Conducting Cytocompatible Scaffolds: Composite of Sodium Hyaluronate and Colloidal Particles of Conducting Polymers

Novel bio-inspired conductive scaffolds composed of sodium hyaluronate containing water soluble polyaniline or polypyrrole colloidal particles (concentrations 0.108, 0.054 and 0.036 % w/w) were manufactured. For this purpose, either crosslinking with N-(3-dimethylaminopropyl-N-ethylcarbodiimide hydrochloride and N-hydroxysuccinimid or a freeze-thawing process in the presence of poly(vinylalcohol) were used. The scaffolds comprised interconnected pores with prevailing porosity values of ~30 % and pore sizes enabling the accommodation of cells. Good swelling capacity (92 – 97 %) without any sign of disintegration was typical for all samples. The elasticity modulus depended on the composition of the scaffolds, with the highest value of ~50 000 Pa obtained for the sample containing the highest content of polypyrrole particles. The scaffolds did not possess cytotoxicity and allowed cell adhesion and growth on the surface. Using the in vivo-mimicking conditions in a bioreactor, cells were also able to grow into the structure of the scaffolds. The technique of scaffold preparation used here thus overcomes the limitations of conducting polymers (e.g. poor solubility in an aqueous environment, and limited miscibility with other hydrophilic polymer matrices) and moreover leads to the preparation of cytocompatible scaffolds with potentially cell-instructive properties, which may be of advantage in the healing of damaged electro-sensitive tissues.


Introduction
Bioelectrical signals are one of the key players in the development and regeneration of tissues 1 . Due to this fact, electrical stimulation has been studied as a promising tool in disease treatment and wound healing 2 for decades. In this context, the development of novel stimuli-responsive electroconductive biomaterials is of great interest when considering the use of such materials in a wide variety of biomedical applications 3 . Indeed, to facilitate electrical stimulation, it is crucial to use electrically conductive biomaterials. Here, different class of materials can be considered; these include metals, conductive polymers, and piezoelectric materials, which can all transfer electrical, electrochemical, and potentially even electromechanical stimuli to cells 4 . Recently, the preparation of electrically conductive polymers (CP), such as polypyrrole (PPy) and polyaniline (PANI), has become a highly prized goal of the tissue engineering community, as they can e ciently transfer electrical signals at the interfaces with cells due to their intrinsically combined electronic and ionic conductivity 5 . Owing to ionic conductivity, the electrical signal can be transduced to an ionic signal, which is a natural communication system of cells 6 .
Consequently, CPs can be highly bene cial in tissue engineering (TE), especially of cardiac, muscle, and nerve tissues 7,8 . Among additional advantages of CPs are their easy synthesis. Both PANI and PPy can be prepared in various forms such as powders 9 , colloidal dispersions 10 or lms 11 , of which the form facilitating the processing and/or preparation of composites (colloidal dispersion) is especially important. Another shortcoming of CPs is their inability to be prepared in a three-dimensional form (scaffolds). Therefore, naturally derived polymers, such as sodium hyaluronate (HA), have been employed to overcome the limitations related to the fabrication of suitable conducting 3D scaffolds with required mechanical, viscoelastic, and biological properties 12 . Recently, many studies have demonstrated that HA plays a crucial role in various biological processes, including cell proliferation, migration, and differentiation, or in the activation of anti-in ammatory growth factors 13,14 . Sodium hyaluronate is a naturally-occurring glycosaminoglycan exhibiting intriguing viscoelastic properties, excellent biocompatibility, biodegradability, and the ability to be easily modi ed with various functional groups 15 .
Moreover, it possesses other bene ts for TE, including the absence of toxicity and non-thrombogenic and nonimmunogenic properties, in contrast to other synthetic materials 16  However, as far as the authors know, no previously published study has investigated the scaffolds presented here, these prepared by the chemical and physical crosslinking of sodium hyaluronate (HA) with incorporated CP-based colloidal particles. In this work, such scaffolds were prepared using embedded conducting and water soluble colloidal PPy or PANI particles stabilized also with HA. The main aim of the study was to investigate whether -and if so, how -the method of crosslinking and the composition of the material in uence the physico-chemical and biological properties of the scaffolds in terms of cytocompatibility and the ability to facilitate the ingrowth of mouse embryonic broblast cells. This novel and original approach was investigated with the aim of preparing porous, conductive, and cytocompatible scaffolds for TE.

