Paradoxical tunnel enlargement after ACL reconstruction with hamstring autografts when using β-TCP containing interference screws for tibial aperture fixation- prospectively comparative study
verfasst von:
Joon Ho Wang, Eun Su Lee, Byung Hoon Lee
Tibial aperture fixation with a bioabsorbable interference screw is a popular fixation method in anterior cruciate ligament reconstruction (ACLR). An interference screw containing β-tricalcium phosphate (β-TCP) to improve bony integration and biocompatibility was recently introduced. This study aims to compare the clinical outcomes and radiological results of tunnel enlargement effect between the 2 bioabsorbable fixative devices of pure poly-L-lactic acid (PLLA) interference screws and β-TCP-containing screws, for tibial interference fixation in ACLR using hamstring autografts.
Methods
Eighty consecutive patients who had undergone double-bundle ACLR between 2011 to 2012 were prospectively reviewed and randomly divided into two groups based on the type of tibial interference screw: 28 were assigned to the pure PLLA screw group (Group A), while the other 29 were assigned to the β-TCP-containing screw fixation group (Group B). Clinical evaluations and radiological analyses were conducted in both groups with a minimum 2- year follow-up.
Results
There was no significant difference in subjective or objective clinical outcome between the 2 groups. In radiological analyses, the use of a β-TCP-containing screw reduced tunnel widening in the portion of the tunnel with screw engagement compared to the pure PLLA screw, while the use of a β-TCP-containing screw resulted in greater tunnel enlargement in the proximal portion of the tunnel without screw engagement than use of a pure PLLA screw.
Conclusion
Use of a β-TCP-containing interference screw in tibial aperture fixation reduced tunnel enlargement in the vicinity of the screw, whereas greater enlargement occurred proximal to the screw end relative to use of a pure PLLA interference screw. These paradoxical enlargements in use of β-TCP containing screws suggest that for reducing tunnel enlargement, the length of the interference screw should be as fit as possible with tunnel length in terms of using soft grafts.
Level of Evidence: II, Prospectively comparative study.
Trial registration
Retrospectively registered with ClinicalTrials.gov. (NCT02754674), Date of trial registration: February 10, 2016.
Interference screws are commonly used for fixation in orthopedic surgery, especially in tibial aperture fixation for ACL reconstruction. Biodegradable cannulated interference fixation screws made of poly-L-lactic acid (PLLA) were introduced in the early 1990s to improve postoperative imaging, decrease stress shielding, avoid graft laceration, and make revision easier [1, 2]. These screws have a fixation strength equivalent to that of metal screws [3‐5]. Bioabsorbable fixation devices offer advantages over metallic devices in that they can be substituted for bone contrary to metal screws; bone tunnel remodeling is not possible when metal interference screws are in place.
However, there are concerns that explanted pure PLLA biodegradable interference screws may not degrade, and that replacement with bone may be incomplete [1, 6‐8], and the incidence of tunnel enlargements following the use of resorbable devices has been shown to be higher than metallic devices [9‐11]. A variety of biodegradable screws with different material compositions have therefore been introduced. Not all bioabsorbable materials have the same compositions, absorption rates, or tissue reactions. Some of the bioabsorbable materials commonly used for interference screws are polyglycolic acid (PGA), polylactic acid (PLA), polyparadioxanone (PDS), polymers of PGA/PLA, and various stereoisomers of lactic acid (PDLA).
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The Matryx® (Linvatec Corp, Largo, FL, USA) screw, made of 96 L/4D poly lactic acid (PLA) and 30% β-tricalcium phosphate (β-TCP), was introduced to enhance osteoconduction and to be more biocompatible with bone than existing screw materials. However, to the best of our knowledge, the effect of this screw against tunnel widening effect by osteoconduction and bony integration around tunnels has not been investigated in a clinical setting. Therefore, we sought to investigate the clinical advantages of β-TCP containing biodegradable screws under their theoretical advantages.
