Liquid-Infused Poly(styrene-b-isobutylene-b-styrene) Microfiber

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A Liquid-Infused Poly(styrene#b#isobutylene#b#styrene) Microfiber Coating Prevents Biofilm Attachment and Thrombosis Shuaishuai Yuan, Zhibo Li, Lingjie Song, Hengchong Shi, Shifang Luan, and Jinghua Yin ACS Appl. Mater. Interfaces, Just Accepted Manuscript • DOI: 10.1021/acsami.6b06407 • Publication Date (Web): 02 Aug 2016 Downloaded from http://pubs.acs.org on August 6, 2016

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ACS Applied Materials & Interfaces

A Liquid-Infused Poly(styrene‑ ‑b‑ ‑isobutylene‑ ‑b‑ ‑styrene) Microfiber Coating Prevents Bacterial Attachment and Thrombosis Shuaishuai Yuana,b, Zhibo Lia,*, Lingjie Songb, Hengchong Shib, Shifang Luanb,*, Jinghua Yinb,* a

School of Polymer Science and Engineering, Qingdao University of Science and

Technology, Qingdao 266042, People’s Republic of China b

State Key Laboratory of Polymer Physics and Chemistry, Changchun Institute of

Applied Chemistry, Chinese Academy of Sciences, Changchun 130022, People’s Republic of China

ACS Paragon Plus Environment


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ABSTRACT: Infection and thrombosis associated with medical implants cause significant morbidity and mortality worldwide. As we know, current technologies to prevent infection and thrombosis may cause severe side effects. To overcome these complications without using antimicrobial and anticoagulant drugs, we attempt to prepare a liquid-infused poly(styrene‑b‑isobutylene‑b‑styrene) (SIBS) microfiber coating, which can be directly coated onto medical devices. Notably, the SIBS microfiber was fabricated through solution blow spinning. Compared to electrospinning, the solution blow spinning method is faster, less expensive and easy to spray fibers onto different targets. The lubricating liquids then wick into and strongly adhere the microfiber coating. These slippery coatings can effectively suppress blood cell adhesion, reduce hemolysis and inhibit blood coagulation in vitro. In addition, Pseudomonas aeruginosa (P. aeruginosa) on the lubricant infused coatings slides readily, and no visible residue is left after tilting. We furthermore confirm that the lubricants have no effects on bacterial growth. The slippery coatings are also not cytotoxic to L929 cells. This liquid-infused SIBS microfiber coating could reduce the infection and thrombosis of medical device, thus benefiting human health.

Keywords: Thermoplastic elastomer, solution blow spinning, microfiber, slippery coating, antibacterial, hemocompatibility


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INTRODUCTION Infections and thrombosis of medical devices are important problems and, when these complications occur, surgical removal is inevitable.1 To modify the surface property of implants without sacrificing the bulk properties, surface coating seems to be an attractive approach to prevent these complications.2 Fabrication of bactericidal and antifouling surfaces are two main methods for the inhibition of the adhesion and proliferation of bacteria on the surfaces of medical devices. However, bactericidal coatings based on drug elution strategy, such as silver ions,3 antimicrobial peptides4 and antibiotics,5-6 only have short-term antimicrobial effect, and could cause bacterial resistance and toxicity. Cationic polymers, in solution form, can disrupt the pathogen cytoplasmic membrane.7-8 When they are immobilized on the implant surface, their antimicrobial activities mainly depend on the concentration of cationic polymers.9 Macrophage on positively charged surfaces can also phagocytose bacteria.10 However, cationic surfaces probably suffer from poor biocompatibility, and the adhesion of dead bacteria on cationic surfaces can block their antibacterial functionality.11 For avoiding bacterial infection, an alternative approach is to create antifouling surfaces with hydrophilic polymers, such as poly(ethylene glycol) (PEG),12-14 poly(carboxybetaine

methacrylate),11

poly(2-methacry-loyloxyethyl

phosphorylcholine),15-17 poly(sulfobetaine methacrylate),18-20 poly(acrylamide)s,21 and polysaccharides.22 Moreover, bacteria-release surfaces can effectively manipulate the attachment and detachment of bacteria.23-25 The superhydrophobic surfaces with self-cleaning properties can also be used for inhibiting bacterial adhesion.26-28