Synthesis of polyaniline and polypyrrole colloids
Samples of colloidal PANI and PPy were prepared via the oxidation of the respective monomer, aniline hydrochloride (AH) or pyrrole (Py), with ammonium peroxydisulfate (APS) in the presence of sodium hyaluronate (HA). The colloidal particles are designated HaPANI and HaPPy. Brie y, HA was dissolved to a 1% (w/w) solution in MilliQ water under stirring at 55°C overnight. For dispersion polymerization, AH (0.2M) in 1% (w/w) HA solution was prepared, and polymerization was started at room temperature by adding 0.1M aqueous APS solution to the reaction mixture. The mixture was stirred for 5 min, and left at rest to polymerize. The reaction was completed within 2 h. Correspondingly, PPy was prepared using 0.2M Py monomer solution in 1% (w/w) HA and 0.25M aqueous APS, which were mixed and left to polymerize for 2 h. In order to remove residual impurities, the colloidal dispersions were transferred into Spectra Por 2 membrane dialysis tubing (cut-off 12 000 -14 000; Spectrum Laboratories Inc., U.S.) and puri ed through exhaustive dialysis against 0.2M hydrochloric acid. Each of the colloidal dispersions was employed for the preparation of scaffolds.

Preparation of scaffolds
Samples were prepared in two different ways, speci cally by means of chemical ( Ch ) and physical ( Ph ) crosslinking procedures. The composition of the samples is given in Table 1.
On the basis of preliminary studies, the hyaluronan scaffolds containing PANI or PPy colloids chemically crosslinked with EDC and NHS (designated HaPANI Ch , HaPPy Ch ) were made according to 23 . A stock solution of HA with a concentration of 1% (w/w) was prepared by dissolving the polymer in Milli-Q water for 24 h at 50°C. The crosslinking agents EDC (100 mM) and NHS were added to the 1% (w/w) HA solution in a ratio of 1:1.5 (w/w) and the mixture was stirred for 1 h at 25°C. Subsequently, the solution was titrated under continuous stirring, with PANI colloid dispersed in 0.2M HCl to adjust the pH to 4.5-4.7. Correspondingly, PPy-containing scaffolds were prepared.
The crosslinking of scaffolds using the physical freeze-thaw method [24][25][26] was carried out using PVA, and the samples were designated HaPANI Ph , HaPPy Ph . A stock solution of PVA with a concentration of 10% (w/w) was prepared by dissolving the polymer in Milli-Q water for 24 h at 80°C. The PVA was added to the 1% (w/w) HA solution in a ratio 1:2 (w/w) and stirred for 1 h at 25°C. Subsequently, the solution was titrated under continuous stirring, with the colloidal dispersion of PANI (in 0.2M HCl) to adjust the pH to 4.5-4.7. Correspondingly, PPy containing scaffolds were prepared. The concentrations of CP-based colloidal particles in the scaffold were 0.108, 0.054 and 0.036% (w/w), these values used as superscripts for sample labelling.
The solutions from both preparation routes (chemical or physical) were then poured into polystyrene moulds and rst frozen at −18°C for 60 h, then freeze-dried in an ALPHA1-2 LD plus freeze-dryer (Christ, UK). As a result, cylindrical specimens were obtained with a diameter of 28 mm and a height of 5 mm. Size and morphology of colloidal particles The particle size and size distribution were determined on dialysed samples using dynamic light scattering (DLS) (Zetasizer Nano ZS, Malvern Instrument, UK). The hydrodynamic radii of colloidal particles, expressed as z-average particle diameters, were measured at 25°C at a scattering angle of 173°.
The polydispersity index (PDI) describing the width of the particle size distribution in a given sample was Page 6/25 also determined. Samples were prepared for measurement by diluting 10 µL of freshly prepared dispersion in 1 mL of 0.1 M HCl. The analyses were run in triplicates with average values and standard deviations reported.
The morphology of colloidal particles was assessed with a transmission electron microscope (TEM) JEOL JEM 2000 FX (Japan).

