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Accepted Manuscript
Three-Dimensional Bioprinting for Bone Tissue Regeneration
Shiva Kalyani, Nandini Dhiman, Anindita Laha, Chandra S. Sharma, SeeramRamakrishna, Mudrika Khandelwal
PII: S2468-4511(17)30021-1
DOI: 10.1016/j.cobme.2017.03.005
Reference: COBME 12
To appear in: Current Opinion in Biomedical Engineering
Received Date: 6 March 2017
Accepted Date: 8 March 2017
Please cite this article as: S. Kalyani, N. Dhiman, A. Laha, C.S. Sharma, S. Ramakrishna, M.Khandelwal, Three-Dimensional Bioprinting for Bone Tissue Regeneration, Current Opinion inBiomedical Engineering (2017), doi: 10.1016/j.cobme.2017.03.005.
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Three-Dimensional Bioprinting for Bone Tissue Regeneration
Shiva Kalyani,a Nandini Dhiman,b Anindita Laha,c Chandra S. Sharma,d Seeram Ramakrishnae and Mudrika Khandelwala,*
a Natural and nature inspired material for society Laboratory Department of Materials Science & Metallurgical Engineering,
Indian Institute of Technology, Hyderabad, Kandi-502285, INDIA
b Department of Biomedical Engineering, Indian Institute of Technology, Hyderabad, Kandi-502285, INDIA
c Department of Chemical Engineering, Indian Institute of Technology, Hyderabad, Kandi-502285, INDIA
d Creative & Advanced Research Based On Nanomaterials Laboratory,
Department of Chemical Engineering, Indian Institute of Technology, Hyderabad, Kandi-502285, INDIA
e Department of Mechanical Engineering, National University of Singapore, Singapore
Abstract
Three-dimensional bioprinting can prove to be a promising technology for bone tissue
regeneration as it facilitates good spatio-temporal distribution of cells in scaffold. The feed
for bioprinting is bioink, which comprises of cells incorporated in the scaffold material.
Progress has been made on the incorporation of growth factors in the bioink, which not only
enables efficient regeneration but at the same time proves the feasibility of large constructs.
Important parameters which determine the suitability of bioink have been discussed here.
Lack of vascularization limits the success of this technology in its present form. Advances in
inducing vascularization and growth factors have also been discussed. Towards the end,
challenges and opinions in the area of bioprinting of bone tissue regeneration have been
presented.
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• Corresponding author: Email: [email protected]
Keywords: Bioink; Growthfactors; Controlled release; Angiogenesis; Osteogenesis;
Introduction
Three-dimensional (3D) printing has advanced the field of bone regenerative medicine by
overcoming engineering challenges of biomimicking biological tissues or organs. The
conventional 3D printing approach involves the predefined layered printing of scaffolds
followed by cell seeding and perfusing the construct before implantation. However, this
method suffers from a lack of uniform spatial and temporal distribution of cells and growth
factors in the construct. A new class of 3D printing called bioprinting – printing along with
the cells – promises to overcome all these limitations.
In this mini review, we report the most recent advances in the field of 3D bioprinting of bone
with respect to methods, bioink properties and growth factors/drug aided vascularization in
the constructs. Later, we present our opinion and the challenges needed to overcome, to
advance the field of bone bioprinting.
Bioprinting Techniques and Bioinks
Current focus has been to develop novel bioinks which can be 3D printed in cell-compatible
conditions to fabricate a cell-laden 3D structure. Bioink comprises of cells embedded in a
printable material which aids proliferation of cells by maintaining a supply of nutrients,
oxygen and growth factors (GFs). Bioinks can be in the form of hydrogels, viscous fluids or
micro-carriers [1]. Polymeric hydrogels are preferred as they mimic native extracellular
matrix (ECM) and facilitate cell adhesion and matrix integration [2]. Selection of suitable
combination of bioprinting method and bioink is very essential for a successful fabrication of
tissues [3]. The widely employed bioprinting techniques include drop based or inkjet, laser-
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assisted and extrusion bioprinting [4], some of which are summarized in Table 1. The
essential properties required for bioink vary with different bioprinting method employed
(Table 2).