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However, stable bacterial attachment eventually occurs on these antifouling surfaces mentioned above because of the inescapable surface defects. Fabricating a surface that possesses nanoscale dynamic features may prevent interactions between the biological fouling and the solid surfaces.29 Construction of a liquid interface is a promising method to creating dynamic surfaces. Inspired by Nepenthes pitcher plant, slippery liquid-infused porous surfaces (SLIPS) possessing unique antifouling behaviors have been developed. The first example of SLIPS was reported by Aizenberg and co-workers through wicking perfluorinated lubricant into Teflon porous membranes.30 Since then, the development of SLIPS has been the focus of both practical application and fundamental research.31-32 However, relatively few studies have focused on creating liquid-infused coating. For example, Li et al. fabricated a hydrophobic liquid-infused porous coating with bacteria-resistance.33 Manna et al. reported preparation of slippery surface coatings through infusion of oils into nanoporous polymer multilayers.34 A critical requirement to produce slippery coating is to make micro/nanotextured rough substrates with large surface area, which is necessary to infuse lubricating fluid. Generally, electrospinning is widely used to fabricate porous coating. However, electrospinning suffer many disadvantages, such as low deposition rate, high voltages, and electrically conductive targets. These constraints limit the extensive application of electrospinning particularly on irregular objects. In contrast, solution blow spinning only requires a simple apparatus with compressed gas and polymer solution. Several groups have successfully obtained nanofibers by means of this technique using commercial airbrushes.35-38 It was


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demonstrated that solution blow spinning was safer, faster, less expensive and able to spray fibers onto a wider range of substrates than electrospinning. In this work, we present novel slippery coatings based on SIBS microfiber infused with lubricants. Compared to other methods, the solution blow spinning method used to make SIBS microfiber coating is unique, low-cost, passive, and it can paint arbitrary surfaces. SIBS was used as “ink” to explore the feasibility of solution blow spinning method for following reasons: i) SIBS has good hemocompatibility, biocompatibility and long-term stability,39-42 ii) it has been used as hot melt pressure-sensitive adhesives and can form a strong bond with biological implants.43 The biological performances of the lubricant infused SIBS microfiber coating were comparatively evaluated through several experiments, such as blood coagulation, hemolysis, cytotoxicity and antibacterial efficacy.



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EXPERIMENTAL SECTION Materials Poly(styrene-b-isobutylene-b-styrene) thermoplastic elastomer (SIBS, 103T) was obtained from Kaneka corporation. Tetrahydrofuran (THF) and AgNO3 were provided by Sinopharm Chemical Reagent Co., Ltd, and used without further purification. Rhodamine B, phosphate buffered solution (PBS, pH = 7.4), crystal violet, Pseudomonas aeruginosa (P. aeruginosa, ATCC 9027) and lysogeny broth (LB) were purchased from Dingguo Biotechnology Co., Ltd. The medical grade silicone fluid (Dow Corning® 360 Medical Fluid, 100 cSt) and perfluoropolyethers (Dupont™ Krytox® 105, 160 cSt) were used as lubricant. Methyl thiazolyl tetrazolium (MTT) was purchased from Sigma-Aldrich. Preparation of Liquid-Infused SIBS Microfiber Coating A commercially available airbrush (HD-130, 0.2 mm nozzle diameter, Ningbo live machinery manufacturing Co., Ltd) designed for painting was used to spray the SIBS solution onto different substrates (glass or medical devices) at distance of 20 cm. The airbrush was linked to a pressurized nitrogen tank, and the gas flow rate was controlled by equipped regulator. Solutions of SIBS were prepared at 5%, 10% and 15% (w/v) in THF. We adopted a nomenclature to immediately distinguish the SIBS-based coatings: MC-x, where x is the solutions concentration. Micro-structured SIBS coating (MC-15) were infused with lubricating liquids (silicone oil and perfluoropolyethers) using the following protocol. Lubricant was


