Tissue regeneration has gained increasing attention in the reconstruction of various body tissues such as the bone and the intestines.1 Intestinal tissue regeneration is a complex process with several limitations.2 Successful intestinal tissue engineering requires specialized biomaterial scaffolds to support cell adhesion and generation of the extracellular matrix.3 Meanwhile, a vascular network, which supply nutrient, oxygen and remove waste, is also vital.4–6
In this regard, the vascularized chamber, such as arteriovenous loop (AVL) chamber and flow-through chamber, can support the survival and proliferation of newly-grown tissue.7 The vascularized chamber serves as an in vivo bioreactor to provide an isolated and vascularized microenvironment, thus stimulating tissue regeneration.8 Various studies have demonstrated different model to enhance intestinal defect repair.9 However, only a few studies have attempted to apply the vascularized chamber model in intestinal regeneration or construct tissue engineering chamber with biomaterial.
Natural biomaterials such as gelatin (Gel), collagen, or chitosan, and synthetic biomaterials such as polycaprolactone (PCL), and hydroxyapatite (HA), can be manipulated to simulate the extracellular matrix (ECM).10,11 Gelatin is a natural biomaterial widely used in tissue regeneration. It is a derivative of collagen, acquired by denaturing the triple-helix structure.12 Although various studies have revealed that the electrospun gelatin fibers had similar fibers average diameter, mechanical properties and ultimate elongations with collagen fibers.13 Gelatin exhibited a higher tensile modulus than collagen fibers. Also, compared with collagen, gelatin exhibits excellent biodegradability, non-antigenicity, and cost efficiency.13,14 However, gelatin has poor mechanical properties. This drawback can be modified using various agents to improve the mechanical properties.15
Graphene oxide (GO) is a modified form presenting oxygen-containing functional groups of graphene, a crystalline form of carbon.16 With excellent inherent properties, it was recently reported on increasing tensile strength and Young’s modulus of biomaterials.17 In addition, GO is highly biocompatible with living cells due to the hydrophilic functional groups on the surface. Besides, GO-Gelatin (GO-Gel) scaffold can be fabricated by electrospinning technology, which permits the production of ECM-like three-dimensional structures with nanoscale fibers.18 Thus, GO-Gel scaffold is a promising biomaterial to construct tissue engineering chamber.
In this study, we hypothesized that a pre-vascularized GO-Gel (V-GO-Gel) chamber could be optimized to repair intestinal wall defects. Therefore, a nanofibrous GO-Gel scaffold was constructed by electrospinning technology, which permits the production of ECM-like three-dimensional structures with nanoscale fibers. The mechanical and biological properties of the materials were characterized to determine optimal scaffold properties. The V-GO-Gel chamber was built by implanting the scaffold around the mesenteric vessels to ensure vascularization. Then it was harvested and used to repair the wounded intestine. Histology and immunofluorescence assays were used to assess tissue regeneration. Figure 1 is a schematic representation of the experimental design.
Figure 1 A schematic diagram of the experimental procedure.
Materials and Methods
Fabrication of GO-Gel Scaffolds
Gelatin (250g Bloom, type B) was purchased from Macklin Biochemical Co. (Shanghai, China). Hexafluoroisopropanol (HFIP), N-(3-Dimethylaminopropyl)-N’-ethylcarbodiimide hydrochloride (EDC), and N-Hydroxysuccinimide (NHS) were purchased from Aladdin Reagent Co. (Shanghai, China). GO was prepared using the Hummer’s Method as previously described.19 Gelatin was dissolved in HFIP under continuous magnetic stirring for 24 hours to obtain a solution with a gelatin concentration of 50% w/v. On the other hand, GO was dissolved in deionized water using ultra-sonication in an ice bath for 4 hours to obtain homogeneous GO dispersion with GO concentrations of 0, 0.5, 1, and 1.5% w/v. After that, different concentrations of the GO dispersion were distributed in Gel/HFIP solution using ultra-sonication in an ice bath to obtain homogeneous GO-Gel solution. The electrospinning precursor solution was prepared by mixing gelatin (25% w/v) with 0, 0.25, 0.5 and 0.75% w/v GO.
