**Novel Therapies for the Management of Sports Injuries**

Robi Kelc, Jakob Naranda, Matevz Kuhta and Matjaz Vogrin

Additional information is available at the end of the chapter

http://dx.doi.org/10.5772/53593

## **1. Introduction**

With the contemporary active lifestyle and widespread professionalism in sport, the need for high-end injury therapies is growing. Conservative principles in managing various sports injuries usually do not meet the need of athletes and their coaches. In order to achieve better and faster recovery after injuries, significant effort has been made in the recent decade among researchers. Local growth factor application, targeted therapies using recombinant proteins and tissue engineering represent promising groups of future therapeutic options with promising results.

Healthy tendons and ligaments get injured either by a single application of force or by a re‐ peated or sustained action that alters their mechanical characteristics. Genetic disorders, ag‐ ing, decreased vascularity, endocrine influences, nutritional status, inactivity, immobilization, and exercise may cause tendon degeneration, thus rendering the tendon or ligament more susceptible to injury when force is applied. Hypovascularity is hypothesized to play the major role in this degeneration, both directly by causing an ischaemic environ‐ ment for the fibroblast and indirectly both by contributing to the production of free radicals and by allowing for tissue hyperthermia to occur. Conservative management, such as rest, corticosteroid injection, orthotics, ultrasound, laser treatment, or shockwave treatment pro‐ vide pain relief but, when they fail, surgery is required. Local growth factor application and tissue-engineering strategies, such as the development of scaffold microenvironments, re‐ sponding cells, and signalling biofactors are currently generating potential areas for addi‐ tional prospective investigation in tendon or ligament regeneration.

Cartilage tissue also comprises of limited intrinsic potential for healing due to the lack of blood supply and subsequent incomplete repair by local chondrocytes with inferior fibrocar‐ tilage formation. Surgical intervention is often the only option, but the repair of damaged

cartilage is often less than satisfactory, and rarely restores full function or returns the tissue to its native normal state. The new concept of cartilage tissue preservation uses tissue engi‐ neering technologies, combining new biomaterials as a scaffold, applying growth factors and using stem cells and mechanical stimulation.

Agency (WADA) prohibits any use of myostatin inhibitors in athletes, their potential to act only therapeutically at the site of injury without any performance enhancement may play an important role in muscle injury therapy in the future. In the following chapters, various agents are described that reportedly have beneficial effects on muscle healing after injury.

Novel Therapies for the Management of Sports Injuries

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5

Mannose-6-phosphate (M6P) N-acetylcysteine (NAC)

**Table 1.** Agents with proven anti-fibrotic effects in *In vitro* or *In vivo* studies of skeletal muscle regeneration after injury

*Follistatin* is an autocrine glycoprotein expressed in nearly all tissues of higher animals, with multiple effects on skeletal muscles as well as other tissues [5]. It is a functional antagonist of several members of the TGF-β family of secreted signalling factors, including myostatin the most powerful inhibitor of muscle growth characterized to date [6, 7]. Follistatin was previously known as FSH-suppressing protein (FSP) as it was found to have inhibitory ef‐ fect on pituitary secretion of follicle-stimulating hormone (FSH) [8]. Research into the devel‐ opment of therapies to antagonize myostatin has led to the discovery of several new functions exhibited by follistatin [9]. Several *In vivo* studies on follistatin have shown that it directly inhibits myostatin and also reduces myostatin-induced muscle wasting after sys‐ temic administration [5, 10]. In recent research, Zhu et al. reported on the stimulative effect of follistatin on MyoD, MyF5, and myogenin expression, which are myogenic transcription factors that promote muscle differentiation. They also showed its inhibitory effect on myo‐ statin, activin A, and TGF-β, all of which are negative regulators of muscle cell differentia‐ tion [9]. Although various myostatin inhibitors have been described, follistatin can modulate other regulators of muscle mass in addition to myostatin [11]. For example, follistatin ad‐ ministration to MSTN-1- mice caused muscle mass increases beyond that stimulated by my‐ ostatin depletion [12, 13], suggesting that this may be a more potent approach than targeting myostatin alone. Intramuscular administration of gene therapy vectors expressing follistatin has increased muscle mass and strength in both young and aged mdx mice, as well as in nonhuman primates [14]. In order to investigate the mechanisms of the follistatin-induced muscle hypertrophy, Gilson et al. used irradiation to destroy the proliferative capacity of satellite cells. They found that not only inhibition of MSTN, but also of activin (ACT) and

Angiotensin receptor blockers (ARBs)

Follistatin Decorin Interferon-γ Suramin Relaxin

**Class Agent**

Autologous growth factors Platelet-rich plasma (PrP)

**2.1. Recombinant proteins in muscle regeneration**

Recombinant proteins

Other bioactive agents

Skeletal muscle, on the other hand, has a great regenerative capacity; however, this process if often incomplete because of partial fibrous scar formation. Conservative therapies includ‐ ing cryotherapy, resting, physical therapy and pain relief medications don't often give satis‐ factory results and can even be controversial. While surgery is reserved for bigger tissue defects, the need for antifibrotic agents to improve muscle repair after injury is obvious. These and platelet-derived growth factors represent the future of biological therapies for this common type of sports injury.

Novel tissue-specific therapies are mainly molecular, based on pathophysiological processes after injury. Although they seem to significantly accelerate healing and shorten the recovery time, their true goal is to achieve better and more functional repair.

## **2. Biological therapy for better muscle regeneration**

While spontaneous muscle fibre regeneration usually occurs after muscle injury, this process can often be slow and incomplete and accompanied by fibrotic infiltration, which compro‐ mises the restoration of contractile function [1]. Scar formation is the result of excessive wound healing leading to a poor functional outcome after trauma and surgery [2]. Success‐ ful muscle repair after injury is important for restoring mobility and patients' quality of life. We therefore have an important medical need for drugs that can promote or hasten muscle fibre regeneration, reduce fibrosis, and enhance muscle function [1].

Despite the clinical significance of muscle injuries, current treatment principles for injured skeletal muscle lack a firm scientific basis, and are based on performing RICE (Rest, Ice, Compression, Elevation) and sometimes prescribing non-steroidal anti-inflammatory drugs (NSAIDs). However, increasing evidence indicates that the administration of NSAIDs de‐ creases regeneration and increases fibrosis by inhibiting inflammation [3, 4].

Incomplete muscle fibre regeneration and fibrotic infiltration can lead to long-term function‐ al deficits and physical incapacitation [1]. In recent years of muscle regeneration research, many agents have been described to have a significant antifibrotic effect in patients with heart or kidney disease and systemic sclerosis. Consequently, researchers are testing these for muscle healing, as therapeutic targets are the same. Although these agents play a lifesaving role in the previously mentioned diseases, their importance for muscle injuries could be substantial and for athletes specifically, vital.

Transforming growth factor-Beta (TGF-β) and myostatin have been identified as the main factors that stimulate fibrotic differentiation. It has been shown in *In vitro* and *In vivo* studies that drugs with anti-fibrotic properties that can prevent or minimize scar formation have the potential of standalone or adjuvant therapies (Table 1). Although the World Anti-Doping Agency (WADA) prohibits any use of myostatin inhibitors in athletes, their potential to act only therapeutically at the site of injury without any performance enhancement may play an important role in muscle injury therapy in the future. In the following chapters, various agents are described that reportedly have beneficial effects on muscle healing after injury.


**Table 1.** Agents with proven anti-fibrotic effects in *In vitro* or *In vivo* studies of skeletal muscle regeneration after injury

#### **2.1. Recombinant proteins in muscle regeneration**

cartilage is often less than satisfactory, and rarely restores full function or returns the tissue to its native normal state. The new concept of cartilage tissue preservation uses tissue engi‐ neering technologies, combining new biomaterials as a scaffold, applying growth factors

Skeletal muscle, on the other hand, has a great regenerative capacity; however, this process if often incomplete because of partial fibrous scar formation. Conservative therapies includ‐ ing cryotherapy, resting, physical therapy and pain relief medications don't often give satis‐ factory results and can even be controversial. While surgery is reserved for bigger tissue defects, the need for antifibrotic agents to improve muscle repair after injury is obvious. These and platelet-derived growth factors represent the future of biological therapies for

Novel tissue-specific therapies are mainly molecular, based on pathophysiological processes after injury. Although they seem to significantly accelerate healing and shorten the recovery

While spontaneous muscle fibre regeneration usually occurs after muscle injury, this process can often be slow and incomplete and accompanied by fibrotic infiltration, which compro‐ mises the restoration of contractile function [1]. Scar formation is the result of excessive wound healing leading to a poor functional outcome after trauma and surgery [2]. Success‐ ful muscle repair after injury is important for restoring mobility and patients' quality of life. We therefore have an important medical need for drugs that can promote or hasten muscle

Despite the clinical significance of muscle injuries, current treatment principles for injured skeletal muscle lack a firm scientific basis, and are based on performing RICE (Rest, Ice, Compression, Elevation) and sometimes prescribing non-steroidal anti-inflammatory drugs (NSAIDs). However, increasing evidence indicates that the administration of NSAIDs de‐

Incomplete muscle fibre regeneration and fibrotic infiltration can lead to long-term function‐ al deficits and physical incapacitation [1]. In recent years of muscle regeneration research, many agents have been described to have a significant antifibrotic effect in patients with heart or kidney disease and systemic sclerosis. Consequently, researchers are testing these for muscle healing, as therapeutic targets are the same. Although these agents play a lifesaving role in the previously mentioned diseases, their importance for muscle injuries could

Transforming growth factor-Beta (TGF-β) and myostatin have been identified as the main factors that stimulate fibrotic differentiation. It has been shown in *In vitro* and *In vivo* studies that drugs with anti-fibrotic properties that can prevent or minimize scar formation have the potential of standalone or adjuvant therapies (Table 1). Although the World Anti-Doping

time, their true goal is to achieve better and more functional repair.

**2. Biological therapy for better muscle regeneration**

fibre regeneration, reduce fibrosis, and enhance muscle function [1].

be substantial and for athletes specifically, vital.

creases regeneration and increases fibrosis by inhibiting inflammation [3, 4].

and using stem cells and mechanical stimulation.

this common type of sports injury.

4 Current Issues in Sports and Exercise Medicine

*Follistatin* is an autocrine glycoprotein expressed in nearly all tissues of higher animals, with multiple effects on skeletal muscles as well as other tissues [5]. It is a functional antagonist of several members of the TGF-β family of secreted signalling factors, including myostatin the most powerful inhibitor of muscle growth characterized to date [6, 7]. Follistatin was previously known as FSH-suppressing protein (FSP) as it was found to have inhibitory ef‐ fect on pituitary secretion of follicle-stimulating hormone (FSH) [8]. Research into the devel‐ opment of therapies to antagonize myostatin has led to the discovery of several new functions exhibited by follistatin [9]. Several *In vivo* studies on follistatin have shown that it directly inhibits myostatin and also reduces myostatin-induced muscle wasting after sys‐ temic administration [5, 10]. In recent research, Zhu et al. reported on the stimulative effect of follistatin on MyoD, MyF5, and myogenin expression, which are myogenic transcription factors that promote muscle differentiation. They also showed its inhibitory effect on myo‐ statin, activin A, and TGF-β, all of which are negative regulators of muscle cell differentia‐ tion [9]. Although various myostatin inhibitors have been described, follistatin can modulate other regulators of muscle mass in addition to myostatin [11]. For example, follistatin ad‐ ministration to MSTN-1- mice caused muscle mass increases beyond that stimulated by my‐ ostatin depletion [12, 13], suggesting that this may be a more potent approach than targeting myostatin alone. Intramuscular administration of gene therapy vectors expressing follistatin has increased muscle mass and strength in both young and aged mdx mice, as well as in nonhuman primates [14]. In order to investigate the mechanisms of the follistatin-induced muscle hypertrophy, Gilson et al. used irradiation to destroy the proliferative capacity of satellite cells. They found that not only inhibition of MSTN, but also of activin (ACT) and proliferation of satellite cells are involved in follistatin-induced muscle hypertrophy [12]. Follistatin thus might offer a novel therapeutic strategy for muscular injuries and dystrophy by suppressing the progression of muscle degeneration and permitting skeletal muscle mass restoration [15]. However, before translating follistatin-based therapies from the bench to the bedside, clear mechanisms of how follistatin promotes muscle regeneration require ex‐ tensive investigation.

istration of an IFN-γ receptor-blocking antibody to wild-type mice impaired induction of interferon response factor-1, reduced cell proliferation and decreased the formation of re‐ generating fibres [29]. In 2008, Chen et al. reported a synergistic effect of IFN-γ and IGF-1, which is known to have beneficial effects on muscle regeneration after injury. They showed that IFN-γ injected into injured muscle has the effect of anti-fibrosis, which is more significant than that of IGF-1. They concluded that a combined injection could improve muscle regeneration, while inhibiting fibrosis simultaneously, and promote the healing of injured muscle [34]. *Suramin*, an antiparasitic and antitumor drug, acts as a TGF-β inhibitor by competitively binding to the growth factor's receptor [35, 36]. It has been evaluated for potential clinical applications and has shown antifibrotic effects in chronic kidney diseases, wound healing of rabbit conjunctiva and glaucoma after trabe‐ culotomy [37, 38]. Chan et al. showed that suramin effectively inhibits fibroblast prolifer‐ ation and neutralizes the stimulating effect of TGF-β on the proliferation of fibroblasts *In vitro*. *In vivo*, they showed that the injection of suramin two weeks after strain injury re‐ duces muscle fibrosis and enhances muscle regeneration, and thereby leads to improved muscle strength recovery [39]. Although suramin can lead to side effects when adminis‐ tered intravenously, local intramuscular injection may not elicit the same deleterious ef‐ fects and could be very useful in improving muscle healing [39]. Taniguti et al. evaluated the effect of suramin on fibrosis in mdx mice, where TGF-β is highly unregu‐ lated in the diaphragm and the quadriceps muscle. Mice received suramin for seven weeks while performing exercise on a treadmill to worsen disease progression. Suramin protected limb muscles against damage and reduced the exercise-induced loss of strength over time. These findings support the role of TGF-β in fibrogenesis and myo‐

Novel Therapies for the Management of Sports Injuries

http://dx.doi.org/10.5772/53593

7

*Relaxin*, a polypeptide cytokine/growth factor, is a member of the insulin-like growth factor (IGF) family. The historical role of relaxin has been in reproduction, in which it functions to inhibit uterine contraction and induce growth and softening of the cervix. It can reduce type I and type III collagen deposition, increase procollagenase synthesis, and, by doing so, re‐ duce fibrous scar tissue formation in many tissues [41, 42]. In an *In vivo* model of pulmonary fibrosis, relaxin treatment dramatically decreased bleomycin-induced collagen content in the lung, alveolar thickening, and improved the overall fibrosis score [43]. Recent studies using the relaxin-null mouse model have demonstrated age-associated pulmonary fibrosis in these animals that can be reversed by relaxin treatment [42]. In an innovative study, adenoviralmediated delivery of relaxin was used to treat cardiac fibrosis caused by transgenic overex‐ pression of the β2-adrenergic receptor, resulting in a dramatic decrease in interstitial collagen content in the left ventricle, but not other (nonfibrotic) chambers of the heart [44]. In a recent study, Mu et al. injected relaxin intramuscularly into the injured site of the mouse to observe its function *In vivo*. Results showed that relaxin promoted myogenic differentia‐ tion, migration, and activation of matrix metalloproteinases (MMPs) of cultured myoblasts *In vitro*. Relaxin also promoted activation of muscle satellite cells and increased its local pop‐ ulation compared with non-treated control muscles. Meanwhile, both angiogenesis and re‐ vascularization were increased, while the extended inflammatory reaction was repressed in

necrosis during the later stages of disease in mdx mice [40].

the relaxin-treated injured muscle. [45]

*Decorin* is a component of the extracellular matrix in all collagen-containing tissues [16] and is expressed at high levels in skeletal muscle during early development [17]. It is a small leu‐ cine-rich proteoglycan that can modulate the bioactivity of growth factors and act as a direct signalling molecule to various cells [18]. It was found to neutralize the effects of myostatin in both fibroblasts and myoblasts. It has been implicated in cell proliferation and differentia‐ tion due to its ability to bind growth factors and has been found to interact with collagen, fibronectin and thrombospondin, hence influencing processes such as fibrillogenesis, cell ad‐ hesion, and migration [19]. Fukushima et al. proved that decorin also inactivates the stimu‐ lating effect of TGF-β in myofibroblasts *In vitro*, which has a beneficial effect in muscle fibrosis and leads to enhancement of muscle regeneration and strength [20]. Recent reports showed that the injection of decorin into lacerated muscle improves both muscle structure and function, enabling nearly complete recovery of muscle strength [20-22]. Besides reduc‐ ing fibrosis, decorin promotes muscle cell differentiation by upregulating follistatin, PGC-1α, and myogenic genes, including MyoD [23]. Thus, decorin appears to be a new mol‐ ecule in the myostatin-signalling pathway [24-26]. It has been reported that muscle cells pro‐ duce decorin and myostatin proteins at the same time, and that prenatal and postnatal expression of myostatin is similar [17].