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placed onto the coating and spread over the surface. The samples were tilted to 90 degrees for 4 h to remove the excess of lubricant by gravity-driven before use. Characterization of Surface Morphology and Property Porous structure of the obtained microfiber coating was examined after being sputter coated with gold, with a field emission scanning electron microscopy (FESEM, XL 30 ESEM FEG, FEI Company). The cross-sectional view of the MC-15 was also observed by FESEM. The average fiber diameter distributions of MC-15 were analyzed in triplicate using Image-J software. Chemical compositions of coatings were examined by attenuated total reflectance-fourier transform infrared spectroscopy (ATR-FTIR, Bruker Vertex 70) in the range from 400 to 4000 cm-1. The static, advancing, and receding water contact angles (WCAs) of the coatings were measured by a contact angle measuring device (Kruss Gmbh, Germany). The advancing (θA) and receding (θB) contact angles were measured as follows: 2 µL water droplet was deposited onto coatings, and then slowly increase or decrease the volume of a sessile droplet at a constant rate (30 mL/min) until the contact line starts to advance or recede. All samples were tested in triplicate. The difference between θA and θB is termed as contact angle hysteresis (CAH). The aqueous droplet of rhodamine B dye (100 µL) was used to characterize the slippery property of liquid-infused micro-structured coating at an inlination angel of 10 degrees. Antibacterial Assay Bacterial strain P. aeruginosa used to determine the antibacterial activity was incubated in growth broth at 37 °C for 24 h. The bacteria were resuspended to ~1 ×



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108 cells/mL after centrifuged at 2700 rpm for 10 min. The concentration of bacterial cell was calculated by measuring the optical density at 540 nm relative to a standard calibration curve. The standard calibration curve used in this study was prepared by aerobic plate count method and optical density measurement.44 Absorption (A) of the bacteria supernatant was measured by microplate reader (Tecan Sunrise, Swiss). It confirmed that an optical density reading of 1.0 at wavelength of 540 nm is corresponded to the concentration of ∼109 cells/mL.45 The samples were transferred to 48-well plate and incubated with bacterial suspension (1 mL, 108 cells/mL) for 24 h at 37 °C. After incubation, 2 mL of PBS was used to rinse all the samples (37 °C, 5 min, 120 rpm) to remove non-adherent bacteria. The amount of adherent bacteria on the incubation samples was quantitatively determined by crystal violet staining method. Briefly, crystal violet (0.1 wt%) was used to staine the samples for 1 h. The stained samples were then put into a new 48-well plate and rinsed with distilled water for six times, and then acetic acid (10 vol%) was used to dissolve the bound crystal violet for 10 min. 100 µl crystal violet-acetic acid solution was transferred to a 96-well plate. Absorbance of crystal violet-acetic acid solution was measured with microplate reader at 590 nm. Optical densities of crystal violet-acetic acid solution were normalized by making a subtraction of backgrounds (acetic acid solution only). To test the bacterial attachment property on liquid-infused SIBS microfiber coating, P. aeruginosa LB culture was deposited and statically incubated on MC-15, silicone oil and perfluoropolyethers infused samples. After 24 h incubation, the samples were tilted to test bacterial


