Received Date: November 23, 2016; Accepted Date: January 06, 2017; Published Date: January 09, 2017
Citation: Sunitha S, Adinarayana K, Pankaj T, Sravanthi Reddy P, Sonia G, et al. (2017) Fabrication of Surgical Sutures Coated with Curcumin Loaded Gold Nanoparticles. Pharm Anal Acta 8:529. doi: 10.4172/2153-2435.1000529
Copyright: © 2017 Sunitha S, et al. This is an open-access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.
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Sutures are biomaterials regarded as a major cause of Surgical Site Infections (SSIs). Present work aims at a novel strategy to reduce nosocomial infections by coating sutures with antimicrobial drugs. Gold Nanoparticles (GNPs) coated with antimicrobial drugs are well known for their antimicrobial activity. Hence, synthesis of gold nanoparticles by chemical reduction method followed by preparation of curcumin pegylated GNPs (CPGNPs) were carried out. The formation of the gold nanoparticles, thiolated gold nanoparticles (PGNPs) and CPGNPs was characterized by UV-Vis absorption spectroscopy, Fourier Transform Infrared Spectroscopy (FT-IR) and Scanning Electron Microscopy (SEM) techniques. The average particle size and polydispersity index of drug conjugated gold NPs were found to be 147.8 nm ± 2.03 nm and 0.286 respectively. The plain sutures (purchased from local market) were coated with curcumin pegylated GNPs by dipping technique and characterized by SEM to ensure the coating of curcumin conjugated gold nanoparticles on plain sutures. The CPGNPs coated sutures were evaluated for mechanical properties, drug release studies, biocompatibility, haemo-compatibility, sensitization and for in vivo studies. Histopathology was also done to study the effect of coated sutures on inflammation and cell repair at the site of surgery. The optimized coated sutures exhibited sustained drug release for 4 days and the antibacterial activity of the coated sutures was noticed in comparison to the uncoated sutures. From in vivo studies, it was clearly evident that coated sutures healed the tissue much faster than the uncoated sutures and less inflammation was observed. The same was concluded by the histopathology reports. The successful designing and development of drug-coated biodegradable sutures highlight the applicability of novel technique of coating for effective reduction of SSIs during the hospital stay.
Biocompatibility; Escherichia coli; Nano-biotechnology; Nanomicelles
Recent advances in the area of biomaterials have revolutionized the field of tissue engineering and regenerative medicine. Sutures are biomaterials widely used in wound closure with an aim to ligate injured blood vessels and to draw divided tissues together in clinical settings [1,2]. At present medical-surgical market is splendid with a large number of suture material which is different with reference to composition, tensile strength, structure, origin, type of absorption, treatment or purpose and is available in different sizes and indications. Several parameters like tensile strength, breaking strength, elasticity and capillarity are among important physical characteristics of sutures . Depending on origin sutures can be broadly classified as natural or synthetic with degradation time varying from 60 days for absorbable sutures and longer for non-absorbable sutures [4,5]. Structurally they can be multifilament or monofilament with different resistance and flexibility [6-9].
Surgical site infections (SSIs) are the most common nosocomial infections that occur during long hospital stay . According to national nosocomial infections surveillances system Staphylococcus aureus, coagulase-negative staphylococci, Enterococcus spp. and Escherichia coli are among the most frequently isolated pathogens at surgical sites . Sutures are mainly responsible for approximately 23% of SSIs due to bacterial adherence and colonization in clinical settings with 5 fold increase in cost and extent of hospital stay by 20- fold . Most of the commercially available sutures do not possess antimicrobial activity; this is where biomaterials with antibacterial property have been investigated by many research groups [13-15]. Vicryl Plus was the first marketed antimicrobial suture approved by the US FDA  but there are constant concerns that triclosan, when used as a coating agent, could lead to bacterial resistance and side effects due to its systemic absorption. One of the ways to prevent SSIs is by impregnation or coating the sutures with antimicrobial agents simultaneously taking care of prevention of bacterial resistance .
