The Potential of Novel Chitosan-Based Scaffolds in Pelvic Organ Prolapse (POP) Treatment through Tissue Engineering

The growing number of female reproductive system disorders creates a need for novel treatment methods. Tissue engineering brings hope for patients, which enables damaged tissue reconstruction. For this purpose, epithelial cells are cultured on three-dimensional scaffolds. One of the most promising materials is chitosan, which is known for its biocompatibility and biodegradability. The aim of the following study was to verify the potential of chitosan-based biomaterials for pelvic organ prolapse regeneration. The scaffolds were obtained under microwave-assisted conditions in crosslinking reactions, using dicarboxylic acids and aminoacid as crosslinkers, including l-glutamic acid, adipic acid, malonic acid, and levulinic acid. The products were characterized over their physicochemical and biological properties. FT–IR analysis confirmed formation of amide bonds. The scaffolds had a highly porous structure, which was confirmed by SEM analysis. Their porosity was above 90%. The biomaterials had excellent swelling abilities and very good antioxidant properties. The cytotoxicity study was performed on vaginal epithelial VK2/E6E7 and human colon cancer HCT116 cell lines. The results showed that after certain modifications, the proposed scaffolds could be used in pelvic organ prolapse (POP) treatment.


Introduction
Disorders of the female reproductive system affect women not only during their perimenopausal years, but also during their childbearing age. Depending on the procedure and treatment, there might be physical changes to the urogenital organs, both internally and externally. These changes can have a severe impact on the genitourinary tract, including sexual dysfunction. Currently available therapies, such as laser treatments or administration of hyaluronic acid or serum, are neither sustainable nor supported by clinical research. Therefore, there is a great need in designing a new material that is not only safe but that can also provide structural corrections, while maintaining optimal vulvo-vaginal aesthetics and allowing for a pain-free intercourse [1][2][3][4].  The spectrum of pure chitosan exhibited bands that are typical to this polymer. Free hydroxyl groups could be noticed at 3359 cm −1 , and free amino groups were present in deacetylated mers at 1572 cm −1 and 1150 cm −1 . Bands typical for amide bonds present in N-acylated mers appeared at 1651 cm −1 . Bands typical for glycosidic bonds between chitosan units were visible at 1066 cm −1 and bands characteristic of pyranose ring at 892 cm −1 were also visible. Additionally, bands typical for aliphatic groups were noticeable at 2918 cm −1 and 2875 cm −1 , as well as at 1423 cm −1 and 1376 cm −1 , respectively. FT-IR spectrum of the samples 1-4 showed some changes that confirmed the crosslinking reaction. First, it could be noticed that after crosslinking under microwave-assisted conditions, new carboxyl groups appeared, probably due to the slight surface degradation (sample 1-3072 cm −1 , sample 2-3064 cm −1 , 3-3070 cm −1 , and 4-3082 cm −1 ). Intense bands at 1647 cm −1 (sample 1) and at 1654 cm −1 (sample 3) proved formation of amide bonds between free amino groups and carboxylic groups from the applied acids. On the other hand, one could observe that in the case of samples 2 and 4, the crosslinking process occurred between free hydroxyl and free carboxyl groups. This could be confirmed by the presence of bands at 1691 cm −1 (sample 2) and 1700 cm −1 (sample 4), corresponding to the newly formed ester bonds. More importantly, FT-IR spectra of all aerogels still showed bands coming from amino groups of various intensity, which suggested that biomaterials are capable of interaction with the cell membrane components of cultured cells. Additionally, bands typical for aliphatic groups, glycosidic bonds, as well as pyranose rings were still present, which confirmed that chitosan did not undergo decomposition during the reaction [25][26][27][28][29].

Porosity and Density Study
Biomaterials dedicated to tissue engineering must be characterized by low density and high porosity, which should be at least 90% [23]. Multiple pores with interconnecting channels provide nutrients and oxygen delivery and enable CO2 and metabolite removal. Such porosity is also needed for the new tissue formation in three dimensions as well as angiogenesis and neovascularization processes. Figure 3 shows that all samples met the aforementioned requirement of excellent porosity. It could be noticed that this parameter was correlated with density and was below 0.06 g/cm 3 , which is typical for aerogels.