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adhesion. The adhesion of bacteria on the coatings after sample tilting was taken photo with camera. Toxicity Screening P. aeruginosa in LB were incubated in the presence of the following reagents (1 vol%): silicone oil, and perfluoropolyethers, as well as with 0.1 wt% of AgNO3. Control samples with only P. aeruginosa in LB were also prepared. Samples were shaken cultured in a thermostatic shaker (37 °C, 130 rpm). Optical density at 540 nm were recorded after 0, 5, 10, and 30 h incubation by microplate reader. Whole Blood Cells Attachment and Blood Clotting Time Approval for the blood-related experiments was obtained form the Ethical Committee of the Chinese Academy of Sciences. Fresh whole blood was obtained from a healthy rabbit and mixed immediately with sodium citrate solution (3.8 wt%) at a dilution ratio of 9:1. MC-15, silicone oil and perfluoropolyethers infused samples were placed into a 48-well plate. Whole blood solution (2 mL) was then placed on the samples and incubated for 6 h at 37 °C. The adhered blood cells on the samples were fixed by 2.5 wt% glutaraldehyde (4 °C, 10 h). Finally, the fixed blood cells were dehydrated with a series of ethanol solution (30, 50, 70, 90, and 100 vol%). After leaching of the oil phase of silicone oil infused coating,34 the samples were gold-sputtered and observed with FESEM. For perfluoropolyethers infused coating, it is difficult for the lubricant to leach from the sample. The blood clotting index (BCI) of samples was evaluated according to our previous protocols.45 Hemolysis Rate Test



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Fresh rabbit blood were centrifugated (3000 rpm, 5 min) at 4 °C. Erythrocytes were separated from plasma and lymphocytes and diluted with PBS. The diluted erythrocytes was then placed on the samples. After incubation on thermostatic shaker for certain time at 37 °C, the plate was centrifuged at 3000 rpm for 5 min. The supernatant from each well was transferred to 96-well plates. Absorption (A) of the supernatant was read at 540 nm. In this assay, erythrocytes treated with distilled water were used as a negative control, and the absorption (B) was also measured. The hemolysis percentage was calculated as (A/B) × 100%. The hemolysis data were expressed as mean of three replicates. Cytotoxicity Assay The cytotoxicity of the coatings was investigated by MTT assay.22 The cell was cultured according to our previous protocols.45 Briefly, Murine fibroblasts cell line L929 was cultured in Dulbecco’s modified Eagle’smedium (DMEM, Beijing Solarbio Science & Technology) supplemented with 10 vol% fetal bovine serum, 100 units/mL penicillin and 4.5 g/L Glucose. The cell suspension (1 mL, 105 cells/mL) was added to 24-well plates, and cultured under 5 vol% CO2 atmosphere at 37 °C for 24 h. The samples were rinsed with sterilized PBS and then gently placed on the top of cell layer. The control experiment was conducted only using the culture medium. The samples and culture medium was removed after incubation for another 24 h at 37 °C. 100 µL of MTT solution with 900 µL culture medium was added to each well with continuous culture for 4 h. After removing the medium and MTT solution, dimethyl sulfoxide (DMSO, 1 mL) was added to dissolve the formazan crystals. Supernatant


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(200 µL) was then transferred to a 96-well plate, and the optical density was measured at 490 nm by microplate reader. The data were expressed as mean and standard deviation of three replicates.



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RESULTS AND DISCUSSION As illustrated in Scheme 1, solution blow spinning was used to fabricate SIBS microfiber coating by a commercial airbrush, compressed N2 and polymer solutions (Scheme 1 (A)). The solution blow spinning technique can be used for rapid deposition of microfiber onto any substrate. After infusion oil into SIBS microfiber, water droplets slide off unimpeded on the stable slippery liquid-infused microfiber coating (Scheme 1B). The lubricant spread and formed a thin oil layer on top of the coating. Scheme 1 (C, D, and E) shows the images of an aqueous droplet of rhodamine B dye (100 µL) rolling down on the coating tilted at angle≈10°.

Scheme 1. (A) Schematic showing the solution blow spinning approach for fabricating micro-structured coating. (B) Schematic showing water droplet sliding on a oil-infused micro-structured coating. (C-E) Images of droplet of a rhodamine B aqueous (100 µL; angle ≈10°) sliding on a micro-structured coating infused by silicone oil for 0 s (C), 2 s (D) and 6s (E), respectively.