Coating with polymers is based on grafting the polymer functional groups such as carboxyl and attaching antibacterial agent. This suffers from problem of reduction in the mechanical properties of sutures. Among natural polymers chitosan and alginates are well explored for wound treatment with antibacterial and antifungal activity [18,19]. Coating sutures with natural antimicrobials in the form of nanoparticles can prevent the formation of bacterial colonies without compromising the mechanical properties. One of the promising approaches to overcome bacterial resistant infections is by using of metallic nanoparticles . Reports are available in the literature to coat sutures with silver nanoparticles since it is found to have antibacterial property [21,22]. Gold Nanoparticles (GNPs) have attracted significant interest as a novel platform for various applications such as nano-biotechnology and bio-medicine as they offer convenient surface bioconjugation with molecular probes and remarkable plasmon-resonant optical properties.
Colloidal GNPs represents a completely novel technology in the field of particle based targeted drug delivery. The property of GNPs to bind proteins and molecules without altering their activity has given rise to their use in immuno-diagnostics as well as in histo-pathology. Owing to the small size and higher surface-to-volume ratio, makes GNPs to have better contact with microorganisms and increases the biological, chemical activities associated with high antibacterial activity . Therefore, combining or conjugating antibiotics with GNPs increases the concentration of antibiotics at the infection site.
Hence, coating sutures with natural antibiotics which release drug in a controlled way can be quite useful against SSIs. Curcumin, a natural polyphenolic compound, obtained from Curcuma longa (turmeric) has many therapeutic applications with wound healing as a major advantage [24,25]. Preclinical trials have demonstrated low toxicity of curcumin even used at relatively high doses. The main drawback of curcumin lack of bioavailability because of low water solubility. Approaches like nanoparticles [26,27] liposomes, nanomicelles , phospholipids complexes  were used to improve the bioavailability of curcumin . Manju and Sreenivasan reported the synthesis of GNPs of curcumin using polymer for conjugation to deliver to cancer cell . But it was observed that upon conjugation the drug was less bioavailable for its activity as an important therapeutic group of the drug was bound irreversibly with conjugating agent . Hence it is necessary to see that during conjugation the activity of the drug is maintained and at the same time imparting multi-purpose qualities.
In this context, we reported a new protocol for the formation of curcumin conjugated GNPs using thiolated Polyethylene Glycol (PEG) as a drug carrier. Thiolated PEG was selected as polymer which aids in conjugating the drug with gold nanoparticles. The thiolated PEG-drug conjugates have an advantage of prolonged resistance in the body with decreased degradation by metabolic enzymes.
Hence, the present study made an attempt to design and develop curcumin loaded gold nanoparticles and their incorporation on the surface of the selected sutures to release the drug in a controlled manner for a long time. Evaluation of the coated sutures for their efficacy, safety, and stability using standard procedures were carried out for establishing scientific evidence for clinical use.
Curcumin, poly (ethylene glycol) methyl ether thiol (mol.wt 2000), sodium alginate, aurochloric acid (HAuCl4) and sodium tetra borohydride were purchased from Sigma-Aldrich. TRUGLYDE FAST-absorbable surgical suture U.S.P (Synthetic), Polyglycolic acid sutures were procured from local market. Escherichia coli, Staphylococcus aureus were purchased from NCCS, Pune. Dialysis membrane (M.W cut off 12000 to 14000), agar and trypticase soya broth were purchased from Himedia. All the glassware used for the synthesis was washed with aqua regia which is a mixture of nitric acid and hydrochloric acid. Then the glassware was rinsed with double distilled water followed by drying at 80-100°C in a tray dryer for 12 h. All other solvents were purchased from Sd fine chem Ltd. Synthesis of gold nanoparticles (GNPs), Pegylated GNPs (PGNPs) and Curcumin pegylated GNPs (CPGNPs) (Figure 1).
Preparation of GNPs
Gold nanoparticles were prepared by wet-solvent precipitation method. Initially 10 mL of aurochloric acid solution (5 mM) was heated and stirred (300 rpm) on a magnetic stirrer for 1 h followed by dropwise addition of aqueous sodium tetra borohydride (2 mM) (reducing agent) solution under continuous heating at 60°C ± 2°C for about 8-10 min.
