The Use of Scaffolds in Musculoskeletal Tissue Engineering

Frances Henson1, Alan Getgood*, 2
1 Department of Veterinary Medicine, University of Cambridge, Cambridge, CB3 0ES, UK
2 The Fowler Kennedy Sport Medicine Clinic, The University of Western Ontario, Ontario, Canada

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© Henson and Getgood; Licensee Bentham Open.

open-access license: This is an open access article licensed under the terms of the Creative Commons Attribution Non-Commercial License ( which permits unrestricted, non-commercial use, distribution and reproduction in any medium, provided the work is properly cited.

* Address correspondence to this author at the Fowler Kennedy Sport Medicine Clinic, The University of Western Ontario, Ontario, Canada; Tel: +1 (0) 4036 097286; Fax: +1 (0) 4036 097285; E-mail:


The use of bioengineering scaffolds remains an integral part of the tissue engineering concept. A significant amount of basic science and clinical research has been focused on the regeneration of musculoskeletal tissues including bone, articular cartilage, meniscus, ligament and tendon. This review aims to provide the reader with a summary of the principals of using material scaffolds in musculoskeletal tissue engineering applications and how these materials may eventually come to be incorporated in clinical practice.

Keywords: Musculoskeletal tissue engineering, scaffolds.

Tissue Engineering (TE) is the use of a combination of engineering, materials and cells to improve or replace biological functions. TE solutions are usually, but not always, based upon a scaffold (synthetic and/or biological), alone or in combination with precursor or specialist cell types and may include modifications such as the inclusion of bio molecules [1]. In recent years increasingly more complicated structures are being created and tested in the quest to find the ‘ideal’ analog to replace or encourage repair of the damaged tissue. The aim of this review is to provide an overview of the use of scaffolds in musculoskeletal TE.

Which Musculoskeletal Tissue Repair Might Benefit From the Use of Scaffolds?

Scaffolds can potentially enhance the repair or replacement of any of the tissues in the musculoskeletal system for a variety of reasons. Some of the tissues in the musculoskeletal system have a poor intrinsic repair capacity. For example, cartilage is notoriously poor at healing [2]; it has a slow rate of turnover and very limited capacity to repair defects. It is well recognized that partial thickness cartilage defects do not really heal at all, and that full thickness defects heal by recruitment of bone marrow derived stem cells from the underlying bone, often to form poor quality, disorganized fibrocartilage instead of the required hyaline cartilage [3]. However, even marrow progenitor cell recruitment can only heal osteochondral lesions up to critical sizes [4], beyond which defects in the articular surface remain. Scaffolds might therefore represent an excellent strategy to assist healing of both chondral and osteochondral lesions.

Tendons, menisci and ligaments are also considered to have relatively poor healing compared to most tissue types [5], although their healing is not as poor as cartilage. Similar also to cartilage, damaged tendon and ligament is often repaired by disorganized, weaker tissue which is prone to re- injury [6] and the use of scaffolds to promote more functionally appropriate healing would be highly advantageous.

In contrast to these tissues, bone and muscle have excellent healing capacities and are usually able to achieve an effective repair [7]. However, in some circumstances even these tissues are not able to completely repair. For example, bone repair can be poor for a number of reasons resulting in delayed and non unions [8]. In large defects created during the treatment of bone or muscle neoplasia there may simply be too big a physical gap for normal healing to bridge [7]. In each of these clinical challenging scenarios, scaffolds represent an excellent strategy to assist healing by providing a support structure for cells, a source of cells and/or biological factors or a combination of all of these.

What Makes a Good Scaffold?

Scaffolds designed for use in musculoskeletal TE should meet several criteria [9] including:

  1. They should be biodegradable and biocompatible – the scaffolds must be able to be absorbed by the tissue once the functional life of the scaffold is reached or integrated into the tissue.
  2. The scaffold should not promote and inflammatory or immune response in the tissue.
  3. The scaffold surface and porosity should permit cell adhesion and growth and permit the expression of the appropriate cellular phenotype.
  4. The material should have the mechanical properties required to withstand the biological demands made upon it during the reparative period.
  5. The material must be able to be produced reproducibly.
  6. The scaffold must be able to be supplied sterile, in an appropriate size for surgical placement.
  7. The scaffold should have good handling properties i.e. are able to be trimmed to fit defects and be amenable to manipulation with surgical instruments.


