Abstract
Purpose
Three-dimensional (3D) printed patient-specific instruments (PSI) have been introduced to increase precision and simplify surgical procedures. Initial results in femoral and tibial osteotomies are promising, but validation studies on 3D planning, manufacturing of patient-specific cutting blocks and 3D evaluation of the attained results are lacking.
Methods
In this study, patient-specific cutting blocks and spacers were designed, fabricated, and used to perform a high tibial osteotomy (HTO). After segmentation of CT data sets from 13 human tibiae, 3D digital planning of the HTO was performed with a medial opening of 8 mm. These 3D models were used to fabricate patient-specific cutting blocks and spacers. After the surgical procedure, accuracy was evaluated measuring 3D joint angles and surface deviations.
Results
The lowest mean deviation was found to be 0.57° (SD ± 0.27) for the MPTA. Medial and lateral tibial slope deviated from the 3D planning by an average of 0.98° (SD ± 0.53) and 1.26° (SD ± 0.79), respectively, while tibial torsion deviated by an average of 5.74° (SD ± 3.24). Color analysis of surface deviations showed excellent and good agreement in 7 tibiae.
Conclusion
With 3D cutting blocks and spacers, the 3D planning of the HTO can be translated into reality with small deviations of the resulting joint angles. Within this study, the results of the individual steps are examined for errors and thus a critical evaluation of this new and promising method for performing patient-specific HTOs is presented.
Similar content being viewed by others
Explore related subjects
Discover the latest articles, news and stories from top researchers in related subjects.Avoid common mistakes on your manuscript.
Introduction
Medial open-wedge high tibial osteotomy (HTO) is an effective procedure to adjust the coronal and sagittal alignment of the tibial plateau [1,2,3,4]. The need for coronal alignment correction can be indicated by isolated medial tibiofemoral compartment osteoarthritis in younger and physically active patients. The correction can delay the progression of osteoarthritic joint degeneration with a probability of survival between 85.4 and 91.6% at 10 years [1, 5, 6]. On the other hand, sagittal tibial slope correction can be used as a powerful tool in patients with cruciate ligament deficiencies or prior to the ligament reconstruction to prevent mechanical failure of the graft [7,8,9].
Conventional HTO largely remains an unguided procedure involving preoperative two-dimensional (2D) planning based on standing full-leg radiographs [10]. In clinical practice, analysis and planning of deformity correction are performed by the treating surgeon using 2D radiographs, based on commonly known definitions and criteria (e.g., Paley Book) [11]. But three-dimensional (3D) changes in the anatomy cannot sufficiently be depicted or planned with these images and occur unintentionally in many cases of HTO [12,13,14]. However, 3D imaging is possible with computer tomography (CT) and magnetic resonance imaging (MRI), and 3D HTO planning, as well as surgical implementation with 3D-printed PSIs, shows promising clinical results [15,16,17,18]. However, the 3D analysis and planning procedures are complex and constitute intellectual property of the manufacturing companies. Although the physician is involved in the planning process, potential sources of error and validation of the individual steps often remain unknown. Therefore, the group developed a standardized, validated 3D analysis and implemented reference values based on 3D analysis of a young cohort [19,20,21].
To better evaluate the implementation of 3D HTO planning, 3D printed patient-specific instruments (PSIs) and spacers were designed, manufactured and used in this study. To avoid large soft tissue detachment, the 3D printed cutting blocks were designed to be smaller than in previous published studies [15, 16].
Based on the group`s investigations, it was hypothesized that an accurate tibial realignment can be performed with the help of 3D planning. 3D planning and postoperative results were compared by different means: Medial proximal tibial angle (MPTA), medial and lateral tibial slope as well as tibial torsion.
Material and Methods
The study consisted of three steps. In the first step, 13 surface models of human tibiae created with CT scans were subjected to standardized 3D HTO planning using 3D software. Second, patient-specific sawing templates and spacers were created based on the virtual planning before the HTO (8 mm standardized gap) procedure took place. Third, the realigned tibiae were reevaluated by additional CT scan and the joint angles were compared with the original 3D plan. Furthermore, discrepancies between plans and outcomes were visualized by false color analysis.