The reaction completion was manifested by the change of colorless solution to purple indicating the formation of gold nanoparticles. The synthesis of GNPs was optimized by different concentrations of aurochloric acid, sodium tetra borohydride (mM) and different processing conditions as represented in Table 1.
|S. No||HAuCL4 (5 mM)||NABH4 (2 mM)||Ratio||Size ± S. d||PdI ± SD|
|1||0.125||1||0.25:1||95 ± 4.04||0.312|
|2||0.25||1||0.5:1||132 ± 3.05||0.291|
|3||0.375||1||0.75:1||123 ± 2.88||0.245|
|4||0.5||1||1:1||79 2 ± 0.51||0.281|
|5||0.5||0.25||1:0.25||843 ± 0.05||0.372|
|6||0.5||0.5||1:0.5||104 ± 2.51||0.267|
|7||0.5||0.75||1:0.75||157 ± 2.52||0.381|
|8||0.5||2||1:2||123 ± 2.72||0.437|
|9||0.5||3||1:3||197 ± 3.2||0.341|
|10||0.5||4||1:4||243 ± 3.7||0.273|
|11||0.5||5||1:5||172 ± 2.1||0.675|
|12||1||1||2:1||64 ± 1.5||0.391|
|13||1.5||1||3:1||83 ± 2.5||0.243|
|14||2||1||4:1||97 ± 1.5||0.275|
|15||2.5||1||2:5||222 ± 2||0.632|
Table 1: Data of optimization design for preparation of Gold NPs using different mM ratios of gold solution and sodium borohydride.
Pegylation of GNPs
Prepared GNPs were coated with poly (ethylene glycol) methyl ether thiols as reported earlier by Sahoo et al. . In brief, thiolated polyethylene glycol solution (1% w/v) was added to GNPs at room temperature and stirred for 3 h for the formation of pegylated GNPs (PGNPs). The formed nanoparticles were centrifuged at 10000 rpm for 30 min to remove unbound polymer and the sediment is redispersed in 10 mL of distilled water. Coating of poly(ethylene glycol) methyl ether thiol was confirmed by measuring the UV-Vis absorbance at 541 nm supported by its plasmon resonance mechanism of metallic nanoparticles.
Preparation of Curcumin pegylated GNPs (CPGNPs)
Curcumin drug solution (2% w/v in acetone) was added to 50 mL PGNPs solution under magnetic stirring for 3 h at room temperature. The formed CPGNPs were separated by centrifugation at 1000 rpm for 30 min to remove the unattached drug. The prepared CPGNPs were freeze-dried and used for further analysis.
Coating of CPGNPs onto sutures
Coating of CPGNPs onto the sutures is done by the slurry dipping technique with the use of sodium alginate as an immobilizing agent. Accurately, 10 mL of 2% w/v sodium alginate was added to 10 mL of 0.1% w/v sodium chloride (NaCl) under magnetic stirring for 8 h at room temperature. CPGNPs (10 mg/mL) were added to above mixture with stirring for 30 min for the formation of alginate-curcumin gold colloidal nanoparticles. Sutures of length 2 cm were dipped in the formed alginate-curcumin gold colloidal NPs solution for 10 min followed by air drying for 5 min. The above process was repeated 10 times for adequate coating of the sutures. The coating was optimized per the parameters are given in Table 2. For cross-linking coated sutures were immersed in 4% w/v calcium chloride solution and kept for 30 min to ensure complete cross-linking followed by washing with double distilled water .
|Formulation||Z-Average (d. nm)||PdI||ZP (mV)|
|GNPs||64.80 ± 1.54||0.391||-31.9|
|PGNPs||96.80 ± 1.89||0.222||-30.47|
|CPGNPs||147.8 ± 2.03||0.286||-29.63|
Table 2: Particle size and PdI of optimized CPGNPs.
The percentage of drug coating onto the sutures was calculated by using the below formula:
Where W1: Weight of uncoated suture, and W2: Weight of coated suture.
The synthesized GNPs, PGNPs and CPGNPs were characterized by UV-Vis spectrophotometry (V 650, Jasco) and FT-IR (Perkin Elmer).