We hypothesized that use of β-TCP-containing interference screws would improve coaptation of the graft to the tunnel with replacement of the degraded screw by new bone formation, and result in better tunnel remodeling by preventing tunnel widening. The purpose of this study was to evaluate whether use of a β-TCP-containing interference screw resulted in superior clinical and radiological outcomes (esp, the preventive effect on tunnel enlargement during in vivo degradation within the tunnel) in ACL reconstruction using autologous hamstring grafts compared to a commercially available pure PLLA biodegradable screw.
Methods
Level of Evidence II, prospectively comparative study
From February 2011 to June 2012, a total of 119 patients with ACL injury were enrolled in this study. Inclusion criteria were patients who underwent a primary anatomical double bundle ACL reconstruction with tibial aperture fixation by Bioscrew® (Linvatec Corp, Largo, FL, USA), which is made of 100% poly-L-lactic acid (PLLA) or Matryx® (Linvatec Corp), which is made of 70% 96 L/4D poly lactic acid (PLA) & 30% β-TCP, and who were at least 20 years of age; patients younger than 20 years of age were treated on the basis of adolescent ACL and single-bundle reconstruction with no interference screw placed in the tibial tunnel if open physis. Of these 119 patients, 39 were excluded for the following reasons: single-bundle reconstruction (4), revisional ACL reconstruction (7), combined surgeries such as meniscal allograft transplantation (2), any previous ligament surgery or bony procedure in the area of graft attachment (10), degenerative arthritic knee (1), pregnancy (1), and other reasons (14) (Fig. 1). After exclusion, 80 patients underwent DB-ACLR according to a trial comparing two different interference screws. Eighty patients were randomly assigned to either the PLLA screw group or the β-TCP screw group on the day of surgery using permuted block randomization [12], and 74 underwent knee computed tomography (CT) immediately and 1-year after the operation (Fig. 1).
To assess differences in tibial tunnel widening according to fixation device, the cross sectional areas at four locations were compared between the two groups on the immediate postoperative and 1- year follow-up CT images. All operations were performed by a single surgeon (J.H.W.) experienced in ACLR using both the transportal and outside-in techniques. All patients underwent CT examination twice on the same CT device using the same protocol within 3 days after the initial surgery and at the postoperative 1-year follow-up. The current study received Institutional Review Board approval from our institution (Samsung Medical Center 2010–08-116) before study onset, and our protocol was also approved. Informed consent was obtained from all participants (ClinicalTrials.gov identifier: NCT02754674).
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Surgical technique and rehabilitation
All operations were performed using an arthroscopic-assisted technique. Femoral and tibial tunnels were created in the centers of the respective anatomic insertions. Semitendinosus and gracilis tendons were harvested from the affected limb. The tunnels were prepared to be the same size as the graft, and the femoral tunnel was drilled to this diameter by matching the drill and/or dilator to the graft size while accounting for the size of the native insertion site. The drill diameter for the femoral and tibial tunnels was determined based on the diameter of the prepared graft. Grafts were inserted retrograde via the tibial tunnel into the femoral tunnel, and fixed with a cortical suspension system using the shortest possible loop (10 to 15 mm) to ensure maximal contact between the graft and the tunnel walls on the femoral side, and with bioabsorbable interference screws with a post tie on the tibial side for all cases.
Graft was normally trimmed to retain its original size with a length of 26 to 30 cm. Then, it was folded and sutured together with the use of no. 1 absorbable sutures to form two triple-strand grafts. A 6-stranded graft, composed of triple semitendinosus (6.5 to 9.5 mm) for the anteromedial (AM) bundle and triple gracilis (4.5 to 7 mm) for the posterolateral (PL) bundle, was created for each group.
Anatomic tibial insertion sites of both bundles were marked with an ArthroCare device (ArthroCare, Sunnyvale, CA, USA), and the tip of the guide was aimed at the centers of the AM and PL bundle remnant tibial insertion sites. A 3.2-mm guide pin was inserted into the bases of the AM and PL tibial insertion sites. The AM and PL tibial tunnels were then drilled with a cannulated drill. Bioscrew® or Matryx® (length 30 mm) with a diameter 1 mm larger than the tunnel diameter was used for tibial aperture fixation at 0o of knee flexion and applying a 30–35 N tension to the graft using the dedicated tie tensioner [13], and an additional extracortical screw with a spike washer was applied. Interference screws eccentrically compress the graft against the wall of the tibial bone tunnel. The type of all screws was blinded at insertion to surgeon for randomized allocation.
