Introduction

Because of physiological impairments, injury to the peripheral nerves has a significant impact on a patient’s quality of life. The increase in the number of injuries indicates that PNI is a worldwide clinical problem; PNI was diagnosed in 551,612 patients during 2009–2018, of whom nearly 22% had a history of physical activity and sports [1]. The axons have the ability to regenerate when the defect is small (≤ 3 mm) and follow 3 main cascades to do so: Wallerian degeneration, axonal regeneration, and end-organ reinnervation [2]. The severity and the type of the injury determine the success of the self-regeneration or end to end surgery. When the injury causes complete transection and the gap between the proximal and distal parts is ≥ 3 mm, microsurgical interventions become compulsory grafting or use of artificial nerve guides is applied [3]. End-to-end suturing is not possible when the gap is larger because the tension created during suturing becomes excessive (≥ 3 mm). Methods used for larger defects (≥ 10 mm) like autografting, xenografting or allografting may also have some disadvantages such as donor site morbidity, immune reaction, cross contamination and limited supply of donor tissue. Thus, considering the limitations of the end-to-end suturing and grafting methods, the nerve conduits have emerged among researchers [4, 5].

The gold standard strategy (autografting) includes the fibrin cable production by the patient for nerve regeneration in the nerve conduits. When a hollow nerve conduit is used in the treatment of a peripheral nerve damage, its lumen is filled with a fluid that infiltrates among the undamaged fibrin cables (a “blood clot”) that extend over the gap between the proximal and distal nerve stumps. Fibrin cables operate as a microarchitectural cue to direct migrating Schwann cells (SCs) into the damage site [6]. Extracellular matrix (ECM) proteins like collagen and laminin are secreted by the cells (neuronal or non-neuronal) which migrate to the injury site. Scar formation is decreased by this highly controlled environment and nerve stumps that produce growth factors [7]. Nerve conduits aim to mimic the autografts in terms of supporting axon growth. General properties for the scaffold constructs should include to be suitable for cell migration, proliferation and differentiation. Nerve conduits have been designed using a variety of biopolymers. Due to their poor mechanical properties, the polymers are difficult to be fabricated. On the other hand, the slow biodegradability of the synthetic polymers limits their use in the development of nerve conduits. Hybrid conduits composed of both synthetic and natural biopolymers are an obvious choice for use in nerve conduits. Natural polymers such as hyaluronic acid (HA) [8], collagen [9], gelatin [10], chitosan [11], alginate [12]; synthetic polymers such as polydimethylsiloxane [13], polylactic acid [14], polyglycolic acid [15] and poly(2-hydroxyethylmethacrylate) (pHEMA) [16] and also their blends [17, 18] have been used for nerve tissue engineering applications. Nervous tissue is one of the soft tissues and its ultimate tensile strength (UTS) is 1,400 kPa and tensile modulus is 576 kPa [19]. Thus, one of the most appropriate materials to be used in nerve tissue engineering applications are hydrogels due to their mechanical properties and the hydrated structure. Hydrogels have ability to absorb water and become soft rubbery; making them suturable and having mechanical properties similar to nerve tissue [20]. In the present study, pHEMA hydrogel nerve conduit is presented together with methacrylated gelatin (GelMA)-methacrylated HA (HaMA; GelMA-HaMA) interpenetrating network (IPN) filler. To support and guide axonal regeneration, SCs were seeded into the nerve conduits, and the distal part of the conduit was loaded with netrin-1 protein. pHEMA hydrogel is hydrophilic, transparent, biocompatible, and non-degradable, and has mechanical properties to be customised according to the application such as wound dressings, soft contact lenses, ocular drug delivery, artificial skin, artificial cornea, catheters, breast augmentation, and nerve tissue engineering [21]. The GelMA-HaMA filler of the presented nerve conduit was considered to be supportive for regenerating axons because of its degradable sturucture. The degradation profile of the IPN structure can be adjusted by changing concentrations of the mixture and initiators, which makes the structure attractive for tissue engineering applications [22].