UV-visible and FT-IR spectroscopy
The maximum absorbance of gold nanoparticles, PEG-coated gold nanoparticles, curcumin gold nanoparticles were identified by measuring the plasmon resonance of metallic nanoparticles in the range of 200-800 nm. An FT-IR spectrometer was used for obtaining spectra in the range of 400-4000 cm-1.
Particle size, polydispersity index (PdI) and zeta potential (ZP)
The particle size, PdI and zeta potential were measured using Zeta sizer (Malvern ZS90, UK). High ZP indicates stabilization of prepared formulation and positive charge which attract the negative charge of skin. Hence increasing the contact time of drug thereby increases the therapeutic activity of the drug.
Scanning electron microscopy (SEM) analysis
Morphological characterizations of synthesized nanoparticles were visualized using SEM (SEM-S-3700N). Samples were prepared by dropping the nanoparticles dispersion on an aluminum stub and air dried at room temperature.
Entrapment efficiency (EE) and drug release
For EE 5 mg of freeze-dried CPGNPs were dissolved in 10 mL of phosphate buffer pH 7.4 and bath sonicated for 15 min to completely dissolve the drug. After filtration and suitable dilution, the drug concentration was determined by UV-Vis spectrophotometer at 431 nm and EEwas calculated using the given formula.
Entrapment efficiency=Amount of drug in NPs/Total amount of drug × 100
The release of curcumin from coated sutures was estimated by performing immersion studies. Coated sutures were placed in cotton plugged sterile conical flask containing 50 mL of simulated body fluid (SBF) solution of pH 7.4 and kept on a magnetic stirrer at room temperature. Samples were withdrawn at respective time intervals (12, 24, 36, 48, 60, 72, 84, 96) h and analysed for drug content using UV-visible spectroscopy at 431 nm [12,33].
To determine the stability of the curcumin molecules bound to the surface of GNPS the functionalized NPs were stored for more than 4 weeks as per ICH storage conditions and monitored for particle size, PdI and EE.
Measurement of mechanical properties
The diameter of the plain sutures and coated sutures were measured using a micrometer different positions of the sutures and an average diameter of the suture was calculated and expressed in millimeter.
An important property of the suture is its tensile strength as it helps the practitioner to make a knot. If the suture is very weak by applying high knotting force the suture may break very easily. Hence, it is very important to determine the tensile strength of the coated suture. Mechanical properties like Tensile Strength (TS), and elongation at break (E/B) were evaluated using ultra test, mecmesin, UK set with 25 kg load cell with minor modifications. Coated suture of 8cm length was taken and fixed between two clamps which were positioned at a distance of 3 cm and the strips were pulled with top clamp at a rate of 1 mm/s till the film breaks. The mechanical properties were calculated using the below formulae . These properties were evaluated to confirm the physical quality of the coated sutures in terms of strength and physical stability.
The antibacterial assay was performed on non-pathogenic Escherichia coli (E. coli ) and Staphylococus aureus (S. aureus ) for curcumin coated sutures and uncoated suture (control). Inoculums (100 μL) of fresh cultures were spread on to nutrient agar medium (NAM) plates. The CPGNPs coated sutures and uncoated sutures of length 2 cm were placed in petri plates after inoculation. The plates were incubated at 37°C for 24 h and zone of inhibition was measured after 48 h. The assay was performed in triplicates.
Haemocompatibility testing of medical devices was performed by total haemolysis test as described according to practice F756-08  using human erythrocytes and the test was performed with isotonic extract of the test material in contact with human blood as described in practice F619-03 . In brief, the coated sutures and uncoated sutures of 2 cm each were incubated in normal saline for 24 h in Biological Oxygen Demand (BOD) incubator at 37°C. After 24 h of incubation, the sample extracts were taken as a test with 0.1% w/v sodium carbonate as a positive control and normal saline of pH 7.2 (0.9% w/v Sodium chloride) as a negative control. For haemolysis testing, fresh 200 μL diluted blood was mixed with each test sample, positive control and negative control. These samples were then incubated for 3 h at 37°C followed by centrifugation to remove any solid particles.
Where Dt: Absorbance of test, Dc: Disease control, Dpc: Absorbance of positive control, Dnc: Absorbance of negative control.
