Optimization and integration of nanosilver on polycaprolactone nanofibrous mesh for bacterial inhibition and wound healing in vitro and in vivo
Authors Liu M, Luo G, Wang Y, He W, Liu T, Zhou D, Hu X, Xing M, Wu J
Received 28 April 2017
Accepted for publication 9 August 2017
Published 12 September 2017 Volume 2017:12 Pages 6827—6840
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Editor who approved publication: Dr Linlin Sun
Menglong Liu,1,2 Gaoxing Luo,1,2 Ying Wang,1,2 Weifeng He,1,2 Tengfei Liu,1,2 Daijun Zhou,1,2 Xiaohong Hu,1,2 Malcolm Xing,1,3 Jun Wu1,2,4
1State Key Laboratory of Trauma, Burn and Combined Injury, Institute of Burn Research, Southwest Hospital, the Third Military Medical University, 2Department of Burns, Chongqing Key Laboratory for Disease Proteomics, Chongqing, People’s Republic of China; 3Department of Mechanical Engineering, University of Manitoba, Winnipeg, MB, Canada; 4Department of Burns, the First Affiliated Hospital of Sun Yat-Sen University, Guangzhou, People’s Republic of China
Abstract: Bacterial infection is a major hurdle to wound healing, and the overuse of antibiotics have led to global issue, such as emergence of multidrug-resistant bacteria, even “super bacteria”. On the contrary, nanosilver (NS) can kill bacteria without causing resistant bacterial strains. In this study, NS was simply generated in situ on the polycaprolactone (PCL) nanofibrous mesh using an environmentally benign and mussel-inspired dopamine (DA). Scanning electron microscopy showed that NS uniformly formed on the nanofibers of PCL mesh. Fourier transform infrared spectroscopy revealed the step-by-step preparation of pristine PCL mesh, including DA coating and NS formation, which were further verified by water contact angle changing from hydrophobic to hydrophilic. To optimize the NS dose, the antibacterial activity of PCL/NS against Staphylococcus aureus, Escherichia coli and Acinetobacter baumannii was detected by bacterial suspension assay, and the cytotoxicity of NS was evaluated using cellular morphology observation and Cell Counting Kit-8 (CCK8) assay. Then, inductively coupled plasma atomic emission spectrometry exhibited that the optimized PCL/NS had a safe and sustained silver release. Moreover, PCL/NS could effectively inhibit bacterial infection in an infectious murine full-thickness skin wound model. As demonstrated by the enhanced level of proliferating cell nuclear antigen (PCNA) in keratinocytes and longer length of neo-formed epidermis, PCL/NS accelerated wound healing by promoting re-epithelialization via enhancing keratinocyte proliferation in infectious wounds.
Keywords: polycaprolactone nanofibrous mesh, mussel inspired, nanosilver, anti-infection activity, wound healing, re-epithelialization
Bacterial infection is considered as the main hurdle to natural wound healing process.1–3 Antibiotics are generally used to provide the antibacterial activity in the clinical setting, but their overuse has caused antibiotic resistance to bacterial pathogens, which further led to the emergence of multidrug-resistant (MDR) bacteria.4,5 Thus, an alternative solution is urgently needed.
Silver materials, such as nanosilver (NS) with nanodimensions of 1–100 nm and silver nanoclusters with ultrasmall size of <2 nm, which possess excellent antibacterial activity, have attracted great interest to solve the antibiotic resistance problem recently.6,7 Specifically, NS has a broad-spectrum antimicrobial activity and highly killing efficacy by destroying the bacterial DNA and membrane, as well as inhibiting respiratory enzyme activity.8 More importantly, few studies have reported that bacteria were resistant to NS, so NS is a promising candidate to replace antibiotics.8,9 However, the cytotoxicity of silver nanoparticles (AgNPs) has aroused public vigilance in recent years.10 Several reports have found that the potential toxic effect caused by NS occurred only at high concentrations, and incorporated NS into biomaterials probably reduce the toxicity of NS.11–13 Consequently, it is available to incorporate an optimized concentration of NS into a material to prepare an antibacterial wound dressing without cytotoxicity.
