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Rotational alignment of the tibial component in total knee arthroplasty is better at the medial third of tibial tuberosity than at the medial border
BMC Musculoskeletal Disorders volume 11, Article number: 57 (2010)
Correct rotational alignment of the femoral and tibial component is an important factor for successful TKA. The transepicondylar axis is widely accepted as a reference for the femoral component. There is not a standard reference for the tibial component. CT scans were used in this study to measure which of 2 tibial landmarks most reliably reproduces a correct femoro-tibial rotational alignment in TKA.
80 patients received a cemented, unconstrained, cruciate-retaining TKA with a rotating platform. CT scans were performed 5-7 days postoperatively but before discharge. The rotational mismatch between the femoral and tibial components was measured. Furthermore, the rotational variance between the transepicondylar line, as a reference for the orientation of the femoral component and different tibial landmarks, was measured.
There was notable rotational mismatch between the femoral and tibial components. The median mismatch was 0° (range: 16.2 degrees relative external to 14.4 degrees relative internal rotation of the femoral component).
Using the transepicondylar line as a reference for femoral rotational alignment and the medial third of the tuberosity as a reference for tibial rotational alignment, 67.5% of all TKA had a femoro-tibial variance within ± 5 degrees, 85% within ± 10 degrees and 97.5% within ± 20 degrees. Using the medial border of the tibial tubercle as a reference this variance was greater, only 3.8% had a femoro-tibial variance within ± 5 degrees, 15% within ± 10 degrees and 68.8% within ± 20 degrees.
Using fixed bone landmarks for rotational alignment leads to a notable variance between femoral and tibial components. Referencing the tibial rotation on a line from the medial third of the tibial tubercle to the center of the tibial tray resulted in a better femoro-tibial rotational alignment than using the medial border of tibial tubercle as a landmark. Surgeons using fixed bearings with a high rotational constraint between the inlay and the femoral component should be aware of this effect to avoid premature polyethylene wear.
Clinical trials registry NCT01022099
The outcome of total knee arthroplasty (TKA) is dependant on multiple factors. In addition to patient-related factors, restoring the mechanical axis and balancing the soft tissue are important factors in obtaining proper rotational alignment of the femoral and tibial components. Rotational malalignment may lead to patellar maltracking, anterior knee pain, femoro-tibial flexion instability and premature wear of the polyethylene inlay [1–5]. Several studies have demonstrated higher revision rates and less favorable clinical results in patients with rotational malalignment of the femoral and tibial components [3, 6, 7]. In addition to these findings, a biomechanical study has demonstrated an increase in the tibial cortex strain at approximately 10° of rotational malalignment .
The transepicondylar axis is widely accepted as the best representation of the functional flexion-extension axis of the knee [4, 9–13]. As a result, the transepicondylar line is used as a reference for the rotational alignment of the femoral component.
However, a standard reference for tibial rotational alignment remains controversial. Several different landmarks can be used for tibial rotational alignment including extraarticular references (i.e., the transmalleolar axis and the second metatarsal bone). Unfortunately, these references vary among patients and are therefore unreliable Intraarticular references (i.e., the posterior tibial condylar line, the transcondylar tibial line or the line between the tibial spines) can be difficult to identify in osteoarthritic knees Therefore, most surgeons use the tibial tubercle and the insertion of the posterior cruciate ligament on the posterior border of the tibia as reference points. These anatomic landmarks provide the most reliable landmarks for rotational alignment of the tibia Three recommended points of the tibial tubercle that are used to determine the rotation of the component are the medial border,  the medial third  and the most prominent point of the tubercle [1, 2]. Nonetheless, these landmarks vary greatly between patients [16–18].
Another option is the "self-seeking method", which aligns the tibial component according to the rotational alignment of the femoral component during trial reduction. This method induces the risk of transfering a femoral malrotation to the tibia .
We have previously reported our results of rotational alignment of the femoral and tibial component after navigated and conventional TKA using postoperative CT scans . In this study we used these CT scans to measure femoro-tibial rotational mismatch in order to investigate which tibial landmark (the medial border or the medial third of the tibial tubercle) is the most reliable for a correct femoro-tibial rotational alignment. This investigation is based on the premise that rotational mismatch between foral and tibial component should be zero degree if both components are ideally implanted.