Porosity and Density Study
Biomaterials dedicated to tissue engineering must be characterized by low density and high porosity, which should be at least 90% [23]. Multiple pores with interconnecting channels provide nutrients and oxygen delivery and enable CO 2 and metabolite removal. Such porosity is also needed for the new tissue formation in three dimensions as well as angiogenesis and neovascularization processes. Figure 3 shows that all samples met the aforementioned requirement of excellent porosity. It could be noticed that this parameter was correlated with density and was below 0.06 g/cm 3 , which is typical for aerogels.

Porosity and Density Study
Biomaterials dedicated to tissue engineering must be characterized by low density and high porosity, which should be at least 90% [23]. Multiple pores with interconnecting channels provide nutrients and oxygen delivery and enable CO2 and metabolite removal. Such porosity is also needed for the new tissue formation in three dimensions as well as angiogenesis and neovascularization processes. Figure 3 shows that all samples met the aforementioned requirement of excellent porosity. It could be noticed that this parameter was correlated with density and was below 0.06 g/cm 3 , which is typical for aerogels.

Swelling Capability Study
Scaffolds dedicated to regenerative medicine applications besides high porosity should exhibit good swelling properties, in order to provide an appropriate environment for cells growth [24][25][26][27][28][29]. The constant access to culture medium is crucial for cell proliferation. Figure 4 shows the results of the swelling ability study. It could be noticed that all samples had excellent sorption properties. The highest swelling degree could be observed for sample 2, which could be assigned to the presence of the highest number of free hydrophilic groups (hydroxyl, amino, carboxyl) as well as very high porosity [29]. Therefore, it could be assumed that the prepared scaffolds could mimic the natural environment of the cells.

Swelling Capability Study
Scaffolds dedicated to regenerative medicine applications besides high porosity should exhibit good swelling properties, in order to provide an appropriate environment for cells growth [24][25][26][27][28][29]. The constant access to culture medium is crucial for cell proliferation. Figure 4 shows the results of the swelling ability study. It could be noticed that all samples had excellent sorption properties. The highest swelling degree could be observed for sample 2, which could be assigned to the presence of the highest number of free hydrophilic groups (hydroxyl, amino, carboxyl) as well as very high porosity [29]. Therefore, it could be assumed that the prepared scaffolds could mimic the natural environment of the cells.

Morphology Study
An important feature of the scaffolds is their morphology, which affects cells attachment, migration and the neovascularization process. Figure 5 shows the SEM microphotographs of the obtained biomaterials. It could be noticed that they were all highly porous. Moreover, the pores were open and interconnected. What is important, all pores had diameter above 50 µm, which would enable cell migration inside the three-dimensional structure, as well as new blood vessel formation. In the case of samples 1 and 2, surface microfolding was observed, which could positively affect cell adhesion. The pore edges of samples 1 and 3 were quite smooth as compared to samples 2 and 4, whose pore edges were a little bit sharp. The morphology provided in Figure 5 suggests that the scaffolds could provide good conditions for cell attachment, proliferation, and migration, followed by the formation of the new tissue in three-dimensions, along with the neovascularization process. Very high porosity suggests that the scaffolds would be able to imitate the extracellular matrix at a high level [24,29].

Morphology Study
An important feature of the scaffolds is their morphology, which affects cells attachment, migration and the neovascularization process. Figure 5 shows the SEM microphotographs of the obtained biomaterials. It could be noticed that they were all highly porous. Moreover, the pores were open and interconnected. What is important, all pores had diameter above 50 µm, which would enable cell migration inside the three-dimensional structure, as well as new blood vessel formation. In the case of samples 1 and 2, surface microfolding was observed, which could positively affect cell adhesion. The pore edges of samples 1 and 3 were quite smooth as compared to samples 2 and 4, whose pore edges were a little bit sharp. The morphology provided in Figure 5 suggests that the scaffolds could provide good conditions for cell attachment, proliferation, and migration, followed by the formation of the new tissue in three-dimensions, along with the neovascularization process. Very high porosity suggests that the scaffolds would be able to imitate the extracellular matrix at a high level [24,29].
The first stage of the three-dimensional cell culture is cell attachment to the scaffold and surface proliferation [29]. Therefore, it is crucial to know its composition. FT-IR analysis provided information about the chemical bonds and functional groups present in the biomaterials. XRF analysis ( Figure 6) presents the elemental composition of the external part of the scaffolds. It was observed that it consisted of carbon, oxygen, and nitrogen. Additionally, some trace amounts of sulfur (all samples) and aluminum (sample 3) could be observed. However, their quantity was negligible. Therefore, it could be assumed that the surface of the scaffolds contained NH 2 groups, which might interact with the negatively charged cell membranes of various cells, resulting in their adhesion. The first stage of the three-dimensional cell culture is cell attachment to the scaffold and surface proliferation [29]. Therefore, it is crucial to know its composition. FT-IR analysis provided information about the chemical bonds and functional groups present in the biomaterials. XRF analysis ( Figure 6) presents the elemental composition of the external part of the scaffolds. It was observed that it consisted of carbon, oxygen, and nitrogen. Additionally, some trace amounts of sulfur (all samples) and aluminum (sample 3) could be observed. However, their quantity was negligible. Therefore, it could be assumed that the surface of the scaffolds contained NH2 groups, which might interact with the negatively charged cell membranes of various cells, resulting in their adhesion.