Cytotoxicity of the coated sutures was evaluated using MTT 3-(4, 5- dimethylthiazol-2-yl)-2, 5-diphenyltetrazolium bromide survival assay . The test sample for cytotoxicity test was prepared according to ASTM standard F619–03. The two different test materials uncoated marketed suture (Control) and CPGNPs coated sutures were added separately in 10 mL Dulbecco’s Modified Essential Media (DMEM) for 24 h at 37°C. After incubation, the prepared media alone was used as a test sample. The 3T3-mouse embryo fibroblast cells were seeded (1.5 × 104 cells/well) in 96 well microtitre plates in triplicate and cultured in DMEM supplemented with 10% fetal bovine serum (FBS) containing sodium bicarbonate (NaHCO3) (1.2 g/L) and penstrep antibiotic (0.025 g/L ampicillin, 0.1 g/L streptomycin) at 37°C in atmosphere of 5% CO2. Then, 100 μL test sample was added to media in triplicates along with fresh media (control). Finally, these samples were incubated for 24 h at 37°C. After incubation, MTT (5 mg/mL) was added to each well and the formazan crystals were dissolved by DMSO. The absorbance was read in a microtitre plate reader (ADD MAKE) at 570 nm, 30 min after the solubilization of the crystals. The percentage cytotoxicity was calculated by the formula:
Cytotoxicity = [(O. D of control–O.D of test)/O. D of control] × 100
Where O.D is Optical Density
In vivo studies
All the animal studies protocols were duly approved by the Institutional Animal Ethics Committee (IAEC) under protocol no NIP/2/2015/PE/132. Swiss albino mice of 20-30 g and 4-5 weeks old were supplied by the Teena labs, India. The animals were acclimatized at a temperature of 25°C ± 2°C and relative humidity of 50-60% under natural light/dark conditions for one week before experiments. Mice were randomized into two groups (n=8). After anesthesia with ketamine (50 mg/kg, i.p) and xylazine (5 mg/kg, i.m) laparotomy was done in mice with a 2 cm cut on ileum near ceacum with scissors. Intestinal defect was closed using single layered, interrupted anastomosis using uncoated and CPGNPs coated sutures in the two groups respectively. The abdominal wall was closed with running suture in both peritoneal-muscular layers and skin layer. All the techniques were performed in the sterile area. At the end of surgery, mice were allowed free access to water and a liquid diet. At the end of day 7, ileum was excised from euthanized animals and observed for adhesion formation scores. The excised ileum samples were stored in formalin buffer until further evaluation of histopathology. The adhesion formation scores were done as per the scoring scale of Van der Ham et al. . Briefly, on macroscopic observation at anastomotic site the score was given as follows: 0: No adhesions; 1: Minimal adhesions between anastomosis and omentum; 2: Moderate adhesions between omentum and anastomosis; and 3: Severe and extensive anastomosis including abscess formation.
The histopathological sections of ileum were scored for parameters like inflammatory cell infiltration and fibroblast growth as per the modified Ehrlich and Hunt numerical scale (0–4) under a light microscope and were scored in a blind fashion [41,42].
Synthesis of gold nanoparticles (GNPs), Pegylated GNPs (PGNPs) and Curcumin pegylated GNPs (CPGNPs)
In the present study GNPs were synthesized using 5 mM aurochloric acid to 2 mM sodium tetra borohydride as a metal precursor and reducing agents respectively (Table 1). The formation of GNPs was indicated by color change as shown in the Figure 2 .
The formation of CPGNPs was carried out by a two-step process. In the first step PGNPs were synthesized by coating 1% w/v thiolated PEG to optimized gold nanoparticles on a magnetic stirrer at 300 rpm .
The coating of the thiolated polyethylene glycol was confirmed by measuring UV spectra followed by conjugation of curcumin to the PGNPs.
