The texturization of the outer shell of breast implants was first introduced in 1968 with the “natural Y” implant, which incorporated a 1.2- to 2-mm polyurethane foam coating on its outer surface.1 It was proposed that this surface prevented organized alignment of myofibroblasts, reducing the risk of capsular contracture.1 In 1991, a specific association between polyurethane and the carcinogen 2,4-toluenediamine was reported.2,3 This led to a voluntary withdrawal of polyurethane-coated silicone implants in the United States, which is still in place. Alternative surface technologies to modify the outer silicone shell were introduced in an attempt to mimic the polyurethane surface. There are four processes for generating surface texture on the external silicone shell: salt loss, vulcanisation, imprinting techniques,4 and a more recently released surface that claims a novel “nano” texture that remains proprietary.5
The benefits of textured implants in reducing capsular contracture remain controversial. Systematic reviews of comparative clinical studies concluded that texturization may reduce the incidence of early capsular contracture in subglandular augmentation.6,7 Many published reports lack adequate description of implant type, surgical technique, and outcome assessment. Smaller comparative or split breast studies are evenly divided as to the benefit of texturization.8–18
Previous published data have confirmed that textured implants are able to support higher rates of bacterial growth in vitro.19 Furthermore, there is a correlation between higher bacterial contamination and host response in vivo, which suggests a threshold phenomenon where bacterial load triggers a host inflammatory response.20 More recently, bacterial infection has been proposed as one of four factors that may play a role in the genesis of breast implant–associated anaplastic large cell lymphoma (ALCL).21 This study aimed to look at textures of varying morphology to study the relationship among surface area, roughness, and capacity for bacterial attachment and growth in vitro.
MATERIALS AND METHODS
Implant Surfaces Tested
Eleven implant surface types were subjected to testing: Silimed polyurethane (Sientra, Dallas, Texas); Polytech POLYtxt (Polytech Health and Aesthetics, Dieburg, Germany); Mentor Siltex and Mentor Smooth (Mentor Worldwide LLC, Irvine, Calif.); Motiva SilkSurface and Motiva VelvetSurface (Motiva Alajuela, Costa Rica); Allergan Biocell (Allergan, Dublin, Ireland); Allergan Natrelle Smooth (Allergan); Nagor Nagotex (Nagor Ltd, Glasgow, UK); Sientra Smooth (Santa Barbara, Calif.); and Eurosilicone textured (Eurosilicone, Apt Cedex, France). Table 1 lists the manufacturing types for the various textured surfaces.
Implant Surface Imaging
Scanning Electron Microscopy
Following fixation in 3% glutaraldehyde, samples (up to 1 cm2) were dehydrated in ethanol and immersed in hexamethyldisilazane (Polysciences, Inc., Warrington, Pa.) for 3 minutes, and the hexamethyldisilazane was allowed to evaporate overnight. Samples were mounted onto aluminium stubs (ProSciTech, Thuringowa, Queensland, Australia) and sputter-coated with 20-nm gold film in the Emitech K550 gold coater (Emitech, West Sussex, United Kingdom). The gold-coated breast implant samples were visualized using a JEOL 6480LA scanning electron microscope (JEOL Ltd., Tokyo, Japan).
Micro–Computed Tomographic Scan
The specimens were mounted horizontally on a metal pin with adhesive before loading into a pin vice holder. These were then scanned in a Zeiss Xradia MicroXCT-400 system operating in absorption mode with a peak source energy of 50 kV and a beam current of 200 µA (Carl Zeiss, Oberkochen, Germany). The projections were collected every 0.25 degree over a total rotation of 180 degrees, with an exposure time of 3 seconds and saved as 16-bit images in a proprietary file format.
The projections were reconstructed using XMReconstructor v7.0.2817 (Zeiss Xradia) with consistent reconstruction parameters, resulting in 2.2-µm isotropic voxels. Surface area and roughness measurements were taken from this model to calculate the various required material properties. Analysis was performed with Avizo 9.3 (FEI Visualization Sciences Group, Bordeaux, France) and Fiji,22 where a binarized model of the sample was produced by thresholding after noise-reduction filtering of the reconstructed slices.
Surface Area Determination
The three-dimensional–to–two-dimensional sample size surface area ratio was calculated by first measuring the surface area of the interface between the binarized sample and air (SA3D) and then comparing it to the x-y dimensions of the sample itself (SA2D). (See Figure, Supplemental Digital Content 1, which shows the algorithm for calculation of the three-dimensional–to–two-dimensional area ratio, https://links.lww.com/PRS/C956.). All ratios were normalized to smooth implants.