Many different scaffolds exist, at all stages of development from initial material description through to completed clinical trials. Given the rapidly expanding literature in this area, how can the clinician objectively evaluate the data that is generated from the testing of potential scaffolds? The development and use of a scaffold intended for TE falls into four broad categories; the production of the scaffold material itself, in vitro biocompatibility testing, pre-clinical trials in animal models (small and large animal [10]) and human clinical trials. Thus, at any one time scaffolds are at different stages of the evaluation procedure, making it difficult to compare the effectiveness of any given scaffold against its ‘competitors’ (i.e. scaffolds of different structure intended eventually for the same clinical use). In truth, a scaffold can only ever be fully evaluated at the end of a significant number of patient treatments and all intermediate data, while of interest, is merely a guide to potential performance in vivo.

1. Materials

The most common and simple scaffolds that have been used for decades are patients own tissue (auto graft) or cadaveric donor tissue (allograft). Autograft such as hamstring tendons or the patella tendon have been incorporated in anterior cruciate ligament reconstruction since the 1960’s. [11]. Studies have shown host tissue infiltration (ligamentization) by approximately 12 weeks [12]. Similarly allograft has also been used for the same purpose, often taking slightly longer to incorporate. The treatment of bone fracture non-union has been treated extensively with bone autograft, often being harvested from the iliac crest. Not only does this scaffold provides structural osteoconductive support, but also lends itself to having osteoinductive and osteogenic properties. However, donor site morbidity has led many clinicians to use allograft which, due to its processing and storage, only have osteoconductive properties [13]. As a result, in the past two decades a great emphasis has been placed on the production of ‘off the shelf’ scaffolds’ which can be used to treat bone, but also ligament, tendon and cartilage.

Some of the earliest well described scaffolds were made of relatively simple synthetic materials, for example polyethylene meshes [14, 15], carbon implants [16] or carbon-polylactic acid (CPA) polymers [17-19]. However, since these early materials were used, there has been much development of biologic and synthetic materials and combinations thereof.

Biological scaffolds may be classified as to the predominant type of material used e.g. protein or carbohydrate. The most common protein derived scaffolds are those made from collagen. Examples include Matrix Assisted Chondrocyte Implantation (MACI, Genzyme Inc., Oxford, UK) which utilizes a collagen type I/III scaffold/membrane to culture chondrocytes ex-vivo prior to implantation into an articular cartilage defect [20]. Whilst the use of collagen alone as a scaffold has been shown to be a successful strategy, collagen has also been successfully combined with other biological materials to form commercially available tissue repair systems. The addition of a ceramic such as calcium phosphate has been used in a number of osteochondral scaffolds including Chondromimetic (Tigenix, Cambridge, UK) and Maioregen (Finceramica, Italy). The ceramic alone can be used as a scaffold, such as porous Hydroxyapatite as a bone graft substitute (Apapore, Baxter Healthcare, Deerfield IL). This has been in a number of clinical trials with satisfactory outcome [21]. Other naturally occurring substances in cartilage have been added to collagen to help mimic the extracellular matrix, such as chondroitin sulphate in the Novocart 3D (Tetec, Germany) in which autologous chondrocytes are combined with a 3D collagen/chondroitin sulphate scaffold.

Carbohydrate based scaffolds include hyaluronic acid, which has been incorporated in Hyalograft C (Hyaff-11, Fida Advanced Biopolymers, Abano Terme, Italy). This is another naturally occurring material in cartilage and therefore represents a biological treatment option. The BST-Cargel system (Bio-Syntec Inc., Canada) utilizes a chitosan based scaffold infused with uncoagulated whole blood prior to implantation into a microfracture lesion [22]. Chondron (Sewon Cellontech, Korea) is a commercially available fibrin gel based autologous chondrocyte implantation device [23]. Fibrin has also been used as a tissue glue (Tisseel, Baxter, US), which has been used to form a biological scaffold to contain embryonic derived pluripotent cells and used to treat ovine osteochondral lesions [24].