UV-Vis and FT-IR spectroscopy
UV-Vis spectra of (i) GNPs,(ii) thiolated PGNPs, (iii) curcumin and (iv) CPGNPs in aqueous media were depicted in Figure 2. Curcumin shows an absorption peak at 431 nm which indicates basic di aryl heptinoid chromophore group. In case of blank GNPs maximum absorbance was seen at 541 nm which is the characteristic peak for gold nano particles. Absorption peak in spectra of thiolatedPGNPs was seen at 364 nm (thiol group) and 543 nm which is a distinguishing peak of PGNPs arising due to surface plasmon resonance . Curcumin functionalized PGNPs shows two distinct characteristic peaks at 436 nm and 550 nm which confirm the modified functional groups of components in the gold curcumin complex NPs. The increase in wavelength for absorption peak of curcumin by 5 nm and GNPs 7 nm may be ascribed to the conjugation of thiolated PEG functionalized GNPs with the drug.
The results of UV-Vis spectroscopy were also supported by FT-IR. Figure 3 depicts the FT-IR spectra of (i) thiolated PEG, ii) curcumin, iii) Physical mixture, (iv) thiolated PEG capped gold nanoparticles and v) thiolated PEG functionalized GNPs. The signatures of thiolated PEG may be recognized as C-H stretching (2886cm-1), CH bending (1360 cm-1), C-O-C stretch (1000-1300 cm-1). Signatures of curcumin are free OH (3503 cm-1), CH aryl (3013 cm-1), CH methyl (2943 cm-1), C=O and C=C enol (1429 cm-1-1630 cm-1) and C-O-C (1000 cm-1-1300 cm-1) contributed by symmetric and asymmetric contributions of C-O-C chains . Spectrum (iv) illustrates the functionalization of sodium borohydride reduced GNPs with thioPEG with a shift of CH stretch from 2359 cm-1 to 2363 cm-1. Spectrum (v) clearly discloses the characteristic peaks of both thiolated PEG and curcumin. Drug molecules were attached to functionalized GNPs by intermolecular hydrogen bonding with a shift of OH stretching . The basic heptinoid group of curcumin remains integral and negatively charged gold nanoparticles bind with SH group of polyethylene glycol in pegylated nanoparticles. Thus UV-Vis data with the support of FTIR results confirms the formation of CPGNPs.
Coating of CPGNPs on sutures
Alginate represents a family of polysaccharides composed of homo polymeric region of β-D-mannuronic acid and α-L-guluronic acid interspersed with mixed sequences and has been widely used as an immunoisolation membrane for transplantation purposes  and as an immobilization agent for enzymes . Hence, curcumin pegylated GNPs were immobilized before coating onto the sutures. Immobilization provides the inert and biocompatible system with resistance to high temperature with retained activity. The coating of alginate CPGNPs over sutures was done by a slurry dipping technique in the aseptic condition in laminar flow and the same was confirmed by SEM images, drug release studies and antibacterial assay.
Particle size, PdI and zeta potential
The particle size was measured by Malvern zeta sizer in double distilled water. The average particle size of GNPs is 64.80 nm ± 0.4 nm and the average diameter of PGNPs is 96.80 nm ± 2.6 nm with PdI 0.391 and 0.222 respectively. The average diameter of CPGNP is 147.8 nm ± 2.7 nm with PdIof 0.286. The results (Table 2) clearly an indicate an increase in particle size after conjugation of drug. zeta potential was found to be -29.63 mV ± 0.45 mV which provides enough surface charge to stabilize particles from aggregation.
To know the effect of different concentrations (mM) of gold to thiol, the PGNPs were synthesized at different ratios of gold to thiol and their effect on particle size and PdI were measured for which the data is shown in Table 3. From the results it was found that gold/thiol ratio of 2:1 resulted in particle size of 88 ± 0.34 nm with PdI 0.254. Hence it was selected for further studies.
|Formulation Code||Gold /thiol polymer||Particle size (nm)||PdI||ZP||E.E (%)|
|GT1.||1:2||168 ± 1.2||0.322||-31.9||60 ± 2|
|GT2||5:1||254 ± 0.31||0.435||-10.2||68 ± 3.60|
|GT3||1:1||154 ± 2.3||0.126||-19.8||70 ± 2|
|GT4||2:1||88 ± 0.34||0.254||-27.80||84 ± 2.52|
|GT5||2:5||167 ± 1.52||0.472||-29.3||55 ± 2.08|
Table 3: Data of particle size and PdI different concentration of gold to thiol ratio.