Mechanical properties
Mechanical properties in terms of Young's modulus were determined on an Autograph AG-X tensile tester (Shimadzu). The analyses were performed on cylindrical samples with a length of 12 mm and a diameter of 8 mm. Each sample was inserted between two horizontal plates and deformed at a rate of 1 mm min −1 . The measurement time was 3 min and within this short period of time the humidity of the sample was considered constant. Young's modulus was determined as the slope of the linear part of the stressstrain curve. The experiments were performed in compression mode and the relative standard deviation of all values obtained did not exceed 5%.

Surface topography and electrical properties
The surface electrical properties of the scaffolds were analysed by tunneling atomic force microscopy (AFM) using the PeakForce TUNA module on a Dimension ICON instrument (Bruker Corporation; US).
Measurements were performed at ambient temperature using a PFTUNA probe (Bruker Corporation; US) with a spring constant of 0.4 N m −1 , covered on both sides with a conducting Pt/Ir layer. The scanning rate was 0.3 Hz and the TUNA and peak currents were measured by applying a bias voltage of 10 V. The resulting parameters of area roughness and TUNA and peak currents were determined according to the protocol of ISO 25178-2 standard using NanoScope Analysis software v. 1.5. The following parameters were determined: surface roughness (S a ), maximal surface height (S z ), average and maximum TUNA current, and average and maximum peak current. The TUNA current is the average current over one full tapping cycle in PeakForce mode. Peak current corresponds to the current measured at a de ned maximum force in the PeakForce cycle. Data from AFM were processed using Gwyddion 2.5 software (Czech Metrology Institute, Czech Republic).

Morphology and porosity of scaffolds
The surface morphology of lyophilized samples was studied using a scanning electron microscope (Phenom Pro desktop scanning electron microscope (SEM) with a BSE detector (Phenom-World B.V., The Netherlands)) at acceleration voltages of 10 and 15 kV. The samples were cut into sections using a sharp razor blade, to observe the cross-sectional morphologies of their scaffolds. The pore sizes of the scaffolds were measured by analysing the SEM images captured as described above. The method of image analysis was based on the chord length method used in the ASTM standard ASTM E-112 (E-112, 2010). A system of intersecting lines was drawn on the SEM images of the planar sections of the samples, and chord lengths were automatically measured by an in-house algorithm written in the Python programming language. Then, the mean pore size was computed using the protocol of ASTM E-112 standard and expressed as a percentage of pore volume relative to the total volume of the sample.

Swelling of scaffolds
The swelling degree (SD) of the lyophilized samples was determined gravimetrically. Weighted, diskshaped specimens were immersed in phosphate buffered saline (PBS) at 37°C to reach swelling equilibrium. The water uptake was determined by removing the swelled samples from the PBS at selected time intervals, wiping them with tissue paper, and weighing them. The SD was calculated according to the

Cytotoxicity
The cytotoxicity was investigated according to ISO protocol 10993-5, both on freshly prepared scaffolds and after their lyophilization. For the test, 0.1 g of tested material was extracted with 1mL of cultivation medium for 24 h at 37°C under stirring. The cells were pre-cultivated for 24 h and seeded at a concentration of 1×10 5 per well (96 well plates were used). The extracts were diluted with culture medium to obtain a series of dilutions with concentrations of 75, 50, 25, 20, 10, and 1%. After incubation for 24 h, the cell viability was determined by 3-(4,5-dimethylthiazol-2-yl)-diphenyltetrazolium assay (MTT cell proliferation assay kit, Duchefa Biochemie, Netherlands). The absorbance was measured at a wavelength of 570 nm using an In nite m200pro luminometer (Tecan, Switzerland). The viability of the cells was expressed as the reduction in cell viability relative to the reference, i.e., cells cultivated in the absence of extracts. All tests were conducted in quadruplicates. The morphology of the cells was observed using an inverted Olympus phase contrast microscope (Olympus IX81, Japan).

