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To compare the initial fixation strength of osteochondral fragment fixations using osteochondral plugs, bioabsorbable pins, and knotless suture anchors.
Eighteen fresh-frozen immature (6 month old) porcine knees were used. An osteochondral fragment, cut from the articular surface of the medial femoral condyle to achieve a thickness of 5 mm, was used to mimic the unstable osteochondral fragment. It was fixed using three techniques, including two osteochondral plugs (osteochondral plug group), four full-threaded poly l-lactic acid pins (bioabsorbable pin group), and three suture anchors with a 2-0 tape (suture anchor group). Tensile loads at displacements of 1 and 2 mm and ultimate failure load were measured at a cross-head speed of 100 mm/min, and the variables of the three groups were compared statistically using a one-way ANOVA with Tukey’s honestly significant difference test.
There was no significant difference in the tensile load to achieve 1-mm displacement. The load to achieve 2-mm displacement and the ultimate failure load were significantly greater in the suture anchor group than the osteochondral plug group and the bioabsorbable pin group.
Single-pull destructive testing of a fixed articular osteochondral fragment with the force perpendicular to the articular surface, demonstrated no statistical difference in the tensile load to achieve 1-mm displacement, but the load to achieve 2-mm displacement was significantly greater for the three suture anchor-interlocking 2-0 tape constructs than the dual osteochondral plug fixation and the four bioabsorbable pin fixation constructs. Additionally, the three suture anchor-interlocking 2-0 tape construct’s mean single-pull failure load was greater than other two fixation procedures.
To achieve osteochondral fragment union, sufficient fixation strength is critical. However, the initial fixation strength of osteochondral plugs, bioabsorbable pins, and knotless suture anchors for unstable osteochondral lesions remains unclear.
The treatment strategy for knee osteochondral lesions (OCLs), including osteochondral dissecans (OCD) and osteochondral fracture, depends on the stability or quality of the osteochondral fragment. OCL treatment aims to restore articular surface congruity and prevent secondary osteoarthritis and persistent pain. If the osteochondral fragment has sufficient subchondral bone quality, osteochondral fragment fixation is a suitable surgical procedure for unstable OCL.
The benefit of this procedure is that it avoids the risk of donor site morbidity. Because of the same advantage, it has been reported in recent years that a knotless suture anchor is useful for osteochondral fragment fixation.
This technique can provide a wider compression force distribution from the suture bridge configuration. In addition, this procedure has the advantages that the anchor is completely buried under the cartilage, and the implant does not need to be removed.
To achieve osteochondral fragment union, sufficient fixation strength is a seemingly critical factor. However, the initial fixation strength of these surgical procedures remains unclear. The purpose of this study was to compare the initial fixation strength of osteochondral fragment fixations using osteochondral plugs, bioabsorbable pins, and knotless suture anchors. The hypothesis was that the initial fixation strength of the osteochondral fragment fixation with a knotless suture anchor is stronger than that of other previous procedures.
Eighteen fresh-frozen immature (6-month-old) porcine knees were used in this study. This study was approved by institutional review board of Hirosaki University (no. 2011-199). Specimens were stored at −20 °C and then thawed at room temperature for 24 h before testing. All soft tissue structures were removed to expose the joint surface of the distal femur. The proximal part of the femur was placed in a mold of polymethylmethacrylate to rigidly grip testing fixtures. An osteochondral fragment was used to mimic an unstable osteochondral fragment, which was cut from the articular surface of the medial femoral condyle to achieve a thickness of 5 mm (Fig 1). Osteochondral fragments had an anteroposterior diameter of 30.4 ± 2.7 mm and a transverse diameter of 22.5 ± 1.7 mm. Specimens were divided into three groups of six knees each based on fixation techniques. After anatomical reduction, the osteochondral fragments were fixed using three different techniques. The number of fixation devices in each group was the same for clinical osteochondral fragments of the same size.