Surface Roughness Determination
To measure the roughness of the surface of each sample, it was necessary to first wrap the sample to avoid overhangs and cavities. To simplify things, a new surface was created by effectively dropping an thin probe toward the surface at each point. At the point of contact with the sample, the new surface was defined. The arithmetic mean deviation of the assessed profile (Sa) was calculated over this approximated surface by means of the following:
where i and j represent column and row positions, yij is the surface height at ij, and y is the mean surface height across the surface. The roughness was expressed as a multiple of the value for smooth implants.
In Vitro Bacterial Attachment Assay
In vitro analysis was conducted on nine types of implants of varying morphology, against four bacterial types: Staphylococcus epidermidis, S. aureus, Pseudomonas aeruginosa, and Ralstonia pickettii. The implants were prepared by cutting a strip of implant shell from the whole implant and scraping away any residual silicone from the inner surface with the blunt edge of a knife. Sections of the implant shell were obtained using a 5-mm punch biopsy tool. The implants sections were placed outside surface down in a glass petri dish and sterilized under dry heat conditions at 115°C for 39 hours. After sterilization, sterile water was added to each petri dish and the implants were pressed into the water and the air was expelled. Then, 10% tryptone soy broth containing 105 cells/ml of S. epidermidis, S. aureus, and R. pickettii or 104 cells/ml of P. aeruginosa was added to the petri dish and the implants were incubated at 37°C for up to 24 hours.
Implant samples were removed at 2, 6, and 24 hours for S. epidermidis and at 24 hours for S. aureus, P. aeruginosa, and R. pickettii for colony-forming unit determination. The implant samples were washed three times in phosphate-buffered saline. Four implant disks were placed in 0.5 ml of phosphate-buffered saline and subjected to sonication for 20 minutes followed by 1 minute of vortexing as described previously.19 Quantitative numbers of bacteria attached to the implant outer surface were determined by serial 10-fold dilutions and standard plate culture. Each condition was tested five times.
Statistical analysis was conducted using the statistical package Sigma Plot 13 (Systat Software, Inc., San Jose, Calif.). For comparing different implant surfaces and bacterial attachment, the data were transformed and a one-way repeated measures analysis of variance was applied, and all pairwise multiple comparison procedures were performed using the Holm-Sidak method. If data were not distributed normally, the Kruskal-Wallis one-way analysis of variance on ranks test was performed, and all pairwise multiple comparison procedures were conducted using the Dunn method. The relationship between implant three-dimensional–to–two dimensional surface area ratio and number of attached bacteria at 24 hours was tested using Pearson correlation if distributed normally or Spearman rank order correlation if distributed nonnormally. A value of p < 0.05 was set as significantly different.
Scanning Electron Microscopy
Figure 1 demonstrates the surface morphology of some of the implants studied, demonstrating a range of appearance from highly complex with many hidden surfaces to relatively featureless.
Surface Area Determination
Analysis using fine-cut computed tomographic scans and confocal microscopy allowed visualization and calculation of surface area for each of the implant shells. Table 2 summarizes the findings. Figure 2 shows three-dimensional surface area images, which were used for calculating the three-dimensional–to–two-dimensional ratios for three of the implant surfaces. (See Figure, Supplemental Digital Content 2, which shows the polyurethane three-dimensional extraction, https://links.lww.com/PRS/C957. See Figure, Supplemental Digital Content 3, which shows the polyurethane three-dimensional gray-scale reconstruction, https://links.lww.com/PRS/C958. See Figure, Supplemental Digital Content 4, which shows the Polytech POLYtxt three-dimensional extraction, https://links.lww.com/PRS/C959. See Figure, Supplemental Digital Content 5, which shows the Polytech POLYtxt three-dimensional gray-scale reconstruction, https://links.lww.com/PRS/C960.) Figure 3 is a graphic representation of three-dimensional–to–two-dimensional surface area ratio.
There were four groupings for surface area measurements according to three-dimensional–to–two-dimensional surface area ratio. These were as follows: (1) high (>5), (2) intermediate (between 3 and 5), (3) low (between 2 and 3), and (4) minimal (<2).
These categories corresponded generally to implant shell manufacturing processes, with polyurethane open pore having the highest surface area; some salt-loss type and vulcanisation as intermediate; other salt-loss and imprinting type textures as low; and smooth and “nano” labeled surfaces as minimal. Salt-loss textures may vary in surface area dependent on the size of the crystals selected in the process. Interestingly, although the Polytech POLYtxt had a high surface area reading on first analysis, many of these surfaces were contained within the structure of the silicone outer shell and had no direct communication to the outer surface. An analysis of the choke zones (variation between 1 and 10 µm and hidden “caves” of sequestered internal surfaces) allowed an available surface area to be determined using subtractive analysis. The three-dimensional–to–two-dimensional surface area ratio for Polytech POLYtxt was calculated assuming a mean choke size of 5 µm. [See Figure, Supplemental Digital Content 6, which shows the demonstration of caves (sequestered surface area) for Polytech POLYtxt colored red on three-dimensional reconstruction, https://links.lww.com/PRS/C961. See Video, Supplemental Digital Content 7, which shows real-time demonstration of caves (sequestered surface area) for Polytech POLYtxt colored red on three-dimensional reconstruction, https://links.lww.com/PRS/C962.]