Table.1 Additive Manufacturing Techniques for bone tissue scaffold (conventional and bioprinting)
Technique Resolution (µm)
Pore size (µm)
Porosity (%)
Advantages Disadvantages Ref.
1. Photo polymerization based Techniques Stereo lithography (SLA)
14-150
20-1000
<90
Complex internal features; GFs and cell loading possible
Only for photopolymers; Toxic photoresins; shrinkage issue; Need of support structure
[5]
Micro-stereolithography (MSLA)
0.5-10
100-300
<90
Digital light processing
40
500
<90
2. Powder based techniques Selective laser sintering (SLS)
50-1000
30-2500
<40
Solvent free, fast operation; No need of support structure; No post processing required;
Expensive; Surface Powder finishing; Difficult to remove blocked powder; high temperature involved; Resolution depends on diameter of laser beam
[6]
3D Printing
50-300 45-1600 45-60
Mild process conditions
Poor mechanical properties
[7]
3. Extrusion based techniques Fused deposition modeling
100-150 100-2000 <80%
Good mechanical integrity;
Limited filament materials;
[8]
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Solvent and support structure not needed;
material exposed to high temperature; Scaffold with small pore size is difficult to fabricate.
Low temperature deposition
300-500 200-500 <80%
Broad range of material usage; Able to incorporate growth factors;
Solvent usage; Freeze drying is required;
Pressure assisted micro-syringe
10-1000 10-600 70% Very fine resolution
Printable viscosities are limited in range
Robocasting / Direct Ink writing
100-450 5-100 <90%
Independent and customized 3D nozzle movement with high resolution; Highly viscous suspensions can be used; Support is not required; 1mm structures;
Expensive; Optimization of Bioink properties is crucial;
4. Bioprinting Method and material
Resolution (µm)
Droplet size (µm)
Cell viability
Advantages Disadvantages Ref.
Droplet based bioprinting For hydrogels
~50µm 50-300 <85%
Compatible with narrow viscosity range; Compatible with various cells and GFs; Suitable to deposit cells on microarrays or organ-on-a-chip Inexpensive, flexible, and commercially
Non-uniform droplet size; Nozzle blocking in fibrous bioink and in high cell densities; Cross contamination while printing multiple bioinks simultaneously
[9,10]
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available Micro extrusion based Bioprinting Liquids, pastes and gels
5µm - 1mm wide
100µm-1mm
40-80%;
Compatible with wide range of viscosities; Enables printing of scaffold free bioink of tissue spheroids;
Shear stress of highly viscous bioink, tiny nozzle diameter, and large dispensing pressure causes significant cell damage; Not useful for high-throughput bioprinting of tissues; Low resolution limits the microchannel incorporation for vascularization. Limited control on cell–cell and cell– matrix interactions
Laser Assisted Bioprinting Cell suspension;
100-600µm >20µm >95%
Nozzle free technology enables less cell damage; High precision (1cell/droplet); Supports vascular channels
Laborious; Expensive; difficult to print hetero cellular scaffolds; Limited commercial viability
Table 2. Properties for bioink for different bioprinting methods [11]
Parameter Dropwise or Inkjet Laser assisted Extrusion
Viscosity Low (<100 mPa-s) Medium (1-300 mPa-s ) Higher (>6 -108 mPa-s)
Surface Tension Medium Low Low
Gelation Rapid (Sec) Rapid (Sec) Rapid (Sec to min)
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Fabrication speed medium low high
Ink behaviour Rheopectic High viscoelasticity Thixotropic
Adhesion Low Adhesion within layers Low
Natural polymers are preferred over synthetic polymers because of cell affinity and
resemblance to the ECM. However natural polymers undergo uncontrollable degradation and
possess poor mechanical stability. Crosslinking and polymer blending can control the
scaffold degradation kinetics [3,4,12]. Mechanically superior biocompatible synthetic
polymers are used with growth factors (to improve cell adhesive properties) provide better
control over cell specific stiffness and elastic modulus [3,13]. A tabular presentation of
different polymers used as a bioink has been presented in Table 3.
Table 3. Recently reported hydrogel based bio-ink for 3D-bioprinting of bone tissue
Types of
bioink
Biomaterials Bioink compositions Ref.