*Interferon (IFN)-γ* is an inflammatory cytokine that was first identified as an antiviral fac‐ tor [27]. A primary function of IFN-γ is activation of macrophages through the classical pathway, which promotes pathogen killing [28]. Later, IFN-γ was recognized as a pleio‐ tropic cytokine that also plays a role in regulating different immune responses as well as influencing many physiological processes [29]. It has also been shown by Foster et al. in 2003 to not only down-regulate endogenous collagen expression, but also to effectively block TGFβ -mediated increases in collagen protein levels [30]. INF-y also inhibits TGFβ signalling by inducing expression of SMAD 7, which participates in a negative feedback loop in the TGFβ signal transduction pathway [31]. Therefore, IFN-γ is thought to be an antifibrotic factor during tissue repair that can reduce synthesis of the extracellular ma‐ trix by disrupting signalling by the profibrotic cytokine TGF-β [31, 32]. IFN-γ has been found to influence skeletal muscle homeostasis and repair. In 1999 Shelton et al. reported age-dependent necrotizing myopathy in a transgenic mouse that constitutively overex‐ presses IFN-γ at the neuromuscular junction [33]. On the other hand, the administration of IFN-γ appears to improve the healing of skeletal muscle, limit fibrosis and therefore limit the function of a regenerating muscle [30]. In 2008, Cheng et al. showed that IFN-γ is expressed at both mRNA and protein levels in skeletal muscle following injury, and that the time course of IFN-γ expression correlated with the accumulation of macrophag‐ es, T-cells, and natural killer cells, as well as myoblasts, in damaged muscle. The admin‐ istration of an IFN-γ receptor-blocking antibody to wild-type mice impaired induction of interferon response factor-1, reduced cell proliferation and decreased the formation of re‐ generating fibres [29]. In 2008, Chen et al. reported a synergistic effect of IFN-γ and IGF-1, which is known to have beneficial effects on muscle regeneration after injury. They showed that IFN-γ injected into injured muscle has the effect of anti-fibrosis, which is more significant than that of IGF-1. They concluded that a combined injection could improve muscle regeneration, while inhibiting fibrosis simultaneously, and promote the healing of injured muscle [34]. *Suramin*, an antiparasitic and antitumor drug, acts as a TGF-β inhibitor by competitively binding to the growth factor's receptor [35, 36]. It has been evaluated for potential clinical applications and has shown antifibrotic effects in chronic kidney diseases, wound healing of rabbit conjunctiva and glaucoma after trabe‐ culotomy [37, 38]. Chan et al. showed that suramin effectively inhibits fibroblast prolifer‐ ation and neutralizes the stimulating effect of TGF-β on the proliferation of fibroblasts *In vitro*. *In vivo*, they showed that the injection of suramin two weeks after strain injury re‐ duces muscle fibrosis and enhances muscle regeneration, and thereby leads to improved muscle strength recovery [39]. Although suramin can lead to side effects when adminis‐ tered intravenously, local intramuscular injection may not elicit the same deleterious ef‐ fects and could be very useful in improving muscle healing [39]. Taniguti et al. evaluated the effect of suramin on fibrosis in mdx mice, where TGF-β is highly unregu‐ lated in the diaphragm and the quadriceps muscle. Mice received suramin for seven weeks while performing exercise on a treadmill to worsen disease progression. Suramin protected limb muscles against damage and reduced the exercise-induced loss of strength over time. These findings support the role of TGF-β in fibrogenesis and myo‐ necrosis during the later stages of disease in mdx mice [40].

proliferation of satellite cells are involved in follistatin-induced muscle hypertrophy [12]. Follistatin thus might offer a novel therapeutic strategy for muscular injuries and dystrophy by suppressing the progression of muscle degeneration and permitting skeletal muscle mass restoration [15]. However, before translating follistatin-based therapies from the bench to the bedside, clear mechanisms of how follistatin promotes muscle regeneration require ex‐

*Decorin* is a component of the extracellular matrix in all collagen-containing tissues [16] and is expressed at high levels in skeletal muscle during early development [17]. It is a small leu‐ cine-rich proteoglycan that can modulate the bioactivity of growth factors and act as a direct signalling molecule to various cells [18]. It was found to neutralize the effects of myostatin in both fibroblasts and myoblasts. It has been implicated in cell proliferation and differentia‐ tion due to its ability to bind growth factors and has been found to interact with collagen, fibronectin and thrombospondin, hence influencing processes such as fibrillogenesis, cell ad‐ hesion, and migration [19]. Fukushima et al. proved that decorin also inactivates the stimu‐ lating effect of TGF-β in myofibroblasts *In vitro*, which has a beneficial effect in muscle fibrosis and leads to enhancement of muscle regeneration and strength [20]. Recent reports showed that the injection of decorin into lacerated muscle improves both muscle structure and function, enabling nearly complete recovery of muscle strength [20-22]. Besides reduc‐ ing fibrosis, decorin promotes muscle cell differentiation by upregulating follistatin, PGC-1α, and myogenic genes, including MyoD [23]. Thus, decorin appears to be a new mol‐ ecule in the myostatin-signalling pathway [24-26]. It has been reported that muscle cells pro‐ duce decorin and myostatin proteins at the same time, and that prenatal and postnatal

*Interferon (IFN)-γ* is an inflammatory cytokine that was first identified as an antiviral fac‐ tor [27]. A primary function of IFN-γ is activation of macrophages through the classical pathway, which promotes pathogen killing [28]. Later, IFN-γ was recognized as a pleio‐ tropic cytokine that also plays a role in regulating different immune responses as well as influencing many physiological processes [29]. It has also been shown by Foster et al. in 2003 to not only down-regulate endogenous collagen expression, but also to effectively block TGFβ -mediated increases in collagen protein levels [30]. INF-y also inhibits TGFβ signalling by inducing expression of SMAD 7, which participates in a negative feedback loop in the TGFβ signal transduction pathway [31]. Therefore, IFN-γ is thought to be an antifibrotic factor during tissue repair that can reduce synthesis of the extracellular ma‐ trix by disrupting signalling by the profibrotic cytokine TGF-β [31, 32]. IFN-γ has been found to influence skeletal muscle homeostasis and repair. In 1999 Shelton et al. reported age-dependent necrotizing myopathy in a transgenic mouse that constitutively overex‐ presses IFN-γ at the neuromuscular junction [33]. On the other hand, the administration of IFN-γ appears to improve the healing of skeletal muscle, limit fibrosis and therefore limit the function of a regenerating muscle [30]. In 2008, Cheng et al. showed that IFN-γ is expressed at both mRNA and protein levels in skeletal muscle following injury, and that the time course of IFN-γ expression correlated with the accumulation of macrophag‐ es, T-cells, and natural killer cells, as well as myoblasts, in damaged muscle. The admin‐

tensive investigation.

6 Current Issues in Sports and Exercise Medicine

expression of myostatin is similar [17].

*Relaxin*, a polypeptide cytokine/growth factor, is a member of the insulin-like growth factor (IGF) family. The historical role of relaxin has been in reproduction, in which it functions to inhibit uterine contraction and induce growth and softening of the cervix. It can reduce type I and type III collagen deposition, increase procollagenase synthesis, and, by doing so, re‐ duce fibrous scar tissue formation in many tissues [41, 42]. In an *In vivo* model of pulmonary fibrosis, relaxin treatment dramatically decreased bleomycin-induced collagen content in the lung, alveolar thickening, and improved the overall fibrosis score [43]. Recent studies using the relaxin-null mouse model have demonstrated age-associated pulmonary fibrosis in these animals that can be reversed by relaxin treatment [42]. In an innovative study, adenoviralmediated delivery of relaxin was used to treat cardiac fibrosis caused by transgenic overex‐ pression of the β2-adrenergic receptor, resulting in a dramatic decrease in interstitial collagen content in the left ventricle, but not other (nonfibrotic) chambers of the heart [44]. In a recent study, Mu et al. injected relaxin intramuscularly into the injured site of the mouse to observe its function *In vivo*. Results showed that relaxin promoted myogenic differentia‐ tion, migration, and activation of matrix metalloproteinases (MMPs) of cultured myoblasts *In vitro*. Relaxin also promoted activation of muscle satellite cells and increased its local pop‐ ulation compared with non-treated control muscles. Meanwhile, both angiogenesis and re‐ vascularization were increased, while the extended inflammatory reaction was repressed in the relaxin-treated injured muscle. [45]

#### **2.2. Platelet-rich plasma in muscle injury therapy**

Among new therapeutic options for achieving more efficient healing, autologous thrombo‐ cytes have a very important place. Although there is no randomized prospective study con‐ firming its value, platelet-rich plasma as a source of autologous growth factors is thought to be used by many sports physicians for treating muscle injuries. The use of platelet-derived preparations was prohibited by WADA until 2011 but was removed from the list after con‐ sidering the lack of current evidence concerning the use of the method for the purposes of performance enhancement as current studies did not reveal a potential for performance en‐ hancement beyond the therapeutic effect [46].

such as platelet factor 4 (PF4) and CD40L. The roles of the above listed growth factors are

VEGF Blood vessels Stimulates vascularisation by stimulating vascular

TGF-β Blood vessels, skin cells, fibroblasts, monocytes Stimulates fibroblast production Stimulates

PF-4 Neutrophils, fibroblasts Stimulates influx of neutrophils Chemotactic for

*In vitro* studies showed that the application of PrP enhances gene expression of the ECM proteins, has mitogenic activity, promotes tenocyte proliferation and induces secretion of other growth factors [47]. Importantly, animal studies showed that all positive effects of PrP

Proliferative and angiogenic action Stimulates

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9

production of collagen type-I and fibronectin

One of the first growth factors to be expressed

angiogenesis and macrophage activation

stimulates collagen synthesis

Stimulates cytokine secretion

Mainly function on bone/skeletal muscle

Chemotactic for fibroblasts Stimulates protein synthesis Enhances bone formation

Stimulates other growth factor secretion Stimulates

Chemotaxic and proliferative action on fibroblasts,

Stimulates epidermal regeneration and wound healing by stimulating keratinocytes and dermal fibroblasts Promotes cell growth, recruitment,

collagen production

endothelial cells

after injury

differentiation

fibroblasts

adaptation and repair

listed in Table 2 [47, 48, 50].

and other cells

**Factor Target tissue/cell Function**

Blood vessels, smooth muscle, skin fibroblasts

PDGF A+B Fibroblasts, smooth muscle cells, chondrocytes, osteoblasts, mesenchymal stem cells

PD-EGF Blood vessel, skin cells fibroblasts and other cells

IGF-I, II Bone, blood vessel, skin, other tissue fibroblasts

**Table 2.** Growth factors released from platelets and their function

**Growth**

FGF

Myostatin,

Leukaemia inhibitory factor (LIF), mechano growth factor (MGF), Bone morphogenetic protein (BMP) (a member of TGF-β superfamily)

PrP (or platelet-rich plasma) may be defined as a volume of the plasma fraction of autolo‐ gous blood having a platelet concentration above the baseline [47]. Normal platelet counts in blood range from 150000/µL to 350000/µL. Platelet-rich plasma contains a 3 to 5-fold in‐ crease in growth factor (GF) concentrations, sometimes more [47,48]. Platelet-rich plasma can only be made from anticoagulated blood [47]. The process begins by adding citrate to whole blood to bind the ionized calcium and inhibit the clotting cascade, followed by one or two centrifugation steps to separate red and white blood cells from platelets. When using anticoagulated PrP, activation is critical, as clotting results in the release of GF from the pla‐ telet α-granules (degranulation). PrP may be activated immediately before application, or it can occur *In vivo*. There is no consensus on the timing of PrP activation, or even whether activation is necessary at all [47]. Approximately 70% of the stored GF is released within 10 minutes, and more than 95% of the GF is released within 1 hour. Some GF is produced by the platelets during the next 8 to 10 days. Originally, bovine thrombin was used as an acti‐ vating agent; however, a rare but major risk of coagulopathy from antibody formation has restricted its use for activation. Calcium chloride (CaCl2) and autologous prepared thrombin are now used for activation instead. The CaCl2 is added during the second centrifugation step to form a dense fibrin matrix in which platelets are trapped and release GF. Soluble col‐ lagen type I may also be used for activation. It is important to note that the composition of commercially derived PrP products differ qualitatively and quantitatively [49]. The most im‐ portant difference is in the concentration of platelets as well as in the concentration of leuko‐ cytes in the preparation. Whether leukocytes have a positive or negative role is not clear yet. The paradigm suggests that neutrophils infiltrate injured tissue and in the process of assist‐ ing the removal of disrupted tissue, exacerbate or increase the original damage [49].

Platelet-rich plasma can potentially enhance healing by the delivery of various GF and cyto‐ kines from the α-granules contained in platelets. Platelets also contain subpopulations of αgranules that undergo differential release during activation, a potentially important point in understanding how PrP is activated and acts [47, 48]. Platelets contain, synthesize and re‐ lease large amounts of biologically active proteins that promote tissue regeneration. Re‐ searchers have identified more than 1100 types of proteins inside platelets or on their surface [47-49]. The most commonly studied platelet proteins include platelet-derived growth factor (PDGF), transforming growth factor (TGF-β), platelet-derived epidermal growth factor (PD-EGF), vascular endothelial growth factor (VEGF), insulin-like growth fac‐ tor I and II (IGF-I, IGF-II), fibroblastic growth factor (FGF), and cytokines, including proteins such as platelet factor 4 (PF4) and CD40L. The roles of the above listed growth factors are listed in Table 2 [47, 48, 50].

**2.2. Platelet-rich plasma in muscle injury therapy**

8 Current Issues in Sports and Exercise Medicine

hancement beyond the therapeutic effect [46].

Among new therapeutic options for achieving more efficient healing, autologous thrombo‐ cytes have a very important place. Although there is no randomized prospective study con‐ firming its value, platelet-rich plasma as a source of autologous growth factors is thought to be used by many sports physicians for treating muscle injuries. The use of platelet-derived preparations was prohibited by WADA until 2011 but was removed from the list after con‐ sidering the lack of current evidence concerning the use of the method for the purposes of performance enhancement as current studies did not reveal a potential for performance en‐

PrP (or platelet-rich plasma) may be defined as a volume of the plasma fraction of autolo‐ gous blood having a platelet concentration above the baseline [47]. Normal platelet counts in blood range from 150000/µL to 350000/µL. Platelet-rich plasma contains a 3 to 5-fold in‐ crease in growth factor (GF) concentrations, sometimes more [47,48]. Platelet-rich plasma can only be made from anticoagulated blood [47]. The process begins by adding citrate to whole blood to bind the ionized calcium and inhibit the clotting cascade, followed by one or two centrifugation steps to separate red and white blood cells from platelets. When using anticoagulated PrP, activation is critical, as clotting results in the release of GF from the pla‐ telet α-granules (degranulation). PrP may be activated immediately before application, or it can occur *In vivo*. There is no consensus on the timing of PrP activation, or even whether activation is necessary at all [47]. Approximately 70% of the stored GF is released within 10 minutes, and more than 95% of the GF is released within 1 hour. Some GF is produced by the platelets during the next 8 to 10 days. Originally, bovine thrombin was used as an acti‐ vating agent; however, a rare but major risk of coagulopathy from antibody formation has restricted its use for activation. Calcium chloride (CaCl2) and autologous prepared thrombin are now used for activation instead. The CaCl2 is added during the second centrifugation step to form a dense fibrin matrix in which platelets are trapped and release GF. Soluble col‐ lagen type I may also be used for activation. It is important to note that the composition of commercially derived PrP products differ qualitatively and quantitatively [49]. The most im‐ portant difference is in the concentration of platelets as well as in the concentration of leuko‐ cytes in the preparation. Whether leukocytes have a positive or negative role is not clear yet. The paradigm suggests that neutrophils infiltrate injured tissue and in the process of assist‐

ing the removal of disrupted tissue, exacerbate or increase the original damage [49].

