Postsurgical adhesion is an unavoidable complication that can cause morbidity and mortality to patients after medical surgeries. Formation of adhesions leads to various clinical disorders including small bowel obstruction, reoperations and its difficulties, infertility in females and also, chronic pain [1, 2]. In a mechanistic view, an imbalance in fibrin band formation and fibrinolysis processes results in the persistence of the fibrinous mass at the site of surgery. Consequently, fibroblasts foray to that area and secrete extracellular matrix materials such as collagen that results in the formation of adhesions [3, 4].
Surgeons try to decrease adhesion formation with less invasive surgical techniques like Laparoscopy instead of Laparotomy to reduce injury to the parietal peritoneum and serosal surfaces . It was estimated by Ouaïssi et al. that peritoneal adhesion occurs after 93-100% of upper abdominal laparotomies and after 63-93% of lower abdominal laparotomies. In laparoscopy, the incidence of peritoneal adhesion decreases to 45% .
Some commercial barriers for prevention of adhesion have been introduced. However, clinical utilization of these products have not been extensive . Some of the barriers used after abdominal surgery include oxidized regenerated cellulose , hyaluronate carboxymethylcellulose [8, 9], Icodextrin , and polyethylene glycol . Broek et al. have recently reviewed the benefits and harms of adhesion barriers . Lack of awareness and also, underestimating the burden of morbidities of postsurgical adhesions have resulted in the neglect of applying the barriers for adhesion prevention. In spite of severe complications of postsurgical adhesions, there is no suitable medical strategy to prevent adhesion formation .
In the light of recent advances in nanomedicine, new strategies for managing complicated medical problems like postsurgical adhesion have been developed. Over-ally, anti-adhesion agents proposed for postsurgical adhesion are hydrogels [13-16], gels [2, 17], nanofibers [18-20], nanosheets . Nanofibers can be fabricated by self-assembly, phase separation and electrospinning and each one has its own advantages and disadvantages [22-24]. Among different preparation techniques, electrospinning is vastly considered for fabrication of nanofibers for tissue engineering [9, 25, 26], antibacterial membranes  and drug delivery  applications.
Different kinds of polymers have been used to prepare electrospun nanofibrous sheets for anti-adhesion barriers [3, 18-20, 29-31]. It is expressed in many research that drug-loaded nanofibers are more admissible for an anti-adhesion barrier. For decades, scientists are interested in curcumin (Cur) as an antioxidant, anti-inflammatory and anticancer agent [32-34]. In this regard, Cur has been previously loaded into different kinds of nanofibers, such as Polycaprolactone (PCL), PCL/PEG (Polyethylene glycol), PVA (polyvinyl alcohol), PLA (polylactic acid), various medical applications [35-39].
In the present study, electrospun Cur-loaded PCL (Cur-PCL) sheets were successfully prepared to be utilized as an adhesion barrier in mice model. The obtained electrospun sheets were characterized using SEM and ART-FTIR. Also in vitro degradation and drug release were investigated. Finally, the resultant fibrous mats were evaluated in mice model.
MATERIALS AND METHODS
Cur (purity 99%) was purchased from sigma-aldrich, Germany. PCL (Mw 80,000) was purchased Hangzhou Ruijiang Chemical CO., Ltd, China. Chloroform and methanol were obtained from Merck Co., Germany. All of the materials were used without further purification. Electrospinning process was performed by a machine provided by Fanavaran Nano-Meghyas Co. Ltd, Tehran, Iran.
PCL solutions with the 6.0, 7.0, 8.0 and 10% (wt.) concentrations were prepared by dissolving the polymer in a mixture of chloroform/methanol (4/1 v/v) as a solvent system and stirring for 2 hours at room temperature. After complete dissolution of the polymers, Cur (6.0 wt% of total polymer weight) was added to the stirring solutions after 2 h. The stirring process continued for 1h. To electrospun the prepared solutions, a 5ml syringe with a blunt-end 18-gauge needle was used. A rotating drum (300 rpm) covered with an aluminum foil was used as a collector. Applied voltage was 22 kV, the distance between the collector and injecting syringe pump was adjusted to 10 cm and pumping rate was set at 0.7 ml/h. All of the processes were performed at about 30 °C.
For morphological studies, scanning electron microscopy (SEM, XL 30, Philips, USA) was utilized. The samples were observed after gold sputter-coating. Then, the average diameter of about 50 nanofibers in each image was calculated using ImageJ software.
ATR-FTIR spectra were conducted to study the structure of Cur-PCL nanofiber sheets. The scanning range was 600 to 4000 cm -1 and resolution was 2 cm-1 (ATR-FTIR-Tensor 27, Bruker Co, and Germany).