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Microfiber Coating Characterization It is known that electrospinning is a convenient method of fabricating polymer coatings. However, this technique suffers from several disadvantageous, such as high voltages, electrically conductive targets, and low deposition rate. Solution blow spinning that can rapidly and conformally fabricate large areas coating is a low cost alternative technique. Similar to electrospinning, solvent, solution concentration, and specific deposition conditions are important factors in manipulating the structure characteristics of the microtextured coatings produced by solution blow spinning. Previous study showed that a key parameter for the structure was the concentration (c) with respect to the overlap concentration (c*). The solution blow spinning can form a corpuscular (c < c*), beads on a string (c ∼ c*), and fibers morphology (c > c*).37 These findings were also verified in the present study. At relatively low polymer concentration (5 w/v%), a corpuscular layer was observed on the substrate (Figure 1(a)). As the polymer concentration increased to 10 w/v%, the substrate with a beads-on-string morphology was observed (Figure 1(b)). At higher polymer concentrations (15 w/v%), a dense fibrous mesh was produced (Figure 1(c)). The results suggested that the dimaters of SIBS fibers can be easily modulated between 1 µm and 20 µm (Figure 1(d)). Figure 1(e) shows the cross-section images of the MC-15. It can be seen that the thickness of the SIBS microfiber layer on glass is ∼280 µm.



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(a)

(b)

(c)

(d)

(e) Figure 1. Representative FESEM images of blow spun of SIBS in THF. Scale bar for (a) MC-5, (b) MC-10 and (c) MC-15 are 100 µm and 20 µm in the inset. (d) Size distribution of fiber diameter of MC-15. (e) Representative FESEM image of the cross-section of MC-15 (Scale bar is 200 µm). In contrast to electrospinning, solution blow spinning is more convenient and can be easily “paint” more targets with fibers. Herein, SIBS microfibers can be deposited


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by solution blow spinning onto irregularly shaped targets, including syringe, evacuated blood tube, closure-piercing device and drip infusion device. (Figure 2).

(a)

(b)

(c)

(d)

Figure 2. Demonstration of versatility of solution blow spinning to coating different shaped objects. (a) syringe (b) evacuated blood tube (c) closure-piercing device (d) drip infusion device. Surface Characterization Figure 3(a) presents the ATR-FTIR spectra of the samples. After infusion of silicone oil, three new peaks at 1261 cm−1 (Si-CH3, deformation vibration), 1018 cm−1 (Si-O-Si, stretching vibration) and 798 cm−1 (Si-O-Si, stretching vibration) were observed. As for perfluoropolyethers infused samples, new peaks at 1184 cm-1 (CF2-O-CF2) and 1050-1200 cm-1 (C-F2) appeared on the spectrum. The wettability is critical for the adhesion of protein, cells and bacteria onto biomaterials surface. As we known, wettability can be tuned by roughness. In the work presented here, the roughness of polymer coating could be manipulated by the polymer concentration. The static WCA of the SIBS-based coating was increased as the spinning solution concentration increasing (MC-5: ∼120°; MC-10: ∼129°; MC-15: ∼134°). Owing to



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the molecular smoothness interface between the water droplet and the thin oil layer, the values of static WCA become smaller after infused with silicone oil or perfluoropolyethers (silicone oil: ∼89°; perfluoropolyethers: ∼98°; Figure 3(b)). The advancing (θA) and receding (θB) water contact angles of the samples were summarized in Table 1. It is shown that the contact angle hysteresis of MC-15 is ∼46.5°. The dynamic contact angles of silicone oil and perfluoropolyethers infused samples changed with respect to the MC-15. As for silicone oil and perfluoropolyethers infused coatings, the contact angle hysteresis values are ∼2.5° and ∼4.1°, respectively. The liquid-repellency of the lubricant infused coating is associated with how quickly the tested liquid droplets can be removed from the surface. We measured the velocity of 100 µL droplets of aqueous rhodamine B moving on the microfiber coating infused with two kinds of lubricant. Chemical compositions and viscosity of the lubricant can significantly affect the velocity of the droplet. As shown in Figure 3(c), the droplet slides down the coatings at a rate of 0.0 cm s–1, 1.1 cm s–1 and 0.6 cm s–1 for MC-15 (Video in the Supporting Information S1), silicone oil infused coating (Video S2) and perfluoropolyethers infused coating (Video S3), respectively. It presented that sliding velocities of droplet decreased substantially with an increase in contact angle hysteresis of coatings. Since the slippery coatings showed excellent water-repellent characteristics, the antifouling properties subsequently studied.