SCs are support cells that aid in axonal regeneration following injury in the peripheral nervous system (PNS) by secreting neurotrophins. In Wallerian degeneration, neuronal and non-neuronal cells release cytokines that stimulate SCs to produce neurotrophins like brain-derived neurotrophic factor (BDNF) and nerve growth factor (NGF) [23]. SCs’ migration, longitudinal organization, and fibrin cable creation all occur on their own for nerve gaps smaller than 3 mm. Thus, SCs are support cells that aid axonal regeneration following injury in the PNS by secreting neurotrophins. On the otherhand for longer nerve gaps, nerve regeneration typically requires SCs to be introduced to the injury site [24–27]. The production of nerve guidance conduits frequently uses supporting factors for axonal regeneration in addition to support cells. It has been demonstrated that netrin proteins are useful for guiding circumferential axonal projections [28]. Initially, netrin-1 was recognized as a traditional axonal guidance molecule with potent axon elongation abilities. Thus, to support axonal regeneration and guidance in the current work, SCs and netrin-1 were added. SH-SY5Y are well characterized cells and for this reason they have been in use since 1980s in tissue engineering and neurobiological applications. These cells were originally obtained from bone marrow biopsy of a blastoma and possess biochemical and functional properties which are suitable for studying neuronal extensions and organizations [29]. Therefore, SH-SY5Y cells were used as model cells in this study.

This study was aimed to design novel composite nerve guide and test it under in situ and in vitro conditions. The nerve guide composed of pHEMA was prepared and the cylindrical structure was filled with GelMA-HaMA IPN. The nerve guide was evaluated in terms of survival, production of neurite outgrowth and migration of the model SH-SY5Y cells. The positive effects of SCs and netrin-1 protein were shown on the neural cells in vitro and the final suturable nerve guide was developed to be used in further peripheral nerve regeneration applications.

Materials and methods

Preparation of pHEMA nerve guides

The molds containing an outer glass tube together with an innner cylinder and lids printed from Dental SG Resin by stereolithography (SLA 2, Formlabs, United States), were used to prepare cylindrical pHEMA guides (Figure 1A). Solution polymerization was used to prepare pHEMA as described earlier [30]. Briefly, distilled water and 2-hydroxyethylmethacrylate (HEMA) monomer were mixed (44%, 50%, 55%, 58%, v/v; total volume: 3 mL) and crosslinker [ethylene glycol dimethacrylate (EGDMA)] was added (0.4%, v/v; in monomer). Then, Irgacure 2959 was added to the reaction mixture (0.025%, w/v) as an initiator. In order to remove oxygen the solution was purged with nitrogen and reaction was performed under ultraviolet light (UV; 365 nm) for 10 s. The pHEMA was incubated in excess distilled water to remove unreacted molecules were then lyophilized for 6 h. pHEMA hydrogels were then impregnated with collagen by immersing in a collagen solution (1% in acetic acid, w/v) for overnight. The hydrogels were lyophilized after washed with distilled water. Lyophilized pHEMA conduits had outer diameter of 1.2 cm, inner diameter of 0.2 cm and the height of 1.3 cm.

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Figure 1. 

Preparation of conduit materials. A) pHEMA mold sketch of the SLA system; B) methacrylation of gelatin; C) methacrylation of HA

Construction of the final conduit and netrin-1 loading

IPNs were crosslinked following SH-SY5Y cells were introduced to the GelMA-HaMA reaction mixture, and they were subsequently incubated for 7 days. On pHEMA hydrogels, SCs were seeded and cultured for 7 days. In cylindrical pHEMA hydrogels, SH-SY5Y containing IPNs were inserted, and the remaining volume in the tube was filled with cell-free IPN (Figure 2). After 7 days of incubation, netrin-1 protein (100 g/mL, final amount in each construct: 200 ng) was injected into one side of the finished construct. After incubating the cells for 7 days, CLSM analysis was performed on them.

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Figure 2. 

