Chemical composition (in at.%) from the XPS analysis.
Silicone Rubber (SR) and SR-based materials have been used as medical tissue implants in the field of plastic surgery for many years, but there are still some reports of adverse reactions to long-term implants. In our study, three types of carbon ion silicone rubber were obtained by implanting three doses of carbon ions. Then, the surface characteristics, the antibacterial adhesion properties and in vivo host responses were evaluated. These study shown that ion implantation change the surface roughness and zeta potential of virgin SR; it also inhibit bacterial adhesion. At the same time, ion implantation enhance the cell proliferation, adhesion and tissue compatibility. These data indicate that carbon ion implanted silicone rubber exhibits good antibacterial adhesion properties, cytocompatibility and triggers thinner and weaker tissue capsules. In addition, according to the surface characteristics, we speculate that high surface roughness and high zeta potential may be the main factors that induce the unique biocompatibility of carbon ion implanted silicone rubber. In this chapter, we will review these results above and propose that ion implantation should be considered for further investigation and application, and carbon ion silicone rubber could be a better biomaterial to decrease silicone rubber–initiated complications.
- ion implantation
- silicone rubber
- surface modification
Silicone rubber (SR) is a type of biomaterial that exhibits many useful properties, such as thermal stability, chemical resistance, and low cost . It has a long history of use in biomedical and biological applications, ranging from tissue fillers to tubes for dialysis and blood pumps [2–4]. Silicone rubber and silicone rubber‐based materials have been used as medical tissue implants in the field of plastic surgery for many years, but there remain reports of adverse reactions to long‐term implants, such as capsular contracture [5, 6]. Moreover, various prosthetic materials that contain silicone rubber can easily move and can permanently damage the prostheses. In addition, certain materials made from silicone rubber, such as catheters, are widely used in medicine but have several limitations; for example, bacteria can readily colonize the surfaces of silicone rubber, facilitating infection and even causing patient death in certain cases [5, 7–9].
In recent years, many attempts have been made to modify medical materials to reduce bacterial adhesion and to minimize adverse inflammatory or foreign body reactions [10–15]. Among these methods, the surface modification of biomaterials is an economical and effective method to achieve biocompatibility and biofunctionality while preserving the favorable characteristics of the biomaterial, such as particular mechanical properties and thermal stability. Surface modifications, such as ion implantation [16–18], sintering , electrochemical deposition , and the sol‐gel coating method, are common . Among these surface modification methods, ion implantation has become a notably useful method because of its ease of operation and convenience [22–25]. In this context, we implanted three different doses of carbon ions into silicone rubber and obtained carbon ion silicone rubber (C‐SR). Our study was designed to evaluate the surface characteristics and the biocompatibility of carbon ion silicone rubber. We focused on bacterial adhesion, cytocompatibility, and fibrosis/fibrous capsule development. The long‐term goal is to gain a better biomaterial for use by plastic surgeons.
2. Materials and methods
2.1. Sample preparation
SR sheets with dimensions of 100 x 100 x 1 mm were prepared from a two‐component silicone system. Both component A and component B were clinical‐quality liquids provided by Chenguang Research Institute of Chemical Engineering, China. Three doses of carbon ions were implanted using the ion implanter, respectively. The doses are 1 × 1015 ions/cm2 (C1), 3 × 1015 ions/cm2 (C2), and 1 × 1016 ions/cm2 (C3). After that, SR and C‐SR sheets were manufactured into disc‐like samples with a diameter of 6 mm using a hole puncher and into square samples with dimensions of 10 mm × 10 mm × 1 mm. The disc‐like samples were used in in vitro antibacterial adhesion tests, and the square samples were used for in vivo evaluation. All samples were sterilized with 75% alcohol overnight. In all experiments, SR served as the control.
2.2. Surface characterization
The mechanical properties were analyzed by shore A durometer and electronic universal testing machine to gain parameters of the shore hardness and tear strength. The physicochemical properties were analyzed by the FTIR, SEM, XRD, XPS, water contract angel, zeta potential, and AFM experiments. The surface zeta potentials of materials were measured with a Zeta Potential Analyzer (DelsaNano C, Beckman Coulter, Germany). The measurements were carried out in 1 mmol 1‐L NaCl electrolyte solution and with standard particles for flat surface cell (Otsuka Electronic Co., Ltd, Japan). Each sample chooses five points and each point tests 20 times. After that, the samples were scanned by the Environment Control Scanning Probe Microscope (NanoNavi E‐Sweep, NSK Ltd., Tokyo, Japan) and each sample was imaged with a 5 μm × 5 μm scanned area. The surfaces were analyzed by measuring the average surface roughness (Ra) of 5 randomly chosen images per sample from selected areas of 1 μm x 1 μm under Atomic Force Microscope (AFM) analysis software (NanoNavi II, SII Nano Technology Inc., Tokyo, Japan). Ra is defined as the average absolute deviation of the roughness irregularities from the mean line over one sampling length and gives a good general description of height variations. Three replicas were used.
