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Post-operative peritoneal adhesions are common and serious complications for modern medicine. We aim to prevent post-surgical adhesions using biodegradable and thermosensitive poly(ethylene glycol)-poly(ε-caprolactone)-poly(ethylene glycol) (PEG-PCL-PEG, PECE) hydrogel. In this work, we investigated the effect of PECE hydrogel on preventing post-surgical abdominal adhesions in mouse and rat models.
The PECE hydrogel in sol state could be transformed into gel in less than 20 s at 37°C. In addition, the PECE hydrogel could be easily adhered to the damaged peritoneal surfaces, and be gradually degraded and absorbed by the body within 14 days along with the healing of peritoneal wounds. A notable efficacy of the PECE hydrogel in preventing peritoneal adhesions was demonstrated in the animal models. In contrast, all untreated animals developed adhesions requiring sharp dissection. Furthermore, no significant histopathological changes were observed in main organs of the hydrogel-treated animals.
Our results suggested that the thermosensitive PECE hydrogel was an effective, safe, and convenient agent on preventing post-surgical intro-abdominal adhesions.
Post-operative peritoneal adhesions are common and serious complications for patients. The incidence of intra-abdominal adhesions ranges from 67 to 93% after general surgical abdominal procedures and is even up to 97% after gynecologic pelvic opening-operations [1-3]. They can induce a broad range of diseases such as infertility, pain, bowel obstruction, and difficulties experienced during re-operative interventions [4-8].
Peritoneal adhesions generally form in the early post-operative period. For decades, unremitting efforts on the issue are focused on developing products used during laparotomy. Numerous drugs against postoperative adhesion have been tested, and have shown promise in animal models, but few have penetrated into clinical practice [9-11]. An approach to prevent abdominal adhesions is to apply barrier in the form of a polymer solution or synthetic solid membrane, separating the injured regions during peritoneal healing. For polymer solutions such as sodium hyaluronate (HA) and carboxymethylcellulose (CMC), the residence time at the site of administration is relatively brief . For synthetic solid membranes such as oxidized-regenerated cellulose (Interceed) , PTFE , and HA-CMC (Seprafilm) , complete coverage of injured peritoneal surfaces is difficult. In addition, application of those materials in laparoscopy can be cumbersome due to difficulties in handling and fixation to the damaged tissue, which may also compromise their effectiveness as barrier systems [10,11]. The risk of material residues for prolonged periods is also one of the possible negative aspects of solid barriers .
For these limitations mentioned above, in situ crosslinked hydrogel systems have been explored. These crosslinked hydrogel systems are prepared by chemical modification or inconvenient UV illumination [16-18]. Recently, many crosslinked hydrogels based on hyaluronic acid (HA) have been used to prevent the peritoneal adhesion. However, the relatively long gelation time may be impractical . Hence, it is extremely necessary to find an anti-adhesion agent which is not only effective and convenient for application, but also has a short gelation and retention time.
In our previous work, we have successfully prepared an injectable and thermosensitive poly(ethylene glycol)-poly(ε-caprolactone)-poly(ethylene glycol) (PEG-PCL-PEG, PECE) hydrogel based on PEG and PCL which are biocompatible and have been used in several FDA approved products . PECE hydrogel was proved to be biocompatible, bioabsorbable and thermosensitive, which is a flowing sol at low temperature and forms a non-flowing gel at body temperature [19,20]. Here, the thermosensitive hydrogel system was used for preventing abdominal adhesions, which can be easily applied as a mild viscous sol without spatial restriction, and then quickly changes into a durable and flexible gel when the temperature is increased to body temperature. In addition, adhesiveness to peritoneal wounds, dynamic degradation, and effectiveness in preventing adhesions in vivo of the hydrogel were investigated in detail.
Poly(ethylene glycol) methyl ether (MPEG, Mn = 550, Aldrich, USA), ε-caprolactone (ε-CL, Alfa Aesar, USA), hexamethylene diisocyanate (HMDI, Aldrich, USA), stannous octoate (Sn(Oct)2, Sigma, USA), All reagents used in this article were analytic reagent (AR) grade, and used as received.
