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Materials Research

Print version ISSN 1516-1439

Mat. Res. vol.16 no.1 São Carlos Jan./Feb. 2013 Epub Nov 13, 2012

http://dx.doi.org/10.1590/S1516-14392012005000155 

The use of PLDLA/PCL-T scaffold to repair osteochondral defects in vivo

 

 

Andrea Rodrigues EspositoI, II, *; Angelo Carneiro BonadioI; Nathaly Oliveira PereiraI; Túlio Pereira CardosoI; Maria Lourdes Peris BarboI; Eliana Aparecida de Rezende DuekI, II

IBiomaterials Laboratory, Center for Medical and Health Sciences, Catholic University of São Paulo – PUC-SP, Sorocaba, SP, Brazil
IIDepartment of Materials Engineering, Faculty of Mechanical Engineering, State University of Campinas – UNICAMP, Campinas, SP, Brazil

 

 


ABSTRACT

The physiological repair of osteochondral lesions requires the development of a scaffold that is compatible with the structure of the damaged tissue, cartilage and bone. The aim of this study was to evaluate the biological performance of a PLDLA/PCL-T (90/10) scaffold for repairing osteochondral defects in rabbits. Polymeric scaffolds containing saccharose (75% w/v) were obtained by solvent casting and then implanted in the medial knee condyles of 12 New Zealand rabbits after osteochondral damage with a trephine metallic drill (diameter: 3.3 mm) in both medial femoral condyles. Each rabbit received the same treatment, i.e., the polymeric scaffold was implanted on the right side while no material was implanted on the left side (control). Four and 12 weeks later histological examination revealed bone neoformation in the implant group, with the presence of hyaline cartilage and mesenchymal tissue. In contrast, the control group showed bone neoformation with necrosis, exacerbated superficial fibrosis, inflammation and cracks in the neoformed tissue. These findings indicate that the PLDLA/PCL-T scaffold was biocompatible and protected the condyles by stabilizing the lesion and allowing subchondral bone tissue and hyaline cartilage formation.

Keywords: biomaterials, PLDLA/PCL-T, osteochondral repair


 

 

1. Introduction

Arthritis is one of the most common diseases affecting human articulations1. The composition of joint cartilage and subchondral bone is important for a joint to work properly since these materials provide a low friction intra-joint environment capable of excellent movement, with lubrication, stability and uniform load distribution, as well as shock absorption during movement2-4. Cartilage has an important role in protecting subchondral bone from high stress and diminishes the regular contact pressure5. However, cartilage from arthritic joints suffers degradation, resulting in pain, joint rigidity and the loss of movement over time. The limited potential of cartilage for regeneration makes osteoarthritis one of the most important problems in orthopedic surgery. The frequency of osteochondral lesions and osteoarthritis increases with the practice of various sports4.

The cause of wearing in joint cartilage and subchondral bone is still unknown. One possibility is that wearing is related to subchondral bone weakening since as bones become less dense so does their ability to support cartilage when transmitting a load to cortical bone. As a result, cartilage fractures increase4. These osteochondral defects rarely repair themselves, depending on the type, dimension and location of the damage3.

Tissue regeneration can been divided into three phases, namely, necrosis, inflammation and repair6. However, the natural healing of a lesion in joint hyaline cartilage (chondral defect) does not follow these phases, primarily because of the avascular condition of this tissue7,8. However, if such damage extends up to subchondral bone (which has adequate vascularization) then all three phases may occur6.

There are two major approaches for solving joint cartilage loss or lesions. The first is to repair the lesion by stimulating fibrocartilaginous (or eventually cartilaginous) tissue formation through subchondral bone perforation in the damaged area. However, the neoformed tissue that fills the osteochondral lesion usually differs significantly from normal cartilaginous tissue with regard to its composition, biochemistry, biomechanics and arrangement of inner elements9. The lack of perfect integration between the neoformed tissue and cartilaginous tissue enhances the permeability to water. In addition, neoformed fibrocartilaginous tissue has a lower elasticity module compared to cartilaginous tissue3,10,11.

The second alternative aims to replace the cartilaginous tissue with material of similar physical and chemical characteristics3. Unfortunately, the current therapeutic strategy does not guarantee the restoration of a durable joint surface and has not yet been proven to be effective in preventing osteoarthritis. As a result, most studies have addressed the repair of joint surfaces through tissue engineering and the use of porous, three-dimensional synthetic polymeric scaffolds12,13.

