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Logo of nihpaAbout Author manuscriptsSubmit a manuscriptNIH Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
 
Sports Med Arthrosc. Author manuscript; available in PMC Mar 1, 2012.
Published in final edited form as:
Sports Med Arthrosc. Mar 2011; 19(1): 44–49.
doi:  10.1097/JSA.0b013e3182095e5d
PMCID: PMC3073665
NIHMSID: NIHMS265848
The potential for primary repair of the ACL
Patrick Vavken, MD MSc and Martha M Murray, MD
Sports Medicine Research Laboratory, Department of Orthopedic Surgery, Children's Hospital Boston, Harvard Medical School, Boston, MA 02115 USA
Correspondence to: Martha M Murray, MD; Department of Orthopedic Surgery, Children's Hospital Boston, 300 Longwood Avenue, Enders 1016, Boston, Massachusetts 02115, USA. Phone: 001-617-919-2033, Fax: 001-617-730-0170. Martha.murray/at/childrens.harvard.edu
The objective of this work is to assess the feasibility of successfully repairing the torn ACL. Two major motivators for developing a new treatment for ACL injuries are the recently reported high rates of osteoarthritis after conventional ACL reconstruction as well as the problem of how to safely treat skeletally immature patients. A key factor in developing such a technique was the identification of the main inhibitor of intrinsic ACL healing – the lack of clot formation between the two torn ends of the ligament. A bioactive and biocompatible scaffold which could be placed in the wound site to enhance cellular proliferation and biosynthesis was developed. This biomaterial has shown promising functional outcomes in several large animal models of primary repair of partial and complete ACL transection over 4 to 14 weeks, suggesting potential for a successful, future clinical application.
Keywords: Tissue engineering, ACL, regeneration, PRP, animal model, biomechanics
Around the beginning of the 19th century, the discovery of antibiotics and new advances in material science set the stage for the development of orthopaedic implants and durable prostheses. This opened the door for new, highly effective, treatments for diseases like arthritis and osteonecrosis by replacing the damaged tissue with synthetic materials, including polyethylene, metals and ceramics. Later in that century, newly acquired knowledge in both biology and material science offered additional instruments for physicians to further advance treatment options for such diseases. The most influential advances were cell culture techniques and the development of processing techniques to create biocompatible, degradable (bio)materials. These technologies have coalesced into what is commonly known as tissue engineering. As the name implies, this new technology combines knowledge from both engineering and the life sciences, and aims at the creation of biological substitutes or restoration of tissue and organ function by enhanced regeneration.
Despite the undeniably large success of the gold standard treatments such as total joint replacement, the advent of tissue engineering precipitated a move from replacement of damage tissue to enhanced repair and regeneration of tissues; for example, autologous chondrocyte implantation for cartilage defects, bioactive plugs for femoral head necrosis, and autologous cell injections for intervertebral discs. A major driving force behind these developments was a shift in the demographics of the orthopaedic patients with an increasing prevalence of patients with high demand and/or of young age1; 2. This population, given its specific requirements, does not lend itself to classic replacement, mostly because these patients are particularly prone to complications such as wear and loosening of implants over time. Tissue engineering methods potentially offer such patients biological regeneration and repair as a procedure which could delay the need replacement by years, if not for decades.
Developing a regenerative method for repair of the torn ACL begs the question whether there is need for such a technique at all. Three arguments can be made why there is need for such a technique. First, ACL treatment aims at achieving two things, 1) immediately resolving knee instability and pain and, 2) avoiding long-term complications, primarily osteoarthritis. The current gold standard treatment for complete tears of the ACL, reconstruction using an autologous or allogenic tendon graft, yields excellent results for instability and pain in most patients. However, in adolescents there is a higher failure rate than in other age groups with up to 20% to 25% of patients experiencing problems postoperatively3. This problem suggests a different solution may be more optimal for this patient age group. In addition, as more and more systematically gathered long-term follow-up data on ACL reconstructions is becoming available, evidence shows high rates of osteoarthritis despite treatment with ACL reconstruction4-7. These data suggest other options and techniques could improve outcomes.
Second, there are still no standardized treatment options for skeletally immature patients with ACL tears, and the incidence of such injuries has been steadily rising3. ACL reconstruction with transphyseal grafts is still bevlieved to be a risk factor for limb length and angular deformities8; 9 by many, despite the fact that several studies have shown no increase in the rate of such complications10-12. However, the pre-pubescent population could benefit greatly from a regenerative treatment which does not require violation of the physes, and, as has been shown recently, this group of patients may have the potential to respond most strongly to the biological stimuli employed in current enhanced repair techniques13; 14. A repair procedure which does not involve transphyseal drilling therefore has a lower risk profile of physeal complications15.