The electrospinning process was improved from the previous studies.20,21 The precursor solution for the electrospinning process was filled in a 5-mL syringe attached to a 19-gauge needle. Electrospinning was carried out for 10 hours to generate nanofiber mats using the following parameters: supplied voltage, 18kV; needle tip to collector distance, 20cm; flow rate, 0.5mL/h. Then, the nanofiber scaffolds (Gel, 0.25% GO-Gel, 0.50% GO-Gel, 0.75% GO-Gel) were crosslinked by immersing in a 95% ethanol solution containing 5% w/v EDC and 2% w/v NHS for 24 hours. After a thorough wash in distilled water, the materials were dried overnight in a vacuum oven to remove residual solvents.
Physiochemical Characterization of GO-Gel Scaffolds
Field Emission Scanning Electron Microscope (FESEM, Nova NanoSEM 450, FEI, Netherlands) set at an accelerating voltage of 10kV was used to observe the microstructure of the scaffolds. The surface of the scaffolds was sputter-coated with platinum prior to the examination. Thermo Scientific iS50R Nicolet ATR-FTIR and Raman (LabRAM, HR800, Horiba JobinYvon, France) spectrometers were used to record the surface characteristics of the scaffolds. FTIR measurements were determined at a resolution of 4 cm−1 in the frequency range 400–5000cm−1, while the Raman spectrum was determined at a scanning range of 100–4000cm−1. A diode laser with a wavelength of 532nm and power adjusted to 30mW was used as the excitation source. Crystalline phases of GO and GO-Gel materials were evaluated by X-ray diffraction (XRD, Empyrean, PANalytical B.V., Netherlands) with Cu Kα radiation (2θ range 5–90°). Data were analyzed using Image J and OriginPro 9 Software.
Mechanical Property Testing
Mechanical properties of the scaffolds were determined using electropuls instrument (Instron, UK) with a load cell capacity of 100N and speeds of 10 mm/min. Specimens were cut into rectangular strips (25 × 5 mm2) with an average thickness of 0.1mm. Three samples were tested against each concentration of the GO-Gel nanofiber scaffolds. The tensile strength was analyzed using GraphPad Prism 8 Software. Further, Young’s modulus was calculated using the OriginPro 9 Software.
In vitro Cytocompatibility of the GO-Gel Scaffolds
Cell Culture and Seeding on Scaffolds
Human umbilical vein endothelial cells (HUVEC: ATCC) and IEC-6 cells (BMCR, China) were used to perform the cytological experiments. Briefly, the cells were cultured in an atmosphere containing 5% CO2 at 37°C using complete Dulbecco’s Modified Eagle’s Medium (DMEM, Thermo Fisher Scientific, United States) supplemented with 10% fetal bovine serum (FBS, Thermo Fisher Scientific, United States), 1% penicillin/streptomycin (Thermo Fisher Scientific, United States) and 0.1 unit/mL human insulin. When the cells reached 80% confluency, they were washed with phosphate-buffered saline and trypsinized with 0.25% Trypsin-EDTA for passaging and seeding. The gelatin and GO-Gel scaffolds were cut into square shapes (length 5mm) and sterilized overnight with ethylene oxide at 37°C. The sterilized scaffolds were then placed onto a 96-well tissue culture plate and washed thrice with PBS, followed by incubation with complete DMEM for 24 hours. The HUVEC and IEC-6 cells were then seeded into the 96-well culture plates at a density of 3×103 and 5×103 cells per well, respectively.
Determination of Cell Viability, Proliferation, Adhesion, and Morphology
Cell viability and proliferation were determined on the gelatin and GO-Gel scaffolds using the LIVE/DEAD (Sigma-Aldrich) and MTT assays (Sigma-Aldrich) after one, four, and seven days of incubation per the manufacturer’s protocol.
The live and dead cells were stained using Calcein-AM (CAM) and propidium iodide (PI), respectively, and observed using a confocal laser scanning microscope (CLSM, NikonA1Si, Japan.). Green-strained cells were considered living, while red-stained cells were considered dead.