Polymer characteristics such as topography, chemical composition and surface energy and porosity are essential for biocompatibility14. In addition, the material must have favorable biomechanical properties to provide an environment that allows the cells to integrate, differentiate and develop into new tissue15. The polymers most widely studied for biomedical applications are poly(α-hydroxy) acids, primarily because of suitable properties related to degradation, bioreabsorption and biocompatibility16-18.

The copolymer poly(L-co-D,L-lactic acid), PLDLA, combines the mechanical properties of poly(lactic acid) without the long degradation time normally associated with the homopolymer (caused by the high crystallinity of the latter); the higher degradation rate is provided by poly(D,L-lactic acid), although the mechanical properties of this molecule are somewhat inferior to those of poly (lactic acid). By combining the homopolymers it is possible to obtain a product with good mechanical properties and an adequate degradation time for surgical applications19. The addition of low molecular mass molecules, such as polycaprolactone-triol (PCL-T), to PLDLA has led to the development of a less hydrophobic polymer by increasing its chain mobility, there by facilitating interaction with the receptor tissue20. Based on studies in vitro and in vivo, Esposito21 showed that a PLDLA/PCT-T scaffold can be used in cell culturing and tissue engineering because it promotes cellular adhesion and allows tissue growth throughout the scaffold.

The aim of this study was to evaluate the biological performance of a PLDLA/PCL-T scaffold as an implant for osteochondral repair in New Zealand rabbits and to assess its influence on tissue regeneration in vivo.

 

2. Experimental

2.1. Polymeric scaffold

Poly (L-co-D,L-lactic acid) PLDLA and polycaprolactone-triol PCL-T solutions (90/10 composition) were obtained by casting in chloroform (10% m/v; Merck©). After the polymer had completely dissolved, saccharose (75% m/v; Synth©) was added, with the granularity being limited to 250-500 µm. The solutions were poured into Teflon molds 4.1 mm in diameter and 1 cm high. After solvent evaporation the saccharose was removed with polyvinyl alcohol (PVA).

2.2. Assessment in vivo

Twelve New Zealand white rabbits 6 months old were used. The rabbits were anesthetized with an intramuscular injection of ketamine chlorohydrate (30 mg.kg–1) associated with xylazine chlorohydrate (5 mg.kg–1). The femorotibial-patellar joint of both legs was accessed via a medial parapatellar incision done laterally in the joint capsule followed by arthrotomy and lateral dislocation of the patella. By flexing the knee the femoral condyle was exposed and a 3.3 mm × 38.5 mm trephine metallic drill was used to retrieve an osteochondral cylinder 1 cm long from the joint cartilage and the subchondral bone of the trochlear sulcus in both femoral medial condyles (right and left leg). Each rabbit received the same treatment, i.e., the polymeric scaffold was implanted on the right leg while no material was implanted on the left leg, kept without treatment (control). The wound was sutured with 4-0 mononylon using simple interrupted stitches in the capsule and simple suturing in the skin7,8.

The rabbits were sacrificed 4 weeks and 12 weeks (n = 6 to each group) after implantation with an overdose of halothane. The medial femoral condyles and their surrounding tissue were accessed by a medial parapatellar incision and removed for macroscopic examination of tissue repair followed by fixation in Bouin's solution for 24 hours and decalcification in 4.13% EDTA for two weeks.

This study was approved by the Committee for Ethics in Animal Research at UNIVAP (protocol no. A062/CEP/2009).

2.3. Macroscopic evaluation

The macroscopic analysis was based on seven parameters:

  • Repair – healing of the lesion;

  • Continuity – leveling of the lesion and integration of the repaired tissues into the surrounding cartilage;

  • Surface – presence of hyaline cartilage;

  • Brightness – appearance of hyaline cartilage;

  • Consistency – performance of the lesion;

  • Presence of inflammation; and

  • Presence of a visible fracture.

The result was considered to be good (biologically acceptable) when 6-7 of these parameters were satisfactory, or bad (biologically unacceptable) when two or more of these parameters were unsatisfactory.

2.4. Material processing – histological analysis

The samples were processed for histological analysis using techniques commonly applied in conventional light microscopy. Sagittal and longitudinal 5-µm-thick sections of the distal femur were stained with hematoxylin-eosin and picrosirius red. The sections were analyzed and photographed with a Nikon® Eclipse E800 polarized light microscope.