Construction of the final structure. A) Formation of GelMA-HaMA IPN loaded with SH-SY5Y cells; B) SC seeding on pHEMA conduit exterior; C) complete conduit formedon by addition of SH-SY5Y loaded IPNs into the central cavity of pHEMA conduits

Results

MA content of GelMA and HaMA with NMR

Methacrylation extent of GelMA and HaMA were determined with ¹H-nuclear magnetic resonance (¹H-NMR). The degree of methacrylation (DM) was calculated by using Equation 7 [34, 35]. ¹H-NMR spectra of gelatin and GelMA was shown in Figure 3A, the results were normalized to the phenylalanine signal. The signal increase in the protons of methacrylate vinyl group of MA (5.4–5.7 ppm, red arrow on Figure 3A) and the signal decrease of the protons of methylene of lysine signal (2.9 ppm) shows the methacrylation and DM was found as 94% ± 2%.

(7)$$DM=1-\frac{\text{Lysine methylene proton of GelMA}}{\text{Lysine methylene proton of Gelatin}}\times 100$$

HA and HaMA ¹H-NMR spectra are shown in Figure 3B. Since the anomeric proton signals at 2.07 ppm are proportional to the HA concentration and are unaffected by the methacrylation process, the ¹H-NMR spectra were normalized accordingly. DM was calculated by the ratio of the relative peak integrations of the methacrylate protons (6.1, 5.6, and 1.85 ppm) and methyl protons of HA (1.85 ppm) represented by arrows on Figure 3B [36]. The DM was calculated as 60% ± 7% for the synthesized HaMA.

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Figure 3. 

¹H-NMR and FTIR analyses of GelMa and HaMA. A) ¹H-NMR spectra of gelatin and uncrosslinked GelMA (normalized to the signal at 7.3 ppm); B) ¹H-NMR spectra of HA and uncrosslinked HaMA (normalized to the signal at 2.07 ppm). Red arows show methacrylation bonds

FTIR of GelMA-HaMA IPNs

The usual FTIR spectrum of gelatin and GelMA is presented in Figure 4A, which exhibits vibrations at 3,300 cm^–1 (O-H stretching vibrations), 2,922 cm^–1 (C-H stretching), 1,640 cm^–1 (C-O stretching, Amide I), and 1,525 cm^–1 (N-H bending, Amide II). Their intensities increased after the methacrylation of the gelatin, and they decreased back after the crosslinking of GelMA because the crosslinking reaction utilized all the hydroxyl group (-OH) groups around 3,300 cm^–1 [37, 38].

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Figure 4. 

FTIR analyses of GelMa and HaMA. A) FTIR spectra of gelatin, uncrosslinked GelMA and crosslinked GelMA; B) FTIR spectra of HA, uncrosslinked and crosslinked HaMA

The FTIR spectra of HA, HaMA and crosslinked HaMA are shown in Figure 4B. A new peak at 1,731 cm⁻¹ was observed in HaMA when compared to the HA related with the methacrylation and C=C bond peak was also increased at 1,643 cm^–1 [39]. Then upon crosslinking reaction the peaks decreased showing that methacrylate groups went into reaction. A N-H deformation signal was observed at 1,558 cm^–1 because the nitrogen atom of HA did not react with MA. The -OH group’s intra- and intermolecular stretching vibration is linked to the peak at 3,360 cm^–1 [40]. The units of the C-O-C hemiacetalic system are related to the peak at 1,033 cm^–1.

Water content, swelling and degradation of GelMa-HaMA IPNs

Hydrogels absorb water and swell in aqueous media, reducing their mechanical properties (e.g., stiffness) which are important in their application [41]. Pure GelMA and HaMA hydrogels had water contents of 86% and 88%, respectively, and these values were nearly identical (Figure 5A). To understand how mixing in different ratios affect water content, IPNs were prepared in different combinations that resulted in very similar water contents (87%, 88%, 84%, 92% for the ratios of 5:95, 10:90, 15:85, 20:80, respectively). Thus, all the water content values were above 80% for all of them.

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Figure 5. 