For the MTT assay, 50μL MTT working solution was added to each well and incubated at 37°C for 4 hours. After discarding the MTT working solution, 150μL DMSO was added to the wells, and the plate was swayed. Subsequently, 100μL of the supernatant solution was transferred to a new 96-well plate, and the optical density (OD) of the solution was determined using a microplate reader at 490nm.
Cell adhesion and morphology were determined using FESEM. Briefly, after incubation for two days, the HUVEC and IEC-6 cells on the scaffolds were washed thrice with PBS to remove unattached cells. Subsequently, the cells were fixed with 2.5% glutaraldehyde solution for 2 hours. Then, the cells were washed again with PBS to remove residual glutaraldehyde. Dehydration was done using increasing concentrations of ethanol (50% for 60 min, 70% for 30 min, 80% for 20 min, 90% for 15min, and 100% for 30 min). Finally, the samples were air-dried and coated with platinum in a vacuum for 60s and observed using FESEM.
In vivo Study on the Repair of the Intestinal Perforation
All animal treatments and procedures were conducted according to the ethical guidelines of Tongji Medical College and approved by the Animal Ethical Committee of Tongji Hospital, Huazhong University of Science and Technology (NO. 2019-S069).
Two surgeries were performed in the animal models: Implantation Surgery and Perforation surgery. Male Sprague-Dawley rats with an initial average weight of 220–250g were allocated into three groups: Gel group (n=5), GO-Gel group (n=5), and V-GO-Gel group (n=6).
V-GO-Gel group was set as the experimental group, in which the GO-Gel scaffold was first pre-vascularized and then used to repair the intestinal perforation. The rats were anesthetized by intraperitoneal injection of Trichloroacetaldehyde hydrate (7mL/kg). Following shaving and sterilization of the abdominal site, the skin was incised. The mesenteric artery and mesenteric vein that runs from the superior mesenteric artery (SMV) and superior mesenteric vein (SMA), respectively, were identified for the implantation surgery. After that, GO-Gel scaffolds (3.0×1.2cm2) were implanted around the mesenteric vessels. The scaffolds were folded in half along the long side and fixed using 4-0 Prolene with the mesenteric vessels in between. The skin incisions were closed with 3-0 Prolene sutures using continuous and interrupted suturing.
Perforation surgery was performed four weeks after the implantation surgery to ensure vascularization of the implanted scaffolds. The implanted scaffolds and intestines were exposed along the midline abdominal incision. The implanted scaffolds were harvested from the surrounding tissue preserving the mesenteric vessels as the feeding and draining vessels. A 6–8mm perforation was made along the intestine on the proximal side using a scalpel. After disinfection, the wound was covered with the harvested scaffolds, which were then secured with sutures. The Gel and GO-Gel groups, the control groups, were established using non-vascularized scaffolds. After recovery, all the rats were allowed free access to food and water. The mortalities were recorded in each group. Animals were sacrificed four weeks after the implantation surgery, as well as two and four weeks after the perforation surgery to harvest specimens for further tests.
Histology and Immunofluorescence Staining
The tissue samples were fixed with 4% paraformaldehyde, paraffin-embedded, cut into 5μm sections, then dewaxed and dehydrated. The sections were then stained with hematoxylin and eosin (HE) to show granulation and development of new tissues. Masson’s Trichrome stain was used to assess collagen deposition. Further, immunofluorescence staining was used to analyze the expression of CD31, α-SMA, and CD206 to evaluate neovascularization and inflammatory reaction. Immunofluorescence was evaluated using a confocal laser scanning microscope.
Data were expressed as mean±standard deviation. In addition, data were analyzed using GraphPad Prism 8 Software. Tukey’s t-test and one-way ANOVA were used to determine the statistical difference. The level of significance was noted by * and ** referring to a P-value of <0.05 and <0.01, respectively.