Antioxidant Activity Study
Materials for biomedical applications should be characterized by advanced properties, so as to enhance cell growth and proliferation. Scaffolds with three-dimensional structure could protect cells from the external environment and minimize temperature or humidity fluctuations. However, there are other factors that could lead to cells apoptosis. Free radicals constitute a danger to cells. Chitosan is known for its antioxidant properties [25,26]. Nevertheless, polymers dissolved in acidic medium show the best ability for removing free radicals. Figure 7 presents the results of studying the properties of antioxidants. It could be noticed that undissolved chitosan exhibited a low ability of free radicals scavenging, contrary to the obtained scaffolds. Figure 6 shows that all evaluated samples had good antioxidant properties. The best results were obtained in the case of sample 3. The ability of DPPH radicals' removal could be assigned to the presence of free amino groups, as well as glucopyranose rings. Such results suggest that the scaffolds would be able to protect cultured cells from reactive oxygen species (ROS), which could be generated inside the human body.

Antioxidant Activity Study
Materials for biomedical applications should be characterized by advanced properties, so as to enhance cell growth and proliferation. Scaffolds with three-dimensional structure could protect cells from the external environment and minimize temperature or humidity fluctuations. However, there are other factors that could lead to cells apoptosis. Free radicals constitute a danger to cells. Chitosan is known for its antioxidant properties [25,26]. Nevertheless, polymers dissolved in acidic medium show the best ability for removing free radicals. Figure 7 presents the results of studying the properties of antioxidants. It could be noticed that undissolved chitosan exhibited a low ability of free radicals scavenging, contrary to the obtained scaffolds. Figure 6 shows that all evaluated samples had good antioxidant properties. The best results were obtained in the case of sample 3. The ability of DPPH radicals' removal could be assigned to the presence of free amino groups, as well as glucopyranose rings. Such results suggest that the scaffolds would be able to protect cultured cells from reactive oxygen species (ROS), which could be generated inside the human body.

Cytotoxicity Study
To determine the cytotoxicity of the scaffolds, proliferation studies were carried out on the VK2/E6E7 epithelial vaginal cell line, as well as HCT116 colorectal carcinoma cell line. Surprisingly, none of the cultured lines (HCT116, VK2/E6E7) proliferated in the expected manner, even those coated with fibronectin.
The HCT116 cancer cells adhered to each other rather than to the scaffold and created numerous cell clusters (Figures 8 and 9). The number of living cells compared to the control (Figure 10), was significantly lower.

Cytotoxicity Study
To determine the cytotoxicity of the scaffolds, proliferation studies were carried out on the VK2/E6E7 epithelial vaginal cell line, as well as HCT116 colorectal carcinoma cell line. Surprisingly, none of the cultured lines (HCT116, VK2/E6E7) proliferated in the expected manner, even those coated with fibronectin.
The HCT116 cancer cells adhered to each other rather than to the scaffold and created numerous cell clusters (Figures 8 and 9). The number of living cells compared to the control (Figure 10), was significantly lower.

Cytotoxicity Study
To determine the cytotoxicity of the scaffolds, proliferation studies were carried out on the VK2/E6E7 epithelial vaginal cell line, as well as HCT116 colorectal carcinoma cell line. Surprisingly, none of the cultured lines (HCT116, VK2/E6E7) proliferated in the expected manner, even those coated with fibronectin.
The HCT116 cancer cells adhered to each other rather than to the scaffold and created numerous cell clusters (Figures 8 and 9). The number of living cells compared to the control (Figure 10), was significantly lower.