Another essential problem that needs to be taken into account is the NS synthetic method. Generally, NS is prepared using physical or chemical synthetic strategies. Nevertheless, the conventional physical methods are low yield and high energy consumption, and the general chemical methods are expensive and toxic to environment.14–16 This makes an easy and environmentally friendly way to generate NS, which is very desirable for the extended application of NS. Recently, dopamine (DA) is found to be gently self-polymerized under alkaline condition because of its mussel adhesive property, and the formed polydopamine (PD) coating possesses super adhesive ability and strong reduction property.17,18 Only by the coating of DA, silver ion will be efficiently reduced to NS and then immobilized on the surface of biomaterials.19 Furthermore, DA has been well demonstrated to be biocompatible and nontoxic to human body.20,21 Therefore, DA coating is an ideal way to prepare NS.
Apart from the antibacterial property, good biocompatibility and promotion of re-epithelialization are also important factors for an ideal wound dressing.22,23 Polycaprolactone (PCL) is a biocompatible and biodegradable material approved by the US Food and Drug Administration (FDA).24,25 The electrospun PCL nanofibrous mesh possesses high porosity and good mechanical strength, which are important factors for wound dressings.22,26,27 Moreover, the high specific surface area and interwoven nanofibers endow PCL nanofibrous mesh enough space for antibacterial agents residing.28 Due to these attributes, PCL nanofibrous mesh is a predominant substrate to accommodate NS for an antibacterial wound dressing.
The aim of this study was to prepare a biocompatible and antibacterial wound dressing without increasing bacterial resistance. Hence, we assumed, in situ, different doses of synthesized NS on the PCL nanofibrous mesh using eco-friendly DA (Figure 1). Then, the screening of optimized PCL/NS was determined by antibacterial activity and cytotoxicity test. Finally, the efficacy of PCL/NS on infectious wounds in vivo was also adequately investigated.
Figure 1 Illustrative diagrams of the procedure for PCL/NS preparation and the biological effect of PCL/NS in vitro and in vivo.
Materials and methods
PCL (molecular weight [MW] =70,000), dimethylformamide (DMF) and dichloromethane were purchased from Sigma-Aldrich Co. (St Louis, MO, USA). DA hydrochloride was purchased from Solarbio Science & Technology Co., Ltd. (Beijing, People’s Republic of China). Silver nitrate (AgNO3) was purchased from Sangon (Shanghai, People’s Republic of China).
Animals were purchased from the Experimental Animal Department of the Third Military Medical University. All the experimental protocols were approved by the Institutional Animal Care and Use Committee of the Third Military Medical University, and all methods were performed according to the guidelines of the Third Military Medical University.
Preparation of the PCL/NS nanofibrous mesh
PCL nanofibrous mesh was fabricated using an electrospinning process as previously described.26 PCL was first dissolved in DMF/dichloromethane (1:4, v/v) at a concentration of 10 wt%; then, the electrospinning process was carried out with the following parameters: applied voltage, 18 kV; solution feed rate, 1.2 mL/h; spinning time, 4 h; syringe needle gage, 21 G; distance between needle and collector, 15 cm. Subsequently, PCL nanofibrous mesh was immersed in a DA solution (2 mg/mL in 10 mM Tris–HCL, pH 8.5) at 25°C for 16 h. Finally, the DA-coated mesh was immersed in an aqueous silver nitrate solution (AgNO3) at different concentrations (0.5 mM, 1 mM, 2 mM) for 8 h in darkness at 25°C. Then, the specimens were washed with DDH2O three times to remove the residual silver ions and dried at 37°C. The DA- and AgNO3-treated specimens were indicated as PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0, which are discussed in the following sections.
Characterization of the PCL/NS nanofibrous mesh
The morphology and structure of PCL/NS nanofibrous mesh were observed using scanning electron microscopy (SEM; Hitachi S-3400N; Hitachi Ltd., Tokyo, Japan), and the diameter of NS was measured using ImageJ software by two independent researchers (five SEM images). The chemical structure of the surface of PCL, PCL/DA and PCL/NS were characterized using a PerkinElmer Fourier transform infrared (FTIR) spectrometer (100S). The water contact angle was investigated by a contact angle analyzer (Theta Lite 101; Biolin Scientific, Stockholm, Sweden).