Third, regeneration of the ACL, rather than replacement with a similar type of tissue, has the potential to preserve the proprioceptive nerve fibers and the complex architecture of the ligament insertion side, features that are usually not reproduced by tendon grafts16. This could potentially lead to more normal biomechanics of the knee if adequate regeneration is achieved16.
Historically, simple suture repair re-approximating the distal and proximal was one of the earliest suggested techniques for treating ACL tears. As early as 1895, primary repair was described17, but it wasn't until the 1950s that the technique was documented by O'Donoghue18-20. Feagin21 and Cabaud22 were the first to report long-term outcomes in the 1970s. However, these early techniques were reported to fail in over 90% of patients21 and, after Sandberg showed in a randomized controlled trial that there was no difference in outcomes after primary repair versus conservative treatment23, suture repair was soon abandoned for surgical replacement of the ACL. But the question of why these repairs failed remained unanswered. Only recently, when the attention of investigators shifted from reconstruction to new ways of ACL treatment, have some answers begun to be found16. Comparing the cells of the spontaneously healing collateral ligaments of the knee with the cruciate ligaments, there were no significant differences in three important biologic processes in wound repair and regeneration 24; 25 26.(Table 1) However, the ACL, in contrast to extra-articular ligaments, does not form a fibrin-platelet clot at the site of the defect, a clot which is the primary scaffolding material filling the wound of the medial collateral ligament. Without this clot, the gap between the two torn ends remains open, and in addition, the inflammatory cascade leading to cell immigration and tissue remodeling is disrupted at its earliest stage24. The reason for this lacking clot formation may be the intra-articularly circulating plasmin in the synovial fluid, which prematurely breaks down the fibrin clot27; 28 . The synovial fluid has also been shown to inhibit ACL fibroblasts26. Premature loss of this fibrin clot may be one mechanism explaining why the ACL does not heal, neither in the natural history nor after suture repair.
Table 1
Table 1
Response of the ACL and MCL to injury
Identifying this premature loss of scaffold allowed scientists to investigate potential solutions, and one logical answer to the lack of clot formation was to create an artificial substitute for the fibrin-platelet clot that would not be prematurely broken down in the synovial environment. (Figure 2) One suggestion was to use hyaluronic acid, which could be injected into the joint to cover a central defect, but this technique, which does not provide mechanical stabilization with sutures or other methods, does not lend itself to complete tears29. A combination of suturing and a collagen-based construct has also shown some promise. Type-I collagen, the principal constituent of the ACL, is a safe and compatible biomaterial with FDA approved use in human applications and can be delivered in form of a gel or a sponge30. Further research showed that ACL fibroblasts spontaneously migrate into collagen biomaterial and are sustained therein. Hence there is no need for preoperative, ex-vivo cell seeding of a collagen biomaterial, and the material can thus be stored for off-shelf use.
Figure 2
Figure 2
shows the triad of tissue engineering (E. Bell in “Principles of Tissue Engineering). Biomaterials, cells, and signals act together to create a biological substitute. The platelet-concentrate acts as both a source for signals and a biomaterial (more ...)
It is important to remember that the functions of the clot spanning a wound are not confined to structural support, but that the clot also acts as the major source for a plethora of growth factors and cytokines31-33. Thus, solely implanting a collagen scaffold would be insufficient to recreate conditions permissive for ACL regeneration. To obviate this problem, a source of growth factors is needed. One of the currently investigated growth factor delivery processes is autologous platelet-concentrates32; 33. (Figure 3) This platelet concentrate, which can be adjusted to a desired platelet density, releases a number of crucial growth factors that stimulate cell migration, proliferation, and collagen production. The amount of released peptides is a function of platelet concentration, but, interestingly, the effects of these growth factors on functional healing diminish with age13; 14; 34, suggesting that younger patients would benefit more greatly than older ones.
Figure 3
Figure 3
shows the surgical model. (a) The ACL is cut at the junction of the proximal and middle third. An EndoButton loaded with three sutures is passed through a tunnel on the femoral cortex. All sutures are passed through a collagen sponge. Two sutures (red) (more ...)