Generation of a surface model and standardized 3D planning of the HTO
The 13 human cadaveric fresh frozen tibiae without any soft tissues were scanned using CT (slice thickness 0.625 mm; GE HD750 CT, General Electric, Boston, USA). Based on the segmented DICOM data, a surface model (STL file) was generated based on a previously published method by semi-automatic watershed segmentation of the CT data sets utilizing the ImFusion Suite [22]. The resulting surface model was then transferred to the 3D software Geomagic Design 2014. Here, the tibial plateau formed the xy-plane, while the z-axis runs vertically through the tibial knee center (Fig. 1).
As previously published, 14 defined landmarks were placed on the surface of the tibiae in order to analyze the 3D anatomy [21]. The anatomical axis was defined using the midpoints of the tibial shaft at the level of one and two thirds of the shaft length. The medial and lateral tibial slope could be identified by the two lines between the most proximal anterior and posterior points and the anatomical tibial axis [11]. The tibial torsion was defined by two lines (dorsal tangent to proximal tibia plateau and line between the deepest point of the incisura fibularis tibiae and the outermost point of medial malleolus) [23]. Numerous initial values including MPTA, medial and lateral sagittal slope, and tibial torsion were calculated using a Python script [21].
The virtual HTO was performed using biplanar cuts. The first cut in the coronal plane was made one centimeter behind the most ventral point of the tibial tuberosity, parallel to the anterior edge of the tibia. In the second step, the main osteotomy was performed from medial to lateral. The medial cut of the osteotomy was parallel to the medial slope and started distally by half of the maximum of the tibial plateau width (in average 35 mm). The target point of the osteotomy plane was 15 mm distal (z-axis) to the lateral tibial plateau. The hinge axis was defined at the lateral edge of the tibia and the cut ended 15 mm medially to the lateral cortex. The osteotomy gap was always opened by 8 mm (in the z-axis direction) at the most medial point to evaluate the printed cutting guides that should perfectly fit to the individual tibia. During 3D planning, only the MPTA was modified, while slope and torsion remained unchanged.
Generation of 3D printed cutting guides/spacers and surgical realignment
The virtually osteotomized surface models were then converted to volume models using Catia V5 (Dassault Systèmes, Vélizy-Villacoublay, France) using a previously described method [22]. Based on these virtual planning models, PSIs and spacers were designed using the CAD-program Inventor Professional 2020 (Autodesk Inc., San Rafael, CA, USA; Fig. 2a).
For each 3D model, the corresponding cutting block was specifically adapted to the curvature of the tibia. The cutting blocks were designed to be as small as possible to avoid the need for complete detachment of the medial collateral ligament (MCL) complex in real surgery. The sawing guides hence enabled the execution of the cut according to the predefined planning performed in Geomagic (see Figs. 2, 3).
During the actual sawing process, the template also prevented the saw blade from penetrating too deeply, so that the cut ended at 15 mm from the lateral tibial surface (Fig. 3). The guide itself was temporarily fixed to the tibia using four K-wires (2.5 mm).
A separate spacer/wedge was specifically designed for each bone based on the executed planning. The spacers allowed an optimal gap opening of 8 mm by inserting the wedge posteriorly to the plate. The curvature of the spacer allowed a defined positioning and easy removal after plate fixation.
The osteotomy was fixed with 3D printed reverse-engineered plates similar to TomoFix™ which, to simplify the verification of the resultant osteotomy, are used to prevent artifacts from appearing in CT scans. The plate was affixed via two proximal and distal screws. The wedge was then removed.
Using selective laser sintering (SLS) technology, the wedge, spacers, and osteotomy plates were additively manufactured using biocompatible polyamide. The medial open-wedge osteotomies were performed on a total of 13 tibial cadavers.