Natural
hydrogel
based bioink
Alginate Alginate based (low : high molecular weight
1:2) bioinks for fibroblast cell-printing
[14]
Agarose a) Agarose/cell suspension (2%; 20 million
ml−1)
Bone marrow derived mesenchymal stem
cells bioprinting
b) fibroblasts L929 cell-printing using
thermoresponsive agarose- agarose-collagen
composite hydrogel
[15,16]
Collagen Higher concentration (10−20 mg/ mL) [17]
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collagen hydrogels for tissue printing
applications
Chitosan Polyelectrolyte gelatin-chitosan hydrogel
bioink is used to print fibroblast by extrusion-
based printer
[18]
Fibrin Micro-valve bioprinting of fibrin [19]
Gelatin gelatin/sodium alginate/carboxymethyl
chitosan (Gel/SA/CMCS) hydrogel
combining with bone mesenchymal stem
cells (BMSCs) for 3D bioprinting
[20]
Hyaluronic Acid
(HA)
Shear-thinning supramolecular HA-hydrogels
were used as both as an ink and support
material for bioprinting
[21]
Matrigel Extrusion-based bioprinting of matrigel and
collagen
[2]
Synthetic
hydrogel
based bioink
Pluronic F-127 Shear thinning hydrogel Pluronic F-127 is
used as bioink
[22]
Methacylated
gelatin
MG63 osteoblast-like cells loaded Gelatin
methacryloyl (GelMA) hydrogel is bioprinted
by extrusion-based printer
[23]
Poly(ethylene
glycol)
Endothelial and stem cells loaded GelMA,
alginate, and PEGTA hydrogel bioink is used
in multilayered coaxial nozzle bioprinter
[24]
Multimaterial
Bioinks
Sodium alginate
hydrogel-polylactic
Stem cells loaded hydrogel for better
survivability
[25]
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acid (PLA)
nanofiber
PLA nanofibers mimic ECM
HA, Gelatin
methacrylate,
gellan gum
Gum improved viscosity, printing fidelity and
stability of bioink
[10]
Alginate/PVA Micro and macro porous scaffold with protein
and growth factor fabricated in mild
conditions
[26]
Few key material parameters for bioink involve printability, biocompatibility,
biodegradability, mechanical integrity and biomimicry [4,12]. The rheological behavior
(viscosity and shear thinning), surface tension, swelling properties, and gelation kinetics are
significant aspects for printability [2]. Properties of bioink are also dependent on the printing
method. Drop wise nozzle based or inkjet 3D printing can only handle viscosity less than 100
mPa-s [10], due to clogging whereas laser-assisted and extrusion bioprinting can handle
relatively viscous materials. Higher viscosity (due to a higher concentration, molecular
weight or crosslinking) ensures a better post printing structural stability but at the same time
lowers the cell viability due to increased shear force [27]. Thus, optimizing viscosity and
crosslinking is essential to prepare a bioink which is cell-compatible and provides high-
fidelity scaffold structure. Biocompatibility and biomimicry are necessary to mimic the tissue
microenvironment and aid cell viability and proliferation. Multi-material bioinks are
emerging in the past three years, which provide a better structural stability and cell
survivability (Table.3). However, it is important to avoid polymers with a large difference in
swelling ratio to ensure mechanical stability [4,12].
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Vascularization in 3D Bone Constructs
Pre-incorporation of cells in the hydrogel [28], electrospun fibres [29] and microspheres [30]
and, later making a composite with 3D printed scaffold has yielded satisfactory cell
survivability and differentiation in small bone constructs. In vivo, the osteocytes are located
closer than 100 µm from a capillary in the interosseous vasculature, and the natural blood
vessel growth in the implants tends to be very slow (less than 1mm/day) [19]. Although the
small-scale 3D printed tissue constructs are relatively easy to perfuse, physiologically
relevant larger bone constructs cannot survive merely on the diffusion-based supply of
growth nutrients and oxygen due to hypoxia and poor nutrient supply associated with
deprived vascularization [31]. Therefore, it is essential to direct the research efforts on
including vascularization into the design which would help in removing degraded biological
products and preventing necrotic core formation.