All patients began active quadriceps isometric exercise and active range-of-motion exercise immediately after surgery. Four to 5 days after surgery, an ACL limited-motion brace was applied, and joint motion exercise was carried out at 15° increments per week. At 4 and 6 weeks after surgery, 90° and 135° of motion, respectively, were allowed. A pair of crutches was used to allow partial weight bearing from 3 days to 6 weeks after surgery. Patients were educated on performing proprioceptive balancing exercise at 3 months after surgery. Return to competitive sports involving jumping, pivoting, or sidestepping was prohibited until 6 months after the reconstruction [14].
CT evaluation & measurement
A CT scanner Light Speed VCT (GE Medical Systems, Milwaukee, WI, USA) was used for all examinations. All patients were placed in a supine position with knee full extension. The collimation was 16 × 0.625 mm, the tube parameters were 120 kVp and 200 mA, and the acquisition matrix was 512 × 512 pixels. Images were processed for multiplane reconstruction, and cross-sectional area (CSA) was measured using Osirix (version 3.5.1; Pixeo, Geneva, Switzerland). We measured CSAs in the plane perpendicular to the long axis of the tibial tunnel using Osirix at the following four cutting levels (Fig. 2): (1) joint line, which was just below the proximal joint line, (2) center level of the tunnel without screw engagement (mid-tunnel), (3) center level of the tunnel with screw engagement (mid-screw), and (4) tunnel aperture outlet. The difference in CSA at each of the four cutting levels was compared between the two groups on immediate postoperative and postoperative 1-year CT scans (Fig. 3). CSA measurements were performed by two training fellows in sports medicine. If the AM and PL tunnels overlapped around the joint line, the CSA of the joint line was excluded from the statistical analysis because of the inability to measure each value separately.
Fig. 2
Cross-sectional area was measured at the four cutting levels of tibial tunnel in the plane perpendicular to the long axis of the tunnel: (1) joint line, (2) mid-tunnel, (3) mid-screw, and (4) outlet
Fig. 3
Cross-sectional view and area (mm2) measurement of (1) the joint line, (2) the mid-tunnel, (3) the mid-screw, and (4) the outlet cutting level
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×
Clinical evaluation
Clinical follow-up evaluations were then conducted at 12 and 24 months and made by an independent examiner (ARK). The preoperative evaluation was conducted by the Lysholm knee score, Hospital for Special Surgery (HSS) score, Tegner score, the International Knee Documentation Committee Score (IKDC) [15‐17] and a ligament stability assessment by KT-2000® arthrometer (MEDmetric, San Diego, CA) testing with a side-to-side difference of 30 lb. with the knee at 20° of knee flexion. The differences of ligament stability between both legs were calculated by subtracting the laxity measurement of the uninjured knee from the laxity measurement of the injured knee. Intraoperative and postoperative complications were recorded.
Reliability and statistical analysis
Two orthopedic surgeons (independent observers) developed and agreed to the measurement methods together; however, they were blinded to each other’s measurements and their previous measurements. They measured the cross-sectional areas at the four cutting levels for all knees twice with an interval of 2 weeks. Reliability of the measurements was assessed by an independent statistician who examined interobserver reliability using the intraclass correlation coefficient. A priori power analysis was performed to determine the sample size using the two-sided hypothesis test at an α level of 0.05 and a power of 0.8. A post hoc power analysis was performed to determine whether the results of our study of 25 cases indicated adequate power, and the power was 85.21%, which was adequate to detect a difference of 1 mm widening [18, 19]. The paired t-test was applied to compare cross-sectional area at the four cutting levels between both groups on immediate postoperative and 1-year follow-up CT scans. P < 0.05 was considered significant (95% confidence intervals). The 2-sample t-test was applied to compare the cross-sectional areas of “mid-tunnel” and “mid-screw”. The difference of clinical outcome scales between two groups was evaluated with a 2-sample t test or Mann-Whitney test. Statistical analyses were executed using SAS version 9.3 (SAS Institute, Cary, NC).