The study protocol was approved by the local independent ethics committee of the Medical Faculty of the Technical University Dresden on 31.03.2005. All patients signed informed consent before study inclusion.
80 patients with primary or secondary osteoarthritis of the knee, no previous hemi or total knee arthroplasty, a mechanical axis between 20° of varus and 5° of valgus and no severe instability received an unconstrained, cruciate-retaining TKA with a rotating platform during a prospective randomized study comparing navigated and conventional surgical technique . There was no difference between the two surgical techniques for rotational alignment, varus/valgus alignment and demographic data and therefore the data from all 80 patients were pooled for further analysis of best tibial rotational alignment.
Due to the use of the rotating platform the femur and the tibia could rotate against each other as forced by the soft tissues. Therefore rotational deviation between femur and tibia could be measured. Femoro-tibial rotational mismatch was defined as the difference (in degrees) between femoral and tbial component on CT scans. "True" femoro-tibial rotational variance was defined as the difference (in degrees) between an ideal position of the femoral component (transepicondylar line) and a hypothesized ideal position of the tibial component (medial border or medial third of the tibial tubercle).
Radiographic and CT evaluation
Five to seven days after the surgery, all patients received a radiographic and CT assessment. Radiographic evaluation of the leg axis and alignment of the components was performed as previously described . The patellar tilt and the displacement of the patella were measured on a merchant view radiograph. The patellar tracking was defined as neutral if the tilt was ± 5° and the displacement less than 5 mm .
The CT digital images were evaluated using the software ID.PACS Release 3.6 (Image Devices, Idstein, Germany). The rotational alignment of the femoral and tibial components were evaluated on the CT scans as already described The rotational alignment of the femoral component was defined as a line through the centre of both femoral fixation pegs (Fig. 1a). The rotational alignment of the tibial component was defined as a line along the posterior border of the tibial stem. The rotational alignment of the femoral and tibial component were then superimposed and the mismatch between both was measured (Fig. 1b).
In order to obtain the "true" rotational variance between femur and tibia without any implantation failure, the transepicondylar axis (Fig. 2a) was superimposed to the tibia. From this line, a perpendicular line through the rotational center of the tibial tray (fixation peg for rotating platform, Fig. 2b) was drawn. These lines were superimposed on a slice where the tibial tuberosity was visible (Fig. 2c). The tibial tuberosity was divided into three parts (Fig. 2d). A line from the medial border of the tuberosity to the centre of the tibial tray was drawn. The angle between this line and the line perpendicular to the transepicondylar axis was measured (Fig. 2e). Additionally, a line from the lateral border of the medial third to the centre of the tibial tray was drawn. The angle between this line and the line perpendicular to the transepicondylar axis was also measured (Fig. 2f).
Sample size considerations
The primary radiological endpoint of this investigation was the "true" rotational variance between the femur and the tibia, which was quantified by respectively using each of the two tibial alignment landmarks (the medial third or the medial border of the tuberosity). A deviation between femur and tibia of less than ± 10° was considered tolerable from a clinical perspective.
The sample size of the underlying controlled clinical trial was targeted for the comparison of tibial rotational alignment after navigated versus conventional TKA. However, the resulting total sample size of 80 patients can also be regarded sufficient for this investigation.
The confirmatory analysis of this investigation was based on a sign test, which was applied to intraindividually compare the "true" rotational variances' distributions when being assessed by the respective landmarks. The results of this confirmatory test were summarized in terms of a p-value.
To detect a median difference of at least 10° between the resulting mismatch distributions under assumption of a difference standard deviation of 20°, the effective sample size of 80 patients ensures a statistical power of 99%, when a two-sided paired t-test were applied at the 5% significance level. The paired sign test analysis, however, will not severely deviate from a formal t-test evaluation; the statistical power of the above confirmatory analysis concept will therefore certainely be at least 80%.
Data description was based on medians and quartiles for continuous endpoints and on absolute and relative frequencies for categorical endpoints. Sub-sample comparisons were based on two sample Wilcoxon tests for continuous and on exact Fisher tests for categorical variables, respectively. Results of these exploratory significance tests were summarized in p-values, where p < 0.05 indicates locally significant differences between sub-samples. All analyses were performed according to the intention-to-treat principle by a certified medical biometrician (FK) using the SPSS® software (SPSS Inc., Chicago, Illinois, USA, release 12.0 for Windows®).