Combing the platelet concentrate with a collagenous biomaterial offers a delivery system for platelets into the wound site, and, at the same time, protects the platelets from the influence of the abovementioned plasmin. Also, the collagen acts as a platelet activator and initiates the release of a number of growth factors into the sponge material. Thus higher concentrations of growth factors can be reached, sustained, and spatially concentrated.
What was needed after the in vitro proof of principle was confirmation in an in vivo model that closely mimicked that human knee joint. Among the available large animal models, canine models have a long track record for ligament repair models, but procedures that are routinely successful in humans fail in canines, making it a less clinically relevant model. Pigs and sheep are closest in anatomy and biomechanics and are validated and economical models for knee surgery and ligament repair and were therefore chosen for this purpose. The development of the model itself, however, was a two-stage procedure. First, the therapeutic potential of enhanced healing had to be tested in a stable, central, defect before a second variable – mechanical stress – could be introduced in the second step, the complete rupture model.
The central defect model, designed to test the biologic healing capacity of enhance repair, was a canine model. In a randomized trial, a standardized. 3.5mm central defect was created in the central portion of the ACL and either left untreated as a control, or treated with a collagen-platelet-composite (CPC)24; 35. Comparing this central defect model to the biological gold standards of ligament and tendon healing, the medial collateral ligament (MCL) and patellar tendon, the model confirmed the poor healing capacity of the untreated central defect of the ACL and excellent healing of the untreated defect in the MCL and patellar tendon24. In addition, a procedure where the defect was filled in with a collagen-platelet composite (CPC) resulted in healing of the ACL defect that was histologically similar to the MCL and patellar tendon. Further histology and immunohistochemistry of the defect site showed a significant increase in tissue filling, and growth factor expression at 3 and 6 weeks post-op with use of CPC24. Finally, MRI analysis and biomechanical testing was done at 6 weeks post-op to complement the description of the repair tissue's histologic profile35. These analyses showed a significant increase in ACL strength after treatment with CPC, and a significant association of this increase in strength with the amount of wound filling on MRI35.
The stable defect model showed that treatment with CPC resulted in more defect fill and a stronger repair tissue, similar to the tissue seen in the healing MCL. However, a more clinically relevant model would be a complete ACL rupture. In the second stage of in vivo testing, a complete ACL transection model was validated in pigs. A new problem in this model was how to deliver and maintain the CPC in the defect site. In the most recent modification of the technique, a specially processed collagen scaffold soaked with PRP is used as a delivery system.
Briefly, for descriptive purposes, the procedure can be divided into two aspects. The central mechanism is suture bridge which is stabilized proximally with an Endobutton (Smith and Nephew, Andover, MA) on the proximal lateral femoral cortex and then sutures from the Endobutton are brought through the knee and tied over a extracortical button on the anteromedial aspect of the tibia to stabilize the knee during the early post-op period A second set of sutures coming from the Endobutton are ties to the tibial stump of the ACL in an attempt to recreate the initial trajectory of the torn ACL. To accomplish this, six suture limbs, run from the Endobutton through a 4.5 mm tunnel into the knee joint. Four of the suture limbs are threaded through the collagen scaffold and continue to leave the knee through a 2.4 mm tunnel from the tibial ACL insertion onto the medial tibial cortex where they are tied, under tension control, over an extracortical button. These sutures serve to pull the scaffold, soaked with PRP hence malleable, into the knee and to afford initial antero-posterior stability of the joint. Since these sutures are absorbable and lose roughly 25% of their initial strength per week, there is an increasing amount of mechanical stress, or stimulus, on the repair tissue over time until the suture is completely absorbed after approximately 63 days on average (Ethicon, Somerville, NJ). This is the first aspect of the procedure, creating a temporarily stable scaffold for repair in perfect alignment with the original ACL. With two of the three sutures used for scaffold fixation and antero-posterior stability, the remaining two suture limbs running from the femoral Endobutton are tied to a whipstitch running up and down the anterior and posterior side of the tibial ACL stump, pulling the ACL tibial stump into the scaffold. This second aspect of the repair procedure with aligns and stabilizes the distal ACL stump to allow for cell migration into the collagen sponge. At this point, the repair construct is left untouched for 10 minutes before wound closure to allow for complete clotting of the PRP.
The use of three sutures begs the question whether stability in biomechanical testing is confounded by this material, rather than afforded by the repair tissue. However, when compared with suture repair alone, suture repair augmented with a collagen-platelet composite resulted in significant improvement in repair strength at 4 weeks (the time when suture strength approaches 0), and 3 months36; 37. At the same time, there was a significant increase in cellularity with the use of CPC, i.e. a strong, ongoing regenerative response, suggesting even better biomechanical outcomes once these cells produced an organized extracellular matrix36.