For qualitative histological analysis the following parameters were analyzed:

  • The type of regenerated tissue (cartilaginous, fibrocartilaginous or fibrous) on the lesion surface;

  • The characteristics of the cartilaginous surface (smooth, depressed or irregular);

  • Absence or presence of regenerated subchondral bone; and

  • Presence of an inflammatory response.

 

3. Results and Discussion

All of the rabbits (n = 12) survived until the end of the experiment and showed normal behavior and activities throughout this period. There was no post-operative infection or any evidence of a foreign body reaction. The rabbits showed excellent clinical recovery during the post-operative period. Early ambulation was limited to an antalgic gait for two days (on average) followed by a normal gait thereafter.

Macroscopic evaluation showed that all of the rabbits recovered completely from the incision wound without any external scarring. Subsequent examination of the condyles showed that the implanted scaffolds were well-adapted to the tissue, with no apparent rejection, infection or chronic inflammatory response. The pin of one rabbit in the polymer implant group (rabbit #8-12 weeks) slipped out of the cavity, leaving an empty space; this animal was not included in the analysis of the polymer group.

Histologic repair was considered satisfactory only if the regenerated tissue surface was smooth, covered and level with the surrounding hyaline cartilage. Four weeks after implantation, all condyles from the control group were covered by a large amount of fibrous tissue, in contrast to those with the polymeric scaffold implant, which showed no such formation. Twelve weeks after implantation one rabbit developed an exuberant bony callus on the damaged condyle, as well as fibrous tissue growth around it. This neostructure led to deformation of the condyle and subsequent joint deformation. There were clear differences between the groups in the types of healing tissues they showed. The healing surfaces of untreated lesions (control group) were not uniform and contained depressions that indicated an absence of or only partial filling with cartilage (Figure 1). In some cases, cracks and fissures were observed at the edges where surrounding tissue and healing tissue met. Similar findings were reported by Xie et al.22.

Table 1 shows the results of the macroscopic analysis. In this table, R indicates the right condyle in which the polymeric PLDLA/PCL-T scaffold was implanted, and L indicates the left condyle (control group) in which no material was implanted in the lesion. The letters U and S mean unsatisfactory and satisfactory, respectively.

Two rabbits showed partially satisfactory results four weeks after polymer implantation in the damaged condyle. In these cases, the polymer showed continuity with the surrounding tissue, as well as consistency and brightness (Figure 2), whereas the control condyles showed 3-4 unsatisfactory items (Table 1).

After 12 weeks, four rabbits in the implant group had six or more satisfactory items (repair, continuity, surface properties and consistency, no inflammation and no fracture), which suggested PLDLA/PCL-T scaffold biocompatibility (Table 1). The only unsatisfactory item was brightness since the regeneration of hyaline cartilage was restricted to the final stage of healing. In contrast, the only satisfactory item after 12 weeks in the control group was consistency, with evident fibrosis and joint surface discontinuity.

After four weeks, fractures were more frequent (four cases) among rabbits in the control group. This finding suggests that the polymeric scaffold had a structural function in stabilizing the fragile damaged area. Two rabbits in the control group had fractures after 12 weeks, whereas no fractures were observed in the implanted group, except for rabbit #8. However, this rabbit was excluded from the subsequent analysis because the polymeric implant did not remain in the osteochondral lesion as mentioned. This stability in conserving the condylar structure, along with the other parameters analyzed (Table 1), indicated satisfactory healing in condyles with polymeric implants.

The histological analysis of control condyles after four weeks shows foreign body-type reactions with necrosis and an exacerbated inflammatory infiltrate containing multinucleated giant cells and necrotic debris (Figure 3a, b). There were small areas of irregular bone neoformation with a membranous aspect, exacerbated fibrosis and a chronic inflammatory infiltrate with synovial proliferation (Figure 3c). The remaining hyaline cartilage was thin and disorganized, and showed fissures and bone sequestration with the presence of hyperplasic chondroblasts. The mature/young bone interface showed an irregular pattern of endochondral ossification and superficial fibrosis. The fibrous tissue was surrounded by rays of striated musculature that suggested rupture of the joint capsule.

Histological analysis of the PLDLA/PLC-T implants after four weeks showed trabecular bone neoformation and the presence of mesenchymal tissue filling the lesion (Figure 4). This tissue consisted of long cells, blastic cells, a few collagen fibers and abundant fundamental amorphous substance. There was no evidence of giant cells associated with a foreign body reaction, thus indicating excellent polymer compatibility. The biocompatibility of mechanical devices is strongly influenced by the degradation rate of the material used since this determines the type and intensity of the inflammatory response23.