Results
Demographics
The mean age was 34.7 years (range, 20 to 60 years) and the mean body mass index (BMI) was 24.6 kg/m2 (range, 19.1 to 35.2 kg/m2). The mean duration of postoperative follow-up was 33 months (range, 24 to 60 months). There were no significant differences between groups in age, gender, BMI, femoral tunneling technique, and tunnel diameter, values of which are shown in Table 1. On immediate postoperative CT, CSA at each cutting level was not significantly different between the two groups in either the AM or PL tunnels. AM and PL tunnel overlap around the joint line was found in five cases in group A and nine cases in group B.
Table 1
Patient demographicsa
Group A[PLLA screw](n = 28)
Group B[β-TCP screw](n = 29)
p - value
Age, y
36.1 ± 8.9
32.7 ± 12.3
0.225
Sex, male/female, n
21:7
24:5
0.473
BMI, kg/m2
24.2 ± 2.6
24.7 ± 3.9
0.848
Femoral tunneling technique, n
TP: OI
11:17
17:12
0.144
Tunnel diameter (drill size, mm)
AM
7.5 ± 0.6 (6.5–9.5)
7.4 ± 0.6 (6.0–9.0)
0.387
PL
5.7 ± 0.5 (4.5–7.0)
5.7 ± 0.5 (4.5–7.0)
0.675
Tunnel length (mm)
AM
39.6 ± 3.9 (34–50)
40.0 ± 2.9 (34–45)
0.661
PL
43.7 ± 3.5 (35–50)
44.8 ± 3.0 (38–50)
0.228
BMI body mass index, TP transportal, OI outside-in
aValue are presented as mean ± standard deviation, with range in parentheses
No cases of complete absorption and replacement of the interference screw with new bone were observed at the 1-year follow-up CT in either group. No clinical evidence of any adverse events related to these interference fixation screws was observed, and degenerative radiographic changes were not noted.
Radiological results (tunnel enlargement)
In both AM and PL tunnels, the average CSAs at the four cutting levels were significantly greater at postoperative 1 year than immediately post-operatively, and the most increased CSAs were observed at the mid-tunnel level (Tables 2 and 3). There were significant inter-group differences in increments of CSAs of the AM tunnel 1 year after surgery at the mid-tunnel and mid-screw cutting levels. At the mid-screw level, mean increase in CSA after 1 year was significantly smaller in group B (β-TCP screw) than in group A (PLLA screw) (16.8% vs. 27.2%, p = 0.024). At the mid-tunnel level, the mean increase in CSA after 1 year was significantly larger in group 2 (β-TCP screw) than in group 1 (PLLA screw) (66.9% vs. 40.1%, p = 0.028) (Table 2). In PL tunnel analysis, there was no significant difference in average increments of CSAs at the four cutting levels (Table 3). The measurement of CSAs at the four cutting levels showed a good reliability (an appendix is available as a Additional file 1: Table S-1).
Table 2
Comparison of the cross-sectional area of the AM tibial tunnel at the four cutting levels between immediate postoperative and postoperative 1 year CT scans
Cutting level
Cross sectional area (mm2)
Group
Immediate postop.
1YR
Difference
†P
Joint line
1
41.5 ± 6.6
54.6 ± 11.3
13.2 (31.7%)
< 0.001
2
42.0 ± 9.1
57.3 ± 12.1
15.4 (36.6%)
< 0.001
*P
0.523
Mid-tunnel
1
41.8 ± 7.2
58.6 ± 11.6
16.8 (40.1%)
< 0.001
2
41.9 ± 8.7
70.0 ± 19.5
28.1 (66.9%)
< 0.001
*P
0.028
Mid-screw
1
61.0 ± 10.5
77.6 ± 13.3
16.6 (27.2%)
< 0.001
2
63.3 ± 9.8
73.9 ± 14.2
10.6 (16.8%)
< 0.001
*P
0.024
Outlet
1
62.0 ± 10.6
69.2 ± 15.1
7.3 (11.7%)
< 0.001
2
61.6 ± 11.3
68.4 ± 14.4
6.8 (11.0%)
< 0.001
*P
0.833
1YR; postoperative 1 year
*Comparison of the increments in cross-sectional area 1 year after surgery between the two groups at the each cutting level
†Comparison of the cross-sectional area between immediate postoperative and postoperative 1 year CT scans
*Values of P < 0.05 are displayed in bold
Table 3
Comparison of the cross-sectional area of the PL tibial tunnel at the four cutting levels between immediate postoperative and postoperative 1 year CT scans
Cutting level
Cross-sectional area (mm2)
Group
Immediate postop.