In the osteochondral plug fixation group (osteochondral plug group),
the osteochondral fragment was fixed with two osteochondral plugs (6.0 × 15 mm) harvested from the lateral femoral condyle in the same knee. For osteochondral grafting, the Osteochondral Autograft Transfer System (OATS; Arthrex, Naples, FL) was used. Press-fit osteochondral graft implantation was achieved by inserting an osteochondral graft of 6.0 mm in diameter obtained from the donor site into a smaller recipient hole of 5.0 mm in diameter. A tube harvester of 6.0 mm in diameter was set at a depth of 15 mm in the bone; the cylindrical osteochondral plug was then detached at the base of the tube by rotating the tube harvester 90°. At the recipient site, the recipient hole was created at a depth of 15 mm using a tube harvester of 5.0 mm in diameter. The obtained osteochondral plug was inserted into the recipient hole directly from the tube harvester (Fig 2A). During bioabsorbable pin fixation, the osteochondral fragment was fixed with four full-threaded poly l-lactic acid (PLLA) pins (1.5 × 20 mm, Takiron Co., Osaka, Japan) after drilling a hole of 2.0 mm in diameter (bioabsorbable pin group) (Fig 2B). During knotless suture anchor fixation, the osteochondral fragment was fixed with three PushLock anchors (2.4 × 11.3 mm, Arthrex, Naples, FL) with a 2-0 Mini SutureTape (Arthrex, Naples, FL) (suture anchor group). The suture anchor consists of a radiolucent body and a separate eyelet made of polyetheretherketone (PEEK) (Fig 2C). To determine the tension of the 2-0 tape, the total depth of the anchor insertion and the distance between anchors were calculated. The tension was adjusted, so that the 2-0 tape did not infiltrate the cartilage surface, which would cause cartilage damage during anchor fixation. After fixation, the specimen was mounted on a material-testing machine (Instron 4465; Instron Corp., Canton, MA) and was rigidly fastened in place using a specially designed clamp. The load cell size of material testing machine was 5 kN. A metal screw of 3.5 mm in diameter was inserted into the osteochondral fragment and then advanced perpendicular to the osteotomy plane, so that it could be clamped during tensile load testing, with the tensile load applied perpendicular to the osteotomy plane. Moreover, to reduce the osteochondral fragment anatomically, the subchondral bone of the osteochondral fragment was excavated, so that the screw head was completely buried in the subchondral bone (Figs 1 and 3).
The macroscopic appearance of the osteochondral fragment after testing and mode of failure were examined. Tensile loads at displacements of 1 and 2 mm and ultimate failure load were measured at a cross-head speed of 100 mm/min. A total of 6 biomechanical tests were performed in each group.
The tensile strength and ultimate failure load of the three groups are shown as mean and standard deviations. Variable normality was determined using the Shapiro-Wilk test. Biomechanical data were compared between groups using a one-way analysis of variance, with Tukey’s honestly significant difference test. Results showed that the standard deviation of the overall ultimate failure load was 75.4 N. When six specimens were used in each group, a post hoc power analysis revealed that type I error and its effect size were .854 and 1.065, respectively (P = .05). All statistical analyses were performed using SPSS version 27.0 (IBM Corp., Armonk, NY), and a P value <.05 was considered statistically significant.
There was no macroscopic osteochondral fragment fracture, articular cartilage crack, or clamped metal screw loosening after testing in all groups. The pull-out of the osteochondral fragment from the femoral condyle was observed in all specimens without breaking the osteochondral plug, bioabsorbable pin, suture anchor, and 2-0 tape.
The tensile load at a displacement of 1 mm was 30.8 ± 18.9 N in the osteochondral plug group, 49.8 ± 28.4 N in the PLLA group, and 55.3 ± 20.2 N in the suture anchor group, indicating that there were no significant differences between groups (P = .240) (Table 1). The tensile load at a displacement of 2 mm was significantly higher in the suture anchor group than in the osteochondral plug (P = .002) and bioabsorbable pin (P = .017) groups (37.0 ± 26.0 N in the osteochondral plug group, 52.8 ± 24.1 N in the bioabsorbable pin group, and 100.4 ± 21.5 N in the suture anchor group) (Table 1). Moreover, the ultimate failure load was higher in the suture anchor group than in the osteochondral plug and bioabsorbable pin groups (P < .001, both) (40.8 ± 25.8 N in the osteochondral plug group, 59.9 ± 29.1 N in the bioabsorbable pin group, and 188.4 ± 41.7 N in the suture anchor group) (Table 1).
Table 1The Results of the Tensile Load at a Displacement of 1 and 2 mm and Ultimate Failure Load
Single-pull destructive testing of a fixed articular osteochondral fragment with the force perpendicular to the articular surface, demonstrated no statistical difference in the tensile load to achieve 1-mm displacement, but the load to achieve 2 mm displacement was significantly greater for the three-suture anchor-interlocking 2-0 tape constructs (100.4 ± 21.5 N) than the dual 6-mm osteochondral plug fixation (37.0 ± 26.0 N, P = .002) and the four 1.5-mm bioabsorbable pin fixation constructs (52.8 ± 24.1 N, P = .017). Additionally, the three suture anchor-interlocking 2-0 tape construct’s mean single-pull failure load (188.4 ± 41.7 N) was greater (P < .001) than that of both the dual 6-mm osteochondral plug fixation (40.8 ± 25.8 N) and the four 1.5-mm bioabsorbable pin fixation constructs (59.9 ± 29.1 N).