Figure 5 provides histological images from the control group after 12 weeks. There was bone neoformation with extensive superficial fibrosis (Figures 5a, b). Along the edges of the surface synovial membrane there was cellular proliferation and a chronic inflammatory response. Only two cases showed hyaline cartilage, although the joint surface was fibrotic (Figure 5c, d). One condyle showed bone neoformation on the surface, with fibrosis and bone sequestration suggestive of necrotic post-fracture remains observed in the four-week interval.

Twelve weeks after PLDLA/PCL-T scaffold implantation there was bone regeneration that included trabecular bone with beams in the medulla (Figure 6a, c). The joint surface had an extensive covering of mature hyaline cartilage that advanced along the edges (Figures 6b, d); a superficial area with fibrosis was also observed. There was no inflammatory infiltrate. The bone diaphysis had an endochondral pattern of bone neoformation with foci of cartilage. This uneven cartilage distribution resulted in a mixture of thin and thick (hyperplasic) areas, all of them with evident bone neoformation.

In the last decade, huge steps forward have been made in the field of cartilage regeneration. The treatment of osteochondral lesions that involve load-supporting joints, especially the knee, is a great challenge for orthopedics, mainly because of the characteristics of hyaline joint cartilage8. When such wounds result in large lesions, the bone tissue is incapable of repair and generates fibrous tissue that results in a loss of mechanical function24.

The most recent trend for treating chondral/osteochondral lesions is based on the application of smart biomaterials that could lead to "in situ" regeneration of not only cartilage, but also subchondral bone, preferably through a single step procedure to reduce the costs and the morbidity for the patient. This innovative approach is currently under investigation as several scaffolds have been proposed in clinical practice, with or without the aid of cells25.

The velocity of degradation and the extent of the foreign body reaction are determined by the initial molar mass and chemical composition of the material. Clinically, the absorption of poly(glycolic acid) PGA and poly(lactic acid) (PLA) polymers and their copolymers such as PLDLA is frequently accompanied by a local foreign body reaction, especially if degradation is fast or if the polymers are not completely absorbed. However, this reaction is of minimal importance for tissue neoformation since it disappears after the complete degradation and bioreabsorption of the polymer18,20,21,26-29.

Porous scaffolds can be prepared by several techniques and have a useful morphology for tissue engineering since their porosity provides physical space for cell growth and colonization. This in turn can contribute to the organization of structures similar to tissues, thereby providing a provisory scaffold for tissue regeneration30. In addition, cells adhered to the scaffold are subject to mechanical pressure that can stimulate the production of new bone matrix4,13.

Emans et al.31 have examined the effect of pore size and pore interconnectivity on cartilage repair in osteochondral defects treated with different scaffolds, using a compression moulding (CM) and a three-dimensional fibre (3DF) deposition technique. Three months post-implantation, cartilage repair was significantly improved after implantation of a 3DF scaffold compared to a CM scaffold. Although not significant, Mankin scores for osteoarthritis (OA) indicated less OA in the 3DF scaffold group compared to empty defects and CM-treated defects. It is concluded that scaffold pore size and pore interconnectivity influences osteochondral repair and a decreased pore interconnectivity seems to impair osteochondral repair.

According to Mikos et al.32, the rate of cell penetration and growth in polymeric bioreabsorbable porous structures is directly related to the pore size and distribution in the material and varies according to the size of the invading cells and the properties of the implant.

The development of new biocompatible materials that can stimulate good adhesion, growth and cell differentiation is a challenge since such material must temporarily replace the mechanical function of bone and degrade at a rate equivalent to that for tissue regeneration24. Shapiro et al.33 described the process of osteochondral repair in rabbits with lesions that reached the spongy bone. Initially, the blood clot was replaced by a web of fibrin with capillary proliferation from the surrounding bone marrow. Mesenchymal cells invaded the clot periphery and spread over the tissue being repaired. Superficially, a fibrous layer with collagen fibers parallel to the joint surface was formed. Deeper in the lesion, mesenchymal cells differentiated into chondroblasts. As cell differentiation proceeded the tissue under repair developed an aspect similar to hyaline cartilage. Endochondral ossification and the intramembranous formation of osteoid, both of which are involved in subchondral bone replacement, occurred in the deepest region of cartilage in repair. The osteochondral and subchondral bone junction with lamellar bone was repaired 24 weeks after surgery.

