Carbon Nanomaterial-Based Hydrogels as Scaffolds in Tissue Engineering: A Comprehensive Review

Abstract

Carbon-based nanomaterials (CBNs) are a category of nanomaterials with various systems based on combinations of sp2 and sp3 hybridized carbon bonds, morphologies, and functional groups. CBNs can exhibit distinguished properties such as high mechanical strength, chemical stability, high electrical conductivity, and biocompatibility. These desirable physicochemical properties have triggered their uses in many fields, including biomedical applications. In this review, we specifically focus on applying CBNs as scaffolds in tissue engineering, a therapeutic approach whereby CBNs can act for the regeneration or replacement of damaged tissue. Here, an overview of the structures and properties of different CBNs will first be provided. We will then discuss state-of-the-art advancements of CBNs and hydrogels as scaffolds for regenerating various types of human tissues. Finally, a perspective of future potentials and challenges in this field will be presented. Since this is a very rapidly growing field, we expect that this review will promote interdisciplinary efforts in developing effective tissue regeneration scaffolds for clinical applications.

Keywords:

• carbon
• biomaterial
• nanotechnology
• tissue engineering
• scaffold

Introduction

Nanomaterials have gained considerable attention in various biomedical applications over the past decade owing to their fascinating physicochemical properties.^1,2 For example, the reduced sizes of nanomaterials allow them to be efficiently internalized into cells by penetrating through cellular membranes or via endocytosis.³ Owing to effects of quantum confinement, a variety of nanomaterials display dissimilar physical properties when compared to their bulk counterparts, such as different optical absorption and emission with engineering aiming for applications in biosensing and bioimaging.⁴ In terms of therapeutic applications, nanoparticles, nanotubes, and nanosheets possess an ultra-high surface area that enables an increased drug-loading capacity, and thus they have been widely applied in nanomedicine.⁵ In addition, some nanomaterials (eg, gold nanoparticles and carbon nanotubes) can also exhibit strong plasmonic effects that enhance the photothermal conversion efficiency. As a result, nanomaterials have also been used as agents for photodynamic therapy (PDT) and photothermal therapy (PTT).^6,7

Among the large family of nanomaterials, carbon-based nanomaterials (CBNs) constitute an important member which has shown tremendous potential in diverse applications for both diagnostics and therapeutics.^3,8 CBNs can display diverse structures ranging from zero-dimensional quantum dots, one-dimensional tubular structure (carbon nanotubes), two-dimensional (2D) sheets (graphene), and three-dimensional (3D) sponges and hydrogels, which are constructed by sp²- and sp³-hybridized carbon bonds. The varied structures and chemical bonds within CBNs also lead to a full spectrum of physicochemical properties ranging from metallic carbon nanotubes (CNTs) and graphene to semiconducting carbon quantum dots (CQDs) and nanodiamonds to insulating graphene oxide (GO).^9,10 A summary of different types of CBNs will be provided in the following section. Furthermore, as-prepared CBNs can also be functionalized with different types of molecules and functional groups through either covalent or noncovalent interactions.⁴ A series of functional properties of CBNs can be tuned by surface functionalization, including but not limited to biocompatibility, dispersibility, and surface reactivity. Due to this functionalization process, many modified CBNs can display low toxicity in biological systems and can be applied in many biomedical applications with minimal adverse effects.¹¹

Carbon-based nanomaterials (CBNs) have found pivotal applications in the realm of tissue engineering, a strategic approach aimed at repairing and replacing defective human tissues.^12,13 Within this domain, CBNs boast attributes such as high mechanical strength, biocompatibility, chemical stability, and electrical conductivity.¹⁴ Notably, the integration of CBNs into hydrogel matrices introduces a transformative dimension to their potential, especially when CBNs transition from being mere fillers to becoming the central component of the hydrogel structure.¹⁵

While there exists a breadth of literature reviewing the application of CBNs in biomedical sciences,^14–17 the novelty of our work lies in its emphasis on hydrogels where carbon-based nanomaterials serve as the primary matrix component, not just an ancillary filler. This distinction is pivotal, as traditional reviews often regard CBNs as secondary elements in polymer-based hydrogel matrices. Here, we underscore the significant advancements and challenges associated with these unique carbon nanomaterial-based hydrogels.

In this comprehensive review, we start by offering an overview of the CBN family, spanning from zero- to three-dimensional systems. This is followed by a presentation of the main findings related to the primary applications of CBNs in core areas of tissue engineering. Finally, we showcase studies that have prominently employed carbon nanomaterial-based hydrogels as scaffolds for tissue regeneration. Critical discussions on future directions, challenges, understanding action mechanisms, and interaction with diverse cellular systems round off our exploration. Our aspiration is that shedding light on the nuanced application of CBNs in hydrogel frameworks will catalyze further research and innovation in tissue engineering scaffolds.

Overview of Carbon-Based Nanobiomaterials

As discussed above, CBNs include a wide range of materials that can be classified by dimensionality from zero-dimensional (0D) CQDs, fullerenes and nanodiamonds, one-dimensional (1D) CNTs, to two-dimensional (2D) graphene, as well as their three-dimensional (3D) assemblies such as nanocarbon sponges and hydrogels (Figure 1). Despite their unique structures and geometrical shapes, many CBNs possess key features such as high mechanical strength and stiffness, the ability to interact with biomolecules such as nucleic acids and proteins, large surface area, and low cytotoxicity, which make them effective biomaterials for tissue engineering.¹⁸ In tissue regeneration, CBNs are usually used as either the matrix material or an additive in bioactive nanocomposites to improve their mechanical properties. Before reviewing the state-of-the-art applications of CBNs in tissue engineering, it is necessary to classify CBNs based on their structures and understand their physicochemical properties. Therefore, an overview of different types of bioactive CBNs is presented in this section.

Figure 1 Different carbon-based nanomaterials used in tissue engineering approaches are categorized by dimensionality from 0D to 3D.

Nanodiamonds (NDs)

Although graphite is the most thermodynamically stable form of carbon experimentally in its bulk state,¹⁹ this changes at the nanoscale because it includes a significant amount of surface energy. Especially in the dimension range smaller than 3–6 nm, tetrahedral hydrocarbons (higher diamondoids) exhibit greater stability than polyaromatic carbons, although the dangling sp³ bonds on the surface have to be either passivated by functionalization or stabilized by reconstruction into sp² hybridized carbons.²⁰ While a fixed structure cannot describe all nanodiamonds (NDs), a more general view can be considered as a nanoparticle of diameter 2–10 nm with an almost perfect diamond crystalline structure with the occasional presence of non-diamond carbon and nitrogen, with surface termination by a graphitic shell or amorphous carbon, saturated by oxygen-containing functional groups such as O=CH₂, O–H, O–CH, O–C=O, –COOH, –C–O–C–, –C=O.^21,22 Nanoscale diamond particles were obtained by detonation (explosion synthesis) in the USSR in the 1960s,²³ but its usual production started in the late 1990s after a series of essential breakthroughs.¹⁰ NDs (4–5 nm) are usually synthesized by detonating explosive molecules in a closed chamber filled with water or inert gas and they are formed by homogeneous nucleation of the supersaturated carbon vapor by condensation and crystallization of liquid nanocarbon at this elevated pressure and temperature in this process.

NDs synthesized in this way contain plenty of impurities and are washed thoroughly with oxidizing agents such as mixtures of acids (solution method) or oxygen plasmas (gaseous method). NDs are more accessible to functionalize without compromising the core structure when compared to other graphitic nanoparticles. Generally, NDs purified by acid or oxygen plasma possess –OH and –COOH groups on the surface, which can undergo further functionalization with acyl chlorides yielding long alkyl chain terminated NDs²⁴ and by silanization.²⁵ Additionally, NDs can be modified by its superficial graphitic carbon through cycloaddition²⁶ and diazonium reaction.²⁴

Raman and infrared (IR) spectroscopies provide valuable information about NDs’ phase, composition, and surface terminations. They can also identify the nitrogen defects present in NDs, which leads to fluorescence properties exploited in quantum computing,²⁷ high-resolution magnetic sensing,²⁸ fluorescence resonance energy transfer,²⁹ and medical imaging.³⁰ These photoluminescent NDs, synthesized at high temperature and pressure, possess a small size (3–50 nm), the same scale of magnitude that other materials used in tissue engineering scaffolds, elevated photostability, bright multicolor fluorescence, comparable to semiconductor quantum dots with much better biocompatibility, non-toxicity effects, and rich surface chemistry, all suitable properties for in-vivo imaging applications.³¹ Apart from optical properties, NDs exhibit robust mechanical properties, high thermal conductivity, negligible conductivity, chemical stability, high surface areas, and tunable surface reactivity.³² In addition to the fact that NDs can self-assemble,³³ they can also bind with various molecules, such as proteins, nucleic acids, and antibodies. This makes NDs very useful for a wide range of applications in lubrication, tribology, bioimaging, sensing, protein mimicry, drug delivery, tissue engineering, and filler material for nanocomposites.³⁴ The surface properties of the NDs, such as topography, wettability, and surface charge, determine the binding capacity and the surface interaction mechanism. For example, oxygen-terminated NDs (O–NDs) exhibit better adhesion to human neural stem cells when compared to hydrogen-terminated NDs (H–NDs).³⁵ The cytotoxicity of NDs can also be altered by suitable functionalization. For example, NDs with the surface, dominated by C=O, –OH, and –NH₂ groups, show no cellular toxicity with several cell lines.³⁶