Control of surgical realignment
After physical osteotomy of the tibiae with the specific instrumentation, the realigned specimen was scanned by CT once more (GE HD750 CT, General Electric, Boston, USA) with a slice thickness of 0.625 mm. The segmentation procedure was repeated on the DICOM data of the osteotomized tibiae in order to create the 13 tibial surface models (ImFusion Suite, ImFusion GmbH, Munich, Germany). The angles were determined again by setting the defined landmarks on the 3D bone models as described previously. The results were then compared with the original 3D plans. The deviations between plans and results were analyzed qualitatively using a distance-based false color analysis. The 3D plan and the surgical result were aligned using the pre-alignment function of the GOM Inspect Suite 2020 (GOM GmbH, Germany) in order to allow for surface comparison between the two. Here, the realigned anatomy is matched to the planned anatomy with the help of an automatic calculation of the best-fit. Because only the identical areas of the anatomies can be used for the regression, the proximal part of the repositioned tibia was separated using Inventor Professional 2020 (Autodesk Inc., San Rafael, CA, USA). The coordinate system was adapted and transferred to the entire anatomy. The surface of both models was then compared in the GOM Inspect Suite 2020 (GOM GmbH, Germany). The software computes the perpendicular distance of each polygonal point on the realigned anatomy to the planned anatomy. The software displays the deviation as a color plot. For quantitative evaluation, deviation in the realignment of more than 1.7 mm was defined as unacceptable. The ranges are displayed using the following color scheme: Very good (green) deviation up to 0.6 mm above/below, good (yellow/light blue) deviation of 0.6–1.2 mm above/below the planned position, acceptable range (orange/blue) 1.2–1.7 mm above/below, unacceptable range (red/dark blue) deviation of at least 1.7 mm above/below the planned position.
Reliability of 3D HTO planning
In order to ensure high reliability, the same sequence of CT scan, segmentation and landmark setting according to preliminary studies was performed [21]. The 13 osteotomized tibiae models were aligned into the same predefined coordinate system and relevant angles of them were automatically calculated again via the same Python script.
Two investigators performed 3D HTO planning of the cadavers and performed the post-interventional measurement of the osteotomized tibiae using the scanned 3D models. As described, the aim of this surgical implementation was to achieve an HTO of 8 mm gap measurement and changing the MPTA while maintaining the medial and lateral slope and torsion. Accordingly, to the consistent 8 mm gap, the templates could evaluated better.
Statistics
Each examiner placed the predefined landmarks on the cadaver tibia and performed an 8 mm osteotomy. Measured angles were given in absolute values. The same procedure was followed with the scanned HTO-tibiae. In both cases, differences across all 13 tibiae were reported as mean values (with standard deviations) between investigators [24]. The averaged values of the examiners were then compared with the planned and real HTO-values. The corresponding deviations were also indicated and further processed using Excel (Microsoft, Redmond, WA, USA).
Results
Reliability of the measurements
Regarding the reliability of the measurements, previous studies of the presenting group revealed an intraclass correlation (ICC) of > 0.75; except the tibial torsion (MPTA 0.98; medial slope 0.8; lateral slope 0.9; tibial torsion 0.69) [21]. The mean differences in two-observer measurements for the models in this study (3D planning and surgical outcomes) are displayed in Table 1.
Deviation of 3D HTO planning versus surgical result
Compared to the 3D planning, the osteotomies showed an average MPTA deviation of 0.57° (SD ± 0.27). Medial and lateral slope differed by an average of 0.98° (SD ± 0.53) and 1.26° (SD ± 0.79), respectively, tibial torsion differed by an average of 5.74° (SD ± 3.24; Table 2). Overall, however, the measurements of both observers—apart from the tibial torsion—showed acceptable to good results.
False color analysis
In the false color analysis using GOM Inspect Suite 2020 (GOM GmbH, Germany), a surface comparison was performed between the 3D plan and the surgical result. Seven tibiae had only minimal surface differences compared to the preoperative 3D plan which are most likely segmentation related color deviations (Fig. 4).