1YR
Difference
†P
Joint line
1
21.1 ± 6.3
28.8 ± 10.5
7.7 (36.3%)
0.002
2
24.5 ± 4.1
34.6 ± 7.5
10.1 (41.5%)
< 0.001
*P
0.411
Mid-tunnel
1
23.0 ± 6.6
30.7 ± 11.8
7.7 (33.5%)
< 0.001
2
25.0 ± 3.8
36.0 ± 10.0
11.0 (44.2%)
< 0.001
*P
0.179
Mid-screw
1
36.6 ± 8.58
42.4 ± 12.8
5.8 (15.8%)
< 0.001
2
40.0 ± 6.83
46.7 ± 13.3
6.7 (16.8%)
0.003
*P
0.734
Outlet
1
33.3 ± 9.4
34.1 ± 11.0
0.8 (2.5%)
0.445
2
36.1 ± 8.0
36.6 ± 10.0
0.5 (1.4%)
0.647
*P
0.845
1YR; postoperative 1 year
*Comparison of the increments in cross-sectional area 1 year after surgery between two groups at each cutting level
†Comparison of the cross-sectional area between immediate postoperative and postoperative 1 year CT scans
Clinical results
Mean Lysholm score, HSS and IKDC values and KT-2000 measurements values are reported in Table 4. At 2 years, the mean side-to-side difference for anterior displacement at 30° flexion was 2.1 mm (SD ± 1.1 mm) in group A and 1.8 mm (SD ± 1.5 mm) in group B. The mean Lysholm score was 94.4 (SD ± 6.8) in group A and 94.1 (SD ± 6.3) in group B. In group A, the mean IKDC subjective score was 85 (SD ± 11.7) in group A and 86.4 (SD ± 9.5). At the last follow-up, both groups reached a satisfactory pain relief and functional improvements, without significant differences. KT-2000 side-to-side differences (p = n.s.) were similar between the two types of screw fixation. In our experience, the difference of tibial tunnel enlargement did not affect clinical results at 2 years.
Table 4
Clinical outcomes
Group A
[PLLA screw]
(n = 28)
Group B
[β-TCP screw]
(n = 29)
p - value
KT-2000™ side-to-side difference (mm)
Baseline
4.5 ± 2.2
4.5 ± 2.2
0.964
24 months
2.1 ± 1.1
1.8 ± 1.5
0.334
Lysholm knee score
Baseline
71.6 ± 21.7
61.9 ± 22.8
0.102
24 months
94.4 ± 6.8
94.1 ± 6.3
0.848
HSS score (/100)
Baseline
92.1 ± 11.8
86.6 ± 15.7
0.131
24 months
99.4 ± 1.7
99.6 ± 1.9
0.691
IKDC subjective score
Baseline
58.2 ± 16.2
51.6 ± 19.0
0.157
24 months
85.0 ± 11.7
86.4 ± 9.5
0.610
Tegner score
Baseline
3.7 ± 1.4
3.8 ± 1.9
0.706
24 months
6.3 ± 1.5
6.3 ± 1.6
0.977
Values are expressed as median ± standard deviation
ROM range of motion, IKDC International Knee Documentation Committee
Discussion
The principal findings of our study were as follows: (1) the use of a β-TCP-containing screw reduced tunnel widening in the portion of the tunnel with screw engagement compared to the pure PLLA screw, while (2) the use of a β-TCP-containing screw resulted in greater tunnel enlargement in the proximal portion of the tunnel without screw engagement than use of a pure PLLA screw. These findings might be explained that in the screw-bone contact area, particles during degradation of β-TCP led to less local reactivity or inflammatory responses under their neutralizing effects, whereas they activated osteoclasts and resulted in osteolysis with mechanical stress or synovial fluid influx in proximal portion without screw engagement.