Morphology of the GO-Gel Scaffolds
A 25% w/v Gelatin and 0.25%, 0.50%, and 0.75% w/v GO concentrations were used to prepare uniform Gel and GO-Gel nanofibrous mats. The macrographs showed that the color of the scaffolds changed from white (Gel scaffold) to light brown (GO-Gel scaffold) following the addition of increasing concentrations of GO (Figure 2A). This phenomenon had been reported in previous study that the intensity of the yellow/brown color increases on increasing GO content of the composites.12
Figure 2 Characterization of the GO-Gel scaffolds. (A) Macrographs, FESEM images, and diameter distribution of the nanofibers (Scale bar: low magnification= 10μm, high magnification=5μm). (B) FTIR spectroscopy, (C) Raman spectroscopy, (D) XRD pattern, (E) tensile stress-strain curve, (F) tensile strength, and (G) Young’s modulus of the scaffolds (mean±SD, *P-value <0.05).
The morphology of the formed nanofibrous mats was evaluated using FESEM (Figure 2A). With or without the GO, the nanofibrous mats showed randomly oriented porous 3D structures. The mean diameter of the Gel scaffold was 1685±231nm. However, after adding different concentrations of the GO (0.25%, 0.50%, and 0.75%), the mean diameter of the scaffold was 1480±175nm, 1033±145nm, and 990±108nm, respectively. The decrease of the fiber diameter was probably due to a change in the properties of the electrospinning solution caused by the incorporation of the GO into the nanofibers. Similar result had been reported in literature.12,18
Physiochemical Characterization of the GO-Gel Scaffolds
The characteristic peaks of the amide bond in the Gel and GO-Gel scaffolds were detected using FTIR spectroscopy (Figure 2B). The FTIR spectra showed characteristic peaks of gelatin at 3283 cm−1, 1635 cm−1, 1531 cm−1, and 1237 cm−1 assigned to amide A, amide I, amide II, and amide III bands, respectively. The GO-Gel scaffolds did not exhibit visible alteration of the FTIR spectra, suggesting that GO blended with the electrospinning solution by physical mixing and not by chemical reaction.22
Further, Raman spectroscopy was used to determine the structural characteristics of the GO-Gel nanofibers (Figure 2C). The GO showed a characteristic peak D band at 1323 cm−1 and G band at 1583 cm−1. Characteristic D and G bands were also observed after incorporation of the GO into the gelatin, indicating the presence of GO in the GO-Gel scaffolds.23
X-ray diffraction was used to investigate the crystalline phases of the materials (Figure 2D). When 2θ was 11°, a diffraction peak appeared in GO but disappeared in the GO-Gel scaffolds, indicating that the GO reduced due to the presence of amino groups in gelatin and dispersed into a single layer during electrospinning.4
Determination of the Mechanical Properties
Mechanical properties are a key consideration in determining the applications of the GO-Gel nanofibrous masts as tissue engineering scaffolds. Figure 2E shows the mechanical properties investigated. The tensile strain (Figure 2F) was evaluated at the highest point of the stress-strain curves, while Young’s modulus (Figure 2G) was determined as the slope of the linear part of the curves. The 0.25% GO-Gel scaffold had the highest tensile strain, while the 0.75% GO-Gel had the lowest tensile strain. However, the difference was not statistically significant. The addition of GO was shown to improve Young’s modulus of the GO-Gel scaffolds compared with the gelatin scaffolds. The Young’s modulus of Gel, 0.25% GO-Ge,0.50% GO-Gel and 0.75% GO-Gel group was calculated as follows:56.04±0.05MPa, 83.74±4.37MPa, 78.54±0.89MPa, 76.17±3.96MPa and 73.69±0.14MPa, respectively. The Young’s modulus of the GO-Gel scaffolds was about 150% higher than that of the gelatin scaffolds. However, difference between the different GO-Gel scaffolds was not statistically significant. Similar observation of increase in Young’s modulus as a result of GO incorporation in nanofiber is reported by Panzavolta et al.12
In vitro Cytocompatibility of the GO-Gel Scaffolds
Cell attachment and proliferation were investigated to evaluate whether the incorporation of GO into gelatin nanofibrous mats satisfied the requirements for tissue engineering. Further, the experiments were carried out to determine the best concentration for use in further experiments. The cells (HUVEC and IEC-6) were cultured on different scaffolds for one, four, and seven days to assess cell viability and proliferation. The HUVEC (Figure 3A) and IEC-6 cells (Figure 3C) showed better cell viability and higher cell proliferation on the other scaffolds in the LIVE/DEAD assay than on the 0.75% GO-Gel scaffolds. These findings were consistent with the results of the MTT assay of the HUVEC (Figure 3E) and IEC-6 (Figure 3F) cells. Specifically, the 0.25% GO-Gel scaffold showed the best cell viability and proliferation rates among the different GO-Gel scaffolds, with no statistically significant difference from the pure gelatin scaffolds. The morphology of the HUVEC (Figure 3B) and IEC-6 (Figure 3D) cells attached to the different scaffolds was evaluated after two days of culture using FESEM. The two types of cells showed successful adherence to the scaffolds. Moreover, they showed typical endothelium-like morphology. The cells attached to the scaffolds were colored in blue, while the scaffolds were colored yellow. In summary, the 0.25% GO-Gel scaffolds showed good cytocompatibility in the in vitro experiments.