Platelet-rich plasma can potentially enhance healing by the delivery of various GF and cyto‐ kines from the α-granules contained in platelets. Platelets also contain subpopulations of αgranules that undergo differential release during activation, a potentially important point in understanding how PrP is activated and acts [47, 48]. Platelets contain, synthesize and re‐ lease large amounts of biologically active proteins that promote tissue regeneration. Re‐ searchers have identified more than 1100 types of proteins inside platelets or on their surface [47-49]. The most commonly studied platelet proteins include platelet-derived growth factor (PDGF), transforming growth factor (TGF-β), platelet-derived epidermal growth factor (PD-EGF), vascular endothelial growth factor (VEGF), insulin-like growth fac‐ tor I and II (IGF-I, IGF-II), fibroblastic growth factor (FGF), and cytokines, including proteins


**Table 2.** Growth factors released from platelets and their function

*In vitro* studies showed that the application of PrP enhances gene expression of the ECM proteins, has mitogenic activity, promotes tenocyte proliferation and induces secretion of other growth factors [47]. Importantly, animal studies showed that all positive effects of PrP are neglected when no mechanical stimuli are applied to the tendon during the healing peri‐ od, e.g. if the tendon is immobilised. Besides increased expression of growth factors, PrP was found to increase the expression of matrix degrading enzymes. PrP may also promote antibacterial effects. In addition to opsonophagocytosis, chemotaxis, and oxidative microbi‐ cidal activity, platelets and leukocytes can release a variety of small cationic peptides (anti‐ bacterial peptides) that have bactericidal activity [47].

factors that control cell functions through direct interactions with extracellular parts of the transmembrane receptors. Because thrombocytes represent a major source of growth factors in blood clots, the idea to concentrate them at the site of injury is well accepted. The effects of several individual growth factors have been studied in muscle regeneration. Results from *In vitro* studies are variable; however, their obvious role in regeneration is not to be neglect‐ ed. Growth factors together with macrophages and products of the cyclooxygenase 2 (COX-2) regulatory pathway regulate the inflammatory phase during regeneration in skele‐ tal muscle [55]. IGF-1 and FGF have been shown to have positive effects on healing and fasttwitch tetanic strength in a murine model of muscle laceration [56]. In case of gastrocnemius contusion, the local application of both GFs lead to higher satellite cell activation in bigger muscle fibre development [57]. Despite the promising potential of PrP for treatment of mus‐ cle injuries, some doubts have arisen concerning their use. Due to application of exogenous TGF-β into the tissue, which has been proven to be highly responsible for tissue scarring, some experts are not defenders of this particular therapeutic option. However, in a recent *In vitro* study using human myoblast cell lines it was shown that PrP-derived growth factors promote satellite and muscle cell proliferation as well as inhibiting fibrotic differentiation,

Novel Therapies for the Management of Sports Injuries

http://dx.doi.org/10.5772/53593

11

To date there are no randomized control studies confirming the real role of PrP in treating muscle injuries [59], nor was any sample in clinical studies large enough to represent rele‐ vant statistical data [48]. However, the preclinical data seems to be promising enough for

*Manose-6-Phosphate (M6P)* is a natural inhibitor of TGF-β, a carbohydrate molecule with structural similarity to TGF-β and has been shown to reduce its activity [2, 60]. In an ex‐ periment by Roberts et al., M6P reduced scarring in incision wounds in rats [61]. In an‐ other recent study M6P significantly reduced TGF-β1-mediated transformation of human corneal fibroblasts into myofibroblasts and is therefore a potential modulator of corneal wound healing that may reduce haze after refractive surgery [62]. Regarding the muscu‐ loskeletal system, only a few studies on tendons had been performed to date. In an ex‐ periment by Bates et al. the antifibrotic effect of M6P was under observation *In vitro* and *In vivo*, where primary cell cultures from the rabbit flexor tendon sheath, epitenon, and endotenon were established and supplemented with TGF-β along with increasing doses of M6P. They also transected and immediately repaired rabbit flexor tendons. M6P solu‐ tion was added to the repair sites and compared to a placebo group. They found that M6P is effective in reducing TGF-β upregulated collagen production, which correlated with the finding that a single intraoperative dose of M6P improved the postoperative range of motion. Because of its nonimmunogenic property and because it is easily pro‐ duced, M6P could be an ideal candidate for clinical application in muscle injuries [2]. Yang et al. studied the effects of M6P on TGF-β peptide and receptor expression in or‐ der to provide the experimental basis for preventing tendon-healing adhesion by M6P. They found that M6P can significantly decrease the expressions of TGF-β peptide, TGF-β

mainly due to down-expression of TGF-β [58].

**2.3. Other bioactive agents to improve muscle healing**

clinical studies to take place.

When treating ligament injuries with PrP, animal studies suggest that use of PDGF-BB may improve the quality of healing medial collateral ligaments, and in a similar way PrP may influence the healing of other ligaments [51]. The effect of PrP may be dose and time-related [52]. However, extra-articular ligaments showed better wound site filling and increased the presence of finbrinogen and GF when healing as compared to intra-articular ligaments (like ACL), but the application of PRP can improve the results after ACL injury [53].

To date, no major adverse effects of PrP have been noted in humans. No adverse effects were observed when PrP was infiltrated in 808 patients, mainly with osteoarthritis [54]. The use of bovine thrombin for activation may cause a hypersensitivity reaction and is therefore avoided in modern preparation techniques [47]. To date, there is no evidence of a systemic effect of local PrP injection or carcinogenesis. The latter may be mainly due to the short *In vivo* half-lives and local bioavailability of GF produced by PrP [47]. At the moment, PrP is permitted by WADA (The World Anti-Doping Agency) by all routes of administration since 2011 [47].

The International Olympic Committee Consensus Statement expresses that current evidence suggests the use of PrP to be safe. They proposed that what type of PrP product is used and how it has been prepared, validated and tested should be made clear [47].

Suggested techniques for the application of PrP and post-injection recommendations of the International Olympic Committee Consensus Statement are [47]:


In the XX *(number needed for chapter: physiology of sports injuries)* chapter of this book, all phas‐ es of healing in an injured tissue are described. They are influenced by a number of growth factors that control cell functions through direct interactions with extracellular parts of the transmembrane receptors. Because thrombocytes represent a major source of growth factors in blood clots, the idea to concentrate them at the site of injury is well accepted. The effects of several individual growth factors have been studied in muscle regeneration. Results from *In vitro* studies are variable; however, their obvious role in regeneration is not to be neglect‐ ed. Growth factors together with macrophages and products of the cyclooxygenase 2 (COX-2) regulatory pathway regulate the inflammatory phase during regeneration in skele‐ tal muscle [55]. IGF-1 and FGF have been shown to have positive effects on healing and fasttwitch tetanic strength in a murine model of muscle laceration [56]. In case of gastrocnemius contusion, the local application of both GFs lead to higher satellite cell activation in bigger muscle fibre development [57]. Despite the promising potential of PrP for treatment of mus‐ cle injuries, some doubts have arisen concerning their use. Due to application of exogenous TGF-β into the tissue, which has been proven to be highly responsible for tissue scarring, some experts are not defenders of this particular therapeutic option. However, in a recent *In vitro* study using human myoblast cell lines it was shown that PrP-derived growth factors promote satellite and muscle cell proliferation as well as inhibiting fibrotic differentiation, mainly due to down-expression of TGF-β [58].

To date there are no randomized control studies confirming the real role of PrP in treating muscle injuries [59], nor was any sample in clinical studies large enough to represent rele‐ vant statistical data [48]. However, the preclinical data seems to be promising enough for clinical studies to take place.

## **2.3. Other bioactive agents to improve muscle healing**

are neglected when no mechanical stimuli are applied to the tendon during the healing peri‐ od, e.g. if the tendon is immobilised. Besides increased expression of growth factors, PrP was found to increase the expression of matrix degrading enzymes. PrP may also promote antibacterial effects. In addition to opsonophagocytosis, chemotaxis, and oxidative microbi‐ cidal activity, platelets and leukocytes can release a variety of small cationic peptides (anti‐

When treating ligament injuries with PrP, animal studies suggest that use of PDGF-BB may improve the quality of healing medial collateral ligaments, and in a similar way PrP may influence the healing of other ligaments [51]. The effect of PrP may be dose and time-related [52]. However, extra-articular ligaments showed better wound site filling and increased the presence of finbrinogen and GF when healing as compared to intra-articular ligaments (like

To date, no major adverse effects of PrP have been noted in humans. No adverse effects were observed when PrP was infiltrated in 808 patients, mainly with osteoarthritis [54]. The use of bovine thrombin for activation may cause a hypersensitivity reaction and is therefore avoided in modern preparation techniques [47]. To date, there is no evidence of a systemic effect of local PrP injection or carcinogenesis. The latter may be mainly due to the short *In vivo* half-lives and local bioavailability of GF produced by PrP [47]. At the moment, PrP is permitted by WADA (The World Anti-Doping Agency) by all routes of

The International Olympic Committee Consensus Statement expresses that current evidence suggests the use of PrP to be safe. They proposed that what type of PrP product is used and

Suggested techniques for the application of PrP and post-injection recommendations of the

**1.** PrP is considered to act best when placed at the site of injured tissue; therefore ultra‐ sound guidance is advisable for accurate needle placement to the injured site.

**2.** With respect to tendon administration, there is no agreement on whether the needle should be placed inside the tendon or in the surrounding tendon sheath. In the pres‐ ence of exudates around the tendon, it is suggested that it be evacuated before PrP is

**3.** If PrP is administered at arthroscopy, it is suggested that the injection be administered after emptying the joint of arthroscopic fluid. In the case of open surgery, the applica‐

**4.** Patients should follow general recommendations after an injection with rest, ice, and limb elevation for 48 hours. Depending on the site of treatment and extent and duration of the condition, patients may follow an accelerated rehabilitation protocol under ap‐

In the XX *(number needed for chapter: physiology of sports injuries)* chapter of this book, all phas‐ es of healing in an injured tissue are described. They are influenced by a number of growth

tion of PrP can be undertaken using one of the gel or semi-solid forms.

ACL), but the application of PRP can improve the results after ACL injury [53].

how it has been prepared, validated and tested should be made clear [47].

International Olympic Committee Consensus Statement are [47]:

bacterial peptides) that have bactericidal activity [47].

administration since 2011 [47].

10 Current Issues in Sports and Exercise Medicine

injected.

propriate supervision.

*Manose-6-Phosphate (M6P)* is a natural inhibitor of TGF-β, a carbohydrate molecule with structural similarity to TGF-β and has been shown to reduce its activity [2, 60]. In an ex‐ periment by Roberts et al., M6P reduced scarring in incision wounds in rats [61]. In an‐ other recent study M6P significantly reduced TGF-β1-mediated transformation of human corneal fibroblasts into myofibroblasts and is therefore a potential modulator of corneal wound healing that may reduce haze after refractive surgery [62]. Regarding the muscu‐ loskeletal system, only a few studies on tendons had been performed to date. In an ex‐ periment by Bates et al. the antifibrotic effect of M6P was under observation *In vitro* and *In vivo*, where primary cell cultures from the rabbit flexor tendon sheath, epitenon, and endotenon were established and supplemented with TGF-β along with increasing doses of M6P. They also transected and immediately repaired rabbit flexor tendons. M6P solu‐ tion was added to the repair sites and compared to a placebo group. They found that M6P is effective in reducing TGF-β upregulated collagen production, which correlated with the finding that a single intraoperative dose of M6P improved the postoperative range of motion. Because of its nonimmunogenic property and because it is easily pro‐ duced, M6P could be an ideal candidate for clinical application in muscle injuries [2]. Yang et al. studied the effects of M6P on TGF-β peptide and receptor expression in or‐ der to provide the experimental basis for preventing tendon-healing adhesion by M6P. They found that M6P can significantly decrease the expressions of TGF-β peptide, TGF-β receptor, TGF-β mRNA and may therefore provide a means of modulating the effects of TGF-β on adhesion formation in flexor tendon wound healing [63].

fibrosis. Myocardium exposed to decreased levels of angiotensin II, either through the use of ACE inhibitors or ARBs, has also demonstrated a measurably improved function [75, 76]. However, it has been suggested that ACE inhibitor-induced positive effects may also be mediated by direct action on the skeletal muscle [70]. Recent studies reported on the beneficial side effects of ACE inhibitors in hypertensive patients free of chronic heart failure [70]. Treatment with ACE inhibitors was associated with better performance and muscular outcomes, and genetic studies also support the hypothesis that the ACE system may be involved in physical performance and skeletal muscle function [77, 78]. More‐ over, elite athletes, particularly those in endurance sports, have also demonstrated find‐ ings consistent with inherent differences in their body's metabolism of angiotensin II, with decreased exposure resulting in improved skeletal muscle function [70, 79, 80]. In an *In vitro* and *In vivo* study by Bedair et al. angiotensin receptor blocker therapy signifi‐ cantly reduced fibrosis and led to an increase in the number of regenerating myofibres in acutely injured skeletal muscle and may therefore provide a safe, clinically available

Novel Therapies for the Management of Sports Injuries

http://dx.doi.org/10.5772/53593

13

Damage to articular cartilage is of great clinical consequence since the cartilage tissue comprises of limited intrinsic potential for healing due to the lack of blood supply and subsequent incomplete repair by local chondrocytes with inferior fibrocartilage forma‐ tion. Surgical intervention is often the only option, but the repair of damaged cartilage is often less than satisfactory, and rarely restores full function or returns the tissue to its

Tissue engineering of articular cartilage still remains challenging due to the special structure of cartilage tissue consisting of multiphasic cellular architecture and great weight-bearing characteristics. Good knowledge and understanding of cartilage structure, its metabolism, and the process of chondrogenesis enables *In vitro* cartilage production in terms of tissue en‐ gineering. The new concept of cartilage tissue preservation uses tissue-engineering technol‐ ogies, combining new biomaterials as a scaffold, the application of growth factors, the use of stem cells, and mechanical stimulation. Scaffolds enable 3-dimensional environmental con‐ ditions to promote hyaline-like cartilage production. Additionally, various types of growth factors, which are the endogenous regulators of chondrogenesis, can be applied locally or in culture condition to promote cartilage development. Further studies are attempting to create the ideal scaffold and explore the synergistic effect of concomitant application of growth fac‐ tors and mechanical loading. In clinical practice, new generations of autologous chondrocyte implantation (ACI) are based on the use of biodegradable materials that serve as temporary cell-carriers for the *In vitro* growth and subsequent implantation into the cartilage defect. Moreover, single stage procedures appear attractive, as they consist of natural chondral tis‐ sue inserted on the carrier and can reduce cost and patient morbidity since they avoid sec‐

treatment for improving healing after skeletal muscle injury [81].

**3. Future perspectives of cartilage tissue repair**

ond operation and cell culturing procedures.

native normal state.

Although *N-acetylcysteine (NAC)* is a non-toxic aminothiol widely known as an antidote to acetaminophen overdose, it has multiple other uses supported by varying levels of evidence, like chronic obstructive pulmonary disease exacerbation, prevention of con‐ trast-induced kidney damage during imaging procedures, and treatment of infertility in patients with clomiphene-resistant polycystic ovary syndrome [64]. Recent studies have emphasized the role of oxidative stress as the molecular basis of lung fibrosis. NAC has a strong reductive capacity that inhibits the TGF-β-stimulated collagen production in cul‐ tured fibroblasts [65]. Moreover, it has been shown by Hagiwara et al. that the aerosol‐ ized administration of NAC attenuates the lung fibrosis induced by bleomycin in mice [66] suggesting the suppressing effects of antioxidant TGF-b1 signalling *In vitro* and *In vivo*. A recent study demonstrated that NAC reduces the disulfide bonds of TGF-b1 and changes the bioactive form to the inactive form [67]. It also changes the binding activity of TGF-b1 to its receptor in hepatic stellate cells, suggesting that the effect of antioxidant NAC is based on a direct blockade of TGF-b1 function and signalling. However, whether NAC can modulate the TGF-b1-induced tissue repair, mediator production, and differen‐ tiation in human lung fibroblasts has not been fully elucidated [68]. Sugiura et al. recent‐ ly reported that NAC affects the production of fibronectin and vascular endothelial growth factor (VEGF), which are believed to be important mediators of repair and re‐ modelling. The effect of NAC on the TGF-β induces differentiation to myofibroblasts by assessing a smooth muscle actin (a-SMA) expression [68]. Although treatment with NAC has been shown to attenuate interstitial fibrosis in mouse models of hypertrophic cardio‐ myopathy mutation and several other pathological states [69], no studies have been per‐ formed on the effects of NAC in muscle regeneration after injury. However, since it has been shown to have beneficial effects on diseases that share the same pathophysiological core with the process of muscle fibrosis, the effects of NAC could potentially be benefi‐ cial in this pathology as well. Because it is a safe, inexpensive, and well-tolerated antioxi‐ dant with a well-defined mechanism of action, a highly favourable risk/benefit ratio and low rate of adverse events [64], researchers will probably study the effects of NAC in muscle repair in the future.