The use of biodegradable interference screws is widely accepted because of their ease of handling and effective fixation. Ideally, a biodegradable interference screw should degrade with minimal or no host-bone reaction. It is reasonable to assume that the faster a material degrades, the earlier the osseous replacement takes place [20, 21]. However, tissue reaction occurs only during and after degradation of the implant [22]. In fact, use of interference screws made of other, more rapidly degrading polymers has been reported to result in collection of fluid at the top of the femoral bone tunnel and significant tunnel widening [23].
In terms of bone-patellar tendon-bone (BPTB) grafts, interference screws have the benefit of reducing the potential space created in bone by the compaction method, which forms the walls of the container [24]. Several MRI studies have showed no signs of container phenomenon or pathologic signals at long-term follow-up. In terms of autologous hamstring tendons, the use for ACL reconstruction has increased in popularity over the recent years [25]. However, even the use of an interference screw with a size matching that of the tunnel diameter will not totally prevent synovial fluid from infiltrating into the tunnel during the biologic transition of thin fibrous tissue into dense fibrous tissue. Practically, although we used only interference screws with a diameter 1 mm larger than the tunnel diameter for tibial aperture fixation in our study, significantly increased CSAs were observed at all four cutting levels at postoperative 1 year in both AM and PL tunnels.
However, our finding of a smaller increase in tunnel widening in the portion of the tunnel with β-TCP screw engagement has demonstrated a better behavior in clinical settings. Our hypothesis was that early degradation and the osteoconduction-promoting effect of β-TCP screws would enhance bony integration and reduce tunnel enlargement. As hypothesized, the tunnel was less enlarged in the section with screw engagement in the β-TCP-containing screw group than the PLLA screw group. The addition of β-TCP to a degradable polymer such as PLLA creates an inorganic osteoconductive scaffold and changes the properties of the scaffold. During degradation, β-TCP breaks down into calcium ions and phosphates, which maintain an elevated pH around the implant [26‐28]. This could act as a buffer to acidic degradation products of lactic acid or glycolic acid. These neutralizing effects around screws could result in less local reactivity or inflammatory responses, thereby reducing tunnel enlargement [29]. In the reconstructed oblique axial view on CT, bony integration was observed in the screw-bone contact area in the mid-tunnel area in the β-TCP-containing interference screw group. There was no gap between the adjacent native bone and implanted screw, and the screw tract was corticated as densely as cancellous bone (Fig. 4). Meanwhile, an enlarged tunnel and sclerotic margin without bony integration around the screw was observed in group A. Furthermore, no ingrowth of neo-bone tissue from the adjacent native bone was observed (Fig. 5). We attributed this to the presence of nondegradable poly L-lactide polymer, which could hinder the ingrowth of new bone from the native adjacent cancellous bone tissue.
Fig. 4
Bony integration was observed in the screw-bone contact area in group B
Fig. 5
Sclerotic margin without bony integration in the screw-bone contact area was observed in group A
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×
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Meanwhile, abruptly increased tunnel enlargement was observed in the proximal portion to β-TCP containing screw relative to a PLLA screw (Fig. 6). This conflicts with previous findings in patellar tendon autografts; bone tunnels in the tibia began to increase in size from the distal end [24]. Most probable explanation for this paradoxical enlargement is the cellular response to calcium phosphate (β-TCP). Particles proximally degraded from β-TCP by mechanical stress or synovial fluid influx likely activated osteoclasts and resulted in osteolysis, similar to the role of wear debris in aseptic loosening in arthroplasty. Many environmental factors are known to be involved in the osteointegration and degradation of calcium phosphate ceramics after implantation, including physiochemical processes and various cell activating molecules and cytokines [30‐32].