PECE copolymer was synthesized as reported previously . Briefly, PEG-PCL diblock copolymer was prepared by ring opening polymerization of ε-CL initiated by MPEG using Sn(Oct)2 as catalyst; PECE triblock copolymer was synthesized by coupling PEG-PCL diblock copolymer using HMDI as coupling agent. Fourier transforms infrared spectroscopy (FTIR, 200SXV Infrared Spectrophotometer, Nicolet, USA) and 1H-nuclear magnetic resonance analysis (1H-NMR, Varian 400 spectrometer, Varian, USA) were used to characterize the prepared PECE copolymer.
PECE triblock copolymer was dissolved in normal saline (NS) at designated temperature at the concentration of 15 wt%, 25 wt%, and 35 wt%, respectively, to form PECE hydrogels, and then these PECE hydrogels were kept at 4°C before use.
The sol-gel-sol phase transition behavior of the PECE hydrogel (35 wt%) was investigated by rheometry (AR Rheometer 2000ex, TA Instruments, USA). PECE hydrogel was placed between parallel plates of 40 mm diameter and a gap of 31 μm. The data were collected under a controlled stress (0.5 dyn/cm2) and a frequency of 1.0 rad/s. The heating rate was 2°C/min. Gelation times of the PECE hydrogel at 25°C and 37°C was also investigated by rheometry.
All animal experiments were approved by the Institutional Animal Care and Use Committee and were in compliance with all regulatory guidelines. Animals were purchased from the Laboratory Animal Center of Sichuan University (Chengdu, China). They were housed at temperature of 20-22°C, relative humidity of 50-60% and 12 h light-dark cycles. Animals were provided with standard laboratory chow and tap water ad libitum. All animals would be in quarantine for a week before treatment.
C57BL/6 mice weighing 20 to 22 g were used to establish the model of surgical adhesion formation [21,22]. We anesthetized mice with a single i.p. injection of 0.15 mL of pentobarbital sodium (10 mg/mL). An anterior midline incision was made through the abdominal wall and peritoneum. The cecum was identified and abraded until visible damage by scrubbing with sterile dry surgical gauze. The damaged cecum was returned to the abdominal cavity, and a 1 × 1 cm apposing parietal peritoneal defect was also created using sterile dry gauze. Then the peritoneum as well as underlying partial muscular layer was excised from the abdominal wall. No attempt of hemostasis or intraperitoneal irrigation was made. The abraded cecum was placed in apposition to the peritoneal wall defect. Then 0.3 mL PECE hydrogel (25 wt%) stored at 4°C was painted on the injured sites and the normal peritoneum around. The incision was finally closed in two layers with 5/0 surgical silk suture. The mice treated with 0.3 mL NS were served as control. Animals were sacrificed by cervical dislocation at predetermined time, and hydrogel adhesiveness to the damaged surfaces or hydrogel residue were investigated. Each animal was evaluated according to the following standard adhesion scoring system, which has been widely used in this field: score 0, no adhesion; score 1, one thin filmy adhesion; score 2, definite localized adhesions; score 3, dense multiple visceral adhesions; score 4, dense adhesions extending abdominal wall visceral.
Wistar albino female rats weighing 230 to 250 g were used to establish the rat sidewall defect-cecum abrasion model [21,22]. The procedure was similar to the methods mentioned above. A 1 × 2 cm peritoneal defect of the cecum with punctate hemorrhage was made by abrasion, and then a 2 × 2 cm apposing parietal peritoneal defect with punctate hemorrhage was created using scalpel in the right abdominal wall. The two injured surfaces were juxtaposed with 3/0 silk suture in order to induce adhesions for the cecum was too floppy in rats. The incision was closed in two layers with 3/0 silk sutures. Forty eight rats were randomly divided into four groups. Each rat in the first group received the treatment of 1 mL NS. The animals in the second, third, or fourth group received the treatment of 1 mL 15 wt%, 25 wt%, or 35 wt% PECE hydrogel, respectively. Two weeks after the procedure, the animals were sacrificed with an overdose of intravenous sodium pentobarbital and examined for adhesion formation by two observers in a double-blinded manner. Each rat was evaluated according to the above mentioned standard scoring system.