Successful osteochondral fragment fixation outcomes mainly depend on the restoration of articular surface congruity and biological fixation. Initial fixation strength is an important factor of successful outcomes; however, it is affected by the properties or thickness of the osteochondral fragment.
demonstrated an in situ fixation of an osteochondral fragment with an autogenous cylindrical osteochondral plug. Osteochondral plug fixation allowed an immediate and reliable whole tissue transfer, including the transfer of the viable hyaline cartilage, intact tidemark, subchondral bone, and bone. Miura et al.
reported the clinical outcomes of 12 osteochondral fragment fixations for knee OCD using osteochondral plug technique. The interface between the osteochondral fragment and subchondral bone disappeared on magnetic resonance imaging in all patients at 3 months postoperatively. Yoshizumi et al.
also reported a good postoperative course, demonstrating that union of the osteochondral plug and the entire OCD lesion was confirmed within 6 months postoperatively using the osteochondral plug technique. Although this procedure has the advantage of biological healing, donor site morbidity is possible.
Regarding bioabsorbable internal fixation for unstable knee OCD, Chun et al.
although the number of patients was relatively small and there were some differences in the union rate depending on the age of patients, good clinical results have been reported. In contrast, low rates of clinical healing and high complication rates after bioabsorbable fixation among skeletally mature patients were suggested.
conducted a magnetic resonance imaging study to investigate the knee joint of children following osteochondral fragment fixation using bioabsorbable nails. They revealed that nail breakage was observed in 26 of 58 patients (45%), with a median time of 6.5 months between operation and the first study, in which a broken nail was observed. Among patients with nail breakage, those who were diagnosed with a new meniscal tear, all broken nails were situated at the site of the torn meniscus. In addition, nail breakage was observed in 57% of cases of patients diagnosed with a new cartilage injury. They concluded that the high prevalence of nail breakage was independent of skeletal maturity and the total number of nails used. Although this procedure does not induce donor site morbidity, there is a risk of insufficient fixation strength and secondary injury to the intra-articular structure due to implant breakage or backout.
Recently, some surgical osteochondral fragment fixation techniques using suture anchors were proposed.
demonstrated the suture anchor fixation technique, which is used in this experiment. They suggested that this technique could fix and press down over a wide area in a triangular structure without suture tying. The results of this biomechanical study supported their new technique as the ultimate failure load was significantly higher in the suture anchor group than in the other two techniques.
In this study, there was no significant difference between groups in terms of tensile strength at a displacement of 1 mm; however, the suture anchor group demonstrated a significantly higher strength at a displacement of 2 mm. This may be due to the suture anchor structure. Because this suture anchor has a separate eyelet and anchor, slight differences in anchor insertion depth may affect tensile strength. This suggests that it is important to insert the anchor at a depth at which it makes full contact with the eyelet; however, if the anchor is inserted deeper than required, the suture will be overtensioned, raising a risk of osteochondral fragment surface damage. Therefore, it is essential to drill and insert anchors to an appropriate depth clinically.
There are several limitations to this study. First, this was a time 0 study that did not consider cyclic loading. Osteochondral plug fixation has advantages when considering the effects of biological unions. Therefore, there may be patients in whom osteochondral plug fixation is indicated, depending on the condition of the osteochondral fragment and the remaining subchondral bone. The second limitation of this study was that the tensile strength when using other fixation devices or other types of fixation has not been examined. In addition, only perpendicular force was applied to the osteochondral fragment; therefore, the sharing force generated in vivo was not reproduced. Since failure mechanism in clinical situation is considered to be caused by sharing force to the osteochondral fragment, it is unclear whether the fixation strength in this result of this study is directly linked to clinical outcome. The third limitation was the experiment environment, including a room temperature or not performing the tensile test in an aqueous environment.
Single-pull destructive testing of a fixed articular osteochondral fragment with the force perpendicular to the articular surface, demonstrated no statistical difference in the tensile load to achieve 1-mm displacement, but the load to achieve 2-mm displacement was significantly greater for the three suture anchor-interlocking 2-0 tape constructs than the dual 6-mm osteochondral plug fixation and the four 1.5-mm bioabsorbable pin fixation constructs. Additionally, the three suture anchor-interlocking 2-0 tape construct’s mean single-pull failure load was greater than other two fixation procedures.