Scanning electron microscopy
SEM analysis revealed morphological features of the prepared GNPs, PGNPs, CPGNPs, plain suture and coated suture. From Figure 4 it was found that the prepared GNPs and drug loaded nanoparticles possess spherical shape with a smooth surface without visible particle aggregation.
SEM analysis of coated suture surface and plain suture surface clearly distinguish uniform coating of CPGNPs over suture (Figure 5).
The surface of the coated sutures was rough indicating the coating of drug loaded CPGNPs .
Entrapment efficiency and drug release
The results of entrapment efficiency of drug loaded GNPS were shown in Table 3. Entrapment efficiency was ranging from 55% ± 2.81% to 84% ± 2.56% and highest entrapment was found when drug to thiolated PEG ratio was 2:1. High entrapment may be attributed to the attachment of two drug molecules to a polymer having two active sites. Hence, this ratio was further selected for coating onto sutures. The percentage drug release was studied in SBF and the release is shown in Figure 6. The drug was released from coated sutures up to 4 days.
Stability studies were done as per ICH guidelines for CPGNPs for two months and monitored for particles size, PdI and entrapment efficiency. The nanoparticles when stored at 40°C ± 2°C, 75% ± 5% RH showed a slight increase in particle size from 147.8 nm ± 2.22 nm to 180 nm ± 3.68 nm and PdI changed from 0.286 to 0.88. The EE was decreased from 84 to 82% (Table 4). From the studies it was found that stability of the drug conjugated gold nanoparticles was not affected even when stored at different conditions.
|Formulation code||Storage conditions||EE||Particle size||PdI|
|Initial (%)||Final (%)||Initial (nm)||Final (nm)||Initial||Final|
|GT4 (2:1)||25°C ± 2°C, 60 ± 5% RH||84||78||147.8||265.9||0.286||0.711|
|40°C ± 2°C,75 ± 5% RH||84||82||147.8||180||0.286||0.88|
Table 4: Data of stability study.
Measurement of mechanical properties
An important property of the suture is its tensile strength and mechanical properties as itdecides the ease with which the practitioner can make a knot. From the current study, the standard marketed suture was found to have a diameter of 0.370 mm ± 0.26 mm with a tensile strength of 3.90 kg/m2 ± 0.156 kg/m2 whereas the coated suture has a diameter of 0.0398 mm ± 0.31 mm with a tensile strength of 3.88 kg/m2. The drug coating did not affect tensile strength of the suture. There was no significant difference in the elongation at break which was around 32.37% ± 2.46% for uncoated suture and around 30.64% ± 3% for drug-coated suture. From the results, it is clear that coating did not affect the tensile strength and elongation at break of the suture, indicating no prominent alterations of the mechanical properties of the coated sutures.
The main purpose of drug coating on to the suture was to inhibit the bacterial growth, thereby facilitating the healing and prevention of SSIs. The antibiotic diffuses out from the coated sutures and inhibits the growth of bacteria resulting in a zone of inhibition. The antimicrobial activity of the studied sutures using agar diffusion method has been represented in Figure 7 and the zone of inhibition values are tabulated in Table 5. Surrounding the CPGNPs coated sutures there was a clear zone of inhibition in both gram positive and negative micro organisms as compared to uncoated sutures.
|S. No||Suture||Antimicrobial assay (Zone of Inhibition in cm)||Hemocompatibility assay(% haemolysis)||Cytotoxicity Assay
|E. coli||S. aureus|
|1||Uncoated||-||-||1.2 ± 0.09||4.2 ± 0.81|
|2||CPGNPs||3.6 ± 0.9||4.2 ± 0.7||0.8 ± 0.04||5.4 ± 0.97|
Table 5: Antimicrobial, hemocompatibility and cytotoxicity of coated sutures. All the data presented were mean SD of triplicates. No significant statistical difference was noted on comparison between groups.
Cytotoxicity of the coated and uncoated sutures on 3T3-mouse embryo fibroblast cells using MTT assay the cytotoxicity of the different sutures has been mentioned in Table 5. The results revealed the biocompatibility of the coated sutures and fibroblast cells were viable up to 94.6% in CPGNPs coated sutures when compared to 95.8% with uncoated sutures. The observed preservation of cell viability can be attributed to not using any organic solvents in the process of preparation of NPs and their coating on sutures. Though acetone has been used in dissolving curcumin it has not shown any cytotoxicity in the cell cultures. Both haemocompatibility and cytotoxicity studies support the safety and biocompatibility of the coated sutures.