In this regard, research has mainly focused on 3D printing of different combination of cells,
like stem cells with the endothelial cells, along with the scaffold material and finding out
ways to control the supply of growth factors [27,31]. Blinder et al. [32] used 3D engineered
vascular tissue constructs to investigate and understand the development of new blood vessels
using live confocal microscopy and showed that neovascular formation happens through a
multi-stage morphogenic process. Kolesky et al. [33] described a method (see figure 1A (i-
iv)) for printing thick 3D vascularized tissues (>1 cm) containing multiple types of cells that
are perusable for a relatively longer time (more than six weeks). Various inks containing
human mesenchymal stem cells (hMSCs) and human neonatal dermal fibroblasts were
printed onto a tailored ECM embedded with vasculature lined with human umbilical vein
endothelial cells (see Figure 1A (v)). The final integrated tissue was then perfused with
growth factors to successfully differentiate hMSCs into bone cells.
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Growth Factors and Delivery Systems for Enhanced Osteo- and Angiogenesis
To enhance angiogenesis and osteogenesis, the focus is now on culturing stem cells with
osteogenic and angiogenic GFs. Angiogenic GFs include vascular endothelial GF (VEGF)
and platelet-derived GF (PDGF) while bone morphogenic factors such as BMP-2 & BMP-7
induce mitogenesis of mesenchymal stem cells (MSCs) and circulating osteoprogenitor cells,
and promote their differentiation into osteoblasts [34]. However, the clinical translation of
GFs is limited due to burst release and rapid clearance from the implanted site in the
conventional delivery system. Also, to achieve minimum effective concentration at the
injured site, GFs are used at supraphysiological levels which lead to heterotopic bone
formation and certain types of cancers. As a result, research has been motivated to design
better delivery systems to reduce dose and control spatiotemporal release [35]. In native
bone, GFs are encrypted in ECM which protects them from hydrolytic and enzymatic
degradation. Hence, maintaining native protein conformation and bioactivity all through the
scaffold and for the duration of in vivo release is a critical challenge in scaffold-based GF
delivery [36]. Recombinant GFs [37] and osteoinductive drugs such as alendronate [38] have
also been used for osteoconduction.
Various methods (physical entrapment, using micro/nanoparticles, hydrogel systems with the
current trend heading towards hybrid approaches dual growth factor delivery and stimuli-
responsive carrier) have been discovered to incorporate growth factors, drugs and peptides
into 3D polymeric and composite scaffold systems [37]. Alendronate loaded 3D printed
tricalcium phosphate (TCP) coated with Polycaprolactone (PCL), showed mechanical
integrity and controlled release of alendronate up to 6 weeks [38]. Poldervaart et al, showed
VEGF loaded gelatin micro-particles in a 3D printed construct promoted rapid
vascularization with a controlled delivery of VEGF up to 3 weeks [39]. In another study, as
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can be seen in Fig. 1(B), 3D printing was used to spatially and temporally control BMP-2 and
VEGF delivery for large-volume bone regeneration by printing mesenchymal stem cells with
BMP-2 in slow releasing collagen hydrogel on periphery and VEGF in a rapid releasing
alginate/gelatin blend in centre (where hypoxic zone forms). Early vasculogenesis and fast
bone regeneration even in the core of a large structure was observed [40]. Sustained release
of VEGF was observed when loaded to porous 2�N, 6�O�sulfated chitosan coated PLGA
hierarchical scaffolds [41]. Haitao Cui et al. achieved highly osteogenic bone construct with
organized vascular networks by alternative layering of biodegradable PLA fibers and cell-
laden gelatin methacrylate (GelMA) hydrogels and immobilizing growth factors (VEGF and
BMP-2) in preselected regions [42,43]. Bose at al. [44] reported a significant increase in
osteogenesis and angiogenesis in vivo by the sustained release of magnesium and silicon ions
from the 3D P TCP scaffolds with three different sizes of interconnected pores.