of coatings

were

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(a)

(b)

(c) Figure 3. (a) ATR-FTIR spectra for MC-15, silicone oil and perfluoropolyethers infused coating. (b) Static water contact angle of samples. (c) The time required for 100 µL aqueous rhodamine B droplet to slide 7 cm on MC-15, silicone oil and perfluoropolyethers infused coating (tilt angle ≈10°). (data shown are average ± standard deviations). Significant difference (*p < 0.05; **p < 0.01; and ***p < 0.001). Table 1. Dynamic water contact angle of the coatings. Sample

θA(°)

θB (°)

Hysteresis (°)

MC-15

137.8 ± 0.9

91.3 ± 1.2

46.5 ± 0.8

silicone oil

91.5 ± 0.4

89.0 ± 0.2

2.5 ± 0.5

perfluoropolyethers 98.5 ± 0.4

94.4 ± 0.6

4.1 ± 0.9

Slippery Coating Inhibits Bacterial Attachment



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Bacterial adhesion is a major cause of biomedical devices failure. Therefore, it is critical to create surfaces that can effectively inhibit the incidence of biomedical-devices associated infections. In this study, the efficacy of the slippery coating in reducing bacterial attachment was estimated using Gram-negative P. aeruginosa, because it is one of the most common species responsible for biomedical device-related infections. As shown in Figure 4, bacteria grown on the MC-15 wets the coating and remains pinned as it is tilted. In contrast, bacteria on the silicone oil and perfluoropolyethers infused coatings slides readily and no visible residue is observed after tilting (Figure 4(a) and (b)). The amount of the adherent bacteria was quantitatively investigated by crystal violet staining method. Compared to MC-15 sample, the amount of attached P. aeruginosa on the silicone oil and perfluoropolyethers infused coatings were reduced by ∼97.3% and ∼97.5%, respectively (Figure 4(c)). The immiscibility between lubricant and bacterial medium is critical to manipulate bacterial adhesion. It is obvious that bacteria can not fix firmly onto the dynamic interface as founded on a solid surface.46 (a)

(b)


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(c)

Figure 4. P. aeruginosa incubated for 24 h on MC-15 (left), silicone oil (middle) and perfluoropolyethers (right) infused surface, before (a) and after (b) being tilted for 60 s to test bacterial adhesion. (c) Quantitatively count of bacteria on the silicone oil and perfluoropolyethers infused surface versus control MC-15 following 24 h of growth. (data shown are average ± standard deviations). Significant difference (*p < 0.05; **p < 0.01; and ***p < 0.001). To confirm that the cytotoxicity of lubricants is not responsible for the inhibition of bacterial adhesion on slippery coating, the effects of lubricants on the growth of bacteria were screened.29 The quantity increasing of P. aeruginosa over time was measured by shaken cultured in LB growth medium with 1 vol% concentrations of silicone oil or perfluoropolyethers. As seen in Figure 5, quantities of P. aeruginosa were measured at 0, 5, 10, and 30 h for all lubricants as compared to the control group (no lubricant). The negative control (AgNO3 solution) was also investigated. As expected, the lubricants have no effects on bacterial growth.