Specimens were taken from the damaged caecum, damaged abdominal wall, and adhesion-associated tissues. Then, the specimens were fixed in 4% paraformaldehyde in PBS and were embedded in paraffin. Tissues were sectioned, stained with hematoxylin and eosin (H&E) and then observed for histological assessment by two pathologists in a blinded manner.
To evaluate possible side effects in the PECE hydrogel-treated mice and rats, all the animals were observed after administration of PECE hydrogel, including the general conditions (the activity, energy, hair, feces, behavior pattern, and other clinical signs), body weight, and mortality. After sacrificing, various organs (heart, liver, spleen, lung, kidney, stomach, intestine, brain, and bone marrow, etc.) were harvested and fixed in 4% paraformaldehyde in PBS. These tissues were sectioned, stained with H&E and observed by two pathologists in a blinded manner.
Adhesion scores did not always follow a normal distribution. For this, statistical inferences were made using Mann-Whitney U-tests, or Fisher's exact test, using SPSS 10.0 software (Chicago, IL). A P value <0.05 on a 2-tailed test was considered statistically significant.
FTIR and 1H-NMR were used to characterize the chemical structure of the PECE copolymer [19,23]. The Mn and PEG/PCL block ratio of PECE triblock copolymer calculated from 1H-NMR spectra was 3630 and 1100/2530 respectively. FTIR and 1H-NMR results indicated that the PECE triblock copolymer were prepared successfully.
Gel temperature was defined as the temperature at which storage modulus (G') and loss modulus (G'') were equal. Fig. Fig.1A1A shows the change in storage modulus (G') and loss modulus (G'') of PECE hydrogel (25 wt%) as a function of temperature. The G' in sol state was less than 10 Pa and increased abruptly by the sol-gel transition at approximately 24°C. When the temperature was 37°C, G' reached about 600 Pa. Then, the dramatic decrease of G' at about 42°C demonstrates the gel-sol transition of PECE hydrogel.
Gelation time was defined as the time when G' became higher than G'' . It reflected the changes in G' and G'' during the gelation process and stood for the gelation speed and gel intensity. Fig. Fig.1A1A shows that the temperature was 24°C. In Fig. Fig.1B,1B, the gel was formed in less than 50 s at 25°C, which is higher than sol-gel transition temperature. When the temperature increased to 37°C, gel formed in less than 20 s. During the gelation process, G' and G'' increased gradually and eventually reached a plateau, at which G' was significantly higher than G''. This indicated that the PECE hydrogel system displayed a predominantly solid-like behavior at body temperature.
The injured surfaces were created on both the cecum and the abdominal wall, and then 0.3 mL of 35 wt% PECE hydrogel was painted on both the wounds and the normal visceral peritoneum around, which quickly transformed into gel state. Animals were sacrificed at predetermined intervals over the next 14 days to assess the adhesiveness and degradation of PECE hydrogel (Table (Table11).
On gross examination, the hydrogel adhered to the affected sites and the normal peritoneum was gradually transformed into lubricous viscous liquid due to intestinal peristalsis and peritoneal fluid dilution, and was absorbed by the body within 14 days after the operation. The hydrogel coating the normal peritoneum gradually reduced, and completely disappeared on the 5th day after the operation. Although the hydrogel coating the injured surfaces was also gradually reduced, the residual hydrogel adhering closely to the damaged parietal and visceral surfaces were still observed in each mouse on the 7th day, and completely disappeared within 14 days, which were accompanied with the complete healing of the damaged peritoneal surfaces.