Going Beyond Three-Dimensions
4D bioprinting has emerged in recent times where, “smart” 3D constructs could be
programmed to alter their shapes or functionalities in the presence of various external stimuli
such as temperature [41], light [45], magnetic [33], and ultrasound [46]. Sawkins et al.
proposed thermoresponsive microparticulate material based on poly (lactic-co-glycolic acid)
for bioprinting mesenchymal stem cells to produce constructs at ambient conditions with
mechanical properties comparable to cancellous bone. Model protein Lysozyme showed
sustained release up to fifteen days and was bioactive till nine days [47]. Recently, Kang et
al. [48] reported a new type of printing technology – integrated organ-tissue printer (ITOP) -
which controls the shape of the tissue construct by translating clinical image data into the
movements of the nozzle. They demonstrated ITOP’s capabilities of successfully fabricating
mandible and calvarial bone, cartilage and skeletal muscle by co-printing cell-laden
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hydrogels and a matrix made of PCL. The bio-printed construct, which overcomes previous
bioprinting limitations on the size, shape, structural integrity, also includes micro-channels to
supply necessary nutrients, oxygen and growth factors. This novel bioprinting technique will
open up a host of new and exciting possibilities of developing patient-specific customizable
tissues or organs and will inspire the future commercialized bio-printers (Figure.2).
Current Opinion and Future Prospects
How much native complexity must be recreated while designing bone tissues remains an
open question in the field of tissue engineering. While 3D bioprinting offers so much in this
regard, designing suitable bioinks remains a challenge. Ideally, the 3D printed bone scaffold
should be able to release the angiogenic and osteogenic growth factors, placed in the central
region and peripheral region respectively, in a biphasic manner with an optimum degradation
rate of the scaffold. Angiogenic growth factors should be released rapidly for the initial few
days to augment the healing of necrotic tissue. As soon as the capillaries develop, release of
osteogenic growth factors should start in the scaffold in a controlled manner. Burst release of
osteogenic growth factors should be closely controlled to prevent the ectopic bone formation.
These ideal characteristics of an engineered bone are big challenges and directions for future
research. Multi-material hydrogels including interpenetrating networks, nanoparticle
composites and supramolecular hydrogels based bioinks pave the future direction to provide a
facile and effective method for attaining desirable bioink characteristics such as printability
and high structural fidelity, high post-printing mechanical strength, biodegradability and cell
viability. Smart-release systems or 4D bioprinting would be the future direction for the
biphasic release to prevent denaturation during printing and aid spatio-temporal release of
bio-actives. Determining the minimal standards necessary for successful integration of a 3D
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bioprinted tissue will need extensive optimization with regard to cells, shapes, and
mechanical integrity as well as pre-clinical research.
Figure 1. (A) Schematic illustration of the vascularized three-dimensional tissue
manufacturing process. (i) Fugitive ink acting as a vascular ink and cell-laden inks are printed
inside a 3D perfusion chip. (ii) ECM material (containing, fibrinogen, gelatin, thrombin,
cells, and TG) is then cast over the printed inks. (iii) Fugitive ink liquefies when cooled and
is evacuated, leaving behind a vascular network, which is (iv) seeded with endothelial cells
and perfused using an external pump. (v) Schematics of a printed tissue construct containing
hMSCs and hNDFs along with vascular channels contained within a perfusion chamber.
Reproduced from Kolesky et al., [33]. (B) Structure designs. Group 1: DPSCs printed
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structure using 2% collagen. Group 2: DPSC/BMP-2 printed structure using 2% collagen.
Group 3: DPSC/dual growth factors printed structure using 2% collagen and 10%
alginate/10% gelatin blend. Reproduced from Park et al., [40].
Figure 2. The future of 3D Bone Bioprinting: ITOP (Kang et. al. [48]) and methods to control
spatio-temporal release of growth factors are currently paving the future of patient-specific
bone tissue engineering. The shape and size of the defect is modeled using clinical imaging
data and a template for 3D printing is developed. Bioink contains hydrogel containing cells, a
supporting material, and sacrificial material for making vascular channels. Growth factors
and drugs may be added in the bioink to aid osteogenesis and angiogenesis in the 3D printed
bone construct.
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Title of the Manuscript: Three-Dimensional Bioprinting for Bone Tissue Regeneration
Highlights:
1. 3D printing using bioinks for bone tissue regeneration
2. Incorporation of growth factors in bioink
3. Advances in inducing vascularization are promising
4. Multifacette challenges but enormous potential to develop tissue/organs in compliance
with patient need