Surface Roughness Determination
There were four groupings for surface roughness measurements. These were as follows: (1) high (>150), (2) intermediate (between 75 and 150), (3) low (between 25 and 75), and (4) minimal (<25). Table 3 and Figure 4 summarize surface roughness findings.
In Vitro Bacterial Attachment Assay
Figure 5 shows the number of S. epidermidis attached to different types of implant outer shells at 2, 6, and 24 hours. Even by the 2-hour time point, the high surface area of textured Silimed polyurethane implants had a significantly larger number of bacteria attached to them than less textured implants with lower surface areas such as Mentor Siltex, smooth (i.e., Mentor, Sientra, and Allergan), Motiva VelvetSurface, and Motiva SilkSurface (p < 0.001). By 24 hours, implants with high or intermediate three-dimensional–to–two-dimensional surface area ratios had significantly more bacteria attached to them than implants with low or minimal three-dimensional–to–two-dimensional surface area ratios (p < 0.001), and although Silimed polyurethane implants had more bacteria attached to them, this was not significantly different from implants with intermediate profiles (Fig. 6, above). Within the salt-loss–produced implants, roughly double the number of S. epidermidis attached to Nagor Nagotex implants (p < 0.4). At 24 hours, the number of bacteria attached to the smooth implant shell was no different from the number attached to implants with a low or minimal profile (p > 0.07); however, it was significantly less than the number of bacteria attached to implants with intermediate to high profiles (p < 0.001). Over time, the number of bacteria attached to implants was positively correlated with the three-dimensional–to–two-dimensional surface area ratio; the higher the three-dimensional–to–two-dimensional surface area ratio, the more bacteria that were attached (R = 0.64; p < 0.001).
Figure 6, below, shows the number of S. aureus attached to different types of silicone implant outer shells at 24 hours. Silimed polyurethane implants had significantly more bacteria attached to them than any other implant (p < 0.05), whereas smooth implants (i.e., Mentor, Sientra, and Allergan) had significantly fewer bacteria attached to them than any other implant (p < 0.001) except Mentor Siltex (p = 0.4). There was no significant difference in the number of bacteria that attached to the three salt-loss implants. The number of bacteria attached to implants was positively correlated with the three-dimensional–to–two-dimensional surface area ratio; the higher the three-dimensional–to–two-dimensional surface area ratio, the more bacteria that were attached (R = 0.75; p < 0.001).
Figure 7, above, shows the number of P. aeruginosa attached to differing implant shells at 24 hours. The maximum number of bacteria attached to Silimed polyurethane implants, followed by Polytech POLYtxt, and the Biocell implant produced by salt loss. The other two salt-loss implants, Eurosilicone textured and Nagor Nagotex, had less bacteria attached at 24 hours, but this was not significantly different from the numbers attached to the Biocell implant (p > 0.09). The number of bacteria attached to implants was positively correlated with the three-dimensional–to–two-dimensional surface area ratio; the higher the three-dimensional–to–two-dimensional surface area ratio, the more bacteria that were attached (R = 0.81; p < 0.001). Significantly fewer bacteria grew on smooth implants compared with all other implants (p < 0.001). In contrast to the findings for staphylococcal species, significantly fewer bacteria attached to Motiva VelvetSurface implants compared with Motiva SilkSurface implants (p = 0.008); the number was significantly less than for all of the other implants (p < 0.001).
Figure 7, below, shows the number of R. pickettii attached to the different types of silicone outer shell at 24 hours. Only Silimed polyurethane, Biocell, and Nagor Nagotex had significantly more bacteria attached than smooth implants (p < 0.001). There was no significant difference in the number of bacteria attached to the three salt-loss–produced implants. The number of bacteria attached to implants was positively correlated with the three-dimensional–to–two-dimensional surface area ratio; the higher the three-dimensional–to–two-dimensional surface area ratio, the more bacteria that were attached (R = 0.87; p < 0.001).
Figure 8 summarizes the proposed surface classification based on combining surface area with surface roughness. The surface grade can then be combined with a nomenclature to define fill, surface, shape, and size of the implant. Table 4 summarizes the proposed classification. A Cohesive Gel 410 Allergan Biocell Anatomic 330-cc implant, for example, would be classified as GF4A330.
These findings support the use of a new classification system for implant outer shells based on measurable parameters of surface area and roughness that correlate with bacterial growth. We now propose a classification of implant surfaces into four grades (high, intermediate, low, and minimal) based on the direct measurement of their surface area and roughness.