*Angiotensin-converting enzyme (ACE) inhibitors and angiotensin receptor blockers (ARBs)* have also shown beneficial effects in studies of muscle healing. ACE is a circulating enzyme that participates in the body's renin-angiotensin-aldosterone system (RAAS), which mod‐ ulates extracellular volume and arterial vasoconstriction. Its inhibitors reduce morbidity, mortality, hospital admissions, and decline in physical function and exercise capacity in congestive heart failure patients. These therapeutic effects are attributed primarily to ben‐ eficial cardiovascular actions of these drugs [70]. Observations have linked pathologic fibrosis in various organ systems to the local effects of angiotensin II. The modulation of angiotensin II with angiotensin-converting enzyme inhibitors or angiotensin II receptor blockers has demonstrated decreased fibrosis and improved function in liver, kidney, and lung tissue [71-74]. Injured cardiac muscle also demonstrates dysfunction related to fibrosis. Myocardium exposed to decreased levels of angiotensin II, either through the use of ACE inhibitors or ARBs, has also demonstrated a measurably improved function [75, 76]. However, it has been suggested that ACE inhibitor-induced positive effects may also be mediated by direct action on the skeletal muscle [70]. Recent studies reported on the beneficial side effects of ACE inhibitors in hypertensive patients free of chronic heart failure [70]. Treatment with ACE inhibitors was associated with better performance and muscular outcomes, and genetic studies also support the hypothesis that the ACE system may be involved in physical performance and skeletal muscle function [77, 78]. More‐ over, elite athletes, particularly those in endurance sports, have also demonstrated find‐ ings consistent with inherent differences in their body's metabolism of angiotensin II, with decreased exposure resulting in improved skeletal muscle function [70, 79, 80]. In an *In vitro* and *In vivo* study by Bedair et al. angiotensin receptor blocker therapy signifi‐ cantly reduced fibrosis and led to an increase in the number of regenerating myofibres in acutely injured skeletal muscle and may therefore provide a safe, clinically available treatment for improving healing after skeletal muscle injury [81].

## **3. Future perspectives of cartilage tissue repair**

receptor, TGF-β mRNA and may therefore provide a means of modulating the effects of

Although *N-acetylcysteine (NAC)* is a non-toxic aminothiol widely known as an antidote to acetaminophen overdose, it has multiple other uses supported by varying levels of evidence, like chronic obstructive pulmonary disease exacerbation, prevention of con‐ trast-induced kidney damage during imaging procedures, and treatment of infertility in patients with clomiphene-resistant polycystic ovary syndrome [64]. Recent studies have emphasized the role of oxidative stress as the molecular basis of lung fibrosis. NAC has a strong reductive capacity that inhibits the TGF-β-stimulated collagen production in cul‐ tured fibroblasts [65]. Moreover, it has been shown by Hagiwara et al. that the aerosol‐ ized administration of NAC attenuates the lung fibrosis induced by bleomycin in mice [66] suggesting the suppressing effects of antioxidant TGF-b1 signalling *In vitro* and *In vivo*. A recent study demonstrated that NAC reduces the disulfide bonds of TGF-b1 and changes the bioactive form to the inactive form [67]. It also changes the binding activity of TGF-b1 to its receptor in hepatic stellate cells, suggesting that the effect of antioxidant NAC is based on a direct blockade of TGF-b1 function and signalling. However, whether NAC can modulate the TGF-b1-induced tissue repair, mediator production, and differen‐ tiation in human lung fibroblasts has not been fully elucidated [68]. Sugiura et al. recent‐ ly reported that NAC affects the production of fibronectin and vascular endothelial growth factor (VEGF), which are believed to be important mediators of repair and re‐ modelling. The effect of NAC on the TGF-β induces differentiation to myofibroblasts by assessing a smooth muscle actin (a-SMA) expression [68]. Although treatment with NAC has been shown to attenuate interstitial fibrosis in mouse models of hypertrophic cardio‐ myopathy mutation and several other pathological states [69], no studies have been per‐ formed on the effects of NAC in muscle regeneration after injury. However, since it has been shown to have beneficial effects on diseases that share the same pathophysiological core with the process of muscle fibrosis, the effects of NAC could potentially be benefi‐ cial in this pathology as well. Because it is a safe, inexpensive, and well-tolerated antioxi‐ dant with a well-defined mechanism of action, a highly favourable risk/benefit ratio and low rate of adverse events [64], researchers will probably study the effects of NAC in

*Angiotensin-converting enzyme (ACE) inhibitors and angiotensin receptor blockers (ARBs)* have also shown beneficial effects in studies of muscle healing. ACE is a circulating enzyme that participates in the body's renin-angiotensin-aldosterone system (RAAS), which mod‐ ulates extracellular volume and arterial vasoconstriction. Its inhibitors reduce morbidity, mortality, hospital admissions, and decline in physical function and exercise capacity in congestive heart failure patients. These therapeutic effects are attributed primarily to ben‐ eficial cardiovascular actions of these drugs [70]. Observations have linked pathologic fibrosis in various organ systems to the local effects of angiotensin II. The modulation of angiotensin II with angiotensin-converting enzyme inhibitors or angiotensin II receptor blockers has demonstrated decreased fibrosis and improved function in liver, kidney, and lung tissue [71-74]. Injured cardiac muscle also demonstrates dysfunction related to

TGF-β on adhesion formation in flexor tendon wound healing [63].

12 Current Issues in Sports and Exercise Medicine

muscle repair in the future.

Damage to articular cartilage is of great clinical consequence since the cartilage tissue comprises of limited intrinsic potential for healing due to the lack of blood supply and subsequent incomplete repair by local chondrocytes with inferior fibrocartilage forma‐ tion. Surgical intervention is often the only option, but the repair of damaged cartilage is often less than satisfactory, and rarely restores full function or returns the tissue to its native normal state.

Tissue engineering of articular cartilage still remains challenging due to the special structure of cartilage tissue consisting of multiphasic cellular architecture and great weight-bearing characteristics. Good knowledge and understanding of cartilage structure, its metabolism, and the process of chondrogenesis enables *In vitro* cartilage production in terms of tissue en‐ gineering. The new concept of cartilage tissue preservation uses tissue-engineering technol‐ ogies, combining new biomaterials as a scaffold, the application of growth factors, the use of stem cells, and mechanical stimulation. Scaffolds enable 3-dimensional environmental con‐ ditions to promote hyaline-like cartilage production. Additionally, various types of growth factors, which are the endogenous regulators of chondrogenesis, can be applied locally or in culture condition to promote cartilage development. Further studies are attempting to create the ideal scaffold and explore the synergistic effect of concomitant application of growth fac‐ tors and mechanical loading. In clinical practice, new generations of autologous chondrocyte implantation (ACI) are based on the use of biodegradable materials that serve as temporary cell-carriers for the *In vitro* growth and subsequent implantation into the cartilage defect. Moreover, single stage procedures appear attractive, as they consist of natural chondral tis‐ sue inserted on the carrier and can reduce cost and patient morbidity since they avoid sec‐ ond operation and cell culturing procedures.

#### **3.1. Tissue engineering of articular cartilage**

The field of tissue engineering uses the principles of cell biology, engineering, and medi‐ cine in order to produce such a construct that can successfully replace damaged tissue. Engineered tissue should comprise of the characteristics of the native intact tissue in terms of histological structure, morphology, function, and mechanical properties. The challenges of tissue engineering of articular cartilage include isolating and culturing cells to gain relevant and reproducible constructs with good durability *In vivo*. A demanding and crucial role in the process of *In vitro* culturing represents phenotype regulation, *In vitro* expansion, scaffold design, the use of bioreactor, etc. All of these components should be optimized to advance cartilage tissue engineering from culturing to clinical ap‐ plication. In particular, there is still a need to develop suitable scaffolds that can provide a 3-dimensional environment for the cell to adhere to and adequately proliferate. Addi‐ tionally, scaffolds should be mechanically strong and biocompatible. Cartilage tissue en‐ gineering usually uses bioactive molecules (growth factors) and mechanical loading to promote differentiation towards a cartilage phenotype [82].

(ether ester) copolymer scaffolds). Additionally, the combination of different materials is ap‐ plied [88], e.g. gelatin and hyaluronic acid have been combined with a fibrin glue and chon‐ droitin-6-suplphate. Furthermore, scaffolds to support bone formation (hydroxiapatite)

Novel Therapies for the Management of Sports Injuries

http://dx.doi.org/10.5772/53593

15

The new approach represents the development of smart matrices that actively support carti‐ lage formation and not only provide mechanical function but also allow control over cell metabolism, tissue formation, enable adjustment of the physical properties, inclusion of ECM motifs and active substances such as GF incorporated in microspheres to allow tempo‐

Although most of these developments seem to be promising for future clinical application, they are mainly used *In vitro* and in animal models [84-87]. Chondrocytes previously ex‐ panded and seeded onto scaffold produce a characteristic ECM rich in proteoglycans, colla‐ gen type II and aggrecan. After implantation in the full thickness femoral defect in rabbits, it promoted healing and regenerated a cartilage-like tissue [89]. The future prospective for car‐ tilage repair is also based on the quality of integration between the newly formed tissue and

Growth factors and their signaling pathways are the essential regulators of chondrogenesis dur‐ ing tissue engineering and thus are the prime candidates for engineering of cartilage tissue. Chondrogenesis is a multistep process that comprises of several steps: precursor cell condensa‐ tion, differentiation towards chondrogenic phenotype, secretion of cartilage specific ECM com‐ ponents (collagen type II, aggrecan and others), chondrocytes proliferation in the area of growth plate, further differentiation towards hypertrophy, and replacement of cartilage with the bone

**Figure 1.** Schematic diagram of different stages of chondrogenesis (including main growth factors and altera‐

tissue. All of the steps are regulated by different and overlapping signals (Figure 1).

were combined with the chitosan to enable the regeneration of osteochondral lesions.

rally and spatially controlled delivery of GF in scaffolds [87].

the native tissue for achieving stable healing.

*3.1.2. Growth factors*

tions in ECM)

#### *3.1.1. Biomaterials and scaffolds*

Scaffolds are engineered extracellular matrices that serve as an artificial structure capable of supporting 3-dimensional tissue formation. Cells are often implanted or seeded into these scaffolds and different biomaterials are used that allow cell attachment, growth, differentia‐ tion, and regeneration of functional cartilage tissue. Scaffolds were developed with the aim to improve the biological performance of chondrocytes as well as render the surgical techni‐ que easier. In cartilage tissue engineering, scaffolds should comprise of the following char‐ acteristics; they should be biocompatible (not triggering inflammatory response and not toxic), offering temporary support to cells, mechanically strong to protect cells and with‐ stand *In vivo* forces during joint movement, and bioactive to provide cellular attachment and migration. Additionally, scaffolds should be biodegradable, serving as a temporary con‐ struct that is later replaced by a newly synthesized extracellular matrix (ECM) [83]. With time, the transplanted chondrocytes take over the function of the cell carrier; therefore they should be degraded once they have served their purpose. The ideal biodegradable scaffold should also enable uniform cell spreading possible [84-87].

In general, scaffolds are divided into natural material, synthetic polymers, and new materi‐ als. Natural materials include collagen, hyaluronic acid, fibrin glue, chitosan, agarose, and alginate. Their advantage is excellent biocompatibility since they are natural bodily constitu‐ ents, thus degradation is physiological and non-toxic. On the other hand, their use includes sourcing, processing, and the risk of disease transmission. Synthetic polymers, especially PLA (poly alfa-hydroxil acid polymers) and PLGA (*poly lactic-co-glycolic acid*) are also widely used due to the approval of the FDA. Their major advantage is the design flexibility (highly porous 3-dimensional structure) and no risk of disease transmission. The disadvantages are acid degradation products, inflammatory response, and chronic inflammation due to high molecular weight proteins. Novel materials have been introduced recently, such as silk, cel‐ lulose, and other synthetic materials (biodegradable elastomer, polycaprolactone, poly (ether ester) copolymer scaffolds). Additionally, the combination of different materials is ap‐ plied [88], e.g. gelatin and hyaluronic acid have been combined with a fibrin glue and chon‐ droitin-6-suplphate. Furthermore, scaffolds to support bone formation (hydroxiapatite) were combined with the chitosan to enable the regeneration of osteochondral lesions.

The new approach represents the development of smart matrices that actively support carti‐ lage formation and not only provide mechanical function but also allow control over cell metabolism, tissue formation, enable adjustment of the physical properties, inclusion of ECM motifs and active substances such as GF incorporated in microspheres to allow tempo‐ rally and spatially controlled delivery of GF in scaffolds [87].

Although most of these developments seem to be promising for future clinical application, they are mainly used *In vitro* and in animal models [84-87]. Chondrocytes previously ex‐ panded and seeded onto scaffold produce a characteristic ECM rich in proteoglycans, colla‐ gen type II and aggrecan. After implantation in the full thickness femoral defect in rabbits, it promoted healing and regenerated a cartilage-like tissue [89]. The future prospective for car‐ tilage repair is also based on the quality of integration between the newly formed tissue and the native tissue for achieving stable healing.

## *3.1.2. Growth factors*

**3.1. Tissue engineering of articular cartilage**

14 Current Issues in Sports and Exercise Medicine

promote differentiation towards a cartilage phenotype [82].

should also enable uniform cell spreading possible [84-87].

*3.1.1. Biomaterials and scaffolds*

The field of tissue engineering uses the principles of cell biology, engineering, and medi‐ cine in order to produce such a construct that can successfully replace damaged tissue. Engineered tissue should comprise of the characteristics of the native intact tissue in terms of histological structure, morphology, function, and mechanical properties. The challenges of tissue engineering of articular cartilage include isolating and culturing cells to gain relevant and reproducible constructs with good durability *In vivo*. A demanding and crucial role in the process of *In vitro* culturing represents phenotype regulation, *In vitro* expansion, scaffold design, the use of bioreactor, etc. All of these components should be optimized to advance cartilage tissue engineering from culturing to clinical ap‐ plication. In particular, there is still a need to develop suitable scaffolds that can provide a 3-dimensional environment for the cell to adhere to and adequately proliferate. Addi‐ tionally, scaffolds should be mechanically strong and biocompatible. Cartilage tissue en‐ gineering usually uses bioactive molecules (growth factors) and mechanical loading to

Scaffolds are engineered extracellular matrices that serve as an artificial structure capable of supporting 3-dimensional tissue formation. Cells are often implanted or seeded into these scaffolds and different biomaterials are used that allow cell attachment, growth, differentia‐ tion, and regeneration of functional cartilage tissue. Scaffolds were developed with the aim to improve the biological performance of chondrocytes as well as render the surgical techni‐ que easier. In cartilage tissue engineering, scaffolds should comprise of the following char‐ acteristics; they should be biocompatible (not triggering inflammatory response and not toxic), offering temporary support to cells, mechanically strong to protect cells and with‐ stand *In vivo* forces during joint movement, and bioactive to provide cellular attachment and migration. Additionally, scaffolds should be biodegradable, serving as a temporary con‐ struct that is later replaced by a newly synthesized extracellular matrix (ECM) [83]. With time, the transplanted chondrocytes take over the function of the cell carrier; therefore they should be degraded once they have served their purpose. The ideal biodegradable scaffold

In general, scaffolds are divided into natural material, synthetic polymers, and new materi‐ als. Natural materials include collagen, hyaluronic acid, fibrin glue, chitosan, agarose, and alginate. Their advantage is excellent biocompatibility since they are natural bodily constitu‐ ents, thus degradation is physiological and non-toxic. On the other hand, their use includes sourcing, processing, and the risk of disease transmission. Synthetic polymers, especially PLA (poly alfa-hydroxil acid polymers) and PLGA (*poly lactic-co-glycolic acid*) are also widely used due to the approval of the FDA. Their major advantage is the design flexibility (highly porous 3-dimensional structure) and no risk of disease transmission. The disadvantages are acid degradation products, inflammatory response, and chronic inflammation due to high molecular weight proteins. Novel materials have been introduced recently, such as silk, cel‐ lulose, and other synthetic materials (biodegradable elastomer, polycaprolactone, poly

Growth factors and their signaling pathways are the essential regulators of chondrogenesis dur‐ ing tissue engineering and thus are the prime candidates for engineering of cartilage tissue. Chondrogenesis is a multistep process that comprises of several steps: precursor cell condensa‐ tion, differentiation towards chondrogenic phenotype, secretion of cartilage specific ECM com‐ ponents (collagen type II, aggrecan and others), chondrocytes proliferation in the area of growth plate, further differentiation towards hypertrophy, and replacement of cartilage with the bone tissue. All of the steps are regulated by different and overlapping signals (Figure 1).