Proliferation test
The ability of cells to proliferate on the tested samples after their lyophilisation was determined using the ATCC CRL-1658 NIH/3T3 mouse embryonic broblast cell line. A cell suspension at a concentration of 1 × 10 6 cells per mL was prepared, and 0.3 mL of the suspension was carefully injected by syringe into each scaffold and onto its surface, and placed into an incubator for 2 h to induce cell adhesion and initiate proliferation. After this period the scaffold was spill over by cultivation medium andcultivated for 7 days. The medium was changed every second day of the experiment. After the cultivation period, the cells were xed and stained with Hoechst 33258 (Molecular Probes, Carlsbad, CA) and ActinRed 555 (Life Technologies, USA). The morphology of the cells was investigated using a confocal microscope (Olympus Fluoview FV 3000, Japan).

Cell ingrowth into scaffolds
Before testing the scaffolds in the 3D environment of a bioreactor, cells were seeded onto the scaffolds and pre-cultivated for 24 h under the standard conditions given above. After pre-cultivation, the samples were placed into a bioreactor, where they were cultivated for the next 7 days to allow cell ingrowth. For testing, an RCCS-4 rotary cell culture system (Synthecon Incorporated, USA) was used. Each of the samples was separately inserted inside the bioreactor and 50 mL of cultivation medium was added. The forward rotation of the reactor was adjusted to 10.5 rpm. The partial oxygen pressure, as well as the temperature were the same as under standard cultivation in an incubator. After cultivation, the scaffolds were xed with 4% paraformaldehyde overnight, washed with PBS, permeabilized with 0.5% Triton X-100 (Sigma Aldrich, Germany), and washed again three times with PBS. The cells were stained using ActinRed™ 555 (Thermo Fisher Scienti c, USA). The tested samples were sliced, and the cell morphology was observed using a confocal microscope (Olympus Fluoview FV 3000, Japan).

Results And Discussion
Conducting colloidal dispersions Colloidal dispersions of CP stabilized with polysaccharides are smart formulations helping to solve the problem of the poor solubility of CP in aqueous environment, and improve the cytocompatibility of the nal composite 27 . Another, not previously mentioned advantage of such composites appears in the case when CPs are mixed with other hydrophilic polymer matrices -for example, when polymer-based scaffolds are fabricated. Here, the better polymer-polymer compatibility of HaPANI or HaPPy colloids containing HA combined with the bulk polymer of the scaffold (also based on HA) is expected in comparison with pristine PANI or PPy.
The size and polydispersity index of colloidal particles used for scaffold fabrication were determined on thoroughly dialysed samples, puri ed of possible impurities which might cause cytotoxic effects 28 . The hydrodynamic diameters of particles were different, with micrometer sizes observed for HaPANI (2200 ± 260 nm) and smaller sizes determined for HaPPy (447 ± 8 nm). Both samples showed, however, similar polydispersity indexes (~0.2). The morphology of particles observed by transmission electron microscopy ( Figure 1A and 1B) conformed with scattering measurements ( Figure 1C and 1D), showing in both cases regular, spherical particles with a smooth surface, and, in the case of HaPANI, the interconnection of such particles to form bigger, loose clusters.