Properties such as biocompatibility, mechanical property, stability, and chemical inertness, of NDs, make them a useful candidate for tissue engineering, especially for bone and neural tissues. Also, its surface tunability through surface charge and surface functional group modification makes it a carrier of practically any type of biomolecule.³⁷ Nanodiamond coatings on biomedical implants can be achieved through scalable and reproducible synthetic methods, such as CVD, whose parameters can be changed to control the topography and surface properties of the NDs.³⁸ The tunable surface hydrophilicity can also increase the osteoblast’s efficiency (a cell that secretes the matrix for bone formation) adhesion of the implant, making it more capable of bone tissue regeneration.³⁹ When combined with other bioactive materials, such as hydroxyapatite, NDs can enhance their osteoinductive properties.⁴⁰ Apart from bone tissue regeneration, NDs have also been used in neural tissue regeneration.⁴¹ Unlike osteoblast, NDs’ surface chemistry does not have much effect on neural growth, indicating that it involves more physisorption of cells on the NDs nanoparticles. Also, due to selectively enhanced neural tissue growth on NDs, microscale patterned NDs created by photolithography and etching can create patterned neural networks.⁴² In addition to using NDs as cell-adhering substrates, they have been used in coating prosthetic implants to improve their tribological properties and decrease their metal ion leaching behavior.⁴³

Owing to their excellent hardness and surface functionality, NDs are also used as nanofillers of polymer composites, generally created by electrospinning, to make tissue scaffolds.⁴⁴ In addition to their potential as nanofillers, NDs can work as a delivery platform for tissue cells, giving rise to multifunctional bioactive scaffolds capable of releasing therapeutic biomolecules.⁴⁵ NDs-polymer composites exhibit homogeneity, mechanical and thermal stability, and chemical resistance with a capacity to load a large number of biological structures onto their surface. Therefore, they can be used in tissue engineering, implants, stents, biosensors, scaffolds for tissue engineering, and other biomedical devices.⁴⁶ These polymers can be woven in mats and are suitable for wound healing applications because of their improved mechanical properties and hydrophobicity upon NDs incorporation.⁴⁷ In addition, advanced multifunctional NDs-based nanocomposites, such as silver-loaded polycation functionalized NDs, have been used as filler in dental resin since its hardness and flexural strength increase due to the presence of NDs when compared with pure resins, whereas the presence of silver enhances the bactericidal property.⁴⁸

Fullerenes

C₆₀-Buckminsterfullerene, the most symmetrical molecule and the first symmetrical carbon nanomaterial, has a spherical cage-like structure formed by sp² hybridized carbon. In 1996, the Nobel Prize in chemistry was awarded to Richard E. Smalley, Robert F. Curl, and Harold W. Kroto for its discovery.⁴⁹ The general formulae of fullerenes can be written as C_2n+20, where n represents the number of hexagons. For example, C₆₀ possesses 20 hexagons and 12 pentagons, forming a truncated icosahedron with a diameter of approximately 1 nm with very high symmetry containing 30 twofold axes, 20 threefold axes, and 12 fivefold axes. C₆₀ has been well characterized by Raman spectroscopy, UV–visible and IR spectroscopy, and C₁₃-nuclear magnetic resonance.⁵⁰ After its accidental discovery, its first large-scale synthesis was achieved in 1990, in which graphite was electrically heated in a helium atmosphere at low pressure in order to evaporate and recondense as soot. The soot was dispersed in organic solvents and separated to isolate C₆₀ crystals.⁵¹ Subsequently, C₆₀ was synthesized similarly by vaporizing other carbon precursors, eg, coal, or by other evaporation techniques (eg, arc-evaporation, laser ablation, and radio frequency plasma).⁵² Other important synthetic routes include the incomplete combustion of benzene in oxygen⁵³ and microwave techniques.⁵⁴

There has also been ample research on fullerenes-containing polymers or polyfullerenes. These are synthesized via the covalent linkage of fullerene units,⁵⁵ organometallic fullerenes,⁵⁶ and cross-linked polyfullerenes.⁵⁷ One- or two-dimensional self-assembled fullerene-based nanostructures, such as C₆₀ nanowhiskers⁵⁸ and C₆₀ hexagonal thin crystalline nanosheets,⁵⁹ are considered fullerene-based nanostructures. Other fullerene composites can be designed by exploiting their charge transfer ability. For example, a hybrid hexagonal nanosheet containing C₆₀ and ferrocene has been built using donor-acceptor interactions.⁶⁰ A silver-fullerene nanocomposite was also prepared by synthesizing silver nanoparticles immersed in the C₆₀ matrix by thermal co-deposition.⁶¹

Although the chemical and physical properties of C₆₀ show great potential towards biological applications, its inherent hydrophobicity and water-insolubility need to be addressed by adequate functionalization.^62,63 In addition, surface functionalization can change the carbon hybridization from sp² to sp³, releasing strain and making the fullerenes more stable. Interestingly, surface functionalization also reduces the cytotoxicity of fullerenes.⁶⁴ The double bonds present in fullerenes can be utilized to facilitate functionalization in order to generate surface-modified fullerenes, such as amine (–NH₂), hydroxyl (–OH), and carboxyl (–COOH) fullerenes. Another approach to functionalizing fullerenes is via the utilization of their electron-deficient nature in order to promote cycloaddition reactions.⁶⁵ Other attempts to overcome the hydrophobicity of fullerenes have been microencapsulation between special carriers such as cyclodextrins⁶⁶ or calixarenes⁶⁷ and suspension with the help of co-solvents. For example, stepwise and slow addition of solvents with increasing polarity, such as benzene, tetrahydrofuran, acetone, then water, followed by the evaporation of all the non-aqueous, low-boiling solvents, can lead to water-soluble C₆₀.⁶⁸ Attempts for dissolving fullerenes include the covalent attachment of water-soluble polymers⁶⁹ or surfactants.⁷⁰

When C₆₀ is excited (visible light), it rapidly decays, producing several reactive oxygen species (ROS) in the environment through an electron transfer pathway. These ROS are responsible for the antibacterial activity of fullerenes and their cytotoxicity.⁷¹ However, the toxicity of fullerenes depends on the preparation method as well as the chemical modification. Cytotoxicity induced by C₆₀ in vitro tests with alveolar macrophages was found to be quite low compared to other carbon nanostructures, such as single-walled carbon nanotubes (SWCNTs) and multi-walled carbon nanotubes (MWCNTs).⁷² In addition, due to dissimilar fullerene-cell wall interactions, C₆₀ has more effect on gram-positive bacteria than gram-negative ones.⁷³ This interaction depends on the surface electrostatic nature of fullerenes. For example, hydroxyl (–OH), carboxyl (–COOH), and amine (–NH₂) functionalized fullerenes show a different effect on E. coli and S. oneidensis.⁷⁴ C₆₀ can also scavenge free radicals without being consumed due to the presence of several double bonds within the fullerene cage, and it is called a “free radical sponge”.

Although the present work focuses on tissue engineering, it is worth highlighting a series of biomedical applications of Fullerene. Polyhydroxylated fullerenes, known as fullerenols, are used for cancer treatments due to their non-toxicity and biocompatibility.⁷⁵ In order to prepare multifunctional biomedical systems, a combination of C₆₀ and iron oxide nanoparticles are used in photodynamic therapy, drug delivery, and magnetic resonance imaging (MRI).⁷⁶ More interestingly, C₆₀ exhibits antiviral activity against human immunodeficiency virus (HIV) since C₆₀ can be introduced into the catalytic cavity of HIV protease, which is the primary enzyme of HIV.⁷⁷ Due to their hydrophilic nature, –OH, –COOH, and –NH₂ functionalized fullerenes can act as effective mediators between biosensor electrodes and recognition sites and improve the efficiency of the biosensors.⁷⁸ Due to their radical scavenging properties, fullerenes can also act as neuroprotective agents.⁷⁹ Gadolinium (Gd), a metal used for MRI, generates several discomforts in patients; however, endohedral Gd-fullerenol, which is less toxic due to its biocompatibility, has been used as an MRI contrast agent.⁸⁰ Because of its free radical scavenging properties described above, fullerenes can also be used in moisturizers and acne-removing creams.⁸¹

Adequate functionalization of fullerenes can lead to water solubility as well as other favorable properties, such as fluorescence or cell selectivity, which can open up the possibility of using fullerene (itself or with any other material) as a tissue scaffold material.⁸² The use of fullerene in bone tissue engineering has been done in recent years.⁸³ Fullerene-coated carbon nanofibers-based microarrays, prepared using a metallic nanomask, could increase the adhesion and proliferation of osteoblastic MG-63 cells.⁸⁴ Pure fullerene (C₆₀) films can be deposited following a similar technology which showed enhanced human osteoblast-like MG-63 cell regeneration, rendering it a promising material in bone tissue engineering, especially as a bioactive coating of bone implants.⁸⁵ Fullerene molecules can also be combined with other materials, such as compounds of Ti, Co, or Ni, to form binary fullerene-metal composites with promising biomedical applications.⁸⁶ For example, C₆₀/Ti composite films were fabricated by co-deposition through the molecular beam epitaxy method and utilized in enhanced human osteoblasts-like MG-63 or U-2 OS cell growth.⁸⁷ Apart from bone tissue, fullerenes can be used in adipose tissue engineering as highly hydroxylated fullerene can inhibit the oxidative stress in adipose tissues through antioxidation, owing to its free radical scavenging properties.⁸⁸