Analysis of bacterial growth over varying implant surfaces showed a significant correlation, with the three-dimensional–to–two-dimensional surface area ratio demonstrating a linear relationship of bacterial attachment and growth as the surface area ratio increased. Figure 5 confirms the exponential growth rates for higher surface area textured implants for S. epidermidis we have reported previously.19 The Silimed polyurethane texture grew significantly higher numbers of bacteria for all species at 24 hours. Interestingly, the intermediate-surface-area implants showed good correlation and were no different from the high-surface-area implants for S. epidermidis and P. aeruginosa. These prolific biofilm formers may well overwhelm the surface area available and reach maximal growth capacity earlier than other species. These species and surface differences for intermediate/low texture require further investigation and may relate to the available surface area, specific bacterial cell size, motility, and capacity to form biofilm together with environmental factors and availability of nutrition.
The Polytech POLYtxt surface showed a high proportion of hidden surface area (caves) within the substance of the texture. These were either walled off entirely from the external environment or had very narrow choke zones to reduce the passage of bacteria and/or host cells. This may also explain higher growth for some species for this texture. Atlan et al.23 have used similar measurement techniques and demonstrated variation in texture morphology on different sites of the same implant. This was beyond the scope of this study but will be the subject of future bacterial attachment analysis.
Previously published morphologic analyses of breast implant outer shells have used confocal microscopy,24–26 scanning electron microscopy,25 and/or light microscopy26 and wettability25 to classify implant surfaces. We have previously used these techniques21 but found significant errors when examining higher thickness implant textures with loss of resolution in deeper zones. The use of the micro–computed tomography method has allowed a more accurate morphologic assessment of the entire implant shell. These authors have also used fibroblast adhesion and/or macrophage activation as surrogate markers for predictors of tissue incorporation and reduction in capsular contracture.25 Although these in vitro factors may be important, they have yet to translate into proven clinical benefit; thus, their functional significance will need to be validated by clinical studies.
The presence of bacteria, by contrast, on the surface of implants has been shown to be a significant potentiator for the formation of capsular contracture in clinical and laboratory studies.19,27,28 Clinical correlation has confirmed a significant correlation of bacterial contamination with increasing grade of capsular contracture.29 In patients with high-grade capsular contracture, polyurethane texture was also shown to support a significantly higher load of bacteria compared with other textured implants.20 Furthermore, translational research has now supported the use of antibacterial mitigation to reduce capsular contracture, thus linking the surface area/bacterial growth relationship directly to a functional clinical outcome.30,31
We are not claiming that textured implants cause more contracture, as is often suggested in commentaries critiquing our previous findings. Surface texture provides a dual opportunity for better host tissue incorporation but also, unfortunately, for bacterial growth and proliferation. In the event that bacterial contamination is kept low, the advantages of a textured surface may well promote better long-term results. High-quality clinical comparative studies are still required to confirm this finding. It is also likely that factors other than implant texture alone have a suppressive effect on the development of biofilm and subsequent capsular contracture, including antibacterial pocket irrigation, prophylactic antibiotic use, avoidance of contamination, anatomical pocket location, and careful atraumatic dissection of the breast pocket.27,32 Strategies to prevent contamination of the implant as it is placed help to reduce the numbers of bacteria and keep the contamination below threshold.33 This underscores the importance of overall bacterial load on breast implants that ultimately drives the clinical outcome.
More recently, an antigen driver for breast implant–associated ALCL has been proposed. This along with surface texture, patient genetics, and time form the unifying hypothesis that explains both observed biology and epidemiology of breast implant–associated ALCL.21 The propensity for high- and intermediate-surface-area textured implants to cause breast implant–associated ALCL is 10 times higher than for low-surface-area texture and is consistent with these data.21 The need for a biological antigen to drive carcinogenesis indicates that it is likely that bacterial proteins rather than inert silicone particles initiate the stimulation and transformation of T cells.34 The pathway from bacterial antigen stimulation to lymphoma has been proven for Helicobacter pylori, gastric mucosa-associated lymphoid tissue lymphoma, and gastric cancer.35 Understanding the interaction among genes, the microbiome, and immunity may well provide new approaches to both the treatment and prevention of cancer.
We support the use of a novel and functional classification of implant outer shells based on objective measurement into four degrees of surface texture: high, intermediate, low, and minimal. The correlation of surface area/roughness with propensity for bacterial growth links this classification to a functional outcome and strengthens its validity as a tool to help surgeons to select the optimal implant surface for both breast augmentation and reconstruction.
The authors acknowledge the facilities and the scientific and technical assistance of the Australian Microscopy & Microanalysis Research Facility at the Australian Centre for Microscopy & Microanalysis at the University of Sydney. The authors would like to thank implant manufacturers for supply of sample implant surfaces for the study.
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