A potential shortcoming of these studies is that the porcine model builds on an ACL transection rather than a complete, traumatic rupture. However, it should be remembered that even in a clinically complete rupture some fiber bundles as well as the synovial sheath are oftentimes preserved. Also, given the anatomy of the porcine ACL, which is a broad ligament that flatly lies on the tibial plateau rather than obliquely crossing the notch, the “transection” is more of a staged process than a single cut, usually resulting in a combination of numerous cuts at various levels of height as well as quite a few ruptured fibers. Finally, it seems worthwhile to consider that tunnels are drilled through both physes, femoral and tibial, to pass sutures. Such tunnels potentially might jeopardize the growth plate and affect growth. However, the tunnels used for this technique are rather small both in absolute diameter and in relation to physeal area, centered, and bear only little tension, i.e. as much tension as four 0.35mm thick sutures are able to withstand. All these parameters have been shown to reduce the risk of growth disturbances38-43.
Many of the initial studies demonstrating the efficacy of CPC enhanced suture repair were performed in juvenile animals. The next series of studies evaluated the effect of age on both intrinsic ACL healing (with no treatment) and suture repair enhanced with CPC44. That study found important effects of age on ligament healing, with skeletally immature animals having a significantly higher return of preoperative ACL strength with intrinsic healing compared to the adult animals. The adolescent animals had less return of ACL strength than the skeletally immature animals with no treatment. However, use of a suture repair enhanced with a collagen-platelet composite resulted in a nearly doubling of the adolescent ACL strength after transection. The skeletally mature animals had less return of ACL strength than immature animals even with the use of a collagen-platelet composite.
In an effort to determine a mechanism for the disparity in healing with age, a histological study of the 3 age groups was performed to examine the early healing response in the ACL after 1, 2, and 4 weeks in three age groups45; 46. The major finding in that study was that the cell density within the wound site was highest in the immature animals. Cellular population of the scaffold occurred in all age groups, but cell density in the adult ligament wound sites lagged 2 weeks behind that in the immature animals. Follow-up in-vitro studies demonstrated the cells from immature ACL both migrate and proliferate more quickly than those from adult ACL, which may represent possible etiologies for the differences observed in vivo. The reason for such differences in cell behavior across age groups, despite the considerable and constant amount of stimulation provided by PRP, might be the cells’ ability to respond to the growth factors released by PRP. Recent studies have shown that expression levels of growth factor receptors depend on age, and that biomechanical outcomes are associated with receptor expression levels47.
In summary, animal age appears to affect the ability of the ACL to repair itself or to respond positively to suture repair. In addition, the preliminary studies performed in juvenile animal were also immediate repairs – that is, the ligament was transected and then repaired right away. The more likely scenario in clinical practice is that 2 to 6 weeks elapse between injury and surgical treatment. Therefore, an additional study was performed to determine the effect of a 2- or 6-week delay on ACL repair strength48. In that study, a delay of either 2 or 6 weeks resulted in a significant loss of ACL strength after 3 months of healing. Possible reasons for this finding include a loss of ACL tissue due to degradation, inflammatory changes in the intra-articular environment and synovial fluid, and loss of secondary structures. Further studies to investigate these hypotheses are needed.
Recent changes in patient populations have supported the principles of tissue engineering and regenerative medicine in orthopedic surgery. Younger and more active patients benefit from such approaches that encourage biological repair since they obviate complications provoked by the high stresses due to high physical demand over a prolonged time after classic replacement with synthetic materials. Currently, methods to enhance biological repair of the torn anterior cruciate ligament are intensively investigated. Such investigations have elucidated the reasons behind the lack of intrinsic healing in the ACL and opened the door for methods to compensate for this lack. A series of in vitro and in vivo studies have resulted in the development of a technique for tissue engineering, enhanced primary ACL repair, using a collagenous scaffold and autologous platelet-rich plasma, allowing for off-shelf availability. Histological assessment has shown a high level of structural equivalence of the repair tissue after such a procedure with that of ligaments and tendons that heal spontaneously, such as the medial collateral ligament. Biomechanical testing has revealed ongoing improvement in repair strength over 3 months. Most recently it was observed that both age and the amount of time between rupture and repair both may play an important role in outcomes.
Figure 1
Figure 1
shows the cascade of events after a complete ACL tear.
Acknowledgments
This work was supported by a grant from NIH R01 AR052772.
Footnotes
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