Fig. 6
In group B, the degree of tunnel enlargement increased abruptly proximal to the screw end
×
Almost studies of explanted biodegradable interference screws have been overstated regarding to concerns about whether claims of bio-absorbability because of limited evidences of degradation [21, 33, 34]. It would be resulted from almost studies have been designed using patellar bone graft with little effect of container phenomenon with interference screw. However, when using hamstring grafts, the effects of the biodegradable interference screw on early tunnel widening must be considered. Despite these radiological observations, the clinical evaluation showed no significant difference, with good outcomes in both groups at the postoperative 2-year follow-up in current study. However, this could stem from the use of an additional extra-cortical screw with a spike washer for tibial aperture fixation.
Several studies have reported that use of β-TCP-containing screws reduces tunnel enlargement [13]. However, to the best of our knowledge, this is the first study to report the paradoxical tunnel enlargement in the proximal portion of tibial tunnel following fixation with the β-TCP-containing fixation screw. Further studies are needed to clarify the factors aggravating tunnel enlargement in ACL reconstruction.
The strength of this study is that to evaluate bone tunnel widening, immediate and postoperative 1- year CT scans were used instead of digital plan radiograph. Tunnel enlargement is believed to occur both intraoperatively and postoperatively. Intraoperative enlargement may be due to eccentric reaming, graft and reamer diameter mismatch, or use of the press-fit technique, so a difference in CSA between the reamer and actual tunnel is inevitable. In the current study, immediate postoperative CT images were used to obtain baselines values, so postoperative enlargement could be evaluated without intraoperative change bias. Furthermore, the tunnel was segmented into four different sections for more precise analysis; this enabled us to observe paradoxical enlargement in the area of the tunnel without screw engagement.
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Nevertheless, the present study had some limitations. First, no histologic data were obtained to confirm complete degradation of the PLLA screws. Second, the follow-up period was relatively short. However, several studies have shown that most tunnel widening occurs during the first 3 months [35‐39]. According to these studies, a one-year follow-up period is sufficient to observe enlargement of the tunnel itself, but tunnel remodeling and screw resorption are still occurring. A longer-term follow-up study is required to obtain a thorough understanding of tunnel enlargement and the fate of the implant and tunnel ossification. Third, the current study is limited by its small sample size. However, a post hoc power analysis was performed to determine whether the sample size had sufficient power. Fourth, we did not account for other confounding factors such as bone mineral density, screw and tunnel length ratio, or variations in tunnel location. However, there were no significant differences in age, gender, or BMI between the two groups of subjects. Another limitation is the lack of a comprehensive review of patients who underwent patellar tendon autograft ACL reconstruction. We investigated only the patients underwent DB-ACLR, might not the standard technique in some countries, not single-bundle method.
Conclusion
Use of a β-TCP-containing interference screw in tibial aperture fixation reduced tunnel enlargement in the vicinity of the screw, whereas greater enlargement occurred proximal to the screw end relative to use of a pure PLLP interference screw. These paradoxical enlargements in use of β-TCP containing screws suggest that for reducing tunnel enlargement, the length of the interference screw should be as fit as possible with tunnel length in terms of using soft grafts.
Acknowledgements
The authors thank all members of the Sports Medicine Center, Samsung Medical Center for their great scientific debates.
Funding
This work was supported by the National Research Foundation of Korea(NRF) grant funded by the Korea government(MSIP) (2015R1A2A1A15054779), and this research was supported by a grant of the Korea Health Technology R&D Project through the Korea Health Industry Development Institute (KHIDI), funded by the Ministry of Health & Welfare, Republic of Korea (grant number: HI10C2020).
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Availability of data and materials
The datasets used and/or analysed during the current study available from the corresponding author on reasonable request.
Ethics approval and consent to participate
All procedures performed in studies involving human participants were in accordance with the ethical standards of the institutional and/or national research committee and with the 1964 Helsinki declaration and its later amendments or comparable ethical standards. The current study obtained Institutional Review Board approval from our institution (Samsung Medical Center IRB 2010–08-116) before study onset, and our protocol was also approved. Informed consent was obtained from all participants. All participates were provided written consent to participate.
Consent for publication
Not applicable.
Competing interests
The authors declare that they have no competing interests.
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Paradoxical tunnel enlargement after ACL reconstruction with hamstring autografts when using β-TCP containing interference screws for tibial aperture fixation- prospectively comparative study