Carbon Quantum Dots (CQDs)

CQDs are amorphous or crystalline carbon quasi-spherical nanoparticles of size below 10 nm, with predominantly graphitic or turbostratic sp² hybridized carbon with diamond-like sp³ hybridized carbon insertions. This unique structure may contain 5–50% oxygen, mainly on the surface as -COOH groups, making CQDs soluble in water, with possibilities of further functionalization and surface passivation, thus altering their physicochemical properties.^89,90

Graphene quantum dots (GQDs) constitute a variation of CQDs and consist of graphene sheets with lateral dimensions less than 100 nm and a few-stacked layers (1–10 layers).⁹¹ Similar to graphene, GQDs have a large surface area with a π–π conjugated network with –COOH and –OH groups functionalized at the edges. The excellent electron donating and accepting properties of GQDs make them good candidates in photo-detection and solar cell applications, whereas their good conductivity makes them useful in electrochemical biosensors.⁹² In addition, both CQD and GQDs exhibit better chemical and photo-inertness with tunable luminescence, low cytotoxicity, and good biocompatibility compared to toxic inorganic metal oxide-based semiconductor quantum dots, thus making them a better choice for bio-applications.⁹³

CQDs can be prepared mainly by the top-down and bottom-up approaches. While the top-down approach could be more attractive because of the abundance of raw materials, large-scale production, and the inherent oxidative reaction conditions leading to surface functionalization, it has some disadvantages, such as low yield and less control over the structure of the final products. These top-down approaches can be further classified as chemical or physical methods. The first discovery of CQDs was reported during the purification of SWCNTs through electrophoresis in 2004.⁹⁴ Subsequently, CQDs were obtained by electrochemical methods using graphite as electrodes in an alkaline or aqueous medium.⁹⁵ In addition, graphene electrodes have been used to produce GQDs with 1–3 graphene layers.⁹⁶ Combustion of carbon-rich precursors and the subsequent purification can result in CQDs.⁹⁷ However, monodispersed CQDs can be synthesized using molecular sieves, such as mesoporous silica or porous carbon as support.⁹⁸ Acid-oxidation of carbon-rich precursors, such as coal, has also prepared GQDs.⁹⁹ Alternatively, hydrothermal conversion and microwave/ultrasonic irradiation of carbon-rich green precursors, such as carbohydrate molecules, can produce a clean synthesis of CQDs.^100,101 Some other methods, such as ozonation, H₂O₂ mediated photo-Fenton reaction, and oxygen plasma treatments of GO, have also been used to synthesize CQDs and GQDs. Apart from these chemical methods, CQDs can be obtained by physical treatments such as arc discharge, laser ablation, and plasma treatments of carbon targets at high temperature and pressure conditions. On the other hand, while the bottom-up methods can control the shape, size, and properties of synthesized CQDs, the complexity of the procedure is challenging, and the general hydrophobic synthetic condition may lead to agglomeration of the resultant CQDs. One example of this approach is Ruthenium catalyzed cage-opening of fullerenes, where structural transitions between graphene and fullerene are utilized to obtain geometrically well-defined GQDs.¹⁰² Other bottom-up approaches, such as cyclodehydrogenation of polyphenylene precursors, stepwise oxidative condensation reactions of carbon precursors, such as glucose can be used.¹⁰³ These top-down and bottom-up approaches can induce size-control and band-gap tuning of the resulting CQDs since these two are responsible factors for their optical properties.

CQDs have also been prepared from biocompatible and natural precursors such as citric acid due to their cost-effectiveness, flexible designability, and straightforward synthesis routes.¹⁰⁴ However, depending on the applications, the synthesis strategy could be modified to achieve surface functionalization, such as amine or aryl functionalization or polyethylene glycol passivation.¹⁰⁵ The cytotoxicity of CQDs varies as a function of their surface molecules.¹⁰⁶ Furthermore, different effects on the cancer cell stages have been reported depending on the surface physicochemical characteristics of modified CQDs with neutral, anionic, and cationic surface functionalities.¹⁰⁷

Another way to modify CQDs’ properties is by doping with other elements, such as nitrogen¹⁰⁸ or fluorine.¹⁰⁹ Novel, non-toxic N-doped chitosan-based CQDs have been synthesized using amino acids where the quantum yield (QY) can be varied by changing the amino acid.¹¹⁰ Biocompatible red-emitting magnesium–nitrogen-doped CQDs were obtained by carbonization of a leaf extract.¹¹¹ CQDs are essential for their photoluminescence (PL) properties, which are tunable by varying the size of the CQDs, utilizing quantum confinement in conjunction with surface modifications to generate emissive trap sites. The PL properties vary with their size; the PL wavelength increases with the increasing size of CQDs as the band gap decreases. However, CQDs show strong electrochemical luminescence (ECL), which is solely a surface-state phenomenon. So, it had been surmised that the most intense PL bands of CQDs are due to their core inherent band gap, which is size-dependent, but the less intense PL bands may be due to surface traps. The CQDs show stable PL and ECL responses over time, and their QY may vary with the synthesis method and the surface chemistry involved. One of the disadvantages of CQDs is their low QY (often less than 10%). However, passivation with organic polymers,¹¹² doping, and reducing the CQDs can increase the QY to 50%.¹¹³

CQDs’ optical and electronic properties can be modified by changing their assembly in the solution or onto the substrate. For example, CQDs are assembled in a plane (face-on) or out-of-plane (edge-on) fashion by electrophoresis or other guiding techniques.¹¹⁴ CQDs can also show upconverted PL (UCPL), which is a multiphoton process involving low-energy photons (in the visible or IR region), thus providing a new way to develop novel photocatalysts combining CQDs and other materials. For example, for TiO₂/CQDs systems, CQDs absorb visible light and then emit in shorter wavelength via up conversion, which excites TiO₂ to generate electron-hole pairs that give rise to ROS, capable of dissociating larger organic molecules, eg, harmful dyes. This can even be exploited in photovoltaics.¹¹⁵ Some metal ions and other compounds, even some biomolecules, such as human immunoglobulin, can quench the PL of CQDs by facilitating non-radiative electron/hole recombination via an effective electron transfer method; thereby, CQDs can act as a sensor for those biomolecules.¹¹⁶ Gold-CQD composite materials exhibited surface-enhanced Raman scattering (SERS) for rhodamine 6G dye molecules due to their improved adsorption on the CQDs surface.¹¹⁷

Because of non-toxicity and excellent PL properties, CQDs are an attractive candidate for in vivo and in vitro imaging and nanomedicine applications.^118,119 CQDs can be used as photosensitizers for photodynamic therapy.^120,121 Smart multifunctional biomaterials can also be synthesized utilizing the unique properties of CQDs. For example, bioactive CQD/organosilica nanospheres exhibit visible-light emission for optical imaging, Near-Infrared photothermal activity used in photothermal therapy, and loading capacity for controlled drug delivery.¹²² A multifunctional core-shell structure composed of olive oil, Fe₃O_4, porous TiO_2, and GQDs can be used in oil-soluble drug delivery as well as magnetic and fluorescence imaging.¹²³

CQDs have also found remarkable applications as a tissue engineering material due to their engineered PL properties, biocompatibility, tunable surface functionalities, and cost-effective synthesis.¹²⁴ Primarily, the enhancement of mechanical properties in bone regeneration scaffolds is attributed to efficient cellular interplay and the process of forming cross-links.¹²⁵ For example, CQDs, combined with hydroxyapatite, show significantly increased cell proliferation, the activity of alkaline phosphatase as well as mineralization.¹²⁶ Another attractive factor is the cheap and easy fabrication procedure. For example, a biological scaffold with enhanced bone regeneration activity containing CQDs, hydroxyapatite, and polyurethane had been synthesized from an eco-friendly one-pot hydrothermal synthesis employing sustainable, renewable bio-based starting materials: calcined eggshell and the water-based extract from a plant, C. esculenta corm (taro).¹²⁷ Besides enhancing the mechanical properties, CQDs improve cell adhesion, proliferation, and anti-bacterial and anti-tumor properties.¹²⁸ CQDs-based nanomaterials are also used in nerve tissue regeneration.¹²⁹ Various metals, such as gold, silver, tin, zinc, and gallium, can be doped in CQDs through simple sonochemical processes, and the resulting doped CQDs have shown excellent biocompatibility against neuronal cells even in relatively higher concentrations.¹³⁰ For example, gallium doped CQDs coated glass substrate was registered to be a very good supporting material for neuronal cells differentiation and growth compared to bare glass substrate.¹³¹ Also, γ-Fe₂O₃/CQDs magnetic nanoparticles were synthesized which, along with high fluorescence and very good biocompatibility, show efficacy to various neuronal manipulations, including cell labeling and magnetic force-driven controlled cell motility.¹³²

Further details on the applications of CQDs, especially pertaining to their role in tissue engineering and regenerative medicine, can be found in two recently published reviews.^133,134

Carbon Nanotubes (CNTs)