Bacterial suspension assay and determination of biofilm formation
The bacterial suspension assay was adapted from previous report with a little modification.29 The commercial bacterial strains including Staphylococcus aureus (American Type Culture Collection [ATCC] 25923, Manassas, VA, USA), Escherichia coli (ATCC 25922) and Acinetobacter baumannii (ATCC 19606) were used for this assay. The S. aureus and E. coli are nondrug-resistant bacteria, and the A. baumannii is a multidrug-resistant bacterium. Briefly, the log-phase bacterial suspension of S. aureus, E. coli and A. baumannii was first diluted at the predetermined starting concentration (optical density [OD] at 600 nm; OD600 =0.07) in Luria-Bertani (LB) medium. Then, 250 μL of diluted bacterial solution was added into each well of a 48-well plate, and the sterilized PCL, PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 samples, 8×8 mm in size, were separately immersed in the bacterial solution. Finally, the 48-well plate was kept at 37°C in a shaker incubator under 50 rpm for 24 h. To detect the number of bacteria, 100 μL of bacterial solution was transferred into a 96-well plate, and the OD600 value was measured. To further evaluate the inhibition efficiency of NS, the bacterial solution after co-incubation was diluted 10,000× in saline solution and 10 μL of diluted solution was uniformly coated on Mueller–Hinton agar plate. After 24 h of incubation at 37°C, the bacterial colonies on agar plate were photographed. In this study, untreated bacterial solution was served as the negative control group, and the PCL and PCL/DA groups were served as the control groups.
To further detect the formation of biofilms on the surfaces of these samples, the PCL, PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films were observed under SEM, and the areas covered by biofilms or bacteria were measured using IPP 6.0 software as previously described.30,31
In vitro cytotoxicity test
Green fluorescent protein (GFP) transgenic neonatal mice (1–3 days) were obtained from the Experimental Animal Department of the Third Military Medical University, and the experimental protocol was approved by the Institutional Animal Care and Use Committee of the Third Military Medical University. The fibroblasts were isolated from the neonatal mice according to the previous study.32 Briefly, the skin tissue of neonatal mice was immersed in 0.5 mg/mL Dispase II (Sigma-Aldrich Co.) at 4°C overnight to separate the epidermis and dermis. Then, the isolated dermis was minced and digested by trypsin (0.25 mg/mL; Boster, Wuhan, People’s Republic of China) for 10 min. Subsequently, 3× Dulbecco’s Modified Eagle’s Medium (DMEM; Thermo Fisher Scientific, Waltham, MA, USA) containing 10% fetal bovine serum (FBS; Thermo Fisher Scientific) was added to terminate the digestion. Finally, after the mixture solution centrifuged at 1,000 rpm for 6 min, the cells were harvested and incubated in DMEM containing 10% FBS, penicillin (100 U/mL) and streptomycin (100 μg/mL) at 37°C in an incubator containing 5% CO2.
The third-passage fibroblasts were seeded on the films as follows. First, the PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films were punched into 6 mm-diameter disks. Second, after sterilized with 75% alcohol, the disks were washed with phosphate-buffered solution (PBS) three times and then placed into each well of a 96-well plate. Third, 3,000 prepared fibroblasts in 100 μL DMEM containing 10% FBS were added into each well. At days 1, 3, 5 post seeding, the films were transferred into another 96-well plate, and 100 μL of DMEM together with 10 μL Cell Counting Kit-8 (CCK8) solution was added to each well. After incubation at 37°C for 2 h, the films were removed, and the absorbance of reserved solution was measured at 450 nm by an enzyme-linked immunosorbent assay reader (Thermo Varioskan Flash, Winooski, VT, USA). Moreover, the morphology of cells on the films at day 3 post seeding was observed by a fluorescence microscopy (Olympus Corporation, Tokyo, Japan).
Silver ion release test
The PCL/NS1.0 films were each cut into (10×10 mm) pieces (n=3) and immersed in 6 mL of PBS in darkness at 37°C. At each predetermined time point, ie, days 1, 3, 5 and 7, the corresponding PBS was entirely harvested and analyzed by inductively coupled plasma atomic emission spectrometry (ICP-AES; Leeman, Hudson, NH, USA).