Preparation and characterization of scaffolds
The CP-based colloidal dispersions HaPANI and HaPPy were used, each incorporated into the used HA matrix and in three different concentrations. Two methods of scaffold preparation were employed, each followed by an identical freeze-drying procedure. The rst route included chemical crosslinking with EDC and NHS, the latter used as the activator of carboxylic groups; the second procedure involved crosslinking by the freeze-thaw method using PVA, hereinafter referred to as the physical route. The question, hence, arose whether -and if so, how -these two preparation methods together with scaffold composition affect the material and biological properties of the given scaffolds. . This E range is actually similar to the E range observed for chemically crosslinked samples (HaPANI Ch ), i.e., from 5000 to 15000 Pa; however, the correlation between the E values and the amount of colloidal particles is different in these samples. In summary, the scaffolds incorporating HaPANI colloidal particles exhibited a low elasticity modulus, which moreover lacked correlation with the colloid content in the sample. In contrast, the behaviour of all scaffolds containing HaPPy colloid was more predictable in terms of E vs particle content. This is surprising, as one would expect more similar behaviour among scaffolds containing PVA irrespective of the type of colloidal particles used, as PVA contribute to a rubbery and elastic texture and higher mechanical strength of scaffolds thanks to the better distribution of the mechanical load along the crystallites of the three-dimensional scaffold structure 30 . The mechanical properties of the scaffolds hence result from the crosslinking routes and the content/type of colloidal particles used for their fabrication.

Surface topography and electrical properties
Lyophilized samples with a medium concentration of the conducting component (0.054% w/w) were analysed using AFM to determine their surface properties and surface conductivity (Figure 3).
The surface roughness (Sa) and maximum surface height (Sz) of the samples as presented in gure 3 shows that the surface characteristics of the scaffolds are rather similar. Their surfaces are irregular with embedded pores, these seen mainly in physically crosslinked samples. Chemical crosslinking gave rise to scaffolds with a ake-like surface structure. The second and third columns of Figure 3 show current maps expressed as TUNA and Peak currents. These unambiguously prove that the scaffolds are conductive and that their average values of TUNA current are similar, lying in the range of 2.1 -3.8 pA, irrespective of the type of conducting particles used and of the fact that the percentage of the conducting component in the chemically crosslinked samples was higher with respect to the total mass of the scaffold than in the scaffolds crosslinked physically. A bigger difference in the measured values can be seen for maximum currents (max TUNA, max Peak current), which were lower for physically crosslinked samples, with a maximum current of about 12 pA. In the case of samples crosslinked chemically, values of 15 and 19 pA for HaPANI Ch _54 and HaPPy Ch _54 , respectively, were measured. This minor difference is a natural consequence of the higher ratio of CP-based colloids in the chemically crosslinked samples. In this respect, both HaPANI and HaPPy colloids performed, within the same type of crosslinking mechanism, similarly. Obviously, as the samples contain particles of intrinsically conducting polymer (CP) with mixed ionic and electron conductivity, and as the surroundings within hydrated scaffolds are also ionically conductive, the scaffolds thus form a suitable environment which can facilitate the adhesion and proliferation of electrically conductive cells and tissues 20 .

Porosity and morphology
Morphology, including the size of pores in lyophilized scaffolds, was assessed by means of the visual observation of SEM images (Figure 4). The images were used for the measurements of pore size and the calculation of porosity, which were both quanti ed according to the chord length method given by the protocol of ASTM E-112 ( Figure 5).
According to the results of the image analysis, the physically crosslinked HaPPy Ph samples with the two lower concentrations of colloidal particles (0.036, 0.054%) exhibited the biggest pores in the scaffolds. The pore sizes were the smallest in the formulation in which the colloid concentration was 0.108% (HaPPy Ph_108 ).
In numerical values, the porosity ranged from 26 -37%, with the lowest value for the highest content of colloidal particles, as observed for HaPPy Ph_108 . The HaPPy Ch samples, prepared with chemical crosslinking, yielded a lower porosity of 22 to 28%, which was lowest for the scaffold with the medium content of colloidal particles (HaPPy Ch_54 ). The physically crosslinked HaPANI Ph samples were, with respect to pore sizes, similar to the above-discussed samples containing PPy colloidal particles, and showed pore sizes of 271, 288, and 177 µm for scaffolds with increasing concentrations of CP-based colloid. Calculated porosity values for these formulations ranged between 27 and 32%. HaPANI Ch scaffolds, prepared by chemical crosslinking, exhibited porosity values comparable to those of scaffolds crosslinked physically, with one exception: the sample HaPANI Ch_36 . This outlying sample contained the lowest concentration of HaPANI colloidal particles and exhibited a porosity of more than 50% and an average pore size of 547 ± 126 µm. The porosities of the other two HaPANI-based samples were 30% and 35% for the medium and highest colloid contents, respectively. According to the image analysis supported by visual evaluation, the bigger pores were always seen in samples with the lowest content of colloidal particles and, in general, the sizes of pores in most of the scaffolds were roughly estimated to be within the range of 200 -300 µm, which is su cient for the ingrowth of cells into the structure and for nutrient supply and metabolite removal.