CNTs consist of one-dimensional (1D) tubular structures, which can be constructed by rolling up sp²-hybridized single- or multi-layered graphene sheets into a hollow, seamless cylinder. The rolling direction can be defined by a chiral vector, a pair of integers (n,m), and CNTs can be either metallic or semiconducting, depending on the tubes’ chirality.^135–137 Experimentally, the synthesis of both SWCNTs and MWCNTs can be achieved by several methods, including laser ablation,¹³⁸ arc discharge, and chemical vapor deposition (CVD). In the arc discharge process, CNTs are produced by creating an electrical arc between two graphite electrodes in an inert atmosphere.¹³⁹ The discharge at the graphite anode generates a high temperature that sublimates graphite and leads to the deposition of CNTs on the cathode. This method usually yields MWCNTs, but it has been found that adding a metal catalyst in the anode and controlling the temperature gradient between the electrodes can also yield SWCNTs.^140,141 An alternative method is to apply a laser pulse to a target containing graphite and metal catalysts, which leads to a similar effect as the electrical arcing and ablates the graphite at a high temperature to produce SWCNTs and MWCNTs.¹⁴² Nowadays, a commonly used technique for the scaled-up synthesis of CNTs is catalytic Chemical Vapor Deposition (CVD).¹⁴³ In the CVD method, carbon-containing precursors (eg, methane, acetylene, or toluene) flow to the hot zone of a furnace inside a tube reactor. The precursor decomposes in the presence of transition metal catalysts (eg, Ni, Fe, Co, and Mo).¹⁴⁴ The resulting morphologies (length, diameter, and crystallinity) of CVD-grown CNTs are controlled by temperature, precursor chemistry, precursor/carrier gas flow rates, catalyst, and growth time, among other experimental parameters.¹⁴⁵ CVD has been reported to produce CNTs at gram-scale,¹⁴⁶ and the individual tube length is usually much larger than the tube diameter, ranging from micrometer- even to meter-scale.¹⁴⁷ The as-synthesized metallic and semiconducting CNTs have been employed as high-performance interconnects in integrated circuits and nanoelectronics such as field-effect transistors.^148,149 The Young’s modulus and strength of high-quality CNTs are measured to be ~1 TPa and tens of GPa, respectively, higher than steel. This leads to CNTs in nanocomposites, where CNTs are employed as fillers to reinforce the mechanical strength and stiffness of the polymer matrix.¹⁵⁰

The obtained CNTs after synthesis generally present a wide range of impurities such as amorphous carbon, graphitic nanoparticles, fullerenes, and particles from catalysts, which can be a problem during the use in tissue engineering, so it is necessary to improve the actual purification techniques besides development of new methods.¹⁵¹ Toxicity is another challenge in the application of those materials. CNTs show more significant toxicity than most other CBNs, second only to graphene, justifying the requirement of new treatment strategies to modify their length, surface and properties.¹⁵²

Carbon Nanofibers (CNFs)

CNFs are linear filaments of sp² hybridized carbon. Unlike conventional carbon fibers with a micrometer or larger diameters, CNFs are characterized by their much smaller diameters (~ 100 nm).¹⁵³ In addition, CNFs should also be differentiated from CNTs, as CNFs can be viewed as stacks of carbon nanocones along the fiber axis, which do not have perfect structural configurations compared to uniform tubular CNTs. CNFs can be synthesized by a catalytic CVD process similar to the growth of CNTs, or by high-temperature carbonization of electrospun polymer nanofibers such as polyacrylonitrile (PAN).^154,155 The as-synthesized CNFs exhibit high mechanical strength and modulus, and they are usually considered biocompatible as CNFs are high-purity carbon with low densities of impurities and functional groups. Thus, CNFs can be assembled into 3D web-like structures as scaffolds for bone tissue regeneration.¹⁵⁶

Graphene and Its Derivatives

Since the successful isolation and identification of graphene in 2004, this two-dimensional (2D) form of sp² hybridized carbon has gained tremendous research attention due to its unique properties, including one-atomic-layer thickness, remarkable mechanical properties (Young’s modulus of 1 TPa, and strength of 130 GPa), along with robust electrical and thermal conductive properties.^140,157 Furthermore, GO can be synthesized on a large scale through partial oxidation and exfoliation of graphite crystals.¹⁵⁸ This technique results in GO sheets that can be dispersed in water, presenting numerous oxygen-based functional groups on their surface. The synthetic GO materials can be further reduced to remove most surface functional groups, forming reduced graphene oxide (rGO) with properties akin to pristine graphene.^159,160

Although the excellent structural and mechanical properties suggest that graphene and its derivatives described above possess the potential to be incorporated into scaffolds for tissue regeneration applications, the unmodified graphene, GO, and rGO can improve their performance by surface functionalization or modification.^14,125 Surface functionalization is needed to mitigate the biocompatibility issue of graphene-based nanomaterials. Two main types of surface functionalization, covalent functionalization and non-covalent functionalization, are commonly applied. Covalent functionalization is usually achieved by reacting with oxygen functional groups on GO and rGO. Examples of covalently functionalized groups include aliphatic amines and amino acids,¹⁶¹ polyethylene glycol (PEG),¹⁶² and poly(vinyl alcohol) (PVA).¹⁶³ Alternatively, non-covalent functionalization relies on the non-bonding interactions between 2D sheets and molecules, such as π-π, hydrophobic and electrostatic interactions.^164,165 Both covalent and non-covalent functionalization are reported to reduce the cytotoxicity of graphene and its derivatives by attaching proper functional groups and/or molecules.¹¹

Due to GO’s physicochemical versatility, it has recently been applied as a biomaterial for tissue engineering and drug delivery. The chemical structure of this compound, including carboxyl (−COOH), hydroxyl (−OH), and epoxy (−O−) moieties, increases its hydrophilic properties, which improves the bioavailability of this biomaterial.¹⁶⁶ These plentiful oxygen-based functional groups can also serve as sites for functionalizing GO with a range of biomolecules, making possible the use of this graphene in drug delivery applications.¹⁶⁷ GO is also an excellent candidate to be applied in connective tissue regeneration once it presents a sizeable π-conjugated structure and surface area (890 m²/g) that shows the potential to absorb proteins and adhere to cells. In addition, this vast surface area allows the GO to create a structure for managing stem cell activity without being invasive, contributing to the liberation of potent biological elements and transport of growth factors, DNA, and man-made proteins that can influence stem cell differentiation and multiplication.^168–170 The electronic configuration of GO also facilitates additional chemical alterations that, together with maintenance of the sp² bonding lattice, endows this compound to be applied in cardiac and nerve regeneration.¹⁷¹ Regarding GO’s mechanical properties, its robustness contributes to a matrix that can resist mechanical forces during bone and cartilage regeneration [165]. Therefore, GO exhibits a range of advantageous characteristics, such as exceptional bio-compatibility, substantial drug-holding capacity, electric conductivity, along with adjustable size and form.¹⁷²

Carbon-Based Nanomaterials as Scaffolds for Tissue Regeneration

In tissue engineering, the purpose of scaffolds is to mimic the structure and function of the native extracellular matrix (ECM) to promote an optimal environment for cell adhesion, migration, proliferation, and differentiation and stimulate the growth of new tissue.¹⁷³ Although different human tissues have distinct characteristics and specific needs within tissue engineering, in general, the design of an ideal scaffold should consider physicochemical and biological characteristics, including biocompatibility and biodegradability in a living organism, bioactivity, mechanical characteristics, microarchitecture, and porosity.^174,175

Progress in the use of nanotechnology within the field of tissue engineering have revolutionized regenerative medicine, resulting in the synthesis of innovative scaffolds. In particular, due to their special chemical, physical, mechanical, electrical, optical, and biological properties, CBNs have played a prominent role in developing these scaffolds, and their application in various human tissues has been investigated.

Building upon the detailed discussions presented in the preceding section regarding individual carbon-based nanomaterials, it is imperative to provide a synthesized perspective for readers. To that end, we have consolidated the primary positive characteristics and challenges associated with each of these carbon-based nanomaterials concerning their application as scaffolds for tissue engineering, aimed at tissue regeneration. This summary is presented in Table 1, offering a succinct comparison that underscores the potential and hurdles of each material within the context of tissue engineering.

Table 1 Overview of Selected Carbon-Based Nanomaterials Highlighting Their Key Advantages and Challenges for Use as Scaffolds in Tissue Engineering

Carbon-Based Nanomaterials	Advantages for Scaffold Use in Tissue Engineering	Challenges for Scaffold Use in Tissue Engineering
Carbon Quantum Dots (CQDs)	Superior biocompatibility offering safer cellular interactions; Distinctive optical properties facilitating cell tracking and imaging; Versatile surface functionalization enabling targeted drug delivery	Variability in synthesis leading to inconsistent properties; Uncertainties surrounding long-term in vivo behavior.
Fullerenes	Strong radical scavenging, offering protection against oxidative stress; Demonstrated biocompatibility in controlled doses; Potential as drug delivery vehicles due to hollow structure.	Potential for bioaccumulation leading to long-term effects; Non-specific interactions can interfere with cell signaling.
Nanodiamonds (NDs)	Excellent biocompatibility making them suitable for various biomedical applications; Robust mechanical properties enhancing scaffold strength; Functionalizable surface for drug delivery or protein attachment.	Tendency to aggregate, potentially influencing cell behavior; Challenges in uniformly dispersing within polymer matrices.
Carbon Nanotubes (CNTs)	Exceptional mechanical strength enhancing scaffold robustness; Conductive properties beneficial for electrically active tissues (eg, cardiac, neural); Potential to guide cell growth due to aligned structures	Raw CNTs can pose toxicity; functionalization required for biocompatibility; Issues with dispersion in aqueous media and potential for aggregation
Carbon Nanofibers (CNFs)	Favorable biocompatibility promoting cell adhesion and proliferation; Mechanical properties mirroring natural tissue extracellular matrix; Amenable to fabrication processes like electrospinning	Heterogeneity in production processes leading to variable properties; Integration and interface challenges with other biomaterials
Graphene	Outstanding mechanical and electrical properties offering multi-functional scaffold applications; Large surface area beneficial for cell adhesion and nutrient transfer; Flexibility in functionalization for specific tissue types	Potential cytotoxicity related to sharp edges or debris; Reproducibility challenges in producing large, defect-free sheets

The following topics summarize the recent and main findings concerning the most common applications of CBNs in tissue engineering (Figure 2).