In vivo wound healing assessment
BALB/c adult mice (male, 20–25 g) used in the experiment were acquired from the Experimental Animal Department of the Third Military Medical University. The animals were individually raised in plastic cages under standardized conditions (room temperature, 25°C; relative humidity, 50%; circadian rhythm, 12 h).
The effect of PCL/NS1.0 on wound healing was detected using an infectious murine full-thickness skin defect wound model based on previous reports with a slight modification.33,34 BALB/c mice were individually anesthetized using an intraperitoneal injection of 1% pentobarbital; then, the dorsal surface was shaved. After rinsed with 75% alcohol, two 6 mm-diameter full-thickness wounds were prepared using a sterile 6 mm punch biopsy tool on either side of the back. Immediately, bacterial suspension of E. coli (10 μL) and S. aureus (10 μL), which were standardized to 0.5 McFarland standards (108 colony-forming units [CFU]/mL), was dropped on the surface of each wound. Then, the wounds were photographed by a digital camera to represent the starting wound area. After that, the wounds were covered with sterile PCL, PCL/DA or PCL/NS1.0 films, and an adhesive biological membrane (NPWT-1, Negative Pressure Wound Therapy Kit; VSD Bio-Tech Co., Wuhan, People’s Republic of China) was used to keep the position. In this study, the mice that had not treated with bacterial suspension and wound dressing were regarded as the blank group, while the mice that had treated only with bacterial suspension were regarded as the control group. Finally, the wounds were photographed at days 1, 3, 5 and 7 post surgery, and the nonhealing wound areas were carefully measured using IPP 6.0 software by two independent researchers. The closed wound area was calculated using the following formula:35
where I refers to the number of pixels of the starting wound area, and R refers to the number of pixels of the nonhealing wound area at the predetermined time.
Hematoxylin–eosin (H&E) staining
The cutaneous wound tissues (10×10 mm) were carefully harvested from mice sacrificed at day 7 post surgery. After fixing with 4% paraformaldehyde for 24 h, the tissues were embedded in paraffin and sliced at a thickness of 5 μm, then stained with H&E. The length of the newly generated epidermis, which is defined as the distance from the border between unwounded skin tissue and wound area to the advancing edges of the epidermis,36 was measured using ImageJ software. The number of inflammatory cells infiltrated in the wound edge was counted using ImageJ software as previously described.37 All measurements using software were performed by two independent researchers.
The expression of proliferating cell nuclear antigen (PCNA) in keratinocytes at day 7 post surgery was detected by immunohistochemistry. Briefly, after deparaffinized and rehydrated, the wound tissue sections were incubated at 95°C in a sodium citrate buffer bath for heat-mediated antigen retrieval. Then, the sections were incubated with 3% H2O2 at 25°C. After 15 min of incubation, the sections were washed with PBS three times, and then blocked in 10% normal goat serum (Zhongshan Bio-Tech Co., Ltd., Guangdong, People’s Republic of China) at 37°C for 30 min, followed by incubation with primary antibody (anti-PCNA antibody ab15497, 1:200 dilution; Abcam, Cambridge, UK) at 4°C overnight. Subsequently, after being washed with PBS three times, the sections were incubated with biotinylated goat anti-rabbit IgG antibody (Zhongshan Bio-Tech Co., Ltd.) at 37°C for 30 min. Then, the sections were further incubated with avidin–peroxidase reagent (Zhongshan Bio-Tech Co., Ltd.) at 37°C for 30 min. Finally, the sections were stained with 3,3′-diaminobenzidine tetrahydrochloride and hematoxylin. The sections were photographed under an optical microscope (CTR6000; Leica Microsystems, Wetzlar, Germany), and the number of PCNA-positive keratinocytes per field in the newly formed epidermis was counted by two independent researchers.
Data are presented as mean ± SD and analyzed by one-way ANOVA. Statistical significance was accepted at p<0.05 (*p<0.05 and **p<0.01).