Degradation profile of Cur-PCL nanofibers was done in PBS solution (pH: 7.4). For this purpose, pieces of Cur-PCL nanofibers were immersed in PBS and SEM images were conducted weekly up to 4 weeks.
In vitro Release study
A calibration curve of standard concentrations of Cur was utilized to calculate the amount of released drug in obtained serial samples. For evaluation of the release profile of fabricated nanofibers, the sheets (45 mg) were immersed in 5 ml of PBS/DMSO mixture (9/1 and pH 7.4) and kept in thermostatic shaking incubator in 37 ◦C at 100 rpm. Sampling was done at intended times for 30 days and 1 ml of release buffer was taken and replaced again with the same fresh solution in order to keep the volume of releasing medium constant. A UV spectrophotometer (Bio Aquarius, Cecil, US) was used to analyze the absorbance of obtained samples at 450 nm.
IN VIVO study
Twenty female Balb/c mice at the age of 8 –10 weeks and 24-28 g were utilized to evaluate anti-adhesion properties of Cur-PCL nanofibers. All of the mice were kept in a controlled environment for humidity and temperature in the animal lab at Stem Cell Technology Research Center. The animal ethical issue was considered in order to avoid pain and unsuitable conditions. Induction of adhesion formation was conducted with simulating a sterile abdominal surgery process in two groups, treatment and control. To stimulate an adhesion animal model, a vertical incision created in the middle of the abdomen of anesthetized mice (100 mg/kg Ketamine, 10 mg/kg Xylazine, intra peritoneal) and abdominal walls were reflected. Then, peritoneum was injured roughly by a blade in vertical and horizontal lines. The outer surface of internal organs was abraded by rubbing with gauze.
Cur-PCL nanofibers were cut into 1.5 ×1.5 cm2 pieces with the 30 µm thickness and were exposed to UV radiation overnight. Thereafter, the samples were fixed with four sutures (at four corners) to the peritoneum of treatment group, and the control groups were left without any treatment. Reoperation was done after 28 days to evaluate and score the probable adhesions in both groups.
ADHESION SCORING SYSTEM
Different scoring systems have been previously used to evaluate various anti-adhesion agents in studies [31, 40, 41]. In the present study, the scoring system which is introduced by Haney et al.  was utilized. Table 1 represents the scoring data. The total score of both groups was calculated and compared.
RESULTS AND DISCUSSION
In the light of the importance of size and morphological profile of nanofibers, SEM was used to evaluate the morphological profile of Cur-PCL nanofibers. A correlation was observed between the concentration of the solution and the thickness of nanofibers. Electrospinning of the drug-nanofibers containing 6.0 wt% PCL solutions was led to the formation of nanofibers combined with some beads and the average diameter of nanofibers was 220±100 nm. Increasing the solution concentration resulted in disappearing of beads which also increased the thickness of nanofibers. The means±SD for a diameter of the nanofibers derived from polymer solutions of 7.0, 8.0 and 10.0 wt% is 255±100, 385±150 and 585±179, respectively (Fig. 1). Indeed, an increase in the concentration of the polymeric solution results in higher polymer chain-chain entanglements that in turn, lead to smooth and bead-free morphologies. Meanwhile, the thickness of fibers increases. As 8.0 wt% concentration could provide appropriate electrospun fibers, it was selected to continue the further experimental and evaluations (Fig. 2).
ATR-FTIR spectra of Cur, PCL and the Cur-PCL nanofibers are reported in Fig. 3. For Cur, stretching of the phenolic O-H, stretching vibration of benzene ring, C=C vibration and C-O-C stretching, have bands at 3085–3552 cm−1, 1588 cm−1, 1512 cm−1, and 1143 cm−1 . Spectral bands of PCL include asymmetric CH2 stretching which appears in 2938 cm-1, symmetric CH2 stretching at 2865 cm-1and C=O at 1724 cm-1 [38, 42].
In ATR-FTIR for Cur-PCL nanofibers there are little changes in 3085-3552 cm−1 which is related to phenolic O-H stretching, also there are changes about 2865 cm-1 which is for symmetric CH2 stretching. As observed in ATR-FTIR spectra of Cur-PCL nanofibers, there are bands which are citing to the PCL and Cur.
IN VITRO DEGRADATION
As increasing attention to nanofibers for medical purposes, the degradation rate of nanofibers in the body is an important issue. Studies on the rate of degradation have been done by weighing or imaging for defined pieces of nanofibers. In this study, we used SEM for evaluating degradation rate, weekly for 4 weeks. According to the SEM images (Fig. 4), little alterations in the morphology and structure of the nanofibers after immersion in PBS (pH 7.4) were observed. The rate of degradation was slow as expected for PCL polymer. However, some disruptions in the integrity of nanofibers are shown by arrows in Fig. 4.