Prevention of the degeneration of affected joints is clinically important for the repair process. Shapiro et al.33 suggested that the ability to maintain cartilage intactness in a healing joint depends on the reconstitution of excised bone tissue. Cartilage undergoing repair did not show the degenerative alterations observed in most of the 24-week post-operatory failures, except for a small number of animals in which subchondral bone was reconstructed7.

Histological analysis revealed the nature of the neoformed tissue for each type of repair. The poor repair of untreated lesions (control rabbits) reflected mainly the retardation of subchondral bone formation and the presence of necrosis at four weeks, possibly because of the high number of fractures. These findings indicate the importance of subchondral bone in tissue reorganization. The predictability of cartilaginous tissue formation in the treated lesions and the predominance of fibrous tissue in the untreated lesions agree with the findings of others authors34.

Our results agree with other reports showing that a four-week interval after implantation is insufficient for osteochondral regeneration; in this period, only the initial performance of the scaffold and the occurrence of an inflammatory response can be evaluated35-38. In contrast, bone neoformation is readily observed 12 weeks after the implantation of PLGA and PLLA18,35.

Fedrizzi and Duek28 showed that PLDLA/PCL-T (90/10 composition) pins were sufficiently biocompatible for bone regeneration in tibia and this polymer combination held promising prospects for osteochondral applications.

In agreement with this, recent work has shown that hybrid, biphasic frameworks can be useful for repairing osteochondral lesions22. The combination of biodegradable polymers and bioactive ceramics in a variety of composite structures is promising in this area, whereby the fabrication methods, associated cells and signaling factors determine the success of the strategies39. In this regard, the use of hydrogels can enhance osteochondral repair40,41.

Recently, Hannink et al.42 evaluated if a porous polycaprolactone-polyurethane scaffold, currently used for partial meniscal replacement in clinical practice, could initiate regeneration and repair of osteochondral defects, and if regeneration and repair were related to mechanical stimulation in New Zealand White rabbits. The results suggest that mechanical forces may not have to be applied over long periods of time to accelerate tissue formation and increase cartilage repair longevity. Osteochondral defects might be treated using porous polymer scaffolds, although several limitations need yet to be overcome.

Additionally, tissue engineering has emerged as an excellent approach for the repair and regeneration of damaged tissue, with the potential to circumvent all the limitations of autologous and allogeneic tissue repair43,44. Cell sources and biological protein incorporation methods are discussed, addressing their interaction with scaffolds and highlighting the potential for creating a new generation of bilayered composite scaffolds that can mimic the native interfacial tissue properties, and are able to adapt to the biological environment39.

Deng et al.45 evaluated the efficacy of a three-dimensional (3D) heterogeneous/bilayered scaffold, consists of gelatin, chondroitin sulphate and sodium hyaluronate (GCH) and ceramic bovine bone (GCBB), to repair large defects in rabbit joints. In summary, this study demonstrated that a novel scaffold, comprising a top layer of GCH, having mechanical properties comparable to native cartilage, and combined with chondrocytes and bone marrow stem cells (BMSCs) could be used to repair large osteochondral defects in joints.

Furthermore, the fascinating potential of mesenchymal stem cells has recently opened new paths of research to discover how and whether these powerful entities can really contribute to tissue regeneration46,47. The first clinical trials have been published but further high quality research is needed to understand their mechanisms of action, their limits, and their clinical efficacy25.

In agreement with the criteria defined by Gogolewski48, the PLDLA/PCL-T scaffold used in this study did not induce an exacerbated foreign body inflammatory response, was not carcinogenic, mutagenic, teratogenic, toxic or allergenic and did not cause hypersensitivity or activate the complement system. Together, these properties indicate that PLDLA/PCL-T could be useful in a variety of therapeutic applications.

In contrast, the empty space seen in the control group could contribute to the greater incidence of bone fractures during healing.

However, longer implant times should be studied to evaluate the tissue regeneration and validate the hypothesis accessed.

 

4. Conclusion

The results of this study show that although bone neoformation was observed in osteochondral lesions of treated and non-treated lesions, treatment with a polymer implant markedly reduced the inflammatory response, bone necrosis and giant cell foreign body reaction compared to the control group. The protective action of the polymer scaffold probably reflected its ability to stabilize the lesion and allow the formation of hyaline cartilage. The good biocompatibility of PLDLA/PCL-T seen here indicates that this material may be useful in tissue engineering.

 

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Received: March 31, 2012
Revised: August 19, 2012

 

 

* e-mail: aesposito@fem.unicamp.br