2.3. Bacterial culture preparation
2.3.1. Plate colony‐counting
After incubation of the samples in the bacterial culture for 1 and 24 h, the bacteria on each sample were gently rinsed with PBS, respectively, and ultrasonically detached in 1 ml of PBS solution. The bacteria in the PBS were recultivated on agar plates for colony‐counting. The antibacterial rates were determined based on the following relationship: antibacterial rate (%) = (CFU of control − CFU of experimental groups)/CFU of control x 100%. This assay was performed in triplicate.
2.3.2. Fluorescence staining
After incubation for 1 and 24 h, various samples were gently rinsed with PBS before staining the bacteria on the samples. The staining was performed by applying LIVE/DEAD® BacLight™ Bacterial Viability Kit (L7029, Molecular Probes®, OR, USA) for 15 min in darkness and was examined by laser scanning confocal microscopy (LEICA TCS SP5, Germany). The areas of green and red color in the pictures were then analyzed by using Image‐Pro Plus version 6.0 (Media Cybernetics, Inc., USA) and then the proportion of red coloration based on the following relationship was calculated: red proportion (%) = red area/(green area + red area) x 100%.
2.3.3. Scanning electron microscopy (SEM) observation
After bacterial incubation for 1 and 24 h, the samples were rinsed with PBS to remove free bacterial cells and then fixed in 2.5% glutaraldehyde for 3 h at room temperature. The samples were then progressively dehydrated in a series of ethanol solutions (15, 30, 50, 70, 80, 90, 95, and 100%) for 15 min each. After that, the specimens underwent critical point drying and coating with a thin conductive layer of Au. Finally, the morphology and adhesion of the bacteria on the various samples were determined by SEM (VEGA 2 SEM, TESCAN Inc., Brno, Czech Republic).
2.4. Animals and surgery
This research was performed in accordance with the Guide for the Care and Use of Laboratory Animals published by the US National Institutes of Health (Washington, DC: The National Academies Press, 2011), and all of the animal protocols were approved by the Institutional Animal Care and Use Committee of the Third Military Medical University, China. A total of 16 female Sprague‐Dawley rats (weighing 160–200 g) were used (4 groups of 4 animals each), and all rats were housed under a 12‐h light–dark cycle with free access to water and food. Prior to surgery, all of the rats were anesthetized with 3% pentobarbital sodium (1 ml/1000 g). The skin was swabbed with iodine, and four parallel incisions (10 mm) were performed. The material samples were implanted subcutaneously along the back region. The implants and their surrounding tissues were retrieved from each group by wide excision at 7, 30, 90, and 180 days after implantation and were then fixed in 4% paraformaldehyde solution. After that, HE and Masson’s staining and immunohistochemistry were carried out.
2.4.1. HE and Masson’s staining
The fixed tissues were sectioned (6 μm thick) and stained using a HE Staining Kit (C0105, Beyotime Inc., Shanghai, China). The thickness of the fibrotic capsule around each implant was determined at five equidistant points for statistical accuracy. Collagen deposition in the tissue around the implants was studied by Masson’s trichrome staining, which was performed using a staining kit (MST‐8003, Maixin Biological Technology Co., Ltd., Fujian, China). All procedures were performed based on the manufacturer’s instructions.
Immunohistochemistry was performed on 4% paraformaldehyde‐fixed cryostat sections of frozen tissue specimens. Endogenous peroxidase and nonspecific antibody binding were blocked with 3% H2O2 and 100% methanol, with a ratio of 1:5 and a blocking time of 30 min. Next, 0.02 M PBS was used for antigen retrieval while heating in a water bath, followed by treatment with 5% blocking reagent at 37°C for 30 min. The slides were then incubated at 4°C for 12 h with a primary antibody against CD68, CD4, TNF‐α, α‐SMA, or elastin (1:25) (Boster Biological Engineering Co., Ltd., Hubei, China). After washing in PBS, a secondary antibody was applied for 30 min. Visualization was achieved by adding 3, 3’‐diaminobenzidine chromogen.
All data are expressed as the mean ± standard deviation (SD), and statistics were analyzed using SPSS statistical software. One‐way ANOVA combined with multiple comparisons performed along with Tukey multiple comparison tests was utilized to determine the level of significance. In all of the statistical evaluations,
3.1. Ion implantation changes the surface roughness and zeta potential of SR
After ion implantation, SEM, AFM, FTIR, XPS, XRD, water contact angle measure instrument, zeta potential detection instrument, shore A durometer, and an electronic universal testing machine were used to investigate the change in properties of carbon ion silicone rubber. The SEM results failed to find any significant differences between virgin SR and three C‐SRs (Figure 1), indicating that carbon ion implantation did not change the macro‐scale surface of SR.