Characterization of the GelMA-HaMA IPNs prepared at different ratios. A) Water content; B) swelling; C) degradation profile of IPNs in PBS; D) degradation profile of IPNs in cell culture medium. Statistical differences (^* P ≤ 0.05, ^** P ≤ 0.01, ^*** P ≤ 0.001, ^**** P ≤ 0.0001) are indicated

To demonstrate the impact of adding HaMA to the IPNs, the swelling degree of the IPNs was computed (Figure 5B). The findings demonstrated that IPN’s swelling capabilities were enhanced by an increase in HaMA content.

The biodegradability of the hydrogels of GelMA, HaMA and GelMA-HaMA IPNs was studied in PBS (Figure 5C) and culture medium (Figure 5D) for 5 weeks and weight loss during this period was determined gravimetrically. During this period GelMA lost 75% of its weight, while HaMA completely degraded in 3 weeks. Hydrogels with IPN structure were more stable when compared to the pure HaMA. Increasing the fraction of HaMA in IPN structure increased the weight loss rate (Figure 4C and D). A statistically significant difference in the degradation profile was not observed in PBS and medium.

Porosity, water content and swelling of pHEMA hydrogels

The outer cylindrical structure of the final conduit prepared in the present study was composed of pHEMA. SEM micrographs of the hydrogels with different water contents are presented in Figure 5. Closed pores were observed on the surfaces of the hydrogel produced with 44% water in the reaction mixture (Figure 6). As the water content of the hydrogels was increased during synthesis, more porous structures developed. The images were analyzed with NIH ImageJ to determine porosity and pore sizes (Figure 7A and B, Table 1). Hydrogels with water concentrations of 44%, 50%, 55%, and 58%, respectively, were found to have porosities of 17%, 33%, 52%, and 50%. Additionally, it was found that the average pore diameters for the hydrogels with water concentrations of 44%, 50%, 55%, and 58%, respectively, are 40.75 µm ± 8.59 µm, 55.09 µm ± 7.15 µm, 15.24 µm ± 3.05 µm and 15.44 µm ± 2.05 µm. The micrographs show the pores of the hydrogels in the dry state; thus, the pores are not the actual pores when the hydrogel is in a swollen state on which the cells are seeded. The hydrogels with the highest capacity of swelling have the smallest pore sizes in their dry states, because they shrink more than the hydrogels with less capacity for swelling.

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Figure 6. 

SEM micrographs of pHEMA hydrogel surfaces prepared with different water contents. A) 44%; B) 50%; C) 55%; D) 58%. Scale bar: 100 µm

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Figure 7. 

Characterization of pHEMA hydrogels prepared with different water content in reaction mixture (44%, 50%, 55%, 58%; v/v). A) Pore size; B) porosity (%); C) water content (24 h); D) repeated swelling profiles of pHEMA hydrogels: the gels were dried and swollen on succesive days and maintained their integrity. Statistical differences (^* P ≤ 0.05, ^** P ≤ 0.01, ^*** P ≤ 0.001, ^**** P ≤ 0.0001) are indicated

Table 1.

Porosity, pore size and water content (%) of pHEMA hydrogels prepared with different water contents

Water content of the reaction mixture (%)	Porosity (%)	Pore sizes (µm)	Water content after swelling (%)
44	17	40.75 ± 8.59	40.27 ± 1.20
50	33	55.09 ± 7.15	42.80 ± 1.24
55	52	15.24 ± 3.05	47.60 ± 1.34
80	50	15.44 ± 2.05	52.17 ± 0.50

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By determining the ratio of water absorption, the equilibrium water contents of pHEMA hydrogels produced with various water compositions were calculated (Figure 7C, Table 1). The water content of the hydrogels became from 40% to 52% as the amount of water in the reaction mixture increased. The difference between the hydrogels of different water contents in the preparation mixture was found statistically significant. To further understand the ability of hydrogels to preserve their integrity, the swelling profiles of pHEMA tubes with various concentrations of water were determined. The gels swelled to their equilibrium value when the tubes were submerged in water (days 2, 4, 6, and 8), and they lost the same quantity of water when they dried (Figure 7D). The gels prepared in this study maintain their ability to reswell repeatedly, without any sign of hysteresis making.