Cytotoxicity Study
To determine the cytotoxicity of the scaffolds, proliferation studies were carried out on the VK2/E6E7 epithelial vaginal cell line, as well as HCT116 colorectal carcinoma cell line. Surprisingly, none of the cultured lines (HCT116, VK2/E6E7) proliferated in the expected manner, even those coated with fibronectin.
The HCT116 cancer cells adhered to each other rather than to the scaffold and created numerous cell clusters (Figures 8 and 9). The number of living cells compared to the control (Figure 10), was significantly lower.   The VK2/E6E7 cells did not flatten and did not proliferate. Such results suggest that certain ingredients in the media negatively affected the cell's growth (Figures 11-16). The cells also did not grow at the bottom of the well, where there was no scaffold present (small photo set in large photographs).
After plating the VK2/E6E7 cells on scaffolds, some cells were harvested after approximately 8 h and were then plated in new wells with fresh medium. The cells grew in size, flattened, and started to proliferate (Figure 16). However, the cultures were in a much worse condition, relative to the control. Thus, it was likely that the components of the scaffold dissolved in the medium and negatively affected the cellular growth. Rinsing the scaffolds in a large volume of PBS for a few days did not help. Figure 17 presents the VK2/E6E7 cells cultured in the presence of commercially used poly(propylene) mesh. It could be noticed that the cells did not growth on the mesh. However, the The VK2/E6E7 cells did not flatten and did not proliferate. Such results suggest that certain ingredients in the media negatively affected the cell's growth (Figures 11-16). The cells also did not grow at the bottom of the well, where there was no scaffold present (small photo set in large photographs).
After plating the VK2/E6E7 cells on scaffolds, some cells were harvested after approximately 8 h and were then plated in new wells with fresh medium. The cells grew in size, flattened, and started to proliferate ( Figure 16). However, the cultures were in a much worse condition, relative to the control. Thus, it was likely that the components of the scaffold dissolved in the medium and negatively affected the cellular growth. Rinsing the scaffolds in a large volume of PBS for a few days did not help. Figure 17 presents the VK2/E6E7 cells cultured in the presence of commercially used poly(propylene) mesh.
It could be noticed that the cells did not growth on the mesh. However, the cells grew in an appropriate manner on the bottom of the culture flask, which meant that the mesh was not cytotoxic to them. Figure 18 presents VK2/E6E7 cultured under standard conditions. When comparing Figures 11-16 to Figure 18, it could be noticed that the amount of viable, flattened cells in the case of the cultures carried out on the scaffolds was significantly lower.

photographs).
After plating the VK2/E6E7 cells on scaffolds, some cells were harvested after approximately 8 h and were then plated in new wells with fresh medium. The cells grew in size, flattened, and started to proliferate (Figure 16). However, the cultures were in a much worse condition, relative to the control. Thus, it was likely that the components of the scaffold dissolved in the medium and negatively affected the cellular growth. Rinsing the scaffolds in a large volume of PBS for a few days did not help. Figure 17 presents the VK2/E6E7 cells cultured in the presence of commercially used poly(propylene) mesh. It could be noticed that the cells did not growth on the mesh. However, the cells grew in an appropriate manner on the bottom of the culture flask, which meant that the mesh was not cytotoxic to them. Figure 18 presents VK2/E6E7 cultured under standard conditions. When comparing Figures 11-16 to Figure 18, it could be noticed that the amount of viable, flattened cells in the case of the cultures carried out on the scaffolds was significantly lower.