At the same time, there is no any significant differences or the difference was very small on the results of FTIR (Figure 2), XRD (Figure 3), shore hardness (Figure 4A), and tear strength (Figure 4B).
From the results of water contact angle, we found that carbon ion implantation significantly decreased the water contact angle of SR, and big doses carbon ions had lowest water contact angle among all C‐SRs (Figure 5).
Besides, the XPS results showed that carbon ion implantation significantly changed the surface silicone oxygen rate and chemical‐element distribution of SR (Figure 6) (Table 1); we noted that with the ion implantation dose increasing, the carbon content in the material increased, while the Si content decreased, suggesting that implanted carbon atom may replace the Si of virgin SR, interrupting the original Si‐O assemble, increasing the surface free energy, and, thereby, theoretically decreasing material’s water contact angle.
|Group||Si 2p||C 1s||O 1s|
Furthermore, AFM images revealed that the surfaces of C‐SRs were composed of larger irregular peaks and deeper valleys, while virgin SR exhibited a relatively smooth and more homogeneous surface (Figure 7A). The surface roughness of the C3‐SR, which underwent most carbon ion implantation, was highest among all three C‐SRs (Figure 7B).
In addition, all samples exhibited negative zeta potentials and reflect that the surfaces of all samples were negatively charged. The absolute value of the zeta potential increased with the ion dose (Figure 8). Considering the influence of surface roughness on contact angle, we propose that ion implantation can change the surface roughness of the material and increase the surface potential of the material.
3.2. Ion implantation inhibits bacterial adhesion on SR
Preventing bacterial adhesion and biofilm formation by improving the surface antibacterial adhesion property of the silicone rubber is critical for eliminating various types of infections. After ion implantation, we used Gram‐negative
After 24 h of incubation, the rates of bacterial adherence were slightly lower, but did not significantly decrease compared with that after 1 h of incubation (
3.3. Carbon ion‐implanted silicone rubber triggers thinner and weaker tissue capsules
After ion implantation, the host responses were evaluated by surveying inflammation and fibber capsule formation that developed after subcutaneous implantation in Sprague‐Dawley rats for 7, 30, 90, and 180 days. The thickness values of tissue capsules around the implants were identified from hematoxylin and eosin‐stained sections of the peri‐implant soft tissues and were analyzed as one of the physiologic responses to implantation. At 7 days after implantation, silicone rubber had the thinnest tissue capsules, and carbon ion silicone rubber had thicker (Figure 11) (
In addition, collagen deposition was revealed using Masson trichrome staining. Our results show that collagen gradually became sparser over time and with increasing carbon ion doses. Carbon ion silicone rubber had obviously lower collagen deposition than silicone rubber (Figure 12) (
To gain insight into inflammatory foreign body responses and capsule contracture to the samples, major biomarkers CD68, CD4, tumor necrosis factor‐α, elastin, and α‐smooth muscle actin were detected using immunohistochemistry. As shown in Table 2, all samples present lower expression of CD68, with no significant differences.
|7 days||30 days||90 days||180 days|
The distribution of CD4 in the inflammatory infiltrate, which was induced by the samples, was investigated to further understand the local immunomodulation against these types of materials. The results show that there were many positive staining areas of CD4 in silicone rubber after 90 days, but positive staining in the carbon ion silicone rubber decreased with time. After 90 days, CD4 significantly decreased compared with silicone rubber (Table 3).
|7 days||30 days||90 days||180 days|
In addition, the expression results of proinflammatory cytokine tumor necrosis factor‐α by macrophage cells show that silicone rubber had an obviously positive staining area (Table 4).
|7 days||30 days||90 days||180 days|
Furthermore, the positive staining areas of α‐smooth muscle actin and elastin have no difference; the positive staining area of α‐smooth muscle actin appeared predominantly in silicone rubber than in carbon ion silicone rubber (Table 5). Elastin was intensely expressed in silicone rubber, particularly after 30 days (Table 6).
|7 days||30 days||90 days||180 days|
|7 days||30 days||90 days||180 days|
Our study evaluated the in vitro antibacterial properties and the in vivo host response to carbon ion‐implanted silicone rubber. The results of our study indicate that the carbon ion silicone rubbers have good biocompatibility, lower bacterial adhesion, and lower foreign body reaction with relatively thin fibrous capsules. All results show that ion implantation should be considered for further investigation and application, and carbon ion silicone rubber might be a better biomaterial for decreasing silicone rubber‐initiated complications.
This work was funded by grants from the National Natural Science Foundation of China (81571918, 81401610) and a grant for Scientific Personnel Innovation from Chongqing (cstc2013kjrc‐qnrc10003).
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