**Figure 1.** Schematic diagram of different stages of chondrogenesis (including main growth factors and altera‐ tions in ECM)

In general, GFs are endogenous regulators of chondrogenesis and their logical choice of use appears to be promising to stimulate anabolic responses and the repair of articular cartilage. For example, in *In vitro* cartilage formation it is essential to promote early chondrocytes dif‐ ferentiation and proliferation while trying to prevent further differentiation towards hyper‐ trophy. However, the design and optimization of all GF's for a particular tissue engineering and/or local application is complex and has to consider the combination of different factors, their timing, concentrations, etc.

cartilage, and fat. Currently, researchers are exploring the possibilities of manipulating the stem cells under laboratory conditions into mature chondrocytes that can then be integrated into scaffolds for later application [94,95]. There are many studies reporting the isolation and characterization of MSCs from adult human synovium and periosteum and providing evidence about their multipotency at the single cell level [96, 97]. It was also demonstrated that human MSCs from different tissues possess distinctive biological properties [98]. Addi‐ tionally, there is still the issue of whether MSCs are capable of forming stable hyaline-like cartilage as opposed to that formed during the process of endochondral ossification, which is later replaced with bone. The variability in biological responses of MSCs and no standar‐ dized MSC bioprocessing to obtain MSC preparations with consistent, reproducible, and quality-controlled biological potency for therapeutic applications limit the use of MSCs in clinical practice. On the other hand, the use of MSCs as chondrocyte substitutes in an ACIequivalent procedure has become highly attractive since MCSs are easily accessible, easy to isolate and capable of expanding into culture as opposed to articular chondrocytes with lim‐

Novel Therapies for the Management of Sports Injuries

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Furthermore, MCSs appear to be immune privileged under certain conditions [94-97]. Alto‐ gether, these properties would allow the generation of large batches of quality controlled MCSs preparations ready for allogenic use. In addition, limitations in patient-to-patient vari‐ ability would be circumvented [93]. In animal models, MSCs have already shown significant potential for cartilage repair and novel approaches using MSCs as an alternative cell source to patient-derived chondrocytes are being tested [89, 99]. However, preclinical and clinical studies should be conducted in order to evaluate whether the implantation of MCSs results in a cartilage formation that is as durable as the one following the implantation of articular chondrocytes. Additionally, the application of MCSs can be further expanded to non-local‐

A potential strategy in cartilage functional tissue engineering comprises of the effect of me‐ chanical stimuli applied during *In vitro* tissue formation. Several studies demonstrated that mechanical forces stimulate the synthesis of ECM and may even enhance the mechanical properties of the developing tissue [101, 102]. After physical stimuli are applied to the tissue, the intracellular mechanisms convert mechanical signals into biochemical events responsible for regulating the transcription of genes governing cell growth and differentiation. This ef‐ fect proved to be further intensified with concomitant application of growth factors and me‐ chanical load in a synergistic manner [103, 104]. Various bioreactor systems have been developed in order to form cartilaginous grafts with similar biomechanical characteristics compared to native intact cartilage tissue [105-107]. Due to the complexity of the load and motion patterns within an articular joint, new bioreactors with multi-axial loading patterns are designed to recreate the *In vivo* situation [106, 107]. The interesting aspect of cartilage re‐ pair in clinical practice represents cell-based strategies that are not culture-intensive and al‐ low single surgical procedure. Hence, a natural environment is the most suitable for tissue

development therefore cell culture and bioreactors may not be required [108].

ited proliferative capacity and rapid de-differentiation *In vitro*.

ized chronic lesions in osteoarthritis patients [100].

*3.1.4. Mechanical load*

The most important factors currently used in tissue engineering are the members of trans‐ forming growth factor β (TGF-β) family, Bone Morphogenetic Protein (BMP), Insulin-like growth factors (IGF), Fibroblast Growth Factors (FGF), especially FGF-2 and FGF-18, Epider‐ mal Growth Factor (EGF) and Vascular-Endothelial Growth Factors (VEGFs). The summary of the effect of different GFs on chondrocytes/cartilage is presented in Table 4. It is becoming increasingly apparent that GFs work synergistically and simultaneously to induce and pro‐ mote cartilage formation; e.g.: TGF-β1 and FGF-2 [90] together with IGF-1 [91], BMP-7 and IGF-1 [91], TGFβ3 and BMP [92], etc. Based on the concept that several different GFs work in combination during cartilage repair, the use of PrP, autologous conditioned serum (ACS), and bone marrow concentrate were used in cartilage repair techniques [93].


**Table 3.** Proven effects of various growth factors on cartilage

#### *3.1.3. Mesenchymal stem cells*

Mesenchymal stem cells (MSCs) are pluripotent cells found in multiple human adult tissues including bone marrow, synovial tissues, and adipose tissues. They are of great interest for scientists involved in cell therapy and tissue engineering since they have self-renewal ca‐ pacity and multilineage differentiation potential. Depending on the cultivation conditions, they can differentiate into adipogenic, ostegenic or chondrogenic cells as well as form bone, cartilage, and fat. Currently, researchers are exploring the possibilities of manipulating the stem cells under laboratory conditions into mature chondrocytes that can then be integrated into scaffolds for later application [94,95]. There are many studies reporting the isolation and characterization of MSCs from adult human synovium and periosteum and providing evidence about their multipotency at the single cell level [96, 97]. It was also demonstrated that human MSCs from different tissues possess distinctive biological properties [98]. Addi‐ tionally, there is still the issue of whether MSCs are capable of forming stable hyaline-like cartilage as opposed to that formed during the process of endochondral ossification, which is later replaced with bone. The variability in biological responses of MSCs and no standar‐ dized MSC bioprocessing to obtain MSC preparations with consistent, reproducible, and quality-controlled biological potency for therapeutic applications limit the use of MSCs in clinical practice. On the other hand, the use of MSCs as chondrocyte substitutes in an ACIequivalent procedure has become highly attractive since MCSs are easily accessible, easy to isolate and capable of expanding into culture as opposed to articular chondrocytes with lim‐ ited proliferative capacity and rapid de-differentiation *In vitro*.

Furthermore, MCSs appear to be immune privileged under certain conditions [94-97]. Alto‐ gether, these properties would allow the generation of large batches of quality controlled MCSs preparations ready for allogenic use. In addition, limitations in patient-to-patient vari‐ ability would be circumvented [93]. In animal models, MSCs have already shown significant potential for cartilage repair and novel approaches using MSCs as an alternative cell source to patient-derived chondrocytes are being tested [89, 99]. However, preclinical and clinical studies should be conducted in order to evaluate whether the implantation of MCSs results in a cartilage formation that is as durable as the one following the implantation of articular chondrocytes. Additionally, the application of MCSs can be further expanded to non-local‐ ized chronic lesions in osteoarthritis patients [100].

#### *3.1.4. Mechanical load*

In general, GFs are endogenous regulators of chondrogenesis and their logical choice of use appears to be promising to stimulate anabolic responses and the repair of articular cartilage. For example, in *In vitro* cartilage formation it is essential to promote early chondrocytes dif‐ ferentiation and proliferation while trying to prevent further differentiation towards hyper‐ trophy. However, the design and optimization of all GF's for a particular tissue engineering and/or local application is complex and has to consider the combination of different factors,

The most important factors currently used in tissue engineering are the members of trans‐ forming growth factor β (TGF-β) family, Bone Morphogenetic Protein (BMP), Insulin-like growth factors (IGF), Fibroblast Growth Factors (FGF), especially FGF-2 and FGF-18, Epider‐ mal Growth Factor (EGF) and Vascular-Endothelial Growth Factors (VEGFs). The summary of the effect of different GFs on chondrocytes/cartilage is presented in Table 4. It is becoming increasingly apparent that GFs work synergistically and simultaneously to induce and pro‐ mote cartilage formation; e.g.: TGF-β1 and FGF-2 [90] together with IGF-1 [91], BMP-7 and IGF-1 [91], TGFβ3 and BMP [92], etc. Based on the concept that several different GFs work in combination during cartilage repair, the use of PrP, autologous conditioned serum (ACS),

**Growth factors Effect on chondrocytes/cartilage**

catabolic activity

degradation

catabolism

synthesis

stimulates ECM

turnover (increased aggrecan degradation)

and bone marrow concentrate were used in cartilage repair techniques [93].

TGF-β Transforming Growth Factor β Stimulates synthesis of ECM Decreases

BMP-2 Bone Morphogenetic Protein - 2 Stimulates synthesis of ECM Increased ECM

BMP-7 Bone Morphogenetic Protein - 7 Stimulates ECM synthesis Decrease cartilage

IGF-1 Insulin-like growth factors Stimulates ECM synthesis Decreases matrix

FGF-18 Fibroblast Growth Factors-18 Increases chondrocyte proliferation and

**Table 3.** Proven effects of various growth factors on cartilage

*3.1.3. Mesenchymal stem cells*

FGF-2 Fibroblast Growth Factors-2 Decreases aggrecanase activity Antagonizes PG

Mesenchymal stem cells (MSCs) are pluripotent cells found in multiple human adult tissues including bone marrow, synovial tissues, and adipose tissues. They are of great interest for scientists involved in cell therapy and tissue engineering since they have self-renewal ca‐ pacity and multilineage differentiation potential. Depending on the cultivation conditions, they can differentiate into adipogenic, ostegenic or chondrogenic cells as well as form bone,

their timing, concentrations, etc.

16 Current Issues in Sports and Exercise Medicine

A potential strategy in cartilage functional tissue engineering comprises of the effect of me‐ chanical stimuli applied during *In vitro* tissue formation. Several studies demonstrated that mechanical forces stimulate the synthesis of ECM and may even enhance the mechanical properties of the developing tissue [101, 102]. After physical stimuli are applied to the tissue, the intracellular mechanisms convert mechanical signals into biochemical events responsible for regulating the transcription of genes governing cell growth and differentiation. This ef‐ fect proved to be further intensified with concomitant application of growth factors and me‐ chanical load in a synergistic manner [103, 104]. Various bioreactor systems have been developed in order to form cartilaginous grafts with similar biomechanical characteristics compared to native intact cartilage tissue [105-107]. Due to the complexity of the load and motion patterns within an articular joint, new bioreactors with multi-axial loading patterns are designed to recreate the *In vivo* situation [106, 107]. The interesting aspect of cartilage re‐ pair in clinical practice represents cell-based strategies that are not culture-intensive and al‐ low single surgical procedure. Hence, a natural environment is the most suitable for tissue development therefore cell culture and bioreactors may not be required [108].

## **3.2. Clinical application of tissue engineering in cartilage repair**

Cartilage repair has gained great interest since autologous cartilage implantation (ACI) has become an established treatment. The first line of treatment options remains microfractur‐ ing, due to low cost, arthroscopic procedure, and ease of performance.

scaffolds is the risk of the harmful effect of degradation products on surrounding tissue. A comparison of the first and second-generation ACI has shown rather equivalent short-term clinical outcomes, with similar complications and a similar rate of reoperation [110]. A variety of scaffolds have been introduced, implanted either through a small arthrotomy or arthroscop‐ ically and will be presented briefly: collagen-covered ACI (CACI or ACI-C), Hyalograft C

Novel Therapies for the Management of Sports Injuries

http://dx.doi.org/10.5772/53593

19

The main innovation in CACI is the use of bioresorable collagen membrane cover instead of the periosteal cover. Initial reports showed clinical improvements of this second generation ACI with fewer complications compared to classical ACI. The clinical and functional assess‐ ment after two years showed that 74% of patients had good or excellent results following CACI compared to 67% after classical ACI (ACI-P or PACI – periosteal ACI). Revision ar‐ throscopy was required in 36.4% in the PACI group one year after surgery due to shaving for hypertrophy compared to none in the CACI group [111]. In the systemic review of ACI procedures including 82 studies they reported that the failure rate was highest in PACI (7.7%) compared to CACI (1.5%). Similarly, the highest rate of unplanned re-operation was

Matrix-induced ACI (MACI) was first introduced in 1998. In this technique, cells are seeded directly onto the surface of a biodegradable type I/III collagen membrane and as such over‐ come the shortcomings of the original periosteum-covered technique. The membrane is a bilayer structure, smooth on one side and rough and more porous on the inner side, with incorporated cells to stimulate cartilage matrix specific molecules. It was shown that chon‐ drocytes can adhere and maintain their phenotypic characteristics while seeded onto a type I/III collagen membrane [113]. The procedure requires limited exposure of the joint ensuring shorter operation time and less morbidity. The rate of failure was low (0-6.3%) and mainly due to symptomatic graft hypertrophy or detachment. However, clinical, arthroscopic, and histological outcomes are comparable for CACI and MACI [114]. Additionally, MACI was also significantly more effective after two years compared to microfracturing [115]. Al‐ though significantly improved results after 5 years were reported, MACI still remains the

Hyalograft C implants autologous cells onto an esterified hyaluronic acid scaffold. It was re‐ ported that 76% of patients had no pain and 88% had no mobility problems. Additionally, 96% of patients' treated knee was assessed to be normal by the surgeon and cartilage repair was graded arthroscopically as normal or nearly normal in 96%. The majority of secondlook biopsies showed hyaline-like cartilage and a very low rate of complications were re‐ corded [117]. Several other studies also reported positive clinical results with Hyalograft C [118, 119]. Similarly, in two comparative studies, researchers found superiority over hyalur‐ onic-acid based chondrocytes transplantation at five years follow up in respect to microfrac‐

Recently, further technological advances have led to a third-generation ACI, where chon‐ drocytes are embedded into three-dimensionally constructed scaffolds (i.e. 3-dimensional

based on hyaluronic acid and membrane/matrix induced ACI (MACI) and others.

in the PACI group (27%) compared to CACI (5%) [112].

cost-intensive alternative [116].

ture in young, active patients [120, 121].

*3.2.2. Third and fourth generation ACI*

Bone marrow stimulation techniques as well as ACI represent the cell-based approach for tissue regeneration in which the attendance of specific cells with the ability of proliferation and differentiation in desired cell phenotype plays a crucial role. In the case of bone marrow stimulating techniques, these cells are recruited from the bone marrow either by drilling or microfracturing; as such they are released from the medullar canal and subsequently form the blot clot on the side of the lesion. However, the final result is fibrous cartilage with infe‐ rior biomechanical properties compared to native hyaline cartilage. On the other hand, the histological analysis of random biopsy specimens after ACI procedure indicated the pres‐ ence of type-II collagen and hyaline-like cartilage within the healing tissue.

ACI is both technically demanding and associated with a high percentage of reoperations. The modification of this cell therapy was designed to reduce complications such as perios‐ teal hypertrophy, the need for second look arthroscopy, the development of fibrocartilage tissue with variable amount of hyaline cartilage, etc. The next generation of ACI was devel‐ oped by replacing the periosteal patch with a biocompatible matrix and selecting cells of po‐ tentially improved chondrogenic potential. For example, second generation ACI uses collagen-covered autologous cultured chondrocyte implantation and in third-generation ACI, special cell carriers or cell-seeded scaffolds were created. Fourth generation cartilage repair focuses on growth factors and gene therapy, the use of stem cells and tissue engineer‐ ing [109, 110]. In general, arthrotomy and a two-stage procedure are the most commonly used, but all-arthroscopic techniques and one-stage procedures (e.g. technique with minced articular cartilage) have become highly attractive treatment techniques. Additionally, preimplantation chondrocyte phenotype manipulation has also shown excellent outcomes.

## *3.2.1. Second generation ACI*

Second generation ACI is still a two-step procedure, but in contrast to classical ACI it involves culturing in 3-dimensional conditions, which favours the maintenance of phenotypic stability of chondrocytes. In particular, chondrocytes are cultured on the scaffold that is biocompatible, enables cellular growth, and as such represents the graft to be transplanted. These scaffolds/ matrices containing the chondrocytes are implanted on the chondral lesion and attached with fibrin glue. In this manner, periosteal grafts and their suturing onto healthy cartilage are not necessary. These techniques were developed in an attempt to resolve some of the most com‐ mon problems indicated by the standard ACI technique such as periosteal hypertrophy, which is a source of complaints about localized pain among some patients.

The scaffolds used in second generation ACI should comprise all of the following futures: bio‐ compatibility (no inflammatory response), biodegradability (controlled rate of degradation), bioactivity (promote maintenance of phenotype and proliferation), and permeability (to en‐ sure nutrition). Natural and synthetic scaffolds can be used. The concern about the synthetic scaffolds is the risk of the harmful effect of degradation products on surrounding tissue. A comparison of the first and second-generation ACI has shown rather equivalent short-term clinical outcomes, with similar complications and a similar rate of reoperation [110]. A variety of scaffolds have been introduced, implanted either through a small arthrotomy or arthroscop‐ ically and will be presented briefly: collagen-covered ACI (CACI or ACI-C), Hyalograft C based on hyaluronic acid and membrane/matrix induced ACI (MACI) and others.

The main innovation in CACI is the use of bioresorable collagen membrane cover instead of the periosteal cover. Initial reports showed clinical improvements of this second generation ACI with fewer complications compared to classical ACI. The clinical and functional assess‐ ment after two years showed that 74% of patients had good or excellent results following CACI compared to 67% after classical ACI (ACI-P or PACI – periosteal ACI). Revision ar‐ throscopy was required in 36.4% in the PACI group one year after surgery due to shaving for hypertrophy compared to none in the CACI group [111]. In the systemic review of ACI procedures including 82 studies they reported that the failure rate was highest in PACI (7.7%) compared to CACI (1.5%). Similarly, the highest rate of unplanned re-operation was in the PACI group (27%) compared to CACI (5%) [112].

Matrix-induced ACI (MACI) was first introduced in 1998. In this technique, cells are seeded directly onto the surface of a biodegradable type I/III collagen membrane and as such over‐ come the shortcomings of the original periosteum-covered technique. The membrane is a bilayer structure, smooth on one side and rough and more porous on the inner side, with incorporated cells to stimulate cartilage matrix specific molecules. It was shown that chon‐ drocytes can adhere and maintain their phenotypic characteristics while seeded onto a type I/III collagen membrane [113]. The procedure requires limited exposure of the joint ensuring shorter operation time and less morbidity. The rate of failure was low (0-6.3%) and mainly due to symptomatic graft hypertrophy or detachment. However, clinical, arthroscopic, and histological outcomes are comparable for CACI and MACI [114]. Additionally, MACI was also significantly more effective after two years compared to microfracturing [115]. Al‐ though significantly improved results after 5 years were reported, MACI still remains the cost-intensive alternative [116].