Haemocompatibility assay is considered to be a simple, reliable and reproducible method for estimating compatibility of biomaterials as per ASTM guidelines (ASTM; F 756–08). Based on their hemolytic index (hemolysis%) as per the guidelines materials were classified into three different categories. If the percentage of hemolysis is over 5% the material is considered as highly hemolytic; while the one with a haemolytic index between 5% and 2% are said to be slightly hemolytic and if hemolysis percentage is below 2%, the material is considered as a non-hemolytic material. This assay has been carried out to study the compatibility of coated sutures with blood cells and components as haemolysis by biomaterials is prime factor deciding their toxicity. The % hemolysis of different sutures has been tabulated (Table 5) and it was observed that the CPGNP scoated sutures falls in non-hemolytic category similar to that of uncoated sutures explaining their biocompatibility.
In vivo study
The in vivo studies were done and the images of the animals with coated sutures and their absorption after 7 days is seen in Figure 8 and the histopathology studies revealed that uncoated sutures have shown numerous thick adhesions around anastomosis whereas loose, minimal adhesions were found in both the groups sutured with coated sutures (Figures 8 and 9). Results of the in vivo intestinal anastomosis model have demonstrated better healing and less inflammation with coated sutures. The incidence of any pus, abscess and sepsis are not found in any of the experimental groups. The adhesion score is referred as an excellent macroscopic parameter which gives an idea about the quality of healing.
The mean inflammatory cell infiltration and fibroblast deposition were presented in Table 6. The inflammatory scores were significantly lower with coated sutures in comparison with uncoated sutures which can be attributed to the well-known anti-inflammatory property of gold and curcumin used for coating sutures. But, the infiltration of fibroblasts was not much varying between the groups at the examined time point. Wound healing is majorly determined by the collagen and fibroblast levels which increase post 48 h of injury and reaches normalcy gradually as reported by Christensen et al. . This indicates merit of further investigation at different time points will help understanding the process in a better way. From the present reports, we can summarize that anti-inflammatory property of the drug in coated sutures promoted fewer adhesions and better healing in the studied groups.
|S. No||Suture||Adhesion score||Inflammatory cell infiltration||Fibroblast infiltration|
|1||Uncoated||3.2 ± 0.81||3.65 ± 0.27||1.6 ± 0.9|
|2||CPGNPs||0.8 ± 0.11*||0.72 ± 0.21*||1.2 ± 0.5|
Table 6: In vivo study–Adhesion and histopathological score. All the data presented were mean ± SD of 8 observations. *: p<0.05 on comparison with uncoated group.
In the present work, curcumin colloidal gold NPs were prepared by wet-solvent precipitation method with 2:1 ratio using polyethylene glycol methyl thiol ether as a carrier. The prepared gold nanoparticles were coated onto the surface of absorbable suture. The particle size and PdIwere measured for blank gold nanoparticles, thiolated PEG gold nanoparticles and curcumin colloidal gold nanoparticles. The particle size and PdI was significantly affected by varying the concentration of gold and reducing agent. Curcumin colloidal gold nanoparticles coating on suture was done by a slurry dipping method to improve the antibacterial property. The coated sutures showed an excellent antibacterial activity against gram positive and gram negative bacteria and drug release was observed up to 4 days. In vivo studies proved that coated sutures healed the tissue faster as compared to uncoated sutures. Hence it is concluded that the drug loaded sutures are quite suitable for preventing surgical site infections. The clinical usage of the present work should be explored in clinical trials for nosocomial infections and antimicrobial property of the coated sutures with different broad spectrum antibiotics can be explored.
The authors declare that there is no conflict of interests regarding the publication of this paper.
The authors would like to thank DST-SERB for funding the project with sanction no: SB/EMEQ-019/2013. Dr. Ahmed Kamal, Project Director, Prof N. Satyanarayana, Registrar, NIPER Hyderabad, for providing facilities for the research.