In vitro studies

SC proliferation on pHEMA hydrogels

SC attachment and viability on pHEMA with 50% water content were studied with MTT cytotoxicity assay and live-dead analysis. The cell numbers were determined 24 h after cell seeding (5 × 10⁴) (Figure 8). On pHEMA hydrogels, about 70% of the planted cells were discovered to be adhered. After 7 days, there were 5 times as many cells on the pHEMA as there were in the attached sample. The number almost doubled during the course of the following 7 days, and in the last week, it climbed slightly less. All of the cell number increases were determined to be statistically significant. Results of a 3-week live-dead assay using SCs on pHEMA hydrogels are shown in Figure 9A. On day 7, a significant portion of the seeded cells were able to adhere to and grow on the hydrogels (Figure 9A–F). They were dispersed over the pHEMA coated with collagen on day 14 (Figure 9G–I). The living cell fraction of the SCs is growing over time, as seen in Figure 9B. It demonstrates that SCs can adhere to and proliferate on pHEMA.

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Figure 8. 

Proliferation of SCs on pHEMA hydrogels (MTT test). Statistical differences (^* P ≤ 0.05, ^** P ≤ 0.01, ^*** P ≤ 0.001) are indicated

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Figure 9. 

Live-dead analysis of SCs on pHEMA. Confocal micrographs of A) Dead and live cells and merged form of SCs (2 weeks). Scale bar: 100 µm; B) quantitative analysis of SCs on pHEMA hydrogels by using ImageJ software

Proliferation of SH-SY5Y neuroblastoma cells in GelMA-HaMA IPNs

SH-SY5Y cells were chosen as a substitute for neural cell to study their behavior in the nerve conduit prepared. Film versions of GelMA-HaMA gels were developed for experiments on cell adhesion and proliferation. Almost 70% of the cells had adhered by the first day. The cells were able to grow exponentially on IPN surfaces as seen by the weekly cell number doubling or tripling (Figure 10). A two-week live-dead cell viability assay (Figure 11A) was carried out, and ImageJ was used to count the number of cells visible on the micrographs. Indicating that the hydrogel for the cells was cytocompatible, the live cell percentage of the cells was above 80% for the first week and above 90% on the second and third weeks (Figure 11B).

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Figure 10. 

Proliferation of SH-SY5Ycells in GelMA-HaMA IPNs (MTT test) for 4 weeks. Statistical differences (^* P ≤ 0.05, ^** P ≤ 0.01, ^*** P ≤ 0.001) are indicated

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Figure 11. 

Live-dead analysis of SH-SY5Y cells in GelMA-HaMA IPNs. Confocal micrographs of A) Dead and live cells and merged form of SH-SY5Y cells (2 weeks). Scale bar: 100 µm; B) quantitative analysis of SH-SY5Y cells in GelMA-HaMA IPNs by using ImageJ software

In vitro cell staining on the final conduit

Cells were stained to study cell proliferation and cell-material and cell-cell interactions. In order to obtain final cell including structure SH-SY5Y cell containing IPN was prepared and placed into the proximal end of the pHEMA cylinder. The central and distal parts of the pHEMA tubes were filled with cell free IPNs. For the actin cytoskeleton the cells were stained with FITC-phalloidin and with DAPI for nucleus. The cells were examined for 3 weeks to study the ability of migration through the conduit (Figure 12). At the end of 7 days of incubation after placing cell containing IPNs in pHEMA tubes, cells had started to migrate through the conduit towards the distal end. On day 14 it was possible to see the cells throughout the cylinder. At the end of day 21 number of the cells at the distal part had increased (Figure 12).

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Figure 12. 

Distribution of SH-SY5Y cells in the IPN in the neve guide. A) Schematic representation of a conduit and the cellss; B) SH-SY5Y cell proliferation in proximal, middle and distal parts of the conduit structure on days 7, 14 and 21. Scale bar: 50 µm

β-III Tubulin and NeuN antibody staining

The present study SH-SY5Y cells were stained with both early (β-III tubulin) and late (NeuN) neuronal markers to evaluate their cellular state (Figure 13). NeuN expression was increased in 14 days of incubation, because it is a late neuronal marker. However, no significant increase was observed between days 7 and 14 in terms of β-tubulin.