Hyalograft C implants autologous cells onto an esterified hyaluronic acid scaffold. It was re‐ ported that 76% of patients had no pain and 88% had no mobility problems. Additionally, 96% of patients' treated knee was assessed to be normal by the surgeon and cartilage repair was graded arthroscopically as normal or nearly normal in 96%. The majority of secondlook biopsies showed hyaline-like cartilage and a very low rate of complications were re‐ corded [117]. Several other studies also reported positive clinical results with Hyalograft C [118, 119]. Similarly, in two comparative studies, researchers found superiority over hyalur‐ onic-acid based chondrocytes transplantation at five years follow up in respect to microfrac‐ ture in young, active patients [120, 121].

## *3.2.2. Third and fourth generation ACI*

**3.2. Clinical application of tissue engineering in cartilage repair**

18 Current Issues in Sports and Exercise Medicine

ing, due to low cost, arthroscopic procedure, and ease of performance.

ence of type-II collagen and hyaline-like cartilage within the healing tissue.

*3.2.1. Second generation ACI*

Cartilage repair has gained great interest since autologous cartilage implantation (ACI) has become an established treatment. The first line of treatment options remains microfractur‐

Bone marrow stimulation techniques as well as ACI represent the cell-based approach for tissue regeneration in which the attendance of specific cells with the ability of proliferation and differentiation in desired cell phenotype plays a crucial role. In the case of bone marrow stimulating techniques, these cells are recruited from the bone marrow either by drilling or microfracturing; as such they are released from the medullar canal and subsequently form the blot clot on the side of the lesion. However, the final result is fibrous cartilage with infe‐ rior biomechanical properties compared to native hyaline cartilage. On the other hand, the histological analysis of random biopsy specimens after ACI procedure indicated the pres‐

ACI is both technically demanding and associated with a high percentage of reoperations. The modification of this cell therapy was designed to reduce complications such as perios‐ teal hypertrophy, the need for second look arthroscopy, the development of fibrocartilage tissue with variable amount of hyaline cartilage, etc. The next generation of ACI was devel‐ oped by replacing the periosteal patch with a biocompatible matrix and selecting cells of po‐ tentially improved chondrogenic potential. For example, second generation ACI uses collagen-covered autologous cultured chondrocyte implantation and in third-generation ACI, special cell carriers or cell-seeded scaffolds were created. Fourth generation cartilage repair focuses on growth factors and gene therapy, the use of stem cells and tissue engineer‐ ing [109, 110]. In general, arthrotomy and a two-stage procedure are the most commonly used, but all-arthroscopic techniques and one-stage procedures (e.g. technique with minced articular cartilage) have become highly attractive treatment techniques. Additionally, preimplantation chondrocyte phenotype manipulation has also shown excellent outcomes.

Second generation ACI is still a two-step procedure, but in contrast to classical ACI it involves culturing in 3-dimensional conditions, which favours the maintenance of phenotypic stability of chondrocytes. In particular, chondrocytes are cultured on the scaffold that is biocompatible, enables cellular growth, and as such represents the graft to be transplanted. These scaffolds/ matrices containing the chondrocytes are implanted on the chondral lesion and attached with fibrin glue. In this manner, periosteal grafts and their suturing onto healthy cartilage are not necessary. These techniques were developed in an attempt to resolve some of the most com‐ mon problems indicated by the standard ACI technique such as periosteal hypertrophy, which

The scaffolds used in second generation ACI should comprise all of the following futures: bio‐ compatibility (no inflammatory response), biodegradability (controlled rate of degradation), bioactivity (promote maintenance of phenotype and proliferation), and permeability (to en‐ sure nutrition). Natural and synthetic scaffolds can be used. The concern about the synthetic

is a source of complaints about localized pain among some patients.

Recently, further technological advances have led to a third-generation ACI, where chon‐ drocytes are embedded into three-dimensionally constructed scaffolds (i.e. 3-dimensional environment) for cell growth [122]. This novel approach uses: chondro-inductive or chon‐ dro-conductive matrix; autogenous or alogenous cells treated *In vitro* in order to induce cell proliferation, differentiation and production of ECM; a single-stage surgical approach; and mechanical stimulation to improve the material properties and maturation of the implant [123]. Such mature tissue might ensure shorter rehabilitation and shorten the time to achieve clinical efficiency. For example, the DeNovo Engineered Tissue (ET) graft (Zimmer, War‐ saw) is generated from juvenile cartilage cells under special laboratory conditions and is hyaline-like. It is engineered by ISTO Technologies and the FDA approved ISTO's Investiga‐ tional New Drug (IND) application for Neocartilage in 2006, which allowed them to pursue clinical trials of the product in humans.

chondrogenic GF. Gene transfer enables localized exposure of bioactive proteins or gene products to the site of tissue lesions. There have been numerous cDNAs cloned and used for biological stimulation of cartilage healing in terms of mitosis induction, synthesis of ECM components, induction of chondrogenesis by progenitor cells, inhibiting inflammatory re‐ sponse, etc. Researching involves identification and specific gene combinations that could be incorporated into vectors and delivered to target cells [127]. Current data indicates that effi‐ cient delivery and expression of certain genes may have an effect on overall healing re‐ sponse in cartilage tissue and is capable of turning the repair response towards the synthesis of a more hyaline cartilage tissue [128]. The novel approach in cartilage tissue engineering is the use of cell population certification (screening of gene markers, positive and negative fac‐ tors, gene expression score - ChondroCelect), which enables prediction of whether cells are capable of making stable hyaline-like cartilage *In vitro*. By selecting those characterized cells with a high probability of maintaining a chondrogenic phenotype, the effectiveness of trans‐

Novel Therapies for the Management of Sports Injuries

http://dx.doi.org/10.5772/53593

21

Recent directions in cartilage repair are moving towards the possibility of performing onestep surgery, including the use of MCS and GF, and to avoid the first surgery, harvesting cell material, and subsequent cell cultivation. Numerous studies reported that bone marrow stem cells are a useful source for restoring cartilage defects. Additionally, by the concomi‐

Single stage procedures can be divided into two categories: cell free implants (scaffolds) and cell-based implants (further subdivided according to the cell type utilized; auto- and allog‐ rafts). One of the most common cell-free procedures is AMIC (autologous matrix-induced chondrogenesis). The technique requires a cell free implant that is "smart" enough to pro‐ vide the appropriate stimuli to induce orderly and durable tissue regeneration. Moreover, it should be capable of inducing in situ cartilage formation. The AMIC procedure comprises of microfracturing combined with the implant of a porcine collagen type I/III bilayer matrix to

The first reports on the AMIC technique were promising and the results were comparable to standard ACI with the advantage of a single stage technique and no donor site morbidity [129]. In a study with the mean follow up rate of 37 months, they reported highly satisfacto‐ ry results in 87% with MRI showing moderate to complete filling and normal to hyperdense signal [130]. Another possibility is to use bone marrow concentrate (BMC) for MCS in treat‐ ing cartilage defects. The technique consists of harvesting 40-60ml of bone marrow aspirate from the iliac crest, centrifugation, and the use of special enzymes to activate the BMC and produce the sticky clot material that is placed on the side of the lesion; finally the defect is

An attractive option in terms of cell-based technologies is represented by minced articular cartilage procedures for repairing articular cartilage, as they are one-staged, autologous and inserted on scaffold carriers that provide chondro-milieu, mechanical protection and even distribution of the cells within the defect. The principle of the minced cartilage procedure is

tant use of PRP and MCS it is possible to develop a single step procedure.

planted chondrocytes would be maximized.

*3.2.3. One-step surgery*

stabilize blood clot formation.

covered with a collagen membrane.

Likewise, Neocart (Histogenics, Waltham, MA), a bioengineered tissue patch containing an autologous chondrocyte population matured in a biodegradable collagen matrix, uses bioreactor technology (hydrostatic pressure with modified flow rates and low oxygen) to stimulate ECM accumulation and suppress long-term degradation. A recent randomized study suggests that the safety of autologous cartilage tissue implantation, with the use of the NeoCart technique is similar to that of microfracture and associated with greater clin‐ ical efficacy at two years after treatment [124]. However, there are still technical prob‐ lems remaining regarding the initial fixation technique, subchondral and edge integration, long-term durability, etc. [125].

A number of new generation ACI methods for implanting cultured autologous chondro‐ cytes in a biodegradable matrix are currently in development or testing. These include Chondroselect (characterized chondrocyte implantation, TiGenex, Phase III trial), BioCart II (ProChon Biotech, Phase II trial), Cartilix (polymer hydrogel, Cartilix), MACI® (matrix-in‐ duced ACI, Verigen, available outside of the U.S.), Cartipatch (solid scaffold with an agar‐ ose-alginate matrix, TBF Tissue Engineering, Phase III trial), NeoCart (ACI with a 3 dimensional chondromatrix, Histogenics, Phase II trial) and Hyalograft C (ACI with a hyaluronic acid-based scaffold, Fidia Advanced Polymers). Although the clinical use of these second-generation ACI products has been reported in Europe, none are approved for use in the U.S. at this time [126].

The future of fourth generation cartilage repair focuses on gene therapy, the use of stem cells (bone marrow, adipose, or muscle derived) and tissue engineering. MSCs are an attrac‐ tive cell source due to their differentiation capacities. To expand and deliver MSCs to the site of defect, the cells should be seeded into an appropriate scaffold that is biocompatible, mechanically stable, permeable, and biodegradable. A variety of biomaterials were intro‐ duced, e.g. carbohydrate polymers (hyaluronan, agarose, alginate, PLA/PLGA) that are pro‐ tein-based (collagen, fibrin, gelatin) in order to obtain homogenous distribution within a 3 dimensional matrix.

Future generations of cartilage tissue engineering will also include methods to control the genome to direct chondrogenic differentiation towards a hyaline-like pathway. In this man‐ ner, the local cellular environment can be coordinated by a tightly regulated GFs that signal molecules to regulate cellular maturation and proliferation. Additionally, with the use of gene therapy, either viral or non-viral vectors can be applied into cells, which then express chondrogenic GF. Gene transfer enables localized exposure of bioactive proteins or gene products to the site of tissue lesions. There have been numerous cDNAs cloned and used for biological stimulation of cartilage healing in terms of mitosis induction, synthesis of ECM components, induction of chondrogenesis by progenitor cells, inhibiting inflammatory re‐ sponse, etc. Researching involves identification and specific gene combinations that could be incorporated into vectors and delivered to target cells [127]. Current data indicates that effi‐ cient delivery and expression of certain genes may have an effect on overall healing re‐ sponse in cartilage tissue and is capable of turning the repair response towards the synthesis of a more hyaline cartilage tissue [128]. The novel approach in cartilage tissue engineering is the use of cell population certification (screening of gene markers, positive and negative fac‐ tors, gene expression score - ChondroCelect), which enables prediction of whether cells are capable of making stable hyaline-like cartilage *In vitro*. By selecting those characterized cells with a high probability of maintaining a chondrogenic phenotype, the effectiveness of trans‐ planted chondrocytes would be maximized.

## *3.2.3. One-step surgery*

environment) for cell growth [122]. This novel approach uses: chondro-inductive or chon‐ dro-conductive matrix; autogenous or alogenous cells treated *In vitro* in order to induce cell proliferation, differentiation and production of ECM; a single-stage surgical approach; and mechanical stimulation to improve the material properties and maturation of the implant [123]. Such mature tissue might ensure shorter rehabilitation and shorten the time to achieve clinical efficiency. For example, the DeNovo Engineered Tissue (ET) graft (Zimmer, War‐ saw) is generated from juvenile cartilage cells under special laboratory conditions and is hyaline-like. It is engineered by ISTO Technologies and the FDA approved ISTO's Investiga‐ tional New Drug (IND) application for Neocartilage in 2006, which allowed them to pursue

Likewise, Neocart (Histogenics, Waltham, MA), a bioengineered tissue patch containing an autologous chondrocyte population matured in a biodegradable collagen matrix, uses bioreactor technology (hydrostatic pressure with modified flow rates and low oxygen) to stimulate ECM accumulation and suppress long-term degradation. A recent randomized study suggests that the safety of autologous cartilage tissue implantation, with the use of the NeoCart technique is similar to that of microfracture and associated with greater clin‐ ical efficacy at two years after treatment [124]. However, there are still technical prob‐ lems remaining regarding the initial fixation technique, subchondral and edge

A number of new generation ACI methods for implanting cultured autologous chondro‐ cytes in a biodegradable matrix are currently in development or testing. These include Chondroselect (characterized chondrocyte implantation, TiGenex, Phase III trial), BioCart II (ProChon Biotech, Phase II trial), Cartilix (polymer hydrogel, Cartilix), MACI® (matrix-in‐ duced ACI, Verigen, available outside of the U.S.), Cartipatch (solid scaffold with an agar‐ ose-alginate matrix, TBF Tissue Engineering, Phase III trial), NeoCart (ACI with a 3 dimensional chondromatrix, Histogenics, Phase II trial) and Hyalograft C (ACI with a hyaluronic acid-based scaffold, Fidia Advanced Polymers). Although the clinical use of these second-generation ACI products has been reported in Europe, none are approved for

The future of fourth generation cartilage repair focuses on gene therapy, the use of stem cells (bone marrow, adipose, or muscle derived) and tissue engineering. MSCs are an attrac‐ tive cell source due to their differentiation capacities. To expand and deliver MSCs to the site of defect, the cells should be seeded into an appropriate scaffold that is biocompatible, mechanically stable, permeable, and biodegradable. A variety of biomaterials were intro‐ duced, e.g. carbohydrate polymers (hyaluronan, agarose, alginate, PLA/PLGA) that are pro‐ tein-based (collagen, fibrin, gelatin) in order to obtain homogenous distribution within a 3-

Future generations of cartilage tissue engineering will also include methods to control the genome to direct chondrogenic differentiation towards a hyaline-like pathway. In this man‐ ner, the local cellular environment can be coordinated by a tightly regulated GFs that signal molecules to regulate cellular maturation and proliferation. Additionally, with the use of gene therapy, either viral or non-viral vectors can be applied into cells, which then express

clinical trials of the product in humans.

20 Current Issues in Sports and Exercise Medicine

integration, long-term durability, etc. [125].

use in the U.S. at this time [126].

dimensional matrix.

Recent directions in cartilage repair are moving towards the possibility of performing onestep surgery, including the use of MCS and GF, and to avoid the first surgery, harvesting cell material, and subsequent cell cultivation. Numerous studies reported that bone marrow stem cells are a useful source for restoring cartilage defects. Additionally, by the concomi‐ tant use of PRP and MCS it is possible to develop a single step procedure.

Single stage procedures can be divided into two categories: cell free implants (scaffolds) and cell-based implants (further subdivided according to the cell type utilized; auto- and allog‐ rafts). One of the most common cell-free procedures is AMIC (autologous matrix-induced chondrogenesis). The technique requires a cell free implant that is "smart" enough to pro‐ vide the appropriate stimuli to induce orderly and durable tissue regeneration. Moreover, it should be capable of inducing in situ cartilage formation. The AMIC procedure comprises of microfracturing combined with the implant of a porcine collagen type I/III bilayer matrix to stabilize blood clot formation.

The first reports on the AMIC technique were promising and the results were comparable to standard ACI with the advantage of a single stage technique and no donor site morbidity [129]. In a study with the mean follow up rate of 37 months, they reported highly satisfacto‐ ry results in 87% with MRI showing moderate to complete filling and normal to hyperdense signal [130]. Another possibility is to use bone marrow concentrate (BMC) for MCS in treat‐ ing cartilage defects. The technique consists of harvesting 40-60ml of bone marrow aspirate from the iliac crest, centrifugation, and the use of special enzymes to activate the BMC and produce the sticky clot material that is placed on the side of the lesion; finally the defect is covered with a collagen membrane.