Characterization of PCL/NS nanofibrous mesh
SEM images of the PCL, PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 are shown in Figure 2. The native PCL film was composed of a nanofibrous network, and the diameter of the nanofibers ranged from 200 nm to 1,000 nm. No significant change was observed in the morphology after DA coating, except that the nanofibers of PCL/DA were a bit rougher than that of pristine PCL. However, it was clearly seen that plenty of AgNPs were uniformly distributed on the nanofibers of PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films, as shown in Figure 2C–E, and the density of NS gradually increased with the increase of the concentration of AgNO3 rising. As shown in Figure 2F, the average diameter of NS measured by ImageJ software was 73.3±33.6 nm, 74.3±30.4 nm and 72.2±26.3 nm in PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films, respectively, and no significant difference was observed among them.
FTIR analysis of the PCL, PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films is shown in Figure 3. In PCL spectrum, two characteristic absorption peaks at 1,166 cm−1 and 1,726 cm−1 were related to C–O–C and C=O bonds, and peaks at 2,864 cm−1 and 2,930 cm−1 corresponded to the C–H bond.33,38,39 After DA coating, a broad peak around 3,100–3,600 cm−1 corresponding to the stretching vibration band of phenolic hydroxyls was observed in the spectrum of PCL/DA.13 The peak became sharper in the PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 spectra, suggesting the interaction between NS and DA.40 In addition, the stronger peaks at 1,166 cm−1, 1,726 cm−1 and 2,930 cm−1 also indicated the deposition of NS on the PCL nanofibers.
Figure 3 FTIR spectra of the following: A, PCL; B, PCL/DA; C, PCL/NS0.5; D, PCL/NS1.0; E, PCL/NS2.0 (n=3).
As shown in Figure 4, the water contact angle of PCL, PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 was 107.9°±1.2°, 27.7°±1.7°, 25.7°±3.8°, 27.5°±4.0° and 29.2°±3.0°, respectively.
Figure 4 Water contact angle of (A) PCL, (B) PCL/DA, (C) PCL/NS0.5, (D) PCL/NS1.0 and (E) PCL/NS2.0 (n=3).
In vitro antibacterial property of PCL/NS
A bacterial suspension assay was used to detect the antibacterial activity of PCL, PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films. After 24 h of incubation with bacterial suspensions, the OD600 values of the PCL/NS1.0 and PCL/NS2.0 groups were significantly lower than those of the control, PCL, PCL/DA and PCL/NS0.5 groups for S. aureus, E. coli and A. baumannii (Figure 5A–C). No significance was observed in the OD600 values between the PCL/NS1.0 and PCL/NS2.0 groups. Furthermore, in line with the OD600 values, the numbers of bacterial colonies cultured from the co-incubation suspension of S. aureus, E. coli and A. baumannii (Figure 5D–I) were obviously more in the control, PCL, PCL/DA and PCL/NS0.5 groups than those in the PCL/NS1.0 and PCL/NS2.0 groups.
The bacteria can adhere to a surface and secrete a polymeric substance matrix to form biofilms, which protect bacteria from external harm such as antibiotics.41,42 Therefore, it is important for a wound dressing to inhibit the formation of biofilms when covered on the wound.1 To further investigate the formation of biofilms on the surfaces of PCL, PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films, the samples after co-incubation with bacteria were observed by SEM, and the areas covered by biofilms or bacteria were measured. As shown in Figure 6, extensive bacterial colonization produced by the proliferation of S. aureus, E. coli or A. baumannii was grouped on the surfaces of PCL, PCL/DA and PCL/NS0.5 films, and partial bacteria were encased in the polymeric matrix, which suggested the formation of biofilms.43,44 In contrast, even though several bacteria could be observed on the surfaces of PCL/NS1.0 and PCL/NS2.0 films, no obvious polymeric matrix was found around the S. aureus, E. coli and A. baumannii bacteria, indicating that PCL/NS1.0 and PCL/NS2.0 could inhibit the formation of biofilms. Moreover, the area covered by the biofilms or bacteria on PCL/NS1.0 and PCL/NS2.0 surfaces were significantly smaller than that on the PCL, PCL/DA and PCL/NS0.5 surfaces.