The rotational mismatch in extension between femoral and tibial component was in median 0° (range: 16.2° relative external to 14.4° relative internal rotation of the femoral component). 71 TKA (89%) showed a femoro-tibial mismatch within ± 10° and 9 TKA (11%) outside of the ± 10° range.
"True" femoro-tibial rotational variance
The "true" rotational variance showed a statistically significant better femoro-tibial rotational alignment when referenced to the medial third of the tibial tubercle (p < 0.001, Fig. 3). The rotational deviation between the transepicondylar line and the medial border of the tuberosity was in median 17.4° relative external rotation of the femur (range: 32.9° relative external to 13.8° relative internal rotation of the femur). The deviation to the medial third of the tuberosity was in median 1.6° relative internal rotation of the femur (range: 15.9° relative external to 24.1° relative internal rotation of the femur).
Using the medial third of the tuberosity as a reference for tibial rotational alignment, 67.5% of all TKA had a "true" femoro-tibial variance within ± 5°, 85% within ± 10°, and 97.5% within ± 20°. Using the medial border of the tibial tubercle as a reference, the variance was greater with only 3.8% having a "true" femoro-tibial variance within ± 5°, 15% within ± 10° and 68.8% within ± 20° (Table 1).
The multivariate re-analysis of the mismatch between the femoral and tibial components as well as the "true" rotational variance did not reveal additional information as compared to the univariate analysis above. Multiple logistic regression modelling did not identify any clinical or radiographical cofactors as significantly associated with the primary endpoints. The assigned surgical treatment (navigated or conventional), the preoperative axis nor the BMI, sex or age of the patients did not have a statistically significant association with the primary endpoints.
The patella was centred with a medio-lateral displacement of < 5 mm in all patients. The lateral tilt was in median 2.5° (range: 10.6° lateral to 2.7° medial tilt). Patellar tracking was neutral in 80% and showed a lateral tilt of > 5° in 20% of all patients. In the group with a tolerable mismatch (< ± 10°), 14 patients (20%) showed a lateral tilt of > 5° and 2 patients (22%) in the group with more than 10° of rotational mismatch showed a lateral tilt of > 5°.
Rotational malalignment has been demonstrated as an important cause of failure in total knee arthroplasty. While there is consensus about the transepicondylar axis as a reference for the femoral rotational alignment [4, 9–13] there is no comparable agreement for the tibial rotational alignment.
To the author's knowledge, there has been no CT-controlled study performed to measure the variance between femoral and tibial component after TKA with correction of a femoral rotational malalignment.
Eckhoff et al.  implanted TKA in seven fresh frozen anatomic specimen knees and found as much as 19° of external rotation of the tibial component relative to the femoral component using the tibial tubercle as a reference for rotational alignment of the tibia. However, this study was performed on non-osteoarthritic knees.
Bindelglass et al.  measured intraoperatively the distance between the medial third of the tibial tubercle and the alignment of the tibial tray when seeking its own position during trial reduction. This resulted in 25 of 30 TKAs with an internally rotated tibial component relative to the tibial tubercle. It must be mentioned that a 3° of femoral external rotation relative to the posterior condylar line was used as a reference in the aforementioned study and not the transepicondylar axis. No correlation to the transepicondylar axis was performed. Therefore this relative internal rotation may be caused by a transferred femoral malrotation.
Incavo et al.  studied MRI scans of 30 normal knees. He templated an symmetric tibial baseplate using the femoral epicondylar axis as reference and measured the intersection of the midaxis line and the patellar ligament. This resulted in 22 of 30 knees with an optimal position of the tibial baseplate, defined as intersection of the midaxis line of the tibial template between the midpoint of the ligament and the midpoint of the medial third of the patellar ligament, which is consistent with our findings. However, this study was done on non-osteoarthritic knees and the patellar ligament was used as reference which may be difficult to obtain intraoperatively when everting the patella.
Akagi et al.  measured the angle between a line perpendicular to the transepicondylar axis and different landmarks on healthy subjects. They found the lowest variability in an axis from the medial border of the ligamentum patellae to the posterior cruciate ligament. However, this measurement was done on non-osteoarthritic knees and it is difficult to define the middle of the posterior cruciate ligament on CT scans after total knee arthroplasty. Furthermore the medial border of the ligamentum patellae could be difficult to identify after medial arthrotomy.