photographs).
After plating the VK2/E6E7 cells on scaffolds, some cells were harvested after approximately 8 h and were then plated in new wells with fresh medium. The cells grew in size, flattened, and started to proliferate (Figure 16). However, the cultures were in a much worse condition, relative to the control. Thus, it was likely that the components of the scaffold dissolved in the medium and negatively affected the cellular growth. Rinsing the scaffolds in a large volume of PBS for a few days did not help. Figure 17 presents the VK2/E6E7 cells cultured in the presence of commercially used poly(propylene) mesh. It could be noticed that the cells did not growth on the mesh. However, the cells grew in an appropriate manner on the bottom of the culture flask, which meant that the mesh was not cytotoxic to them. Figure 18 presents VK2/E6E7 cultured under standard conditions. When comparing Figures 11-16 to Figure 18, it could be noticed that the amount of viable, flattened cells in the case of the cultures carried out on the scaffolds was significantly lower.                 VK2/E6E7 cells were more resistant to external factors than primary cells. Therefore, the cytotoxic effect of the scaffolds was unexpected, especially as numerous studies confirmed the biocompatibility of the chitosan-based materials [27][28][29][30][31]. It could be observed that the cytotoxicity of the scaffolds was not correlated with their sterility. Additionally, it could be concluded that the application of ethylene oxide as a sterilizing agent did not significantly affect their chemical structure and did not affect the cell culture. Taking into consideration the cell culture studies, the synthesis parameters, and the FT-IR and XRF analyses, it could be deduced that the crosslinking process did not occur with the 100% efficiency, leading to the presence of free acids inside them. In all probability, free acids that were not chemically bonded to the chitosan interacted electrostatically with the polymeric functional groups. Thus, they were very hard to wash out using distilled water and PBS. It could be assumed that these were slowly released during the cell culture, leading to a culture  VK2/E6E7 cells were more resistant to external factors than primary cells. Therefore, the cytotoxic effect of the scaffolds was unexpected, especially as numerous studies confirmed the biocompatibility of the chitosan-based materials [27][28][29][30][31]. It could be observed that the cytotoxicity of the scaffolds was not correlated with their sterility. Additionally, it could be concluded that the application of ethylene oxide as a sterilizing agent did not significantly affect their chemical structure and did not affect the cell culture. Taking into consideration the cell culture studies, the synthesis parameters, and the FT-IR and XRF analyses, it could be deduced that the crosslinking process did not occur with the 100% efficiency, leading to the presence of free acids inside them. In all probability, free acids that were not chemically bonded to the chitosan interacted electrostatically with the polymeric functional groups. Thus, they were very hard to wash out using distilled water and PBS. It could be assumed that these were slowly released during the cell culture, leading to a culture medium with a significant pH value decrease. VK2/E6E7 cells were more resistant to external factors than primary cells. Therefore, the cytotoxic effect of the scaffolds was unexpected, especially as numerous studies confirmed the biocompatibility of the chitosan-based materials [27][28][29][30][31]. It could be observed that the cytotoxicity of the scaffolds was not correlated with their sterility. Additionally, it could be concluded that the application of ethylene oxide as a sterilizing agent did not significantly affect their chemical structure and did not affect the cell culture. Taking into consideration the cell culture studies, the synthesis parameters, and the FT-IR and XRF analyses, it could be deduced that the crosslinking process did not occur with the 100% efficiency, leading to the presence of free acids inside them. In all probability, free acids that were not chemically bonded to the chitosan interacted electrostatically with the polymeric functional groups. Thus, they were very hard to wash out using distilled water and PBS. It could be assumed that these were slowly released during the cell culture, leading to a culture medium with a significant pH value decrease.
It is not very likely, that the crosslinked chitosan was cytotoxic by itself, since the previous study on the L929 cell line and MSC primary cells showed that it was not only non-toxic, but also had a positive impact on cell proliferation [25][26][27][28]. However, previously described chitosan scaffolds were prepared by using only one or two aminoacids at the time. In all probability, the combination of dicarboxylic acid, which are much more acidic than acid containing one carboxyl and one amino group, negatively affect the crosslinking process and in the future, the composition of crosslinkers should be better adjusted and the ready products purification method should be refined. Otherwise, their cytotoxic effect is comparable to the currently used polypropylene materials and their in vivo application might be associated with some serious side-effects, such as the emergence of inflammatory states, As compared to alternative solutions like biomaterials prepared from collagen or estradiol [8,9].
The scaffolds did not decompose after being stored in the medium in an incubator (37 • C), for a month, which meant that the materials were stable in the cell culture medium and could be potentially applied in a long-term cell culture, after certain modifications.

Chitosan Scaffolds Synthesis
For obtaining the chitosan scaffolds, each time 1.0 g of the biopolymer with 80% deacetylation degree was dissolved in an aquatic solution of acetic acid (4%) on a magnetic stirrer and was left until a homogenous mixture was obtained (1 h). In the next step, an appropriate amount of crosslinking agents and 10 mL of propylene glycol were added to each sample. Then, the reacting mixtures were placed in Prolabo Synthewave 402 microwave reactor. All syntheses were carried out in the field of microwave radiation, in various synthesis conditions (Table 1). Obtained chitosan hydrogels were washed out from the crosslinking agents' residues, using distilled water. Finally, the hydrogels were frozen and lyophilized.