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Figure 13. 

Increase in neuronal markers (NeuN and β-III tubulin) in SH-SY5Y cells in the nerve conduits. (A–D) Day 7; (F–H) day 14. The images were taken from the proximal end of the conduits. Scale bar: 50 µm

Netrin-1 effect on SH-SY5Y cells

In the GelMA-HaMA IPNs, the SH-SY5Y cells were able to migrate through the pHEMA conduit and form neurite extensions in the current study. The neurite extensions, however, were not directed (Figure 12). The protein netrin-1 was loaded to the distal end of the conduit in order to direct the extensions. On days 7 and 14 following netrin-1 loading, the neurite extension was examined using β-III tubulin antibody staining. With better aligned extensions through the nerve conduit, SH-SY5Y cells began to stretch their extensions toward the distal end (Figure 14, yellow arrows).

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Figure 14. 

β-III Tubulin expression of SH-SY5Y cells. A) Schematic representation of a conduit showing cell seeding and netrin-1 loading sites; B) SH-SY5Y cells in the nerve conduits presenting nucleus (DAPI, blue), β-III tubulin (β-III tubulin antibody, red) and merged images. Yellow arrows show extensions. The images were taken from the proximal end of the conduits. Scale bar: 20 µm

Discussion

Peripheral nerve injury, caused by physical trauma can result in loss of neural communication. As a result of any acute nerve injury, neuronal capabilities may be lost. The nerve can regenerate its own damaged axons through complicated mechanisms including Wallerian regeneration [2]. In the absence of segmentation loss or when the gap is significantly smaller than 3 mm, regeneration and repair in the PNS begin quite rapidly in the presence of moderate damage. In more severe injuries, there is an initial shock phase, followed by months of regeneration and repair ending with unsuccessful regeneration due to axonal sprouting. SCs are essential for promoting regeneration as they produce more cell surface adhesion molecules and form basement membranes containing ECM proteins [3]. Another option for lesions less than 3 mm is end-to-end suturing. However, suturing method can create tension that lead to in loss of neuronal communication in larger gaps. When end-to-end suturing is not possible, grafting methods are used. On the other hand, grafting materials (autografts, allografts, xenografts) have some drawbacks like cross-contamination, donor site morbidity, immune rejection and limited supply of donors. To overcome these limitations, researchers have focused on the construction of nerve conduits for axonal regeneration after nerve injury [5, 7]. These conduits are fabricated using synthetic or natural polymers. In some cases hybrid constructions are considered to adapt the mechanical and structural properties for nerve regeneration [13].

In the present study, a cylindrical nerve guidance conduit with an inner IPN structure is presented. The outer tube was made of pHEMA coated with collagen for cell attachment and the inner IPN was made by combining of GelMA and HaMA. As supportive materials, SCs and netrin-1, a molecule involved in axon guidance and cell migration, were used. In situ and in vitro characterization of the outer pHEMA and inner GelMA-HaMA IPN structures was performed to determine their suitability for axonal regeneration after nerve injury in terms of degradation, water content, mechanical properties, hydrophilicity and porosity.