Swelling
The course of swelling was similar for all samples, and the initial increase in swelling degree (SD), observed within the rst approx. 100 min, was followed by equilibrium (Figure 6). At equilibrium, the SD of physically crosslinked HaPPy Ph scaffolds ranged from 92 to 96% and decreased with growing colloid content in the sample. In comparison, differences in the swelling of all chemically crosslinked HaPPy Ch samples were only minor and their equilibrium SD was 93 -95%. Scaffolds containing HaPANI exhibited lower SD for physically crosslinked samples in comparison with samples that were crosslinked chemically. With short swelling times, the lowest SD of 87% was recorded for HaPANI Ph_54 , while the highest equilibrium SD of 93% was observed for the sample containing the highest concentration of particles. Chemically crosslinked HaPANI Ch scaffolds swelled better, their SD ranging from 95 to 97%. In this respect, SD is in uenced by PVA in the hydrogel matrix; in chemically crosslinked samples with PVA absent, the naturally high ability of HA to take up water prevailed and the SD was, therefore, higher. When in a mixture, the crystallinity of PVA affects the hydrogel structure, which is less loose compared with samples containing solely HA. As a result, physically crosslinked gels absorb less water, this resulting in lower SD. Nevertheless, regardless of the observed differences, the SD values were similar and all scaffolds showed good swelling characteristics.

Cytotoxicity
The absence of cytotoxicity is one of the fundamental requirements that biomaterials must meet. The cytotoxicity of a full set of samples was therefore tested. To show representative information, the protocol of ISO 10993-5 standard was employed, including the use of an appropriate cell line; i.e., NIH/3T3 broblasts. The cytotoxicity was determined on native samples prior to lyophilisation and on lyophilised scaffolds, which are marked with the superscript L .
The summary of cytotoxicity data recorded for chemically crosslinked scaffolds and presented in Figure   7 unambiguously demonstrates that all the native scaffolds prepared by chemical crosslinking, HaPANI Ch or HaPPy Ch , can be classi ed as non-cytotoxic, with cell viabilities higher than 70%. The situation was, however different for lyophilised scaffolds. After lyophilisation, the cytotoxicity increased, especially in the case of HaPPy containing scaffolds, the lyophilised HaPPy Ch_L scaffolds showing cytotoxic effects with concentrations of extract higher than 25%, irrespective of the concentration of the colloidal particles used. In the case of HaPANI Ch_L containing HaPANI colloid, the cytotoxicity was lower and only the two highest concentrations of extracts (70 and 100%) exceeded the threshold for cytotoxicity, and moreover only slightly. The effect of lyophilisation on cytotoxicity can be related to the protocol of testing given by the ISO standard. The procedure de nes the ratio of material/extraction medium according to the mass.
In the case of lyophilised samples with water removed, the ratio of the mass of dry matter (which in fact contains impurities) to the amount of extraction medium is higher. This situation can lead to the higher cytotoxicity of lyophilized samples, despite the fact that the procedure itself should not produce additional cytotoxic compounds.
The behaviour of physically crosslinked samples (Figure 8) prior to lyophilisation was similar to that observed for scaffolds crosslinked chemically, and only in a few cases did the samples show a cytotoxic effect, which was, moreover, observed at only the highest extract concentration. Only the highest extract concentration of native HaPANI Ph scaffold signi cantly exceeded the cytotoxicity threshold, and the effect correlated with the concentration of HaPANI colloidal particles in the sample. Contrary to the situation observed for scaffolds prepared by chemical crosslinking, here lyophilisation decreased the negative impact of the scaffolds on cell viability. This could actually be observed in the case of all samples, especially in the case of HaPANI Ph_L , where none of the lyophilised hydrogel samples was cytotoxic.
The difference in the behaviours of lyophilized scaffolds prepared by chemical and physical crosslinking could, to some extent, be expected, as physically crosslinked scaffolds lack the possible residues of cytotoxic crosslinking agents, which can be released during the lyophlization process. We can also hypothesise that the difference is related to the different pore structures and the type of bound cytotoxic residual compounds within the scaffold structure.