Figure 2 Schematic illustrating the application of carbon-based nanomaterials in tissue engineering. In order to generate new tissues and/or promote the regeneration of body parts (such as heart, skeletal muscle, bone, and articular cartilage), cells are grown on carbon-based nanomaterial scaffolds, promoting an environment in which cells can adhere, migrate, proliferate and stimulate the tissue formation. In addition, mechanical and/or biochemical signals can be added to improve cell differentiation and the growth of neotissue.

Bone Tissue Engineering Applications

Bone is a mineralized tissue with a hierarchical structure formed by cells and an ECM that consists predominantly of water, collagen (mainly type I), and a calcified matrix in which hydroxyapatite (HAp) is the most abundant component. As a fundamental member of the human musculoskeletal system, bones play an essential role in the mechanical support and movement of body segments, in addition to protecting organs, maintaining the homeostasis of key electrolytes, and hosting the bone marrow.^176,177

Unlike other human tissues, bones exhibit a high level of regeneration and self-repair, and most of the time, Bone damage and breaks recover without the development of scar tissue.¹⁷⁸ However, for fractures or large bone defects, bone healing fails. Thus, many people require skeletal reconstruction or bone defect replacement caused by conditions such as high-energy trauma, bone tumor resection, congenital diseases, and bone infection. Accordingly, these bone defects are managed based on bone graft, the second most commonly transplanted human tissue (after blood transfusion).^179,180

Although autologous bone grafting or autografts still are the gold standard for repairing large bone injuries, they carry limitations such as high morbidity at the harvesting site, secondary damages, and low availability. In addition, allografts and xenografts are also options available in clinical practice. However, these methods have disadvantages, including the risk of disease transmission and graft rejection.^176,181

In the search for better therapeutic strategies, tissue engineering has emerged as a potential approach for bone regeneration since it can overcome some limitations of bone grafts and enhance the healing processes of bone fractures and bone damage. More specifically, bone tissue engineering aims to induce the repair and regeneration of new tissues based on the synergistic interaction between cells, signals, and the biomaterial scaffold.¹⁷⁶ A suitable scaffold for bone regeneration should be biodegradable, biocompatible, bioactive, osteoconductive, and osteoinductive, and have optimal mechanical properties.^125,176

Carbon-based nanocomposites continue to be some of the most popular approaches to constructing scaffolds for bone regeneration. Their key benefits over other biomaterials include superior biocompatibility without harm to bone cells, biodegradability, robust mechanical characteristics, inherent antibacterial action, and remarkable impacts on gene expression and the multiplication of osteoblasts.¹²⁵ In this context, several CBNs have been investigated for their use in the field of bone tissue reconstruction, highlighting graphene and its derivatives and CNTs. Here we describe current progress and the most recent findings of these nanomaterials for bone repair applications. An even more detailed reading on the CBNs in bone tissue engineering applications can be found in two recently published comprehensive reviews.^124,125

Graphene itself has demonstrated its excellent ability to promote cellular osteogenic differentiation^169,182,183 and has been used as filler in nanocomposite scaffolds for bone regeneration. The conjunction of graphene with bioactive glass,¹⁸⁴ HAp,¹⁸⁵ and HAp with natural polymer¹⁸⁶ has been shown to significantly enhance the mechanical properties, proliferation, and cell differentiation of the scaffold.

However, the oxidized variant of graphene, known as GO, is more frequently employed in in tissue engineering applications. Besides the high adhesion ability, excellent osteogenic cell differentiation outcome, mineralization promotion, and improved mechanical strength, incorporation¹⁸⁷ into polymer-based scaffolds^188–191 demonstrates the potential of GO to improve the performance and interaction between biopolymers and bioceramics in composite scaffolds, by introducing strong electrostatic and π-π interactions.^192–194 In addition, similar to GO, the incorporation of rGO improves mechanical properties and promotes osteogenic differentiation (Figure 3), thus enhancing the performance of bioceramics-based^195–197 and polymer-based scaffolds.¹⁹⁸

Figure 3 Schematic representation of the rGO incorporation polymer-based scaffold to increase the mechanical properties and promotes osteogenic differentiation.

GO has shown potential as a useful platform for bone injuries, as it replicates both the chemical and mechanical attributes of bone. Moreover, it encourages the differentiation of stem cells, thereby aiding in the regeneration dependent on cells.¹⁶⁸ For example, Wang et al linked hydroxyapatite to GO, demonstrated adherence and growth of mouse-derived mesenchymal stem cells (MSCs), and stimulated the osteogenic gene osteocalcin expression, thus promoting differentiation of MSCs into bone.¹⁹⁹ Afterward, Fu et al incorporated poly(lactic-co-glycolic acid) (PLGA) into these compounds, which promoted the mechanical stability of the scaffolds, and induced alkaline phosphatase activity, gene expression related to osteogenesis, and mineral deposition.²⁰⁰ Boga et al documented that a fabricated scaffold, consisting of 3D cylindrical tricalcium phosphate (TCP) and alginic acid (AA) functionalized with GO, could offer a temporary structure for human osteoblast (hOB) cells to attach. The in vivo studies were realized in mice models. The findings revealed a satisfactory osteoinductive response following the non-covalent alteration of the graphene oxide (GO) surface using recombinant human bone morphogenetic protein 2 (rhBMP-2), a potent growth factor known for its remarkable capability to guide mesenchymal stem cells (MSCs) towards osteogenic specialization.²⁰¹ Another important study performed by Xue et al²⁰² demonstrated that graphene oxide (GO) facilitates the differentiation of bone marrow-derived mesenchymal stem cells (BMSCs) towards an osteogenic lineage. This effect is achieved by inducing the release of inflammatory cytokines and enhancing the expression of vascular endothelial growth factor (VEGF) pathway in human umbilical vein endothelial cells (HUVECs). These findings suggest that GO exhibits dual functionality in promoting both bone formation and the formation of new blood vessels, which are critical processes for successful bone regeneration. Thus, all these effects are correlated to the incorporation of graphene and GO, which simultaneously promotes differentiation and greatly improves the mechanical strength of biocomposites. A recent study by Wang et al aimed to evaluate a novel zwitterionic hydrogel incorporated with GO for bone tissue engineering.²⁰³ In vitro and in vivo tests showed that the hydrogel with GO greatly augmented the osteogenic differentiation of BMSCs in a dose-dependent manner, with 2 mg/mL GO being the optimum concentration. The incorporation of GO in the scaffold reduced its cytotoxicity and slowed down the release rate.

Another carbon-based nanomaterial of prominence in bone tissue engineering is CNT. Although it has already been investigated in isolation as the only component of the scaffold and has shown promising results in osteogenic differentiation, cell proliferation, and inhibition of osteoclast,^204–206 the main potential of CNTs for bone regeneration is as a reinforcing agent in nanocomposite scaffolds. Nevertheless, in addition to the increase in mechanical performance, even with the incorporation of small CNTs concentrations, CNTs have shown an important role in improving cellular attachment, proliferation, and promoting osteogenic differentiation, both in conjunction with polymers^207,208 or HAp^209,210 or in scaffolds based on mixtures of polymers with Hap.^211,212

Much less frequent in the literature than GO or CNT, fullerene-based scaffolds have also been investigated for bone tissue engineering. Although it has the disadvantages of only nonpolar carbon-carbon bonds, the ability to produce detrimental reactive oxygen species (ROS), and difficulty forming 3D porous scaffold,^124,213 some benefits have been reported with the use of fullerenes for bone regeneration, mainly regarding the orientation of the adhesion and growth of osteoblastic cells.^84,85,214 Fullerenes may also incorporate more hydrophobicity and roughness in a composite scaffold, increasing the ability to control the cell attachment.¹²⁵

Fullerene’s greater ROS production also is useful for osteoporosis treatment. For this reason, hydrophilic bisphosphonate groups like hydroxyapatite (applicable in osteoporosis) were coupled with fullerene, preparing a tissue-vectored compound, namely C60(OH)16AMBP.²¹⁵ This compound was able to contribute to osteoclast differentiation beginning with RANK-RANKL signals, as well as to help the treatment of osteoclast hyper-resorption on osteoarthritis.²¹⁶ Therefore, it has been proved that fullerene can reduce joint destruction and suppress bone resorption caused by osteoclasts²¹⁵ and that the fullerenols stimulate osteogenesis in bone marrow.²¹⁷

NDs represent an alternative form of carbon-based nanobiomaterial applied to bone tissue regeneration. As a result of its intense fluorescence, a scaffold with NDs could be used to monitor the scaffold behavior in vivo during bone tissue growth.²¹⁸ Furthermore, together with anti-inflammatory properties, studies have indicated that NDs promote cellular attachment and enhance cell proliferation, osteogenic activity, and mechanical properties when incorporated into polymeric matrices such as Poly-L-Lactic Acid (PLLA)²¹⁹ and Poly-Lactic-co-Glycolic Acid (PLGA),²²⁰ making this carbon-based nanomaterial a promising biomaterial for the management of large bone defects.