Cytotoxicity of PCL/NS
To evaluate the cytotoxicity of NS, cell morphology observation and a CCK8 assay were used. As shown in Figure 7A–C, the fibroblasts at day 3 post seeding showed a characteristic spindle shape with well adhesion and spreading on the PCL/DA, PCL/NS0.5 and PCL/NS1.0 films. However, the number of fibroblasts was obviously less on the PCL/NS2.0 films (Figure 7D). The CCK8 result also showed that the OD value of the PCL/NS2.0 group was significantly lower than the PCL/NS0.5 and PCL/NS1.0 groups at day 3 post seeding (Figure 7E). Nevertheless, no significant differences in the OD values were observed among the PCL/DA, PCL/NS0.5 and PCL/NS1.0 groups.
Taking the results of bacterial suspension assay and cytotoxicity evaluation into account, the PCL/NS1.0 that showed excellent antibacterial property and biocompatibility was selected as the optimized film for the following experiments.
Silver ion release in PBS
Silver ions released from PCL/NS1.0 were detected at days 1, 3, 5 and 7 in PBS by ICP-AES (Figure 8). At day 1, a burst release of silver ions was observed, whose concentration was about 0.32 μg/mL. Then, the silver ions gradually released slowly in the following time points. After 7 days, sustained silver ion release could still be observed, and the total released concentration of silver ions was up to 0.57 μg/mL.
Figure 8 Silver ion release profile of PCL/NS at days 1, 3, 5 and 7.
Effect of the PCL/NS1.0 on the healing of infectious wound in vivo
The effect of PCL/NS1.0 nanofibrous mesh on the healing of infectious wound was detected by an infectious murine full-thickness skin defect wound model. As shown in Figure 9, no significant difference was observed in the wound closure area among all the groups at day 1 post surgery. Nevertheless, at day 3 post surgery, thick yellow pus was found in the wounds of the control, PCL and PCL/DA groups (Figure 9A). In addition, the skin around the wounds was obviously red and swollen in those groups. However, exudate was seldom found in the wounds of blank and PCL/NS1.0 groups, and the area of wound closure in these groups was significantly larger than that in the PCL group. At days 5 and 7, there were still plenty of purulent exudates in the wounds of the control, PCL and PCL/DA groups, and the wound healing area in these groups was significantly lower than the blank and PCL/NS1.0 groups. After 7 days, the area of wound closure was 78.7%, 55.3%, 38.3%, 48.5% and 77.8% in the blank, control, PCL, PCL/DA and PCL/NS1.0 groups, respectively (Figure 9B). No significant difference in the area of wound closure was observed between the blank and PCL/NS1.0 groups at all days.
The length of newly generated epidermis at day 7 post surgery was further histologically analyzed by H&E staining. The results showed that the length of neo-formed epithelium was significantly longer in the blank and PCL/NS1.0 groups than that in the control, PCL and PCL/DA groups (Figure 10).
Effect of PCL/NS1.0 on keratinocyte proliferation
As PCL/NS1.0 nanofibrous mesh could promote re-epithelialization (Figure 10), we further investigated the underlying mechanism, and the PCNA levels in keratinocytes were detected by immunohistochemistry. We could found more PCNA-positive keratinocytes at the wound edge in the blank and PCL/NS1.0 groups, compared with other groups, as shown in Figure 11. Moreover, the statistical analysis result also revealed that the number of positive keratinocytes per field was higher in the blank and PCL/NS1.0 groups than that in other groups.
Effect of PCL/NS1.0 on inflammation in vivo
To investigate the effect of PCL/NS1.0 on inflammation, the inflammatory cells infiltrated in the subcutaneous areas of wound edge after 7 days have been histologically analyzed and counted. As shown in Figure 12, the number of inflammatory cells infiltrated in the wound edge was much more in the control, PCL and PCL/DA groups than that in the PCL/NS1.0 group, but no significant difference was observed between the blank and PCL/NS1.0 groups.
Cutaneous wounds that are infected or at risk of infection are known to be a global issue.1,45 Management of wound dressings containing antibacterial agents is expected to be a feasible way to solve the problem.1 However, improper use of antibiotics has led to serious antibiotic resistance problem, so it is necessary to find an alternative approach. To meet this demand, a PCL nanofibrous mesh impregnated with NS nanocomposite was prepared using environmentally friendly and mussel-inspired DA in this work (Figure 1).