GelMA-HaMA IPN structures were prepared using different combinations of GelMA and HaMA. The water contents of all IPNs were very similar to each other; they were above 80%, which is suitable for soft tissue applications such as neural differentiation and neurite outgrowth [42–44]. It was also previously shown that GelMA based hydrogels had ability to swell up to 100 times over their lyophilized dried weights. Compared to the pure GelMA and HaMA hydrogels, the swelling ability of IPN structure was increased by combining GelMA and HaMA. The IPN with the composition of GelMA-HaMA in the ratio of 90:10 showed a percentage swelling about 900%. The degradation profiles of the IPNs were examined in both PBS and cell culture media. Increasing the fraction of HaMA in IPN structure increased the weight loss rate. This can be explained by the crosslinking efficiencies of GelMA and HaMA. The methacryloyl groups introduced to GelMA and HaMA are important for the crosslinking density. Degrees of methacrylation are 94% ± 2% and 60% ± 7%, for GelMA and HaMA, respectively. Thus, increasing the HaMA fraction in the IPN results in a decrease in the amount of MA groups in IPNs, and therefore, in the crosslinking efficiency, resulting in a higher rate of degradation. During degradation and cell ingrowth, cells deposit new ECM that supports tissue regeneration. Therefore, timing for degradation is also important; degradation time should coincide with the time of ECM deposition and cell proliferation [45]. Slow degradation may hinder ECM deposition, while too rapid degradation may result in a mechanically unstable structure due to the lack of ECM molecules. The present results showed that the IPN with GelMA-HaMA in a ratio of 85:15 had a water content of 80% and a swelling capacity of 800% and degraded within 4 weeks, which was suitable for the refeneration of neural tissue; the degradation of the IPN structure as a sacrificial material should aloe the expansion of rebenerating axons. Therefore, it was selected for the construction of final conduit. Similar degradation results were observed in a different study in which the sacrificial material GelMA was used to develop a scaffold; this material was thought to be suitable for cell ingrowth during axon regeneration [37, 46–48]. The outer pHEMA tube was optimized for porosity, water content, mechanical strength and hydrophilicity. Hydration and mechanical support are provided by the hydrogels in swollen state. In addition to mimic natural tissues, it is possible to tune their swelling and stiffness. For cell ingrowth, nutrient diffusion and vascularization, interconnected porous structures are the most suitable environment. Scaffold porosities, pore size distributions, and average pore dimensions are crucial [49–52]. The preparation mixture’s water content changed to find the best conduit for neuronal regrowth. For water contents of 44%, 50%, 55%, and 58%, respectively, the hydrogels’ porosities were determined to be 17%, 33%, 52%, and 50%, and their pore diameters to be 40.75 µm ± 8.59 µm, 55.09 µm ± 7.15 µm, 15.24 µm ± 3.05 µm and 15.44 µm ± 2.05 µm. Thus, the porous structure of pHEMA conduit in the present case is especially useful for nutrient permeation, waste removal and for ECM protein deposition. SCs seeded on the pHEMA conduit are expected to produce growth factors for axonal regeneration and elongation and thus the growth factors produced go through the walls of the conduit through the pores interconnected with each other along the length of the tubular conduit [53]. In order to produce nerve guides, hydrogels with an interconnected porosity structure and a water content of 50% were selected.

It was observed that the equilibrium water content of pHEMA tubes with different water contents of the preparation mixture increased up to 52% with increasing water content of the preparation mixture. Since solute diffusion and mechanical properties of scaffolds are affected by variations in equilibrium water content, 52% was considered appropriate for nerve conduit applications [54]. The pHEMA tubes fabricated in this study are capable of repeated swelling without producing hysteresis, indicating that they maintain their integrity. This makes the tubes a good choice for soft tissue engineering applications [18]. Protein adsorption and cell adhesion are directly related to the hydrophilicity of a scaffold material. Therefore, for cell attachment and growth, the contact angle is an important parameter [16]. Cells are mostly able to adhere to highly hydrophilic surfaces, but the cell-cell interaction is unfavorable due to the good interaction between the cells and the surface. Moreover, mostly hydrophobic surfaces are not preferable for biomedical applications because cells cannot attach to these surfaces [55]. In the present study, the contact angles of the surfaces were shown to be suitable for SC attachment (31.0° ± 7.6° for the pHEMA prepared with 50% water).

Another important parameter for the use of biomaterials as medical devices is suitable mechanical properties, with tensile strength mainly influencing the suturing of hydrogel implants during surgery [44]. In the literature, acellular nerve tissue is reported to have a tensile strength of 1,400 kPa and a tensile modulus of 576 kPa [19]. Acellular tissue has a much lower UTS than the conduits in the current study, while pHEMA prepared with 44% and 50% water content had tensile modulus values equivalent to those of nerve tissue (548.6 kPa ± 23.4 kPa and 570.9 kPa ± 92.1 kPa, respectively). Thus, the pHEMA tubes in the study are suitable for cell migration and attachment, as well as for suturing in future operations for nerve injury as a substitute material for the application of nerve tissue.