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Figure 5. Growth curves of P. aeruginosa incubated in LB growth medium including 1 vol% of the silicone oil and perfluoropolyethers as compared to the control groups at 0, 5, 10, and 30 h. (data shown are average ± standard deviations). Hemocompatibility Assays As coatings on biomedical devices in contact with blood, the hemocompatibility is important. Biomedical device-induced thrombosis is mediated through adhesion and activation of blood components.31 The blood compatibility of the coatings was evaluated from whole blood cells adhesion, blood clotting index (BCI) and hemolysis tests. The FESEM images of blood cells adhesion on the coatings are shown in Figure 6 (a–c). Blood cells, such as platelets and erythrocytes, adhered readily and activated highly on MC-15 surface (Figure 6(a)). FESEM characterization after leaching of silicone oil revealed that nearly no blood cells were observed (Figure 6(b)). As for perfluoropolyethers infused samples, it is difficult for the lubricant to leach from the coating, and the lubricant form a stable oil layer on top of the coating (Figure 6(c)). The ability to reduce adhesion of blood components and inhibit blood coagulation is critical for biomaterials. In this study, lubricant infused coatings could effectivly repell blood, while adhesion of blood components on MC-15 was observed, which can result in undesired blood coagulation (Figure 6(d)). The resistance to blood cells adhesion on the slippery coatings is attributed to their liquid-repellent property. The antithrombosis properties of slippery coatings were assessed by blood clotting index (BCI). Compared to MC-15, the lubricant infused coatings had higher BCI with a value of ∼97% (silicone oil) and ∼93% (perfluoropolyethers), both suggesting the


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best antithrombosis performance (Figure 6(e)). Hemolysis is another major concern for blood contacting biomedical devices. Figure 6(f) shows hemolytic activity of the samples. The degree of hemolysis of MC-15 was ∼6.5%. After infusing with lubricants, the samples showed significantly lower hemolysis degrees (∼0.66% for the silicone oil; ∼0.96% for the perfluoropolyethers).

(a)

(b)

(c)

(d)

(e)

(f)

Figure 6. Representative FESEM images of whole blood cell adhesion on (a)



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MC-15, (b) silicone oil infused surface after extraction of the oil and (c) perfluoropolyethers infused surface. Scale bar are 100 µm and 10 µm in the inset. (d) digital photographs showing the samples that contacted with whole blood for 6 h at 37 °C; (e) blood clotting index (BCI) of the samples; (f) hemolysis ratio of samples. (data shown are average ± standard deviations). Significant difference (*p < 0.05; **p < 0.01; and ***p < 0.001). Cytotoxicity Assay It is necessary to demonstrate the absence of adverse effects on the interaction between the slippery coatings and cells. Therefore, the cytotoxicity of the coatings on L929 fibroblasts cells was studied by MTT assay. The viability of L929 cells on MC-15, silicone oil and perfluoropolyethers infused coatings was higher than 95% (Figure 7). This suggested that the samples did not have significant effect on the activity of cells.

Figure 7. The cytotoxicity of MC-15, silicone oil infused surface and perfluoropolyethers infused surface towards L929 fibroblasts cells. (data shown are average ± standard deviations). The activity of L929 cells on different coatings have no statistically significant difference (p > 0.05) after 1 day incubation. CONCLUSIONS


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A novel approach to fabricate slippery coatings described in this paper can prevent surface bacterial attachment and thrombus formation, without using antibacterial and anticoagulant drugs. The solution blow spinning method used here can generate conformal microfiber coating on any substrate, only utilizing a commercial airbrush and compressed N2. Slippery coatings based on SIBS microfiber and lubricants were stable and slippery when contacted with blood and bacterial cultures. Our results demonstrate that the slippery coating not only suppresses thrombus formation, but also inhibit P. aeruginosa attachment. The lubricants have no effects on bacterial growth. The slippery surface has good biocompatibility in vitro. We anticipate that this approach will be widely applicable for the designing of antibacterial and antithrombosis coating of biomedical devices. ACKNOWLEDGMENTS The authors are grateful to the financial support of the National Natural Science Foundation of China (Project Numbers: 51473167). ASSOCIATED CONTENT Supporting Videos: Video showing the sliding behavior of aqueous rhodamine B on MC-15 (Video S1), silicone oil (Video S2) and perfluoropolyethers (Video S3) infused coating. REFERENCES 1.

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423x291mm (72 x 72 DPI)


Liquid-Infused Poly(styrene-b-isobutylene-b-styrene) Microfiber

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