The SEM results showed that the prepared PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 had a three-dimensional network structure, and the nanofibers were uniformly decorated with several spherical NSs (Figure 2). This result is caused by the reducibility of catechol group in DA, which could efficiently benefit for the silver reduction without destroy the primary scaffold structure.18,46 To further investigate the surface chemical structure of PCL/NS after DA coating and NS deposition, the FTIR analysis was used. As shown in Figure 3, the results demonstrated the successful DA coating and NS formation. Because the surface hydrophilicity could influence the biological behavior of scaffold material,46 water contact angle was measured subsequently. We found that the water contact angle was significantly lower on the PCL/DA, PCL/NS0.5, PCL/NS1.0 and PCL/NS2.0 films than that on the pristine PCL (Figure 4), indicating that the surface hydrophilicity was obviously improved after DA coating and NS deposition, which might be helpful for better cytocompatibility. Overall, PCL/NS was successfully fabricated, and the surface structure was well improved.
To detect the antibacterial activity of prepared wound dressing in vitro, the bacterial suspension assay was used and the biofilms formation was detected. As shown in Figure 5, the OD600 values of the PCL/NS1.0 and PCL/NS2.0 groups were significantly lower than those of other groups for the E. coli, A. baumannii (Gram-negative bacteria) and S. aureus (Gram-positive bacteria), indicating that they had good and broad-spectrum antibacterial property. Furthermore, the count of bacterial colonies was also less in the PCL/NS1.0 and PCL/NS2.0 groups, demonstrating the released NS from the two films could efficiently inhibit the growth of bacteria. More importantly, PCL/NS1.0 and PCL/NS2.0 could also inhibit the formation of biofilms (Figure 6), which is essential for a wound dressing in practical application.1 This may be because that NS-containing biomaterials could fight bacterial adhesion and clonal growth.30,47 Although the bactericidal mechanisms of NS are not fully understood,8 a possible explanation for the excellent antibacterial activities of PCL/NS1.0 and PCL/NS2.0 could be speculated based on previous reports and our results as follows: NSs have nanodimensions of 1–100 nm and large surface-to-volume ratio. The NS can interact with the sulfur-containing biomolecules of bacterial membrane protein and cause structural changes and damages to the cell membrane.48,49 Moreover, the interaction between NS and thiol groups of protein may induce the release of reactive oxygen species (ROS), which then inhibits the respiratory enzymes and consequently leads to cell death.50,51 In addition, the silver ions (Ag+) released from the NS are able to bind to the negative charge of bacterial cell wall and render bacteria more permeable.52 Then, silver ions and NS enter the bacterial cell body and damage the sulfhydryl group in protein, which severely interfere with the DNA replication, causing cell death in the end.53 As shown in Figure 2, the diameter of NS (approximately 70 nm) incorporated into the PCL mesh was well below 100 nm, meaning that the bacterial membrane that contacted with the film could be efficiently damaged by the nanoparticles and finally leads to the cell death.8 Furthermore, the silver ion release profile of PCL/NS1.0 revealed that silver ions rapidly released at day 1 and the concentration of silver ions (0.32 μg/mL) is enough to kill bacteria.54,55 In addition, after 3, 5 and 7 days, constant silver release was still observed, meaning that bacterial inhibition efficacy of PCL/NS1.0 was prolonged and effective. Therefore, it suggests that PCL/NS1.0 may inhibit bacterial growth by destroying the bacterial membrane and DNA, as well as inhibiting respiratory enzyme activity.
The cytotoxicity was a main concern for the application of NS, so the cell morphology observation and CCK8 assay were used for toxic evaluation. As shown in Figure 7A–D, at day 3 post seeding, a lot of fibroblasts grew well on the surface of PCL/DA, PCL/NS0.5 and PCL/NS1.0 films, but cells were seldom observed on the surface of PCL/NS2.0 film. This indicated that the PCL/NS2.0 film was harmful for the cell growth. Then, the CCK8 result also showed that the cell viability in the PCL/NS2.0 group was worse than the PCL/NS0.5 and PCL/NS1.0 groups (Figure 7E), which further indicated the obvious cytotoxicity of PCL/NS2.0. Nevertheless, the cell viability in PCL/DA was similar with the PCL/NS0.5 and PCL/NS1.0 groups at days 1, 3 and 5, suggesting that the NS in the PCL/NS0.5 and PCL/NS1.0 films could not cause significant cytotoxicity. In line with this result, Figure 8 shows that total silver concentration after 7 days was approximately 0.57 μg/mL, which was well below the toxic concentration of human body (10 μg/mL),56 suggesting that the PCL/NS1.0 was biocompatible with human beings. Therefore, these results indicated that the cytotoxicity of NS occurred at high concentration as previously described.11,12
Because of effective antibacterial activity without observed cytotoxicity, PCL/NS1.0 was chosen as the optimized film for the next experiments. The abovementioned results also demonstrated that an optimized concentration of NS was successfully found as expected.