Further, the unique optical and physical properties have encouraged using CQDs for bone tissue application. In addition to applications in bone crack detection, targeted bone imaging, and drug delivery,^221–223 incorporating CQDs in polymers and bioceramics matrix has shown promising results in repairing bone defects. Among the main advantages of CQDs for bone regeneration described in the literature are the stimulation of osteogenic differentiation, good osteoblast adhesion and proliferation, low toxicity, simple fabrication methods, excellent mechanical properties, and the ability to improve the distribution of HAp in polymer matrix.^{125,128,224–226}

Although further investigations are required to comprehensively explore the complete capabilities of CBNs for bone regeneration, mainly with regards to more complex in vivo assays, understanding of the mechanisms behind biological and physical changes, and clinical translation challenges, evidence points to the area of bone tissue engineering as one of the most promising for applications of these unique materials, mainly due to its admirable ability to stimulate osteogenic differentiation and provide exceptional mechanical properties.

Articular Cartilage and Osteochondral Tissue Engineering Applications

Articular cartilage is a load-bearing and viscoelastic connective tissue that overlays the end surfaces of bones in a synovial joint, reducing shear friction forces, increasing lubrication, bearing and transferring load, and thus performing an essential role in the articular function.²²⁷ Unfortunately, articular cartilage’s avascular structure and poor metabolic activity reflect a limited regenerative capacity. Consequently, damages in articular cartilage caused by trauma or degenerative diseases are irreparable and result in early osteoarthritis, usually accompanied by chronic pain and disability. Osteoarthritis, reported as the most common joint disease, represents the second leading cause of physical disability, with a vast socioeconomic impact worldwide.^178,228,229

Although new approaches have been developed, the management options available in clinical practice today for cartilage injuries are deficient and have controversial results.^227,230 Thus, effective therapies and methods for treating articular cartilage defects remain one of the biggest challenges in orthopedics. In this context, tissue engineering methods have emerged as a potential approach in medicine regenerative for cartilage repair. Particularly, this strategy has been focused on stimulating the regeneration of cartilaginous tissue through the combination of scaffolds, cells, and bioactive substances (eg, growth factors).²²⁷ The effectiveness of the cartilage tissue engineering approach is closely related to the design of biomaterial scaffolds able to support, guide, and stimulate tissue growth. Considering that the most important role of articular cartilage is to resist mechanical loads and absorb shocks, the engineered scaffold for cartilage regeneration should be able to mimic the mechanical properties of the native cartilage.²³¹ In this sense, several researchers have developed scaffolds integrating natural or synthetic polymers with CBNs. Thus scientists, by using carbon-based materials, aim to produce scaffolds with sufficient mechanical strength and with conductive and chemical properties which facilitate the differentiation of MSCs towards a chondrogenic lineage by utilizing the electrical and mechanical cues provided by these materials.

Since CNTs have shown positive effects on chondrocyte adhesion, proliferation, and differentiation,^232–234 CNTs have been used to create reinforced nanocomposites for articular cartilage regeneration. Markowski et al reported a substantial increase in mechanical properties (Young’s modulus and tensile strength) in Polylactic acid (PLA)-based nanofibrous scaffold when small concentrations of CNTs were incorporated (1% wt) without experiencing cytotoxicity and genotoxicity (Figure 4).²³⁵ Incorporating CNTs in bovine articular cartilage decellularized matrix also demonstrated a significant improvement in the mechanical properties of the scaffold without negatively affecting its biocompatibility.²³⁶ Recently, Mirmusavi et al evaluated the potential of combining Poly 3-hydroxybutyrate (P3HB), silk, chitosan, and CNTs for cartilage tissue engineering. In addition to increased tensile strength, the scaffold containing CNTs showed better bioactivity properties and provided a suitable environment for chondrocyte adhesion and proliferation.²³⁷ It is clear that, although load-bearing characteristics of articular cartilage depend closely on its mechanical properties, it is a soft tissue that has its environment much better mimicked by hydrophilic polymeric matrices with a high water content such as hydrogels.²³⁸ Thus, despite all the unique properties of CNTs, mainly of mechanical strength, in articular cartilage tissue engineering, this type of CBN is evidently more linked only as a reinforcement filler and not as the main component of scaffolds.

Figure 4 The effect of the incorporation of CNT in PLA nanofibers on the mechanical properties (A) and cell viability (B), compared with pure PLA and PLA with gelatin (GEL). Adapted from Markowski J, Magiera A, Lesiak M, Sieron AL, Pilch J, Blazewicz S. Preparation and characterization of nanofibrous polymer scaffolds for cartilage tissue engineering. J Nanomater. 2015;2015:1–9. Creative Commons.²³⁵ **Statistical difference P < 0.01 when compared to control.

In the same way, due to its exceptional biocompatibility and impressive mechanical characteristics, graphene has also been applied in cartilage tissue engineering. For example, Liao et al synthesized a hybrid scaffold based on methacrylated chondroitin sulfate (CSMA), methoxyl poly(ethylene glycol)-poly(ε-caprolactone)-acryloyl chloride (PECA) and GO (Figure 5).²³⁹ The results demonstrated a scaffold with porosity, swelling behavior, degradation rate, compression modulus, and biocompatibility with cartilage cells, suitable to mimic the native ECM of cartilage. Furthermore, in in vivo assays, the scaffolds showed good results for the repair of full-thickness cartilage damage. Shamekhi et al researched chitosan-based scaffolds reinforced with GO nanoparticles. In addition to the enhancement in scaffold stiffness and surface roughness with increasing GO content, the authors also reported an increase in the proliferation and improvement of the morphology of human articular chondrocytes.²⁴⁰

Figure 5 Schematic representation showing the CSMA/PECA/GO hybrid scaffold with potential application in cartilage tissue engineering. To produce the scaffold, an aqueous solution containing PECA, CSMA, GO, and Ammonium persulfate (APS, used as the initiator agent) was heated at 60° C for 2 h. Then, after the incorporation of cells, the scaffold was inserted into a defect in rabbit articular cartilage, where it demonstrated an important regenerative capacity after 18 weeks. Reprinted from Liao J, Qu Y, Chu B, Zhang X, Qian Z. Biodegradable CSMA/PECA/Graphene porous hybrid scaffold for cartilage tissue engineering. Sci Rep. 2015;5(1):9879. Creative Commons.²³⁹

Although the mechanical properties of the scaffolds have not been carefully evaluated, Deliormanlı demonstrated the potential chondrogenic differentiation of mouse bone marrow MSCs (mBMSCs) in Polycaprolactone (PCL) scaffolds containing pristine graphene nanopowders. Furthermore, cells seeded onto the scaffolds with graphene showed greater cell viability than pure PCL scaffolds.²⁴¹ The authors suggest that graphene-containing scaffolds’ increased protein adsorption capacity can explain these results. Graphene can readily interact with a wide range of proteins that influence cell proliferation and differentiation when adsorbed on the surface.²⁴² In addition, graphene-containing scaffolds exhibit better electrical conductivity compared to pure PCL scaffolds. Greater electrical conductivity improves cell communication and increases scaffold adhesion and proliferation.²⁴³

Regarding NDs, Wang et al recently used functionalized NDs on their biodegradable scaffold for cartilage regeneration. Adding NDs in polyurethane (PU) composites demonstrated less toxicity, increased crystallinity, and a consequent considerable improvement in tensile properties.²⁴⁴ Although this single published study, NDs have also contributed in another way to treating defects in articular cartilage. Although it is not directly related to stimulating cartilage regeneration, it is worth mentioning that NDs have been used successfully as a long-term cell tracking tool for studying in vivo chondrogenesis without affecting cellular performance, such as proliferation and differentiation.²⁴⁵ Briefly, in this method, stem cells labeled with Fluorescent Nanodiamonds (FNDs) implanted in an animal model can be identified and quantified in the long-term, as well as detecting the chondrocyte-specific markers, such as type II collagen and aggrecan, by Fluorescence spectra of FNDs acquired using a Magnetically Modulated Fluorescence (MMF) spectrometer.²⁴⁶ Accurately tracking stem cells in vivo over the long term is one of the vital requirements in evaluating the efficacy and safety of stem cell treatments and one of the main challenges of regenerative medicine and tissue engineering.

About other types of CBNs less investigated for articular cartilage tissue engineering applications, newly doping CQDs into calcium phosphate has demonstrated the potential to positively affect the differentiation pathway and improve chondrogenesis.²⁴⁷ Concerning the fullerenes, although they have shown a capacity to inhibit inflammation and degeneration by down-regulation of chondrocyte catabolic activity,^248–251 to our knowledge, to date, no research has been published towards the fullerene-based scaffold for cartilage regeneration. Combining the therapeutic effects of fullerene for inflammatory joint conditions with the positive results of cell performance found in studies with other types of cells and applications^84,214,252 leads us to believe that fullerene may be a potential nanobiomaterial for use in the construction of scaffolds for articular cartilage tissue engineering, both as a filler and as a coating surface, however, for this, additional investigations specifically on articular cartilage, need to be carried out.