Chemical Structure Analysis
Chemical structure of the products was evaluated by infrared spectroscopy. FT-IR/ATR analysis was performed using IR Thermo Nicolet Nexus X 470 spectrometer (diamond crystal ATR) (Thermo Fisher Scientific, Waltham, MA, USA). The range was between 400 and 4000 cm -1 with 32 scans and 4 cm -1 resolution.

Porosity and Density Study
The density and porosity of the obtained chitosan materials were determined by isopropanol displacement because it did not wet the sample. The investigated biomaterials were placed into the previously measured volume of isopropanol. After a fixed time (5 min), the change in volume of the alcohol-impregnated aerogel was measured. Then, the studied chitosan scaffold was removed from the isopropanol. In the last step, the difference in isopropanol volume was measured. Based on this, the obtained data density (Equation (1)) and porosity (Equation (2)) was calculated using the following equations:

Swelling Capability Study
To determine the swelling properties of the obtained biomaterials, samples were weighed and placed in distilled water. The samples were weighed after two time-periods (5 min and 24 h) and the swelling degree [%] was calculated according to Equation (3). Experiments were repeated 3 times.
where %SD-swelling degree W t -weight of the investigated sample after time = t, g W 0 -initial weight of the investigated sample, g 3.2.5. Scanning Electron Microscope (SEM) Analysis and X-ray Microanalysis SEM analysis was performed using FEI QUANTA 650 FEG (ThermoFisher Scientific, Oregon, USA). Microphotographs were taken under pressure of 50 Pa and HV of 10.00 kV. X-ray microanalysis of the materials was performed using the energy dispersive spectroscopy method, using the FEI QUANTA 650 FEG microscope, equipped with an EDS detector (Thermo Fisher Scientific, Portland, OR, USA).

Antioxidant Activity Study
Antioxidant properties of the prepared chitosan scaffolds were investigated by a standard DPPH method. For this purpose, a solution of DPPH in methanol was prepared so that the solution absorbance was 1.0 at 517 nm, using Aligent 8453 spectrophotometer. To determine the ability of free radical scavenging, 0.10 g of each sample was placed in 5 mL of DPPH solution and left in darkness for 1 h, with constant shaking. Then, the absorbance of each solution was measured at 517 nm. The percentage of the free radicals removed was calculated using the following Equation (4): where %S-the % of the free radicals that were neutralized Ac-the absorbance of the DPPH solution without the sample As-the absorbance of the DPPH solution containing sample 3.2.7. Cytotoxicity Study VK2/E6E7 and HCT116 cells were grown on the tested scaffolds. Control cultures were grown under standard conditions. The cultures were grown on two types of scaffolds-one sterilized with ethylene oxide and one non-sterilized. Prior to plating the cells, each scaffold was rinsed for about 24 h in PBS, while the non-sterilized scaffold was rinsed in PBS with the addition of antibiotics. Next, the culture medium was added and placed in the incubator for about 24 h. The scaffolds were additionally coated with fibronectin for 24 h. About 200,000 cells were plated on scaffolds. The cultures were run on 6-well plates.

Conclusions
In this article, an attempt was made to obtain a novel chitosan-based scaffold dedicated to urogynecologic regenerative medicine applications. We successfully prepared the new crosslinked chitosan derivatives under microwave-assisted conditions. The crosslinking process was confirmed by the FT-IR method. The biomaterials exhibited excellent porosity and swelling abilities. They also had good antioxidant activity. However, surprisingly they appeared to be cytotoxic to both vaginal epithelial (VK2/E6E7) and HCT116 colorectal carcinoma cells. Such results suggest that the combination of crosslinking agents must be better adjusted and the purification process should be enhanced. In a future study, we will focus on the preparation of scaffolds crosslinked with the bifunctional acids of lower acidity, which would not negatively affect the cultured cells. Overall, it could be concluded that the choice of the right crosslinking agent was crucial for the chitosan biocompatibility maintenance and its effect on the chemical structure was superior to the porous morphology or swelling abilities. Development of the chitosan-based scaffolds applicable in pelvic organ prolapse (POP) treatment must be preceded by careful modifying agent characterization.