SCs were seeded on in a pHEMA tube coated with collagen to facilitate axonal regrowth. Nearly 70% of the cells were able to attach to surfaces and proliferate. SH-SY5Y cells were used as a model for axonal regeneration and seeded into GelMA-HaMA IPN constructs. It was found that the majority of SH-SY5Y cells were also able to attach and proliferate. Cell cytoskeleton and nucleus were stained and examined under CSLM to study cell proliferation and migration after construction of the final conduit (Figure 1). After 3 weeks, the cells were shown to be able to migrate to the mid and distal ends. In addition, the appearance of neurite outgrowth and cell-to-cell communication was considered a positive development, suggesting that the conduit construction containing GelMA-HaMA IPN may be able to accommodate expanding neurons for axonal regeneration in case of injury. In addition, SH-SY5Y cells were examined using neuronal marker labeling. Early neuronal markers include β-III tubulin, a microtubule element, while late neuronal markers include NeuN, a neuron-specific nuclear protein [56, 57]. NeuN expression of SH-SY5Y cells in our study showed increase in 2 weeks. Quantitative immunofluorescence quantification in ImageJ was performed through dividing integrated density of the fluorescence coming from NeuN expression by total cell number following thresholding [58]. It was seen that the intensity was increased 20-fold (from 0.1% to 2%). Actin and microtubule dynamics are involved in the formation of the growth cone during neurite outgrowth. The expansion of developing neurites was seen using β-III tubulin antibody labeling. Hyaluronan and carbon nanotubes were used in Ruiz et al. [59] nerve conduit, and the suitability of the structures for regenerating tubular neural structures was evaluated. They concluded that the nerves on the neural tubes were capable of producing β-tubulin and that the presence of neuronal markers made the neural tubes suitable for use in nerve regeneration. In the present study, the expression of β-tubulin was observed at both day 7 and day 14. The fluorescence intensities of the images did not show any significant difference (23% and 26%, respectively) showing that SH-SY5Y cells were able to produce neurites. Other studies have demonstrated the efficiency of conduits in relation to neurite formation using the anti-β-III tubulin marker, and they all concluded that higher β-tubulin production is favorable for nerve conduits used for axon regeneration after peripheral injury [60–64]. In addition to SCs, the netrin-1 protein was also injected into the distal part of the pHEMA tube as a supporting molecule. In vertebrates, circumferential axonal projections can be directed by netrin proteins [28]. Netrin-1, originally discovered as a traditional axonal guidance protein, is critical for controlling axon pathfinding and migration in neurons. In the present study, on day 7, the extensions were found to extend up to 150 µm, while on day 14 they reached 350–400 µm. In a study by Cai et al. [65], a concentration gradient of netrin-1 was generated by submerging the lower part of a nerve conduit using a controlled diffusion method. The results showed that biological gradients can significantly enhance axon regeneration by triggering axon attraction through intracellular signaling responses and promoting axon extension. In addition, Huang et al. [28] developed a conductive double network (DN) hydrogel scaffold supported by a graphene mesh and enriched in netrin-1. GelMA and alginate were intertwined to produce the hydrogel, which serves as a reservoir for netrin-1. They concluded that netrin-1 loading was even more effective than autologous grafts in improving peripheral nerve regeneration and denervated muscle repair. The results of the present study showed that at the end of the second week, the outgrowths of SH-SY5Y cells were concentrated at the distal end where the netrin-1 protein had been injected. In conclusion, the presented pHEMA tube with GelMA-HaMA-IPN structure is a promising nerve guidance tube considering the properties such as mechanical strength, swelling capacity, degradation profile, and hydrophilicity. SCs seeded on the pHEMA tube along with the IPN structure supported the migration of SH-SY5Y cells, model cells for axonal regeneration. In addition, injection of netrin-1 at the distal end of the tube directed the neural projections of SH-SY5Y cells toward the end. Future studies will test the completed conduit in vivo. It is expected to be useful for peripheral nerve regeneration.