In many cases, the bone located just below the cartilage gets damaged, resulting in a defect known as an osteochondral lesion.²⁵³ For successful osteochondral tissue engineering, scaffolds should possess the capability to regenerate both the cartilage and the underlying subchondral bone, taking into account the distinct characteristics of each tissue, such as mechanical properties, chemical composition, and regeneration capacity.^254,255 Therefore, composites that combine more than one type of biomaterial, frequently polymers, and bioceramics, have been considered since scaffolding based on a single type of matrix has shown a series of limitations for osteochondral defects.^256–259

Recent studies, including CBNs on composite polymer-bioceramic scaffolds, have exhibited encouraging outcomes in the treatment of osteochondral lesions using these approaches. For example, Deliormanlı and Atmaca evaluated the biological behavior of osteoblastic MC3T3-E1 and chondrogenic ATDC5 cells to PCL/bioactive glass bilayered scaffold with graphene.²⁶⁰ For part of the articular cartilage of the osteochondral tissue, the authors used the graphene-containing PCL scaffolds, while the PCL/bioactive glass/Graphene layer was used to replicate the part of the subchondral bone. Higher cell viability, no cytotoxic effects, larger mineralized areas, and increased synthesis of glycosaminoglycans were observed on graphene-containing scaffolds compared with bare scaffolds, demonstrating the positive effects of graphene for this application. Encouraging findings have been achieved through the utilization of composite nanofibers consisting of Chitosan/Poly (vinyl alcohol) (PVA)/GO and biocompatible nanocomposite hydrogel films composed of chitosan/GO (CS/GO) for cartilage tissue engineering. These materials exhibit desirable toughness and strength properties.^261,262 Certain scaffolds, comprising a combination of poly (ethylene glycol) methyl ether-ε-caprolactone acryloyl chloride (MPEG-PCL-AC), chondroitin sulfate (CSMA), and GO, have displayed favorable attributes related to chondrocyte morphology, biocompatibility, and the in vivo restoration of cartilage defects.²³⁹ Two studies conducted by the same research group have shown promising results regarding adhesion and gene expression of both chondrocytes and osteoblasts on porous Poly-d, l-lactic Acid (PDLLA)/Nanohydroxyapatite/CNT scaffold.^263,264 The main findings of the studies suggest the potential of this nanocomposite for osteochondral tissue applications.

Finally, when it comes to joint cartilage regeneration, the recent trends in regenerative medicine are injectable hydrogels. This type of scaffold has the excellent ability to fill irregular tissue defects, requires minimally invasive procedures to be applied, and has reduced therapeutic costs.²⁶⁵ An ideal injectable hydrogel for articular cartilage should be able to preserve the viability of encapsulated cells during administration (low viscosity) and quickly polymerize in situ in a robust hydrogel with mechanical properties similar to native tissue, prerequisites that have not yet been fully resolved by current injectable hydrogels.^265,266 In this scenario, in the future, the incorporation of CBNs should help to overcome these challenges of injectable hydrogels for the articular cartilage and subchondral defects, especially the problems related to mechanical behavior.

Skeletal Muscle Tissue Engineering Applications

While muscle tissue has some regenerative ability, extensive injuries or muscle volume loss require tissue engineering treatments. The primary method used is to design a scaffold that can promote muscle cells’ growth, alignment, and differentiation.²⁶⁷ In this context, carbon nanomaterials are either used directly as the scaffold material or as an additive or coating for some other biocompatible polymer scaffold to harness the benefits of its remarkable electrical conductivity, mechanical strength, and unique surface structure and chemistry of CBNs.²⁶⁸ The effectiveness of various scaffolds incorporating graphene, GO, rGO, and CNTs has been widely studied, typically using the model of C2C12 mouse myoblast cells. These models have shown that CBNs can improve conductivity, myotube formation, and myoblast differentiation.²⁶⁹

It is crucial to mimic the environment of the natural ECM to promote the regeneration of skeletal muscle cells, so the biomaterial used for the scaffold must mimic the ECM’s behavior. Adding graphene or GO to other biomaterials can enable better emulate these properties [300]. Furthermore, owing to their exceptional characteristics such as superior electrical conductivity (0.6 S/m), ultra low density, and exceptional flexibility, graphenated materials demonstrate tremendous potential as ideal cellular substrates for muscle tissue engineering applications.¹⁸ In the case of skeletal muscle, GO-based compounds promote attachment, proliferation, and differentiation of its precursor cells.²⁷⁰ Investigations involving scaffolds incorporating GO for skeletal muscle regeneration have conclusively demonstrated notable improvements in cell viability, aspect ratio, and the expression of myogenic marker genes CD56, myogenin, and desmin. These advancements were notably superior when compared to control surfaces such as glass and collagen.²⁷¹ GO has been incorporated into several biomaterials already used in skeletal muscle engineering and shows a significant increase in the proliferation and attachment of C2C12 skeletal myoblasts, including GO/poly (lactic-co-glycolic acid, PLGA)/Collagen hybrid matrices,²⁷⁰ graphene oxide/polyacrylamide,²⁷² graphene-containing poly(ε-caprolactone) (PCL) nanocomposites.²⁷³

Experiments that culture skeletal muscle myoblasts directly grown on graphene and its derivatives have shown increased differentiation of myoblasts and growth rate of myotubes. Furthermore, patterning graphene allows for control of growth location and improved myotube alignment.²⁷⁴ Likewise, GO and rGO substrates show an improvement of 1.5 to 2-fold in most measures of myoblast growth over growth on glass. Ku and Park propose that surface oxygen improves the uptake of proteins from the growth matrix.²⁷⁰ Due to the good electrical conductivity of CBNs, it is possible to further improve the growth and formation of myotubes through electrical stimulation. By applying an 8V, 1Hz signal during growth, Ahadian et al found a doubling in the myotube coverage area by a combination of electrical stimulation of the myocytes and thermal reduction of GO over unstimulated and un-reduced GO, in addition to improvements in myotube length, and myogenic gene expression.²⁷⁵ In order to overcome the surface area and structural limitations of 2D materials, graphene can be incorporated into 3D scaffold structures. For example, 3D graphene foams and polyurethane foams coated by GO have been shown to promote myogenic growth while assuming a structure that can more easily mimic a natural cell environment.^276,277

Cardiac Tissue Engineering Applications

Cardiac disease is a leading worldwide cause of death, which places cardiac muscle tissue engineering as an important area of research.²⁷⁸ The importance of electrical signals to heart function and the large mechanical strain on cardiac tissue means that an ideal scaffold for tissue engineering should be conductive and contractile.²⁷⁹ Carbon nanomaterials such as CNTs and CNFs have been incorporated into polymer-based scaffolds to improve the scaffold’s electrical conductivity and mechanical properties and improve cardiomyogenesis. Furthermore, at the nanoscale, even individual nanotubes can direct the growth of cells and possess the potential to augment the differentiation of MSCs^280,281 (Figure 6). Ren et al demonstrated that a sheet of aligned CNTs improves cardiomyocytes’ alignment and intercellular coupling, leading to an increased synchronization in spontaneous beating. These same sheets were applied as electrodes for flexible pacemakers on neonatal rat hearts.²⁸² 3D scaffolds constructed with CNTs incorporated into gelatin hydrogels have shown improved contraction and maturation of cardiomyocytes over gelatin scaffolds. In addition, once grafted into a rat host, the CNTs migrate from the scaffold and incorporate into the myocardium structure without cytotoxicity and improving regeneration.²⁸³ Another major complication with cardiac tissue regeneration is fibrosis, scarring due to excessive collagen generation by fibroblasts. Scaffolds constructed from a combination of PDMS and CNTs, and from Collagen and carbon nanohorns both show a decrease in the proliferation of fibroblasts, which can reduce the scar tissue generated.^284,285

Figure 6 The conductivity of CNTs allows the differentiation of MSCs and promotes tissue architecture formation. Reprinted from Namgung S, Baik KY, Park J, Hong S. Controlling the growth and differentiation of human mesenchymal stem cells by the arrangement of individual carbon nanotubes. ACS Nano. 2011;5(9):7383–7390. Copyright © 2011 American Chemical Society.²⁸¹

In the cardiac tissue engineering field, the scaffolds have been meticulously engineered to encompass a diverse spectrum of mechanical characteristics, enabling their application in the restoration of myocardial functionality. Promoting the generation of cytoskeletal structures and facilitating the formation of intercalated disks play vital roles in maintaining cardiac integrity and function. The incorporation of GO nanoparticles into oligo(poly(ethylene glycol) fumarate) (OPF) hydrogels has demonstrated the ability to enhance these essential factors.²⁸⁶ Recently, it has been observed that GO possesses antioxidant properties, allowing it to modulate inflammation and inflammatory polarization by reducing ROS within macrophages.²⁸⁷ Furthermore, GO can serve as a carrier for interleukin-4 plasmid DNA (IL-4 pDNA), facilitating the generation of reparative M2 macrophages for myocardial infarction (MI) treatment. In an in vitro study utilizing a synthetic complex termed the macrophage-targeting/polarizing GO complex, a decrease in ROS levels and inflammatory cytokine release from immune-stimulated macrophages was observed. This led to a reduction in inflammation, promotion of early differentiation into M2 macrophages, mitigation of fibrosis, and improvement in heart function in animal models of MI.¹⁶⁸