Finally, the real effect of PCL/NS1.0 on bacterial invasion and wound healing in vivo was detected using an infectious murine full-thickness skin defect wound model. As shown in Figure 9, from day 3 to day 7, the wounds in the control, PCL and PCL/DA groups were full of purulent exudates, indicating that serious infection occurred. However, in the PCL/NS1.0 group, the wounds were clean and no purulent exudate was observed, which was similar with the blank group, suggesting that the PCL/NS1.0 could efficiently inhibit bacterial growth in vivo. At day 7, about 80% of wound area has been closed in the blank and PCL/NS1.0 groups, but the closed wound area was less than 61% in the control, PCL and PCL/DA groups. This result indicated that infection severely interferes with the normal wound healing in the control, PCL and PCL/DA groups, but coverage of PCL/NS1.0 with effective antibacterial activity could maintain a natural and aseptic microenvironment for wound healing.1
Re-epithelialization is a necessary parameter for wound healing, so the length of newly generated epidermis of tissue sections at day 7 post surgery stained with H&E was histologically analyzed. The results showed that the length of newly regenerated epidermis was significantly longer in the PCL/NS1.0 group than that in the control, PCL and PCL/DA groups, but was similar with that in the blank group (Figure 10). This indicated that PCL/NS1.0 could also accelerate re-epithelialization, which might be due to the good antibacterial activity and biocompatiblility.35,57
To further investigate the underlying mechanism, the PCNA protein, a cell proliferation marker, was detected by immunohistochemistry. In line with the promotion of re-epithelialization, we found that PCL/NS1.0 could enhance PCNA expression in keratinocytes, compared with the control, PCL and PCL/DA groups (Figure 11). This was consistent with the previous study that wound dressing containing NS could promote cell proliferation in vivo.35 In addition, the effect of PCL/NS1.0 on inflammation in vivo was also detected. The result showed that PCL/NS1.0 could prevent the bacterial infection and the subsequent severe inflammation response (Figure 12), which was benefit for the wound healing.37,58
The wound healing is a complex biological process including three stages: inflammation, new tissue regeneration and remodeling.59 The active keratinocyte proliferation and fast re-epithelialization are important for the new tissue regeneration, while the bacterial infection is the main cause of impaired healing.1,59,60 Wound dressings impregnated with antimicrobials can prevent local bacterial infection and maintain the natural microenvironment for cell proliferation and tissue regeneration to promote wound healing.3,61 As described earlier, compared with the control, PCL and PCL/DA groups, the biocompatible PCL/NS1.0 was efficient to protect the wounds from bacterial infection (Figure 9) and maintain a natural and aseptic wound microenvironment without severe inflammation response to promote keratinocyte proliferation (Figures 11 and 12). Thus, the re-epithelialization process was much faster in the PCL/NS1.0 group than that in the control, PCL and PCL/DA groups (Figure 10). Overall, we considered that PCL/NS1.0 with good biocompatibility and antibacterial activity could protect the wounds from bacterial infection and promote wound healing by accelerating re-epithelialization via enhancing keratinocyte proliferation.
The current study reported an ideal wound dressing prepared by an optimized concentration of NS incorporated into PCL nanofibrous mesh using environmentally friendly DA. This wound dressing was biocompatible and effective for inhibiting bacterial growth both in vitro and in vivo, resulting in rapid re-epithelialization and wound closure in the infectious murine wound model. These results indicated that PCL/NS1.0 had a promising application in wound management.
This work was supported by the State Key Laboratory Funding (SKLZZ201221) and National Special Scientific Projects of Public Welfare Industry Funding of China (No 201502015).
The authors report no conflicts of interest in this work.
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