Whilst biological materials are widely used as scaffolds in musculoskeletal TE synthetic materials are also well suited for use as scaffolds as they can be produced reproducibly, are relatively easily modified (both structurally and chemically) and have a minimal risk of provoking an immune response in the host. Since the development of the original synthetic scaffolds, a new generation of bioabsorbable synthetic materials have been investigated for their potential use as scaffolds. These new materials include polylactides, polyglycolides, polydioxanone, e-caprolactone, polycarbonates and their copolymers [25-32]. A number of synthetic musculoskeletal TE solutions are commercially available for use. In the Bioceed-C system (BioTissue, Germany), chondrocytes are seeded into a biodegradable polyglycolic/polylactic acid/polydioxanane based polymer fleece [33]. Scaffolds can also be used to support cartilage fragment implantation as well as cellular therapy. In a recently described cartilage autograft implantation system model, autologous cartilage fragments were added to a polydioxanone scaffold for implantation into chondral lesions [34]. In osteochondral lesion repair the use of the Trufit (Smith and Nephew Endoscopy, Andover, MA) plug (a multiphasic implant consisting of polyglycolic acid and poly-D-L-lactic-co-glycolide fibres plus 10% calcium) has produced good clinical results over reasonably extended recovery timescales in patients [35] and a polyurethane meniscal scaffold has shown promising results as a meniscal replacement in pre-clinical trials (Actifit, Orteq, US) [36] and in a more recent clinical study [37].

In addition to these synthetic and biological scaffold developments, a number of synthetic/biological composite scaffolds have been developed, such as bioglass-collagen-phosphatidylserine scaffolds [38], collagen/PLA composites [39] and bioactive glass/polycaprolactone/biphasic calcium phosphate scaffolds [40], many of which are in the earliest stages of biocompatibility testing and on whom relatively little data is currently available for evaluation. However, one hybrid scaffold, Osseofit, (Kensey Nash Corporation, USA) is commercially available for use as a bone void filler model in pre-clinical trials [9]. This biphasic scaffold is composed of a type I collagen chondral layer and a beta tricalcium phosphate ceramic suspended in a polylactic acid lattice.

2. Biocompatibility Testing

Once a material has been identified suitable for a scaffold then biocompatibility testing (testing the ability of the scaffold to support cell growth and function in vitro) is undertaken. The majority of scaffolds are, at some point in their development, assessed for their ability to support the growth of multipotential cells. The most commonly described cell type grown on scaffolds for musculoskeletal TE is the mesenchymal stem/progenitor cell (MSC), which may be harvested from many musculoskeletal tissues but most commonly from bone marrow [41-43]. More recently, MSC’s have been sourced from human embryonic stem cells [44]. MSCs can differentiate into any of the cell types of the musculoskeletal system when induced by the appropriate in vitro or in vivo cues [43, 45] - the ability of the scaffold to support cells that can become any of the differentiated cells of the musculoskeletal systems may indicate the broad potential of the scaffold as a cellular support.

More specific biocompatibility testing examines to what extent the scaffold can support the differentiated cell type that it is intended to ‘host’ in vivo. Thus in simple experimental systems meniscal scaffolds are tested with fibroblasts of meniscal origin [46, 47], chondral scaffolds with chondrocytes [48-50], tendon scaffolds with tenocytes [51, 52] and so on. However, single cell experiments, whilst informative, do have their limitations. The musculoskeletal tissues are complex. They may be multicellular, containing specialized niches (bone [53]) or composed of cellular sub-types with different properties (cartilage) [54, 55]. They all have inter-tissue regional variations of mechanical stresses and strains, extracellular matrix components and other tissue interfaces [56], which a single cell experiment does not replicate. Thus more complicated biocompatibility assays are devised to test the efficacy of a scaffold. For example, seeding chondrocytes and fibroblasts inside and outside a meniscal scaffold [57]; seeding osteoblasts and fibroblasts onto a ligamentous scaffold [58]; seeding osteoblasts/ endothelial cells on DegraPol (AbMedica, Italy) foam scaffolds in a chick chorioallantoic bone graft model [59]; and, in a highly complex series of experimental steps, seeding chondrocytes, osteoblasts and fibroblasts onto a single scaffold in order to provide the cell types required to fully heal an anterior cruciate ligament (ACL) rupture [58, 60-62]. Assessing how cells behave in these different experimental systems allows judgements to be made as to their suitability for use in musculoskeletal TE. Clearly scaffolds that support the biological functions of the cells that they are intended to ‘host’ in vivo are the most likely candidates to progress through to further assessment. However, there is a danger that TE solutions that become too complicated become difficult to manage in a clinical setting and too expensive for routine use.

3. Pre-Clinical/Animal Model Testing

Evaluating the effectiveness of scaffolds in the treatment of musculoskeletal pre-clinical problems is difficult, as, despite the large number of in vivo and in vitro models described in the literature, no ‘industry standard’ models have yet been adopted within which systems can be tested [63]. In addition to the wide variety of models available in which to test a scaffold, multiple confounding factors affect the interpretation of results. For example, the age of the test subject and of tissue donors [64, 65]; different natural healing rates in similar structures e.g. the ACL heals poorly following damage compared to the medial collateral ligament (MCL) [66]; differences in natural healing biology in, for example full thickness cartilage defects (good healing) compared to partial thickness defects (poor healing) [67, 68].