Figure 3 In vitro cytocompatibility of the scaffolds. Confocal fluorescent images showing CAM/PI staining of (A) HUVEC and (C) IEC-6 cells on the scaffolds after culturing for one, four, and seven days. FESEM images showing (B) HUVEC and (D) IEC-6 cells seeded on the scaffolds (scale bar=10μm). Results of the MTT assay performed on (E) HUVEC and (F) IEC-6 cells seeded on the scaffolds (*P-value <0.05, **P-value <0.01).
The in vivo Study of the Pre-Vascularization Process
The in vitro studies showed that the mechanical strength of the scaffolds was improved following the incorporation of GO and had good cytocompatibility. Therefore, the scaffolds were used for the intestinal reconstruction model.
The scaffolds were first implanted around the mesenteric vessels to ensure pre-vascularization (Figure 4A). After four weeks, the implanted scaffolds were harvested with the mesenteric vessels preserved as the feeding and draining vessels.
Figure 4 Evaluation of the implantation surgery and pre-vascularization process. (A) Time course of the in vivo experiments and photos of the implantation surgery. The black arrow shows the residual scaffold materials, while the green arrow shows the pre-embedded vessels. (B) Panoramic view of the HE staining of the vascularized scaffolds harvested at week 4. (C) High magnification images of the residual scaffold are marked with blue dotted lines. (D) High magnification images of the central area are marked with red dotted lines. (E) Immunofluorescence images of CD31, α-SMA, DAPI, and merger of the central area. (F) Immunofluorescence images of CD31, α-SMA, DAPI, and merger of the scaffold area. Yellow arrow shows the neovessels. (A scale bar=5mm; B scale bar=200μm; C-F scale bar=50μm). (G) Histogram showing the number of blood vessels/area (mean±SD, **P-value <0.01).
Hematoxylin and eosin (HE) staining, CD31, and α-SMA immunofluorescence staining were used to evaluate cell infiltration and formation of blood vessels. In the panorama view of the HE staining for the pre-vascularization of the GO-Gel scaffold, the implanted scaffold was indicated outside the black dotted line, and the central area was within (Figure 4B). In the image of the central area, newly-generated connective tissue could be observed as well as a mount of cell infiltration (Figure 4C). There was increased cell infiltration and neovascularization within the scaffolds (Figure 4D). The CD31 and α-SMA immunofluorescence staining showed vascularization of the whole graft area, with a higher density of neovascularization within the scaffold area (Figure 4E–G).
