Multifunctional hydrogel coatings with high antimicrobial loading efficiency and pH-responsive properties for urinary catheter applications
Multifunctional hydrogel coatings with high antimicrobial loading efficiency and pH-responsive properties for urinary catheter applications
Jiru Miao ab, Xiang Wu bc, Yue Fang b, Mingzhu Zeng b, Zhimao Huang b, Mi Ouyang 
*a and Rong Wang *bd
aCollege of Chemical Engineering, Zhejiang University of Technology, Hangzhou, 310014, P. R. China. E-mail: ouyang@zjut.edu.cn
bZhejiang International Scientific and Technological Cooperative Base of Biomedical Materials and Technology, Zhejiang Engineering Research Center for Biomedical Materials, Cixi Institute of Biomedical Engineering, Ningbo Institute of Materials Technology and Engineering, Chinese Academy of Sciences, Ningbo, 315300, P. R. China. E-mail: rong.wang@nimte.ac.cn
cDepartment of Hepatobiliary and Pancreatic Surgery, Affiliated Li Huili Hospital, Ningbo University School of Medicine, Ningbo, 315000, China
dUniversity of Chinese Academy of Sciences, Beijing, 101408, P. R. China
First published on 20th March 2023
2.2 Preparation of hydrogel coating
Flat PDMS sheets were cut into sizes of 1 cm × 3 cm, cleaned with ethanol, and subjected to glow discharge treatment at a current of 15 mA for 3 min (Glow Discharge Cleaning System, easiGlow 91000, PELCO, United States). The PDMS sheets were then soaked in a benzoyl peroxide solution (10 wt% in acetone) for 5 min, followed by washing with isopropanol, and drying in nitrogen. A pre-gel solution containing 22.3 g of SBMA, 90 mg of poly(ethylene glycol) dimethacrylate, 23 mg of ammonium persulfate, and 20 mL of deionized water was prepared, and 3.7 g of TA (8 wt% of the total weight of the solution) was added. The pre-gel solution was degassed using nitrogen bubbling for 30 min. The PDMS sheet was immersed in the solution, and it was placed in a water bath at 80 °C for 90 min to thermally initiate the polymerization. The PDMS sheet with hydrogel coating formed on its surface was collected, and washed using deionized water. The PDMS sheets with hydrogel coatings prepared from solution with and without 8 wt% of TA were denoted as PT8 and PT0, respectively. After that, the PT8-coated substrate was immersed in 10 mL of physiological saline solution containing 10 mg mL−1 PVP-I, 11.25 mg mL−1 copper sulfate, or 0.2 mg mL−1 nitrofurazone (common concentrations used in the clinic for antibacterial purposes) at 37 °C for 24 h. The antimicrobial-loaded coatings were named PT8-I, PT8-Cu and PT8-NFZ, respectively. PDMS and PT0 substrates were treated with the antimicrobial agent solution in the same procedure for comparison. The concentration of iodine and copper in the solution before and after the coating process was determined by inductively coupled plasma optical emission spectrometry (ICP-OES, ARCOS, SPECTRO, Germany). The concentration of nitrofurazone was determined by measuring the absorbance of the solution at 375 nm using a UV-Vis spectrophotometer (Cary 300, Agilent, United States). The loading content of the antimicrobial agents in the coating was calculated by subtracting the remaining content of antimicrobial agents in the solution from the total content. Silicone Foley catheters were coated in the same procedure for in vivo implantation experiments.
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