When considering pre-clinical models of musculoskeletal damage/repair one must question which is the ideal model to replicate the human situation [63]. An example of the difficulties encountered when choosing an optimal animal model to test a TE scaffold based solution is in the treatment of osteochondral defects. Lesions in the distal femoral condyle of the knee (‘stifle’) are probably the most commonly used model defect in pre-clinical osteochondral scaffold studies but the thickness of the cartilage at this site, compared to man, varies considerably between species. In man the distal femoral cartilage is reported to be 2.2mm in depth with 2% chondrocyte volume density (CVD); of the commonly used species in pre-clinical studies the horse is most similar to man (2mm depth, 6-7% CVD) with the rabbit (a very commonly used pre-clinical study species) being very dissimilar (0.2-0.4mm depth, 2-12% CVD) [63]. However, whilst equine cartilage can be considered the most similar to human, preclinical equine studies are expensive, specialist and subject to strict welfare controls. Thus many research groups use smaller ‘large animals’ such as sheep, goat and pigs, which are easier and cheaper to source and maintain to assess scaffold performance in vivo. However, many scaffolds are evaluated in vivo in small animal models, particularly rabbits and rodents. There are significant complications in the interpretation of results in these species. Rodents are fundamentally different from large animal and human cartilage in that they do not close their growth plates even at maturity and thus have very different chondrocyte subpopulations compared to large animals/humans. Indeed rodent and rabbit cartilage defects naturally heal very rapidly and thus the results of scaffold performance in these animals must be considered in light of these differences – any scaffold in these species will perform well.

4. Clinical Trials

TE scaffold based solutions that are demonstrated to have positive effects on repair and regeneration both in vitro and in pre-clinical trial are then often taken forward into clinical (patient) trials. However, given the relative novelty of this field of research, there is a paucity of information currently available on the performance of TE scaffold based solutions. Once again, difficulties arise as there is currently no ‘gold standard’ for the evaluation of tissue repair. For example, in chondral and osteochondral repair a number of techniques to evaluate tissue repair have been described by research and clinical groups worldwide. These techniques use a variety of scoring systems including radiographic/MRI, second-look arthroscopy and clinical outcome measures. At the current time, these evaluation techniques show that many of the scaffold based repair systems in commercial use have efficacy for the treatment of cartilage lesions in the short and medium term [23, 69], however there is little comparative data available.


The development of scaffolds containing nanomaterials [70] is an interesting development in scaffold technology. Nanomaterials can mimic the architecture of the normal extracellular matrix (ECM) (which contains both nano and microfibers), which is likely to be very important in encouraging the cellular component of the TE construct to behave in a biologically appropriate fashion [71]. Nanofibers provide high surface area-to-volume ratios, increasing the contact area between cells and fibres and offering huge potential to deliver substances such as drugs [72] or growth factors [73] into an area of repair or regeneration [74]. However, the increased pore size and porosity of many nanofibres may lead to inferior mechanical properties compared to micro- or macro-fibres [75]. In order to address these concerns, further engineering of nanoparticle based scaffolds has been performed, for example aligning the nanofibres within the scaffold [76, 77] or producing nanofibre mats with programmed fibre direction [75]. These alterations have been shown to be beneficial to cellular growth and function in vitro and may be required to enhance their use in tissue regeneration. Just as nanofibres can be utilized to provide drug/protein delivery systems, other scaffolds can also be modified to further enhance their TE credentials. Scaffolds can be coated with growth factors such as fibroblastic growth factor-2 (FGF-2) [78, 79] and bone morphogenic proteins (BMPs) [79-81] with or without other bioactive molecules [82]. They can also be made more ‘sticky’ by, for example, coating them with the RGD (Arg-Gly-Asp) cell attachment site [83] to encourage the adhesion of the target cells. Possibly one of the most exciting developments is the design and production of self-assembling natural peptide nanofibre scaffolds that can be used alone or with other scaffolds to enhance tissue repair [84, 85]. These nanofibre scaffolds can be genetically engineered to contain specific peptides designed specifically for the target tissue, for example, osteogenic growth protein and osteopontin cell adhesion motif for designer bone repair scaffolds [86].


Biological and synthetic based material scaffolds have an integral role in the potential application of musculoskeletal tissue engineering. As newer materials and technologies evolve, the pre-clinical testing will be of utmost importance before they can be utilized in widespread clinical use.


None declared.


None declared.


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