The adhesion scores were evaluated on the 7th or 14th day after surgery [22,25,26]. Therefore, we sacrificed all the control mice on the 7th day, in order to compare the intra-abdominal adhesions with those of the hydrogel-treated mice. As shown in Table Table2,2, none of the hydrogel-treated mice developed adhesion (Figs. (Figs.2A2A and and2B),2B), whereas all control mice developed score 4 adhesions (firm adhesion that could only be separated by cutting) (Fig. (Fig.2C)2C) (P < 0.01, Fisher's exact test). The median adhesion score in the control group was 4, whereas was 0 in the gel-treated group, which was significantly lower (P < 0.01, Mann-Whitney U test).
Forty-eight rats received laparotomy as described in the methods section (Fig. 3A, B), and were randomly assigned into the following four groups; PECE hydrogel 15 wt%, 25 wt%, 35 wt%, and the control group, respectively.
The adhesion scores for all animals are given in Table Table3.3. The median adhesion scores in the three hydrogel-treated groups were all significantly lower than that in control group (15 wt% P < 0.01, 25 wt% P < 0.001, 35 wt% P < 0.001, Mann-Whitney U test). No significant difference was observed between the 25 wt% and the 35 wt% group in the median adhesion scores (P > 0.05, Mann-Whitney U test), but were both obviously lower than that of the 15 wt% group (P < 0.05, Mann-Whitney U test). Score 4 adhesion was developed in all control animals (Fig. (Fig.3C),3C), but in neither 25 wt% nor 35 wt% group (Fig. (Fig.3D)3D) (P < 0.001, P < 0.001, Fisher's exact test). Two rats in the 25 wt% group developed score 2 adhesion between the omentum and the sutured incision. In 35 wt% group one rat developed score 2 adhesion between the omentum and the incision.
On the 5th day after the operation, a smooth layer of PECE hydrogel was observed on the damaged cecal wall taken from the hydrogel-treated mice. Under light microscope, the injured cecal wall was covered by a layer of pink-stained material, which indicated residual PECE hydrogel stained with eosin, together with erythrocytes, macrophages, and other inflammatory cells (Fig. (Fig.4A).4A). The hydrogel-treated defects of the visceral peritoneum began to remesothelialize about 7 days after the treatment, with residual hydrogel, foamy macrophages, macrophages and various fibrosis under the spindle neo-mesothelial cells (Figs. (Figs.4B).4B). During the remesothelialization, the hydrogel residues and foamy macrophages under the integral neo-mesothelial cells layer disappeared gradually within the following 7 days, with different degrees of fibrosis (Fig. (Fig.4C).4C). The pathological changes of the damaged parietal peritoneum treated with hydrogel were similar to those in the hydrogel-treated visceral peritoneum (data not shown).
Samples of rats taken from the healed abdominal wall and the healed cecal wall showed integral neo-mesothelial cells layers, with various fibrosis (Figs. (Figs.4D4D and and4E).4E). In contrast, pathological examination of samples taken from the adhesion sites in NS-treated rats indicated that the cecal muscular layer was fused to the abdominal wall musculature, with varying thicknesses of intervening inflammation and fibrosis (Fig. (Fig.4F4F).
No gross abnormalities were observed in the hydrogel-treated mice and rats. Histological examination of liver, spleen, kidney, heart, pancreas, lung, brain, intestine and bone marrow did not reveal any significant differences between the treated and control groups. No apparent abnormalities were found in the mesothelial cells layers of other abdominal viscera in treated animals.
PECE hydrogel presented in this work was suitable for application in peritoneal cavity. Its physicochemical characteristics and degradation kinetics were appropriate as a promising barrier. It was confirmed by good handling properties during surgery and biological outcomes. The benign nature of the hydrogel was exhibited by its biocompatibility and biodegradability in the mouse and rat models, although long-term safety remains to be demonstrated. Meanswhile, hydrogel with concentration of 25 wt% and 35 wt% showed a notable effect in preventing peritoneal adhesion formation.