Cell adhesion, growth and ingrowth
The cytotoxicity of scaffolds, which can be related to the composition of the material and the possible leaching of residual precursors or reagents under extraction was low. The lyophilized samples were therefore subjected to another cytocompatibility study, this involving the determination of bio-interface properties represented by the ability of cells to adhere onto the scaffold surface and subsequently grow. The lyophilized samples were chosen, as their internal architecture was more appropriate for cell ingrowth than that of native scaffolds. The cells were seeded on the surfaces of scaffolds and cultivated for one week. After this time elapsed, the cells were able to adhere and grow on all surfaces. Representative pictures are presented in Figure 9.
Scaffolds suitable for tissue engineering must not only allow the attachment and growth of cells on their surfaces, but also be able to facilitate cell ingrowth into the structure of the scaffold. As mentioned above, an increasing concentration of HaPANI or HaPPy colloidal particles within the scaffold resulted in the higher cytotoxicity of the scaffold. The ingrowth of cells, allowed by their cultivation in a bioreactor mimicking in vivo conditions, was therefore tested only on samples with the lowest concentration (0.036%) of HaPANI and HaPPy ( Figure 10). According to the results, it is obvious that cells were able to efficiently ingrow into the scaffold structure. This test showed not only that the scaffolds prepared here were cytocompatible with respect to basic parameters such as absence of cytotoxicity, but also that their bulk architecture created a friendly environment for cell ingrowth; thus, such scaffolds can be suitable for use in tissue engineering. Furthermore, their inherent conductivity, as a cell-instructive property, assured by the presence of CP-based colloids, opens up their potential use in a wide range of applications relating to the tissue engineering of electro-sensitive tissues.

Conclusion
The preparation and composition of scaffolds have been widely studied for decades, as they are critical factors conditioning the application of scaffolds in tissue engineering. In addition, scaffolds should not only be passive supporting materials for cells, but also enable preferable responses to external stimuli leading to cell-instructiveness. One of the cell-instructive cues of materials is electrical conductivity, which is especially advantageous when electro-sensitive tissues, such as heart, neuronal, or muscle tissues, are considered. The incorporation of conducting polymers into the structures of scaffolds is an advantageous way of inducing conductivity in the materials. The poor solubility of CPs in an aqueous environment and their limited miscibility with other hydrophilic polymer matrices makes the fabrication of scaffolds based solely on CPs di cult. The novelty of the here-presented fabrication techniques lies in their removal of these shortcomings by preparing colloidal particles based on the conducting polymers PANI and PPy and incorporating them into the structure of the biocompatible and biodegradable polymer sodium hyaluronate. In our study, two crosslinking methods were employed -namely, chemical and physical -and the in uence of composition and the route of crosslinking on the nal material, and the biological properties of the scaffolds were determined. In agreement with the presented data, it can be concluded that both used crosslinking techniques allow the e cient incorporation of colloidal particles into the bulk polymer, making thus the nal composites conductive. The battery of characterization methods employed here revealed that the porosity, pore size, mechanical properties, and swelling of the studied samples were rather similar. Also, the results of cytotoxicity tests con rmed that the scaffolds were similarly cytocompatible with respect to this important characteristic. The effect of the lyophilization process on cytotoxicity was found to be greater than the crosslinking route used for preparation. Most crucially, tests conducted in bioreactors mimicking in vivo growth conditions showed that the scaffolds allow the adhesion and growth of cells on their surfaces; moreover, the cells were even able to ingrow into the structure of the scaffolds. The materials presented here thus represent electroconductive and cytocompatible composites with potentially cell-instructive properties.
Declarations Acknowledgement