Uehara et al.  studied osteoarthritic knees with a varus malalignment before TKA. This study demonstrated a mean external rotation of 2,6° of the tibia relative to the transepicondylar axis (range: 16° external to 10° internal rotation) using a line from the medial third of the tibial tubercle to the midpoint of the longest medio-lateral distance.
Huddleston et al.  measured intraoperatively during trial reduction the deviation of the trial insert from the tibial tubercle. This angle was 5,2° external rotation (range: 10° internal to 15° external rotation) of the trial insert relative to the medial border of the tibial tubercle. For femoral rotation they used a mix of flexion-gap blancing, transepicondylar axis, Whiteside's line and posterior condylar line as reference points. No correlation to a possible femoral malrotation was done and the deviation was measured in steps of 5°.
Recently Cobb et al.  described the "anatomical tibial axis", which is the perpendicular to the mid-point of the line joining the medial and lateral condylar centres. This line was more reliable than the posterior condylar line or a line from the lateral tibial spine to the center of the tibial tubercle. However, this "anatomical axis" touches the tibial tubercle lateral of the medial border.
This investigation demonstrates that using an axis from the medial third of the tibial tubercle to the center of the tibial tray as a reference for the tibial rotational alignment leads to a better femoro-tibial alignment in extension than using the medial border of the tibial tubercle. This corresponds with the results of Huddleston  where the trial insert was rotated to a point 5° lateral to the medial border of the tibial tubercle, and results from Uehara  and Cobb's "anatomical axis"  which was lateral of the medial border of the tibial tuberosity.
While the deviation from the transepicondylar axis was low in our study group, there was a considerable range for the tibial rotational alignment as already demonstrated in previous studies [24, 25]. This may be due to difficulties to define the correct landmarks on the tibial tubercle during surgery as well as during measurement. Because rotational alignment was calculated relative to the short axis (tibial tubercle to the centre of the tibial tray), a deviation of one millimeter at the tibial tubercle resulted in a rotational deviation of about five degrees (depending on the size of the tibia). Another limitation of this study is the retrospective design because the original aim was the precision of implant position in navigated and conventional TKA. However, the statistical power appeared to be sufficient to support the results.
However, it must be realized that there is a notable rotational variance between femoral and tibial component using a fixed bone landmark as a reference (even if both components are ideally implanted). This could possibly be compensated by using a rotating tibial platform or a prosthesis with a fixed bearing design, which allows a certain amount of rotational freedom between the femoral and the tibial component. Fixed bearing ultra-congruent inlays restrict the rotation between femoral and tibial component and must be critically discussed when using a fixed landmark for tibial rotational alignment. The rotational restriction of ultra-congruent inlays may result in premature polyethylene wear. Thus using the "self-seeking method" for rotational alignment of the tibial component could help prevent femoro-tibial mismatch. However, this induces the risk of transferring a femoral malrotation to the tibia and caution must be taken with the patellar tracking.
There was no difference in patellar tracking between patients with a "tolerable" rotational mismatch (± 10°) and patients with more than 10° of mismatch between the femoral and the tibial component. This might be due to the use of the rotating platform and could be different with a fixed bearing.
Referencing the tibial rotation on a line from the medial third of the tibial tubercle to the center of the tibial tray resulted in a better femoro-tibial alignment than using the medial border of tibial tubercle as a landmark. Nonetheless, there is great variety in the rotational mismatch between the femoral and the tibial component using a fixed bone landmark (even if both components are ideally implanted). Surgeons using fixed bearing implants with a high rotational constraint between inlay and femoral component should be aware of this effect to avoid premature polyethylene wear.
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The pre-publication history for this paper can be accessed here:http://www.biomedcentral.com/1471-2474/11/57/prepub
The authors are grateful to Claudia Wojciechowski and Claudia Wolf for their valuable assistance in clinical data management and evaluation.
The authors declare that they have no competing interests, although this study was financially supported by Stryker Orthopaedics to cover the costs of the patient's insurance policies.
JL, FK, KPG and SK designed the trial together. JL wrote the manuscript with contributions from FK, KPG and SK. FK was involved as statistician. JL and SK were participating actively in the recruitment of the patients. All authors have read and approved this manuscript.