on the four sides of the groove to fix the fiber mesh. Several hooks are set in the length and width directions, and the hooks are set at a horizontal spacing of 0.5 cm. The mold groove is 5 cm long, 1.5 cm wide, and 1.5 mm deep). The fiber mesh is fixed to the hooks on the four sides of the groove of the rectangular mold as the first layer of conductive fiber mesh structure;

[0055] 3) Prepare a mixed solution of sodium alginate (viscosity 0.02-0.1 Pa·s (10 g / L, 20°C), concentration 3 wt%) and acrylamide (concentration 5 wt%, initiator ammonium persulfate, concentration 0.5 wt%, cross-linker MBAA, concentration 0.05 wt%, and polymerization accelerator tetramethylethylenediamine, concentration 0.03 wt%). Degassing by low-speed centrifugation (1000 rpm, time 5 min) is performed, followed by pouring the solution into a rectangular mold and in-situ polymerization (in-situ polymerization temperature 35°C, time 6 h).

[0056] 4) Transfer the rectangular mold to a 10 wt% calcium chloride coagulation bath and immerse for 2 h to form a second layer of gel matrix structure with a double network;

[0057] 5) After complete dialysis, the gel was immersed in a mixed solution of 0.25 v / v% stearic acid / 3 v / v% polydiethylsiloxane / 0.5 v / v% olive oil (solvent: dichloromethane) for hydrophobic modification to form a third waterproof layer structure on its surface. After completion, it was dried in nitrogen at 25°C for 8 h to finally obtain a hydrogel biosensor.

[0058] Compared with Example 1, this example reduces the addition of nanosilver. Figure 3 As shown in the negative control in B; the contact angle is about 153°; the tensile strength of the hydrogel is tested using a universal testing machine, and when its elongation at break is about 1368%, the maximum tensile strength is about 988kPa; it does not break after 50 cycles of stretching at 500% strain; when it is applied to a biological strain sensor, the resistance change rate is linearly related to the strain, and it does not absorb sweat during use, but mildew spots appear on the surface of the gel after a few days of use.

Claims

1. A method for preparing an antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh, characterized in that: The following steps are involved: 1) Graphene composite elastic spandex conductive fibers were prepared by solution dry spinning and woven into a fiber mesh; 2) designing a rectangular parallelepiped mold, and fixing the fiber mesh in the rectangular parallelepiped mold as a first layer of conductive fiber mesh structure; 3) preparing a sodium alginate / acrylamide mixed solution blended with nanosilver, and pouring the mixed solution into the rectangular parallelepiped mold after centrifugal degassing to perform in-situ polymerization; 4) Transfer the rectangular parallelepiped mold to Ca 2+ Immersed in a coagulation bath to form a second layer of gel matrix structure with a double network; 5) Demolding the rectangular parallelepiped from the mold, performing gel dialysis, and then immersing it in a stearic acid / organic silicone emulsion / vegetable oil mixed solution for hydrophobic modification to form a third waterproof layer structure on its surface. After drying, the hydrogel biosensor is finally obtained.

2. The method for preparing the antibacterial and waterproof hydrogel biosensor based on the conductive spandex fiber mesh according to claim 1, characterized in that: In the dry spinning process of the solution in step 1), graphene, polyurethane prepolymer, and a mixed diamine / diol solution are first prepared. After the reaction, a chain terminator is added to obtain a graphene-compounded spandex stock solution. The spandex stock solution is spun through a spinning head under pressure, and the spandex is twisted, oiled, and wound under hot air conditions to obtain spandex.

3. The method for preparing the antibacterial and waterproof hydrogel biosensor based on the conductive spandex fiber mesh according to claim 2, characterized in that: During the preparation of the spandex stock solution, the graphene has a size of 2-4 microns and a concentration of 0.01-0.1 wt %; the polyurethane prepolymer is one of polyethers, polyesters, and aliphatic isocyanates, and has a concentration of 20-35 wt %; the diamine is one of ethylenediamine, propylenediamine, and pentamethylenediamine; the diol is one of propylene glycol and butanediol, and the total concentration of the two is 2-8 wt %; the reaction temperature is 60-90° C., and the reaction time is 45-60 min; the chain terminator is one of ethanolamine, diethanolamine, triethanolamine, and N,N-dimethylethanolamine, and the concentration is 0.1-1‰ of the diol. During the spinning process, the aperture of the spinning head is 50-100 microns, and the spinning speed is 50-100 m / s.

4. The method for preparing the antibacterial and waterproof hydrogel biosensor based on the conductive spandex fiber mesh according to claim 1, characterized in that: In step 2), a groove is formed in the rectangular mold, and several hooks are evenly fixed on the inner wall of the groove in the middle position of the groove in the depth direction to fix the fiber mesh. The spacing between adjacent hooks is 0.5-1 cm / piece, and the depth of the rectangular mold is 1-3 mm.

5. The method for preparing the antibacterial and waterproof hydrogel biosensor based on the conductive spandex fiber mesh according to claim 1, characterized in that: In step 3), the prepared mixed solution contains a crosslinker, an initiator, and a polymerization promoter. The size of the nanosilver is 20-50 nm, and the addition amount is 0.01-0.05 wt %. The viscosity of the sodium alginate at 10 g / L and 20° C. is 0.02-0.1 Pa·s, and the concentration is 3-4 wt %. The concentration of the acrylamide is 3-10 wt %. The concentration of the crosslinker N,N'-methylenebisacrylamide (MBAA) is 0.02-0.10 wt %. The initiator is one or more of ammonium persulfate, sodium persulfate, and potassium persulfate, and the concentration is 0.5-0.95 wt %. The polymerization promoter is tetramethylethylenediamine, and the concentration is 0.025-0.08 wt %. The centrifugal degassing rate is 1000-2000 rpm, and the time is 3-8 min; The in-situ polymerization temperature is 30-35° C. and the time is 4-12 hours.

6. The method for preparing the antibacterial and waterproof hydrogel biosensor based on the conductive spandex fiber mesh according to claim 1, characterized in that: In step 4), during the coagulation bath, the Ca 2+ Specifically, it is one or more of calcium chloride, calcium bicarbonate, and calcium gluconate, with a concentration of 5-20wt%, and the immersion time is 30min-4h.

7. The method for preparing an antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh according to claim 1, wherein: In step 5), during the preparation of the stearic acid / organic silicone emulsion / vegetable oil mixed solution, the stearic acid concentration is 0.05-0.5 v / v%; the organosilicon is one or more of polydiethylsiloxane, dodecyltriethylsilane, polymethyltrifluoropropylsiloxane, polymethylvinylsiloxane, hexadecyltriethoxysilane, polydimethylsiloxane, hexadecyltrimethoxysilane, and methyltriethoxysilane, with a concentration of 1-5 v / v%; the vegetable oil is one or more of olive oil, soybean oil, and sesame oil, with a concentration of 0.5-2 v / v%; and the solvent is one of dichloromethane, acetone, and trichloroethane. The drying is carried out using nitrogen drying, the time is 6-12 hours, and the temperature is 25-30°C.

8. An antibacterial and waterproof hydrogel biosensor based on a conductive spandex fiber mesh, characterized in that: The method is as described in any one of claims 1 to 7.

Images