Carbon-Based Hydrogel Scaffolds in Tissue Engineering

The effectiveness of regenerative medicine tissue engineering approaches relies significantly on the meticulous design of the scaffold. In this context, hydrogel scaffolds have captured considerable attention from researchers, attributed to their inherent resemblance to the structural composition of the native ECM.²⁶⁵ A hydrogel is a 3D network structure formed by strongly hydrophilic crosslinked polymers, able to hold huge amounts of water.^288,289 Hydrogels are broadly divided into two classes according to the cross-linking type: physical or chemical. Hydrogels formed by physical crosslinking through non-covalent interactions, such as ionic interactions, hydrogen bonding, and van der Waals forces, provide hydrogels with viscoelastic behavior, generally called reversible gels.²⁹⁰

In contrast, chemically crosslinked hydrogels are formed from covalent bonds, resulting in strong interactions that are more resistant to mechanical forces and provide hydrogels with more elastic behavior.^289,291 In addition, it is common for hydrogels to be classified as natural or synthetic, depending on their origin. In general, natural hydrogels, made of polymers obtained from natural sources, possess better biocompatibility and biodegradability, while synthetic hydrogels exhibit more tunable properties, low-cost and wide availability.^288,292,293

Due to their hydrated and porous 3D structure, with high surface area and highly adjustable properties, hydrogels have emerged as one of the most promising and versatile classes of biomaterials for soft tissue engineering. Hydrogel-based scaffolds can be designed to provide an appropriate microenvironment similar to the ECM native allowing the diffusion of oxygen, nutrients, and biomolecules, thus supporting cell adhesion, migration, proliferation, and differentiation.^289,294

In hydrogels, CBNs play two principal roles: as filler in polymer hydrogels with improved properties, such as conductivity and mechanical resistance,^295–300 and as a central component of the hydrogel matrix, being a gelator to self-assemble into hydrogels. This topic is focused precisely on that last application, collectively called carbon-based hydrogels. Graphene appears as the most widely used carbon-based material for hydrogel construction. In fact, there is a lack of evidence in the literature on the formation of hydrogels by other CBNs.

Graphene-based hydrogels are 3D structures derived from their corresponding two-dimensional forms.³⁰¹ The unique characteristics of graphene, such as high thermal and electrical conductivity, excellent mechanical performance, and large surface area, have made graphene hydrogels an important topic of research for various applications, eg, water treatment,^302,303 supercapacitors,^304–306 lithium-ion batteries,^301,307 wearable sensors.³⁰⁸ In addition, as a result of its wettability, GO has shown cytocompatibility, and its presence can favor cell adhesion and proliferation.³⁰⁹ Thus, its biocompatibility, high swelling, softness, and elasticity resembling living tissues have attracted attention in tissue engineering.

To synthesize a graphene-based hydrogel, Lim et al applied a hydrothermal method.³¹⁰ This simple and environmentally friendly methodology, originally described by Xu et al,³⁰³ can prepare a hydrogel from GO suspension using a single-step hydrothermal reduction process in which 2D graphene sheets are self-assembled in 3D macrostructures (Figure 7). These authors conducted in vitro studies to assess the viability of MG63 cells in the synthesized scaffold and found good biocompatibility and potential for biological applications of GO hydrogel.

Figure 7 Synthesis of self-assembled graphene hydrogel by hydrothermal reduction reaction. The homogeneous GO dispersed in water was sealed in a Teflon-lined autoclave and hydrothermally treated at 180 °C for 12–44 hours. Next, the autoclave is cooled to room temperature, and the synthesized self-assembled graphene hydrogel is removed and dried with filter paper to remove the water adsorbed on the surface.

Li et al designed an oxide-graphene-based stimulus-responsive hydrogel to synthesize a smart scaffold for dynamic control of cell release.³¹¹ This active cell scaffold was prepared by in-situ polymerization introducing GO into a monomer solution of Poly(N-isopropylacrylamide) (pNIPAAm). In this method, the polymerization occurs on the GO surface, leading to the composite hydrogels of GO and polymer.³¹² The developed hydrogel scaffold, which also included the addition of arginine-glycine-aspartic acid (RGD) to improve biocompatibility, was able to change its morphology in response to the photothermal effects resulting from the application of Near-Infrared (NIR) light. Briefly, when the NIR light is applied, the hydrogel undergoes a transition from a swollen hydrophilic state to a non-swollen hydrophobic state, releasing the cells seeded into the hydrogel together with the water (Figure 8).³¹¹

Figure 8 3D graphene oxide/Poly (N-isopropylacrylamide composite hydrogel responsive to near-infrared light for capturing and releasing cells on demand. Reprinted from Li W, Wang J, Ren J, Qu X. 3D graphene oxide-polymer hydrogel: near-infrared light-triggered active scaffold for reversible cell capture and on-demand release. Adv Mater. 2013;25(46):6737–6743.³¹¹

To fabricate a scaffold with antibacterial properties for wound repair, Fan et al fabricated a graphene/Ag composite hydrogel synthesized by the crosslinking reaction of graphene with acrylic acid and N, N ′-methylene bis-acrylamide³¹³ (Figure 9). In addition to exhibiting excellent biocompatibility, strong antibacterial abilities, high swelling ratio, and adequate extensibility, in vivo studies indicated that the graphene/Ag hydrogel significantly accelerated the healing process of wounds in rats, indicating a potential for applications in wound dressing.

Figure 9 Scheme illustrating the synthesis of the graphene/Ag composite hydrogel. First, a solution of Ag(NH₃)₂OH is obtained by slowly adding NH₃H₂O to an AgNO₃ solution. This resulting solution is poured into a GO solution, and a glucose solution is added (as a green, reducing agent). Then, crosslinking was achieved by incorporating acrylic acid and N, N ′-methylene bis-acrylamide. Reprinted from Fan Z, Liu B, Wang J, et al. A novel wound dressing based on Ag/Graphene polymer hydrogel: effectively kill bacteria and accelerate wound healing. Adv Funct Mater. 2014;24(25):3933–3943. © 2014 WILEY-VCH Verlag GmbH & Co. KGaA, Weinheim.³¹³

In their study, Jing et al created a conductive hydrogel based on chitosan/dopamine (DA)/GO that, in addition to electrical conductivity, exhibited rapid self-healing and self-adhesive properties, high stability, strong mechanical and recovery behavior.³¹⁴ The hydrogel was produced by introducing dopamine in the chitosan/GO solution, and following self-polymerization, it was able to form the chitosan/DA/GO composite hydrogel. Therefore, it is essential to highlight that incorporating GO increased the cell viability and proliferation of cardiomyocytes and human embryonic stem cell-derived fibroblasts.

Finally, regarding drug delivery applications of 3D scaffolds, recently, Bayón et al developed an electromagnetic-responsive graphene-based hydrogel.³¹⁵ The graphene/diaminotriazine composite hydrogels, synthesized using graphene solutions dispersed in DMSO as a polymerization medium for diaminotriazine, revealed responsiveness with microwave irradiation (915 MHz), a frequency more suitable for the penetration into deeper tissues than 2.45 GHz, commonly applied to other microwave-responsive soft materials.^316,317 As a result, the authors demonstrated a biocompatible scaffold that can promote the drug-controlled release on demand and potential uses in biomedical applications.

Outlook and Challenges

In summary, this paper offers an overview of the synthesis, intriguing properties, and surface functionalization approaches for 0D to 3D CBNs that enable their applications in tissue engineering. This review also summarizes recent progress using CBNs and, especially, CBN-based hydrogels as scaffolds for many typical tissue regeneration applications. Regarding CBN materials development, an important and challenging task is to perform a systematic cross-comparison regarding the effectiveness of different types of CBNs for certain types of tissue engineering applications. Since different tissues have diverse structures and involve different cell systems, such comprehensive comparison will identify not only the most promising CBNs and/or hydrogels that are currently available for the regeneration of specific tissues but also further trigger the design and functionalization of new CBN materials to tackle the challenges in this field.

In the future, we foresee that N-doped CBNs including N-doped CNTs, and graphene could result in faster and more effective tissue regeneration. This is due to the clear biocompatibility of N-doped species, which reduce the presence of oxygen radicals. The mechanism behind this is that N-doping introduces favorable electronic properties in the nanomaterials, facilitating the scavenging of reactive oxygen species (ROS) and thus decreasing oxidative stress in cells. As a result, several studies indicate that N-doped MWNTs promote (or keep constant) cell viability^318,319 and are prone to biomolecules.^320–322

Regarding the use of carbon-based hydrogels in tissue engineering, a current limitation is a lack of in vivo assays, particularly in long-term and human research. However, before taking this step, further in vitro studies with the direct application of these carbon-based hydrogels to other specific tissues may be necessary. Another critical challenge is the development of in situ-forming injectable hydrogels. As mentioned in the previous section, since minimally invasive procedures can administer and are able to fill tissue defects conformally, this type of scaffold has gained special attention in recent years. Nevertheless, one of the main disadvantages of this hydrogel remains the insufficient mechanical resistance to maintain the loads imposed on the tissues under physiological conditions. The synthesis of more robust carbon-based injectables hydrogels with adequate mechanical characteristics could have a considerable impact, especially for treating bones and cartilage that frequently have non-uniform tissue damage and need stiffness. In the case of anatomically well-defined structures (eg, knee menisci, intervertebral discs, and the heart), bioprinting has been one of the most promising strategies. As the development of new bioink formulations continues to be the main target of interest in this field, engineering novel carbon-based hydrogels and using them as bioink could also contribute significantly to the progress of this area.

Disclosure

The authors report no conflicts of interest in this work.

Acknowledgments

A.O.L would like to thanks to National Council for Scientific and Technological Development (CNPq, grants #310883/2020-2 and #404683/2018-5).