Intraperitoneal adhesion is considered to be an inevitable result of surgical trauma to the peritoneum. Trauma initiates an inflammatory response, followed by increase in vascular permeability and release of fibrin-rich exudates and the formation of fibrinous adhesion. If fibrinolysis through the plasminogen-plasmin cascade is not effective enough, fibroblasts invade the fibrinous adhesion. Subsequently, collagen is deposited, leading to the formation of dense fibrous adhesion [9,27,28]. Anti-adhesion barriers act by effectively separating the traumatized peritoneal surfaces during the critical period of adhesion development at 3-5 days after surgery [29-31].
As a physical barrier, the adhesiveness to the traumatized peritoneal surface and biodegradation play key roles in adhesion prevention. Our results showed that the sol state of PECE hydrogel could quickly transform into gel state at body temperature and easily adhere to the damaged peritoneal surfaces. Possible mechanisms might be as follows. Mesothelial cell can secretes surface glycosaminoglycans and a lubricant surfactant similar to type II pneumocytes under normal circumstances [16,32]. However, the injured surface where mesothelial cell layers were stripped facilitates the hydrogels to adhere to the injured locations. In addition, the adhesiveness of hydrogel might be strengthened by the local exudation. We also observed that the hydrogel could be slowly degraded and absorbed during the remesothelialization, and our data revealed that the remesothelialization of the injured parietal and visceral peritoneum treated with PECE hydrogel needed about 7 to 14 days. It is well known that adhesions can be avoided if the integral neo-mesothelial cells layers cover the peritoneal defects. Although the exact effect of PECE hydrogel in anti-adhesion is not clearly understood in a metabolic perspective, it is supposed to be achieved by preventing the apposition of two damaged surfaces during the critical time of adhesion formation and creating favorable conditions for reparative regeneration of mesothelial cells layer.
The excellent hydrogel adhesiveness and degradation behavior and preliminary efficacy in anti-adhesion in mouse model guided us to use the rat model which is commonly used in assessment of the efficiency of barrier devices . We chose low, medium and high concentrations of PECE hydrogel to estimate their different efficacy of anti-adhesion and optimize their concentration. The results showed that the effectiveness increased with the increasing concentration of PECE hydrogel within a certain range. Although the ideal concentration of such a system remained unknown yet, it is reasonable to expect that ideal properties could be further optimized by adjusting the concentrations of the polymer and other parameters.
An ideal anti-adhesion barrier should be effective, biocompatible, resorbable, applicable in the laparoscope, and adherent to the traumatized and oozing surfaces. Our results suggested that compared with existing barrier systems, thermosensitive PECE hydrogel has a number of unique physicochemical properties for preventing postoperative adhesions. First, it can be easily extruded through needle and adhere to the affected sites without spatial restriction, which could quickly form a pliable and durable physical barrier at body temperature, without requiring additional cross-linking agents such as initiators or UV illumination. Second, PECE hydrogel and its degradation products can be cleared from the abdominal cavity in a relatively short time after the remesothelialization. Finally, although the damaged peritoneal defects with punctate hemorrhage were left in our models, it was not a handicap for PECE hydrogel (25-35 wt%) to prevent adhesions.
The PECE hydrogel was highly effective in preventing the formation of postoperative abdominal adhesions. Its thermosensitivity holds great promise compared with existing anti-adhesion barrier systems. It is easy to handle and can be applied with great flexibility, which provides an excellent physical barrier during the critical period of adhesion formation and can be cleared in a short time after the healing process is completed.
The authors declare that they have no competing interests.
QZY, ZX, WYQ, LF, YB and GCY designed the experiments. And the research funds were supported by WYQ, QZY, ZX and LF. YB, GCY and QXR carried out experiments, analyzed the data, and wrote the manuscript; QZY, ZX, LZY, ZST and ZQ corrected the manuscript. QXR and ZST participated in the animal test of the hydrogels.
All authors approved and read the final manuscript.
This investigation was financially supported by National 863 Project (2007AA021804 and 2007AA021902), National Natural Science Foundation (NSFC20704027 and NSFC30370550), Sichuan Key Project of Science and Technology (2007SGY019), and Chinese Key Basic Research Program (2010CB529906).