In vivo Study of the Repair Process
After the pre-vascularization process, the implanted scaffolds were used to repair the intestinal perforation in the V-GO-Gel group. Meanwhile, the Gel and GO-Gel scaffolds, which were not subjected to prior pre-vascularization process, were used to repair the wounded intestines in the control groups (Figure 5A). After the perforation surgery, three rats died of acute peritonitis within the first three days in the Gel group due to breakage of the scaffolds, while one rat died in the GO-Gel group due to bowel stenosis. All the other rats survived and were sacrificed two or four weeks after the reconstruction surgery (Figure 5B–G). The perforations were evident in all groups after two weeks. However, the rats in the V-GO-Gel scaffolds showed an almost complete wound closure after four weeks. In contrast, wound closure was incomplete after four weeks in the Gel and GO-Gel groups.
Figure 5 Evaluation of the perforation surgery and repair process. (A) Time course of the in vivo experiments and photos of the perforation surgery. The black arrow shows the perforation and repair area. (B–D) Macroscopic photographs showing the intestinal wounds acquired on week 2 after treatment with different scaffolds. (E–G) Macroscopic photographs showing the intestinal wounds acquired on week 4 after treatment with different scaffolds. (A scale bar=5mm; B-G scale bar=2mm).
The HE staining (Figure 6A–C) and high magnification images (Figure 6D–I) showed tissue regeneration in the three groups. The V-GO-Gel group showed complete bridging of the intestinal perforations with regenerated mucosa. In contrast, perforations sealed with the Gel or GO-Gel scaffolds exhibited apparent and larger gaps in the mucosa. The Masson’s trichrome staining showed collagen deposition in the bridged mucosa of the V-GO-Gel group. However, collagen deposition was not evident in the other groups (Figure 6J–R).
Figure 6 Histological analysis of the vascularized scaffolds 4 weeks after perforation surgery. Panoramic view of the H&E staining (A–C) and Masson’s trichrome staining (J–L) of the intestinal wounds acquired on week 4 after treatment with different scaffolds. (scale bar=500μm). High magnification images of the HE staining (D–I) and Masson’s trichrome staining (M–R) of intestinal wounds acquired on week 4 after treatment with different scaffolds (scale bar=100μm). The yellow arrow indicates the residual graphene oxide sheet.
Further, immunofluorescence staining against CD31, α-SMA, and CD206 was performed to determine the effect of different treatments on neovascularization and inflammatory response on the experimental site (Figure 7). CD31 and α-SMA-positive capillaries were mainly concentrated in the scaffolds in the Gel and GO-Gel groups. However, in the V-GO-Gel group, CD31 and α-SMA-positive capillaries were concentrated in the bridged mucosa. CD-206 staining showed no differences between the groups (Figure 7A–F). Quantitative analysis showed no differences in the number of neovessels and inflammatory cells between the groups (Figure 7G–H).
Figure 7 Neovascularization of the intestinal wounds four weeks after perforation surgery. (A–C) Immunofluorescence images of CD31, α-SMA, CD206, DAPI, and merger of intestinal wounds acquired on week 4 after treatment with different scaffolds (scale bar=500μm). (D–F) High magnification images of Immunofluorescence images acquired on week 4 after treatment with different scaffolds (scale bar=20μm). (G) Histogram showing the number of blood vessels/area. (mean±SD). (H) Quantitative analysis of the CD206 cells (mean±SD).
Taken together, these results showed that pre-vascularized GO-Gel scaffolds effectively sealed and promoted regeneration of tissues following intestinal perforation, with no severe inflammatory response.
In this study, the pre-vascularized GO-Gel scaffold constructed showed good mechanical properties and adequate vascularization, thus promoting repair of the intestinal perforation in rats. The pre-vascularized GO-Gel group displayed the following advantages over the Gel and GO-Gel groups: (1) enhanced mechanical strength adapted to the intestinal pressure with ability to prevent leakage leading to peritonitis; (2) vascularized microenvironment, thus stimulating regeneration of the intestinal tissue.