An attractive option in terms of cell-based technologies is represented by minced articular cartilage procedures for repairing articular cartilage, as they are one-staged, autologous and inserted on scaffold carriers that provide chondro-milieu, mechanical protection and even distribution of the cells within the defect. The principle of the minced cartilage procedure is to obtain hyaline-like "minced" cartilage pieces supplemented with the scaffold delivery system. Minced cartilage represents the source of cells and even relatively large defects can be treated with a small amount of cells; specifically, one-tenth of the cartilage that originally covered a defect is required. The proposed advantages of this procedure over conventional treatment are the elimination of the need for in-vitro cell expansion and a second surgical procedure. Several technologies are being investigated and are in current late stage trials [131]. The autograft cell-based procedure CAIC (Mitek, USA) is currently under phase III evaluation. During the procedure, autologous cartilage is harvested with the special shaver device, then morcellized and secured on resorbable polymer mesh with fibrin glue. DeNovo NT Graft ("Natural Tissue Graft", Zimmer, Warsaw) is a similar application used for treat‐ ment of the cartilage lesions limited to an articular surface with intact subchondral bone. It utilizes morcelized juvenile cartilage, which is secured with the fibrin glue. As there is no use of chemicals and minimal manipulation, a DeNovo NT Graft does not require FDA ap‐ proval and is currently available in the United States. Both CAIS and DeNovo NT techni‐ ques rely on chondrocytes migration out of the cartilage tissue with subsequent matrix production to fill the defect [130-132]. Early animal and preclinical models have demonstrat‐ ed hyaline-like cartilage. Clinical experience is limited, with short-term studies demonstrat‐ ing both procedures to be safe, feasible, and effective, with improvements in subjective patient scores, and with magnetic resonance imaging [133].

important in the selection of the graft tissue reconstruction, such as the initial mechanical properties of the graft tissue, morbidity resulting from graft harvesting, graft healing, and

Novel Therapies for the Management of Sports Injuries

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23

Allografts represent an alternative option to autografts for tendon and ligament repair. Be‐ cause of high cost, limited accessibility, associated risk of disease transmission and tissue re‐

Immediately after a reconstruction with autograft or allograft, the fixation site, not the graft midsubstance, is considered to be the weakest point; following that period, the process of ligamentization influences the mechanical properties of the graft, making it

To prevent injuries of the graft until integration into the bone and the process of liga‐ mentization is complete, graft augmentation devices were developed to provide immedi‐ ate post-surgical protection. They share mechanical loads with the biological graft until the graft itself is capable of withstanding local tensile and compressive forces [134]. Graft augmentation devices should be resorbable, but the rate of resorption should be limited

Tissue engineering (TE) combines biological materials and cells into a construct that is eventually able to replace the regenerated tissue [136], through the merging of three areas: scaffold microenvironment, stem cells, and signalling biofactors. The goal is to re‐ construct a ligament/tendon by providing a scaffold seeded with cell-inducing neotissue formation that adequately meets the required biological and mechanical properties [136,137]. Engineering fibrous tissues, such as tendons and ligaments, requires the use of fibre-based scaffolds, because they should possess appropriate mechanical properties to withstand high stresses, but also high porosity and surface area to allow the seeded cells

The purpose of TE with responding cells is to induce a regenerative response instead of scar‐ ring. Tissue engineering can be divided into two subtypes: the *In vivo* approach and the *ex vivo-de novo*. The *In vivo* approach permits the self-regeneration of small tissue lesions [138]. The *ex vivo-de novo* approach is designed to produce functional tissue that can be implanted in the body. Several cells have been used: tenocytes, fibroblasts and stem cells. The latter can be derived from bone marrow, human tendons (ACL, PCL), adipose tissue or embryonic de‐

Upon injury, elongated fibroblast cells resident in the tendon are activated by the inflamma‐ tory response for collagen deposition. To conduct this function, tenocytes are assisted by

by gradual transfer of mechanical loads to the biological graft [134, 135].

the initial mechanical properties of the graft fixation, [134].

jection with the use of allografts, autografts are preferred.

more vulnerable.

**4.2. Tissue engineering**

*4.2.1. Stem cells and scaffolds*

rived stem cells [138].

to proliferate and regenerate the tissue [137].

tendon-derived stem cells (TDSCs) [139].

## **4. Strategies to improve ligament and tendon repair**

Tendons and ligaments are avascular and hypocellular with distinct mechanical features that make them difficult for currently available treatments to reach a complete functional re‐ pair of the damaged tissue. Tendon injuries, whether acute or chronic, are commonly man‐ aged either conservatively or surgically. Conservative management, such as rest, corticosteroid injection, orthotics, ultrasound, laser treatment, or shockwave provide pain relief but, when they fail, surgery is required [134].

Surgical repair may be indicated in acute injuries. In chronic lesions, excision of the involved area might be performed. However, repaired tendons have inferior properties when com‐ pared to healthy ones. The loss of mechanical features is mainly due to a distorted extra cel‐ lular matrix (ECM) composition and a misalignment of collagen fibrils of the scar tissue [134]. Another option is to use tendon or ligament grafts, but graft-augmentation devices and artificial prostheses have also been developed [135]. Because current treatment is subop‐ timal, alternative therapies have been developed, such as the delivery of growth factors, the development of engineered scaffolds or the application of stem cells.

## **4.1. Grafts and graft-augmentation devices**

Autografts are used widely to repair the affected tendon and prevent instability due to the damaged ligament. The most commonly used autografts include hamstring tendons (semite‐ ndinosus and gracilis) and bone-patellar ligament (middle third)-bone. Several factors are important in the selection of the graft tissue reconstruction, such as the initial mechanical properties of the graft tissue, morbidity resulting from graft harvesting, graft healing, and the initial mechanical properties of the graft fixation, [134].

Allografts represent an alternative option to autografts for tendon and ligament repair. Be‐ cause of high cost, limited accessibility, associated risk of disease transmission and tissue re‐ jection with the use of allografts, autografts are preferred.

Immediately after a reconstruction with autograft or allograft, the fixation site, not the graft midsubstance, is considered to be the weakest point; following that period, the process of ligamentization influences the mechanical properties of the graft, making it more vulnerable.

To prevent injuries of the graft until integration into the bone and the process of liga‐ mentization is complete, graft augmentation devices were developed to provide immedi‐ ate post-surgical protection. They share mechanical loads with the biological graft until the graft itself is capable of withstanding local tensile and compressive forces [134]. Graft augmentation devices should be resorbable, but the rate of resorption should be limited by gradual transfer of mechanical loads to the biological graft [134, 135].

## **4.2. Tissue engineering**

to obtain hyaline-like "minced" cartilage pieces supplemented with the scaffold delivery system. Minced cartilage represents the source of cells and even relatively large defects can be treated with a small amount of cells; specifically, one-tenth of the cartilage that originally covered a defect is required. The proposed advantages of this procedure over conventional treatment are the elimination of the need for in-vitro cell expansion and a second surgical procedure. Several technologies are being investigated and are in current late stage trials [131]. The autograft cell-based procedure CAIC (Mitek, USA) is currently under phase III evaluation. During the procedure, autologous cartilage is harvested with the special shaver device, then morcellized and secured on resorbable polymer mesh with fibrin glue. DeNovo NT Graft ("Natural Tissue Graft", Zimmer, Warsaw) is a similar application used for treat‐ ment of the cartilage lesions limited to an articular surface with intact subchondral bone. It utilizes morcelized juvenile cartilage, which is secured with the fibrin glue. As there is no use of chemicals and minimal manipulation, a DeNovo NT Graft does not require FDA ap‐ proval and is currently available in the United States. Both CAIS and DeNovo NT techni‐ ques rely on chondrocytes migration out of the cartilage tissue with subsequent matrix production to fill the defect [130-132]. Early animal and preclinical models have demonstrat‐ ed hyaline-like cartilage. Clinical experience is limited, with short-term studies demonstrat‐ ing both procedures to be safe, feasible, and effective, with improvements in subjective

Tendons and ligaments are avascular and hypocellular with distinct mechanical features that make them difficult for currently available treatments to reach a complete functional re‐ pair of the damaged tissue. Tendon injuries, whether acute or chronic, are commonly man‐ aged either conservatively or surgically. Conservative management, such as rest, corticosteroid injection, orthotics, ultrasound, laser treatment, or shockwave provide pain

Surgical repair may be indicated in acute injuries. In chronic lesions, excision of the involved area might be performed. However, repaired tendons have inferior properties when com‐ pared to healthy ones. The loss of mechanical features is mainly due to a distorted extra cel‐ lular matrix (ECM) composition and a misalignment of collagen fibrils of the scar tissue [134]. Another option is to use tendon or ligament grafts, but graft-augmentation devices and artificial prostheses have also been developed [135]. Because current treatment is subop‐ timal, alternative therapies have been developed, such as the delivery of growth factors, the

Autografts are used widely to repair the affected tendon and prevent instability due to the damaged ligament. The most commonly used autografts include hamstring tendons (semite‐ ndinosus and gracilis) and bone-patellar ligament (middle third)-bone. Several factors are

patient scores, and with magnetic resonance imaging [133].

22 Current Issues in Sports and Exercise Medicine

relief but, when they fail, surgery is required [134].

**4.1. Grafts and graft-augmentation devices**

**4. Strategies to improve ligament and tendon repair**

development of engineered scaffolds or the application of stem cells.

Tissue engineering (TE) combines biological materials and cells into a construct that is eventually able to replace the regenerated tissue [136], through the merging of three areas: scaffold microenvironment, stem cells, and signalling biofactors. The goal is to re‐ construct a ligament/tendon by providing a scaffold seeded with cell-inducing neotissue formation that adequately meets the required biological and mechanical properties [136,137]. Engineering fibrous tissues, such as tendons and ligaments, requires the use of fibre-based scaffolds, because they should possess appropriate mechanical properties to withstand high stresses, but also high porosity and surface area to allow the seeded cells to proliferate and regenerate the tissue [137].

## *4.2.1. Stem cells and scaffolds*

The purpose of TE with responding cells is to induce a regenerative response instead of scar‐ ring. Tissue engineering can be divided into two subtypes: the *In vivo* approach and the *ex vivo-de novo*. The *In vivo* approach permits the self-regeneration of small tissue lesions [138]. The *ex vivo-de novo* approach is designed to produce functional tissue that can be implanted in the body. Several cells have been used: tenocytes, fibroblasts and stem cells. The latter can be derived from bone marrow, human tendons (ACL, PCL), adipose tissue or embryonic de‐ rived stem cells [138].

Upon injury, elongated fibroblast cells resident in the tendon are activated by the inflamma‐ tory response for collagen deposition. To conduct this function, tenocytes are assisted by tendon-derived stem cells (TDSCs) [139].

MSCs do not differentiate spontaneously during *In vitro* culture, which permits a controlled microenvironment, such as to dictate the differentiation of MSCs after implantation. Because they are more easily isolated and banked from bone marrow compared to TDSCs, they rep‐ resent a more optimal source of stem cells suitable for therapeutic use. MSCs have been in‐ duced to differentiate to tenocytes through the Wnt signalling pathway and cyclic mechanical stimulation that mimics normal processes [140]. It was also found that plateletrich plasma (PrP) stimulates both MSCs and TDSCs [139].

mechanical stimulation In vitro, embryonic stem cells exhibited tenocyte-like morphology and positively expressed tendon-related gene markers, as well as other mechanosensory structures and molecules (cilia, integrins and myosin). In ectopic transplantation, the TE ten‐ don under In vivo mechanical stimulus displayed more regularly aligned cells and larger collagen fibres that enabled enhanced tendon regeneration in situ, as evidenced by better histological scores and superior mechanical performance characteristics [145]. In a recent study, rabbit flexor tendons were deprived of cells and exposed to cyclic strain in a bioreac‐ tor, in comparison to a control, which was kept unloaded in a medium for 5 days [147]. The tendons were then implanted to bridge a zone II defect in the rabbit, followed by determina‐ tion of ultimate tensile strength and elastic modulus after 4 weeks. Both were significantly improved in tendon constructs that were exposed to cyclic strain, and the histology showed an increased cellularity in the bioreactor tendons. In another study, it was showed that the material properties of human allograft tissue-engineered constructs can be enhanced by re‐ seeding and dynamic conditioning [148]. It was found that while conditioning duration has a significant effect on material properties, the load magnitude does not. The issue of attrition in biomechanical properties with time following cycle completion must be addressed before bioreactor preconditioning can be successfully introduced as a step in the processing of

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Following acute tendon injury, circulation-derived cells play a crucial role in the healing processes of tissue. It was shown, that locally injected PrP is useful as an activator of circula‐ tion-derived cells for the enhancement of the initial tendon healing process [149]. PrP also improves the mechanical properties of tendons in the early phase following acute injury, in terms of increase in the force at failure, ultimate stress, and stiffness; but the effect seems to vanish in the long-term follow up [150]. To date, there is still a debate regarding the positive effect of PrP following acute tendon injury. There are studies that confirm the positive effect of PrP on tendon healing, since an earlier return to sports, decreased cross-sectional area of tendon, and improved earlier range of ankle motion, following Achilles tendon reconstruc‐ tion was noted [151]. It is speculated that *In vivo* use of PrP, as well as platelet-poor plasma to a certain extent, in tendon injuries might accelerate the catabolic demarcation of traumati‐ cally injured tendon matrices and promote angiogenesis and formation of a fibrovascular callus [152]. A study showed that platelets influence only the early phases of regeneration, but this allows for mechanical stimulation to start driving neo-tendon development at an earlier time point, which kept it constantly ahead of the controls [153]. However, all studies do not confirm the positive effect of PrP; in fact a possible negative effect of PrP on the func‐ tional results after the reconstruction of an Achilles tendon during a long-term follow up

In chronic tendon lesions, especially tendinopathy, the use of PrP is focused on restoring normal tissue composition while avoiding further degeneration. Ultrasound-guided injec‐ tions of PrP were effective in reducing pain in elbow tendinosis, medial epicondylitis [155] and jumper's knee [156]. Until now, few high-quality studies on the use of autologous GF

these constructs for clinical application.

*4.2.3. Growth factors*

was observed [154].

Adipose-derived stem cell (ASC) use for tendon regeneration and repair has recently been taken into consideration. In a recent study, the role of these stem cells in primary tendon healing has been investigated by a local autologous ASC-mixed platelet-rich plasma (PrP) application at the site of tendon injury in a control to PrP application only [141]. The tensile strengths experimental groups were found to be significantly higher in comparison to the control group and, along with higher expression of collagen type I, FGF and VEGF levels in the experimental group, ASCs seems to enhance primary tendon healing.

It is now well accepted that seeded grafts vastly improve outcomes over un-seeded grafts. Recently, collagen matrices cultured with MSCs have appeared on the horizon for tendon repair [142-144]. The isoelectric focusing technique aligns collagen fibres to the parameters of the target tissue, adjusting the density, alignment, and strength of dense connective tissue (Gurkan: Comparison of morphology, orientation, and migra‐ tion of tendon derived fibroblasts and bone marrow stromal cells on electrochemically aligned collagen constructs 2010). These matrices support a higher proliferation rate of MSCs compared to randomly oriented collagen. Currently, the versatility of synthetic polymers shows great promise in tissue engineering. Poly (1.8 octanediol-co-citrate) scaffold (POC) is a highly reproducible elastomeric material capable of being used as a synthetic scaffold to support cell growth. Instead of attaching tendinous grafts to bone via screws, the optimal approach is reconstruction using the collaboration of synthetic materials with MSCs. Paradoxically, the very complexity of the fibrocartilage interface makes it a perfect candidate for POC utilization. A scaffold with three distinct regions would allow formation of a collagenous tendon along one edge, osseous material along the other, and a middle zone representing the transition from tendon to bone. Given the capacity of MSCs to differentiate into osteogenic and tenogenic lineages, a single cell population seeded onto the scaffold could regenerate the complex fibrocarti‐ lage interface. Additionally, POC scaffolds could be crafted according to the target ten‐ don interface, relying on Wolff's Law to govern the dynamics and load of the tendon aimed for reconstruction [139].

#### *4.2.2. Bioreactors*

A bioreactor in TE is a device that simulates a physiological environment in order to pro‐ mote cell or tissue growth In vivo. Tendons respond to mechanical forces by changing the metabolism as well as their structural and mechanical properties. Without the appropriate biomechanical stimulation, newly formed tissue will lack appropriate collagenous organiza‐ tion and alignment for sufficient load-bearing capacity [134, 145, 146]. When subjected to mechanical stimulation In vitro, embryonic stem cells exhibited tenocyte-like morphology and positively expressed tendon-related gene markers, as well as other mechanosensory structures and molecules (cilia, integrins and myosin). In ectopic transplantation, the TE ten‐ don under In vivo mechanical stimulus displayed more regularly aligned cells and larger collagen fibres that enabled enhanced tendon regeneration in situ, as evidenced by better histological scores and superior mechanical performance characteristics [145]. In a recent study, rabbit flexor tendons were deprived of cells and exposed to cyclic strain in a bioreac‐ tor, in comparison to a control, which was kept unloaded in a medium for 5 days [147]. The tendons were then implanted to bridge a zone II defect in the rabbit, followed by determina‐ tion of ultimate tensile strength and elastic modulus after 4 weeks. Both were significantly improved in tendon constructs that were exposed to cyclic strain, and the histology showed an increased cellularity in the bioreactor tendons. In another study, it was showed that the material properties of human allograft tissue-engineered constructs can be enhanced by re‐ seeding and dynamic conditioning [148]. It was found that while conditioning duration has a significant effect on material properties, the load magnitude does not. The issue of attrition in biomechanical properties with time following cycle completion must be addressed before bioreactor preconditioning can be successfully introduced as a step in the processing of these constructs for clinical application.

## *4.2.3. Growth factors*

MSCs do not differentiate spontaneously during *In vitro* culture, which permits a controlled microenvironment, such as to dictate the differentiation of MSCs after implantation. Because they are more easily isolated and banked from bone marrow compared to TDSCs, they rep‐ resent a more optimal source of stem cells suitable for therapeutic use. MSCs have been in‐ duced to differentiate to tenocytes through the Wnt signalling pathway and cyclic mechanical stimulation that mimics normal processes [140]. It was also found that platelet-

Adipose-derived stem cell (ASC) use for tendon regeneration and repair has recently been taken into consideration. In a recent study, the role of these stem cells in primary tendon healing has been investigated by a local autologous ASC-mixed platelet-rich plasma (PrP) application at the site of tendon injury in a control to PrP application only [141]. The tensile strengths experimental groups were found to be significantly higher in comparison to the control group and, along with higher expression of collagen type I, FGF and VEGF levels in

It is now well accepted that seeded grafts vastly improve outcomes over un-seeded grafts. Recently, collagen matrices cultured with MSCs have appeared on the horizon for tendon repair [142-144]. The isoelectric focusing technique aligns collagen fibres to the parameters of the target tissue, adjusting the density, alignment, and strength of dense connective tissue (Gurkan: Comparison of morphology, orientation, and migra‐ tion of tendon derived fibroblasts and bone marrow stromal cells on electrochemically aligned collagen constructs 2010). These matrices support a higher proliferation rate of MSCs compared to randomly oriented collagen. Currently, the versatility of synthetic polymers shows great promise in tissue engineering. Poly (1.8 octanediol-co-citrate) scaffold (POC) is a highly reproducible elastomeric material capable of being used as a synthetic scaffold to support cell growth. Instead of attaching tendinous grafts to bone via screws, the optimal approach is reconstruction using the collaboration of synthetic materials with MSCs. Paradoxically, the very complexity of the fibrocartilage interface makes it a perfect candidate for POC utilization. A scaffold with three distinct regions would allow formation of a collagenous tendon along one edge, osseous material along the other, and a middle zone representing the transition from tendon to bone. Given the capacity of MSCs to differentiate into osteogenic and tenogenic lineages, a single cell population seeded onto the scaffold could regenerate the complex fibrocarti‐ lage interface. Additionally, POC scaffolds could be crafted according to the target ten‐ don interface, relying on Wolff's Law to govern the dynamics and load of the tendon

A bioreactor in TE is a device that simulates a physiological environment in order to pro‐ mote cell or tissue growth In vivo. Tendons respond to mechanical forces by changing the metabolism as well as their structural and mechanical properties. Without the appropriate biomechanical stimulation, newly formed tissue will lack appropriate collagenous organiza‐ tion and alignment for sufficient load-bearing capacity [134, 145, 146]. When subjected to

rich plasma (PrP) stimulates both MSCs and TDSCs [139].

24 Current Issues in Sports and Exercise Medicine

aimed for reconstruction [139].

*4.2.2. Bioreactors*

the experimental group, ASCs seems to enhance primary tendon healing.

Following acute tendon injury, circulation-derived cells play a crucial role in the healing processes of tissue. It was shown, that locally injected PrP is useful as an activator of circula‐ tion-derived cells for the enhancement of the initial tendon healing process [149]. PrP also improves the mechanical properties of tendons in the early phase following acute injury, in terms of increase in the force at failure, ultimate stress, and stiffness; but the effect seems to vanish in the long-term follow up [150]. To date, there is still a debate regarding the positive effect of PrP following acute tendon injury. There are studies that confirm the positive effect of PrP on tendon healing, since an earlier return to sports, decreased cross-sectional area of tendon, and improved earlier range of ankle motion, following Achilles tendon reconstruc‐ tion was noted [151]. It is speculated that *In vivo* use of PrP, as well as platelet-poor plasma to a certain extent, in tendon injuries might accelerate the catabolic demarcation of traumati‐ cally injured tendon matrices and promote angiogenesis and formation of a fibrovascular callus [152]. A study showed that platelets influence only the early phases of regeneration, but this allows for mechanical stimulation to start driving neo-tendon development at an earlier time point, which kept it constantly ahead of the controls [153]. However, all studies do not confirm the positive effect of PrP; in fact a possible negative effect of PrP on the func‐ tional results after the reconstruction of an Achilles tendon during a long-term follow up was observed [154].

In chronic tendon lesions, especially tendinopathy, the use of PrP is focused on restoring normal tissue composition while avoiding further degeneration. Ultrasound-guided injec‐ tions of PrP were effective in reducing pain in elbow tendinosis, medial epicondylitis [155] and jumper's knee [156]. Until now, few high-quality studies on the use of autologous GF injections for the management of chronic tendinopathy showed no significant improvement compared to a control group, but in those studies, autologous blood was injected and not PrP [157-159]. Currently, there is level 3 (limited) evidence that PrP injections improve pain or function in chronic tendinopathy [160]. More research on basic science and the clinical ap‐ plication of PrP needs to be undertaken before a final recommendation for PrP administra‐ tion for the treatment of tendinosis can be made [47, 160].

neering has an enormous therapeutic potential. In recent years studies revealed that tendon healing and regeneration may be improved by the application of several growth factors and the use of PrP expanded widely. Today, many different producers provide PrP of different composition that makes studies hard to compare. Future studies will have to explain which concentrations of PrP works the best, where it is effective and what the role of accompany‐

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Regenerative medicine holds great promise for sports medicine with aim to develop novel therapies that will replace, repair, or promote tissue regeneration. It is an increasingly ex‐ panding area of research with hopes of providing therapeutic treatments for diseases and/or injuries that conventional medicines cannot effectively treat. Skeletal muscle has a great selfregenerative capacity, but it is unfortunately limited by fibrotic infiltration. Although none of the antifibrotic agents to improve skeletal muscle regeneration have been tested on hu‐ mans to date, its clinical implications are potentially far-reaching and include not only sports-related injuries, but also diseases such as muscular dystrophies and trauma- and sur‐ gery-related injury. With emerging novel therapeutic targets this is an important area of re‐ search and presents a basis for further possibilities to study different mechanisms of action

Biomaterials play an important role in directing tissue growth and may provide another tool to manipulate and control stem cell behaviour. Growth factors and therapies using mesenchymal stem cells, scaffolds, and tissue engineering using bioreactors represent promising strategies for tendon, ligament and cartilage repair. While therapies using growth factors seem to be well established in case of the first two, lack of scientific evidence still makes them questionable. In the future of cartilage repair, the modification of cellular differentiation following microfrac‐ ture could be alternated with the use of exogenous growth factors and scaffolds in order to re‐ tain chongrogenic phenotype and to improve the quality of repair tissue generated in the defect. The important future prospective of cartilage repair is also focused on the quality of the bonding and integration of the newly engineered tissue to native cartilage to achieve stable healing. This holds potential for tissue-engineered strategies that would enable repairing com‐ plex cartilage lesions together with the subchondral bone and other structures. However, as with all innovations, carefully conducted studies should be carried out to access the efficiency for cartilage regeneration. Furthermore, long term prospective randomized studies are needed

and effects drug combinations for improving muscle regeneration.

to confirm the encouraging preliminary results.

Robi Kelc, Jakob Naranda, Matevz Kuhta and Matjaz Vogrin

Department of Orthopaedic Surgery, University Medical Centre Maribor, Slovenia

**Author details**

ing leucocytes is.

**5. Conclusion**

A study performed at our department showed that the administration of PrP when recon‐ structing ACL with a hamstring autograft enhances early graft revascularization in the inter‐ face zone between graft and bone in the tibial tunnel; furthermore, PrP stimulates the formation of a sclerotic bony ring around the graft [161]. Platelet-leukocyte gel, applied lo‐ cally, can also improve knee stability in the first three-month period and especially in the second three-month period [162]. Studies indicate that the delivery of PrP mimics and accel‐ erates physiological healing and reparative tissue processes in graft healing and graft liga‐ mentization process. Therefore, such therapy could improve knee stability and shorten the period of rehabilitation after reconstructive knee surgery. However, not all studies on hu‐ mans confirm the positive effect of PrP. In one study after ACL reconstruction using patellar tendon graft with the application of PrP, researchers did not find any statistically important difference in inflammatory parameters, appearance of the graft on MRI, or clinical evalua‐ tion using validated scores [163]. Still others did not find any differences in graft fixation af‐ ter ACL reconstruction with hamstring allograft and application of PrP [164].

#### **4.3. Extracorporeal shock wave therapy**

Extracorporeal shock wave therapy (ESWT) is a technique used in the treatment of ten‐ don disorders, particularly calcific tendinopathy. The treatment is an extension of renal lithotripsy. It is a non-invasive modality used to stimulate healing, particularly in liga‐ ment, tendon, or bone structures. A high-energy sound wave rapidly increases pressure as it travels through the tissue, which results in cavitation that causes microtrauma. This stimulates an increase in blood flow and new blood vessel formation in the target area. Studies showed an increase in inflammatory cytokines and growth factors, as well as the regulation of tumour necrosis factor, interleukin, and bone morphogenetic protein follow‐ ing ESWT. Studies indicate that differentiated tenocytes are metabolically ''activated'' by ESWT and significantly induced proliferation and production of collagen (mainly type I) compared with untreated cells [165, 166]. Not all studies were able to show a positive ef‐ fect of ESWT, but this was later argued to be a possible consequence of topical anaes‐ thetics that interfere with ESWT treatment [167].

Numerous other substances have been used in the treatment of tendon disorders, including sclerosants, calcium gluconate, heparin, dextrose, and aprotinin; however, more studies have to be performed to prove their efficiency [168]. To date, no optimal treatment modali‐ ties for injured tendons or ligaments have been proposed. In fact, sheathed tendons may heal differently from those not enclosed in sheaths and the process of healing of an intraarticular ligament may differ from an extra-articular ligament. Recent studies support the idea that scaffolds can provide an alternative for tendon augmentation and that tissue engi‐ neering has an enormous therapeutic potential. In recent years studies revealed that tendon healing and regeneration may be improved by the application of several growth factors and the use of PrP expanded widely. Today, many different producers provide PrP of different composition that makes studies hard to compare. Future studies will have to explain which concentrations of PrP works the best, where it is effective and what the role of accompany‐ ing leucocytes is.

## **5. Conclusion**

injections for the management of chronic tendinopathy showed no significant improvement compared to a control group, but in those studies, autologous blood was injected and not PrP [157-159]. Currently, there is level 3 (limited) evidence that PrP injections improve pain or function in chronic tendinopathy [160]. More research on basic science and the clinical ap‐ plication of PrP needs to be undertaken before a final recommendation for PrP administra‐

A study performed at our department showed that the administration of PrP when recon‐ structing ACL with a hamstring autograft enhances early graft revascularization in the inter‐ face zone between graft and bone in the tibial tunnel; furthermore, PrP stimulates the formation of a sclerotic bony ring around the graft [161]. Platelet-leukocyte gel, applied lo‐ cally, can also improve knee stability in the first three-month period and especially in the second three-month period [162]. Studies indicate that the delivery of PrP mimics and accel‐ erates physiological healing and reparative tissue processes in graft healing and graft liga‐ mentization process. Therefore, such therapy could improve knee stability and shorten the period of rehabilitation after reconstructive knee surgery. However, not all studies on hu‐ mans confirm the positive effect of PrP. In one study after ACL reconstruction using patellar tendon graft with the application of PrP, researchers did not find any statistically important difference in inflammatory parameters, appearance of the graft on MRI, or clinical evalua‐ tion using validated scores [163]. Still others did not find any differences in graft fixation af‐

ter ACL reconstruction with hamstring allograft and application of PrP [164].

Extracorporeal shock wave therapy (ESWT) is a technique used in the treatment of ten‐ don disorders, particularly calcific tendinopathy. The treatment is an extension of renal lithotripsy. It is a non-invasive modality used to stimulate healing, particularly in liga‐ ment, tendon, or bone structures. A high-energy sound wave rapidly increases pressure as it travels through the tissue, which results in cavitation that causes microtrauma. This stimulates an increase in blood flow and new blood vessel formation in the target area. Studies showed an increase in inflammatory cytokines and growth factors, as well as the regulation of tumour necrosis factor, interleukin, and bone morphogenetic protein follow‐ ing ESWT. Studies indicate that differentiated tenocytes are metabolically ''activated'' by ESWT and significantly induced proliferation and production of collagen (mainly type I) compared with untreated cells [165, 166]. Not all studies were able to show a positive ef‐ fect of ESWT, but this was later argued to be a possible consequence of topical anaes‐

Numerous other substances have been used in the treatment of tendon disorders, including sclerosants, calcium gluconate, heparin, dextrose, and aprotinin; however, more studies have to be performed to prove their efficiency [168]. To date, no optimal treatment modali‐ ties for injured tendons or ligaments have been proposed. In fact, sheathed tendons may heal differently from those not enclosed in sheaths and the process of healing of an intraarticular ligament may differ from an extra-articular ligament. Recent studies support the idea that scaffolds can provide an alternative for tendon augmentation and that tissue engi‐

tion for the treatment of tendinosis can be made [47, 160].

26 Current Issues in Sports and Exercise Medicine

**4.3. Extracorporeal shock wave therapy**

thetics that interfere with ESWT treatment [167].

Regenerative medicine holds great promise for sports medicine with aim to develop novel therapies that will replace, repair, or promote tissue regeneration. It is an increasingly ex‐ panding area of research with hopes of providing therapeutic treatments for diseases and/or injuries that conventional medicines cannot effectively treat. Skeletal muscle has a great selfregenerative capacity, but it is unfortunately limited by fibrotic infiltration. Although none of the antifibrotic agents to improve skeletal muscle regeneration have been tested on hu‐ mans to date, its clinical implications are potentially far-reaching and include not only sports-related injuries, but also diseases such as muscular dystrophies and trauma- and sur‐ gery-related injury. With emerging novel therapeutic targets this is an important area of re‐ search and presents a basis for further possibilities to study different mechanisms of action and effects drug combinations for improving muscle regeneration.

Biomaterials play an important role in directing tissue growth and may provide another tool to manipulate and control stem cell behaviour. Growth factors and therapies using mesenchymal stem cells, scaffolds, and tissue engineering using bioreactors represent promising strategies for tendon, ligament and cartilage repair. While therapies using growth factors seem to be well established in case of the first two, lack of scientific evidence still makes them questionable. In the future of cartilage repair, the modification of cellular differentiation following microfrac‐ ture could be alternated with the use of exogenous growth factors and scaffolds in order to re‐ tain chongrogenic phenotype and to improve the quality of repair tissue generated in the defect. The important future prospective of cartilage repair is also focused on the quality of the bonding and integration of the newly engineered tissue to native cartilage to achieve stable healing. This holds potential for tissue-engineered strategies that would enable repairing com‐ plex cartilage lesions together with the subchondral bone and other structures. However, as with all innovations, carefully conducted studies should be carried out to access the efficiency for cartilage regeneration. Furthermore, long term prospective randomized studies are needed to confirm the encouraging preliminary results.

## **Author details**

Robi Kelc, Jakob Naranda, Matevz Kuhta and Matjaz Vogrin

Department of Orthopaedic Surgery, University Medical Centre Maribor, Slovenia

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**Chapter 2**

**The Physiology of Sports Injuries and Repair Processes**

Sports injuries are among the most common injuries and therefore present a significant public health problem. Physiologic processes after injuries are often neglected while much more attention is being paid to the management of symptoms. However, compre‐ hension of these processes is becoming more and more important as therapies are get‐ ting increasingly focused on specific molecular and cellular processes. In recent decades, extensive research of tissue regeneration after injury and degeneration, including molecu‐ lar pathways in healing, helped towards better understanding of this process and led to discoveries of new potential therapeutic targets. In this chapter physiology of sports inju‐ ries and the latest advances in understanding pathophysiological processes after injury

For skeletal muscles to act properly they must be attached to the bone. Tendons serve as mediators of force transmission that results in joint motion, but they also enable that the muscle belly remains at an optimal distance from the joint on which it acts. Tendons act as springs, which allows them to store and recover energy very effectively. Ligaments on the other hand attach bone to bone and therefore provide mechanical stability of the joint, guide joint motion through their normal range of motion when a tensile load is ap‐ plied and prevent excessive joint displacement. Although tendons and ligaments differ in function, they share similar physiological features with a similar hierarchical structure

> © 2013 Robi et al.; licensee InTech. This is an open access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/3.0), which permits unrestricted use,

© 2013 Robi et al.; licensee InTech. This is a paper distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/3.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

distribution, and reproduction in any medium, provided the original work is properly cited.

**2. Physiology of tendon and ligament injury and repair**

Kelc Robi, Naranda Jakob, Kuhta Matevz and

Additional information is available at the end of the chapter

Vogrin Matjaz

**1. Introduction**

will be discussed.

and mechanical behavior.

http://dx.doi.org/10.5772/54234