An ideal tissue scaffold should have good biostability, which is dictated by the mechanical properties.24 Linh et al incorporated biphasic calcium phosphate into gelatin to improve the tensile strength of the electrospun membranes.25 Moreover, Satttary et al enhanced Young’s modulus and tensile strength of gelatin by adding nHAp.26 In this study, the GO-Gel scaffolds were fabricated by electrospinning. The tensile strength and Young’s modulus of the mats with low GO concentration were better than that of the pure Gel fibers (Figure 2E–G). Besides, the survival rates in the GO-Gel and V-GO-Gel groups were higher than in the Gel group. This finding suggested improvement in the mechanical strength, thus the anti-leakage effect. The decrease in tensile strength in high GO concentration was due to agglomeration of GO, leading to weak points, hence breakage of the mats. These findings were consistent with results reported by Wan et al and Jalaja et al.18,27
Previous studies reported that GO shows biotoxicity. For instance, Wierzbicki et al reported that GO inhibited cell migration and adhesion and showed cell toxicity.28 Frontinan-Rubio et al reported that cytotoxicity was associated with increased ROS production.29 Thus, the cell proliferation rate was determined using GO-Gel scaffolds fabricated using different concentrations of the GO to determine the optimal concentration of GO within the GO-Gel scaffolds. The results showed that low-concentration GO-Gel scaffold had better cytocompatibility (Figure 3). Moreover, GO can be degraded and eliminated from the body.30 Therefore, we determined that 0.25% GO-Gel scaffold could be used in reconstruction experiments.
Vascularization is the main obstacle in the clinical application of tissue regeneration. Thus, several attempts have been made to develop an ideal vascularization strategy.31 The tissue engineering chamber model entails pre-vascularization using pre-embedded vessels to form membrane blebs that lead to vascular sprouts and assembly of neovessels into a robust capillary bed to support the survival of various constructs. Vascularization is mainly achieved using an arteriovenous loop chamber or flow-through chamber models. In this study, a flow-through chamber model was adopted and modified to repair the intestinal perforation (Figures 4 and 6).
The omentum is composed of blood vessels arranged in an arch similar to the intestinal mesentery. It is a commonly used site to develop vascularized pedicles for the reconstruction of wounded intestines. However, the omentum vessels are not suitable for the development of the vascularization model as they are much smaller and denser.32 The mesentery is the main source of blood supply to the native intestine. The mesenteric vessels emerge from the “root region”, which corresponds to the attachment of the superior mesenteric artery to the aorta. The mesenteric artery then extends radially to the intestinal margin.33 Therefore, in this study, mesenteric vessels were selected to be the feeding and draining vessels. While using the chamber to repair the defect, it can restore the local normal anatomy. Furthermore, the pre-vascularization scaffold model was successfully established using mesenteric vessels. The blood vessels were kept intact during the pre-vascularization process. The GO-Gel scaffold implanted was shown to be highly vascularized (Figure 4). Moreover, the results demonstrated that the pre-vascularization scaffold model showed enhanced intestinal regeneration compared to the non-vascularized groups (Figures 5 and 6). The neovessels were concentrated on the bridge mucosa in the V-GO-Gel group. However, in the other groups, the neovessels were concentrated in the scaffolds (Figure 7). And all these groups did cause critical inflammatory response. This finding may be explained by the fact that the neovessels in the pre-vascularized GO-Gel scaffold supplied nutrients and oxygen, thus promoting regeneration of the intestine in the V-GO-Gel group. However, the non-vascularized group had first to vascularize the scaffolds attached to the perforation.
This study had some limitations. First, the constructed model was simplified compared to the original tissue engineering chamber. Therefore, the regeneration process could not be completely controlled. Therefore, future studies should combine stem cell therapy with biomaterials such as decellularized intestines to improve the model.
In summary, we fabricated a GO-Gel scaffold with enhanced mechanical properties and increased biocompatibility. In addition, a pre-vascularized GO-Gel chamber model was shown to accelerate the process of intestinal reconstruction.
In conclusion, we successfully repaired the intestinal perforation with the pre-vascularized GO-Gel chamber. Our findings revealed that the scaffolds had high mechanical strength, thus preventing peritonitis and death due to leakage of intestinal contents. Besides, pre-vascularization could enhance the reconstruction of intestinal perforation.
This study was funded by National Key R&D Program of China (2019YFA0110500), the National Natural Science Foundation of China (No. 82072198, and 81701922).
The authors report no conflicts of interest in this work.
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