Six tibias were found to be under-corrected, three of them with respect to the MPTA and in two of them at the ventral tibial part (Table 3).
Discussion
Overall, the results of the realignment surgery on cadaveric models using 3D plans and 3D printed cutting blocks are convincing. The 3D approach is superior when compared to conventional two-dimensional (2D) planning and implementation with accepted ranges of ± 3° MPTA [10]. Tibial knee joint angles (MPTA, medial and lateral slope) deviated in average by less than 1.3 degree from the preoperative planning in this study.
One of the main problems in 3D planning and implementation of osteotomies is that the ideal technique of 3D anatomy analysis, the ideal target and the accepted range of accuracy are still subject of discussion in current literature. Even in the 2D there are planning methods which use the Mikulicz line in relation to the tibial plateau or using the Hip-Knee-Angle [25,26,27,28]. However, the strong results in clinical studies showing a deviation of only 0.1° between planning and surgical outcome when using 3D PSI in high tibial osteotomy could not be replicated in this study [29]. In addition, a meta-analysis demonstrates no significant improvement in accuracy by PSI compared with the conventional technique even though outliers were reduced by the presented technique [25].
Results in tibial torsion, a relevant value representing the third dimension, are not included in most published studies investigating PSI in osteotomy [15, 16, 29, 30]. One reason for deviations of tibial torsion in this study (up to 12.67°) could be the manual selection of landmarks on the 3D bone surface model. Liodakis et al. demonstrated that torsion control in the case of fracture or osteotomy is prone to error using 2D imaging only. 3D imaging is listed here as a possible solution [31, 32]. Goleski et al. also described poor torsional reliability of navigated lower limb alignment in HTO, while Liodakis et al. compared different methods of measuring torsion on 2D CT slice images; good values were shown across all measurements [23, 33]. However, our group`s previous work on 3D analysis of lower limb alignment showed that manual landmark determination of tibial torsion led to low reliability [21]. In conclusion, a more precise 3D landmark definition seems to be necessary for tibial torsion. Ideally, this will be achieved by automatic landmark recognition, a method which was recently published by Stephen et al. [34].
False color analysis of surface deviations and angle measurements revealed unintended slope changes in some specimens. Under-correction of the anterior tibia (two cases) is a possible consequence of wedges inserted posteriorly only. Under-correction of MPTA occurred in four specimen which could be explained by post-sintering after removal of the wedge as described by Valkering et al. [35]. Fresh, frozen cadaver bone is more rigid and therefore harder to deform, so these problems are likely to be less severe in vivo. Both aspects could be addressed by bigger allograft wedges or 3D printed scaffolds in future studies.
One limitation of this study is that the osteotomy was performed on cadaveric tibiae only. This means that there was no fibula or soft tissue. Accordingly, the lateral malleolus landmark was placed in the deepest point of the Incisura fibularis tibiae and considering the multi-observer measurements, this landmark appears to have a low reliability, resulting in low accuracy in the measurement of tibial torsion.
Specimens without soft tissue were selected to facilitate the segmentation process and to reduce differences due to repeated CT scans and in the segmentation process. With a slice thickness of 0.65 mm and thresholding segmentation, the differences in the creation of the 3D model were estimated to be minimal [22, 36]. Conclusions about possible soft tissue forces are therefore not possible [37, 38]. At the same time, the absence of soft tissues enabled perfect fitting of the template to the bone.
However, in accordance with previous studies, results of angle measurements and false color analysis indicate a high accuracy for the evaluated 8 mm-osteotomies performed with 3D printed cutting blocks [15,16,17]. Jud et al. showed that a slight deviation of the template does not seem to have a relevant effect on coronal alignment in HTO [39]. Templates can be designed and used according to desired target angles [40]. Even the problem of posterolateral hinge positions in HTO increasing the tibial slope was avoided in this study by using 3D printed PSIs [41, 42].
In future studies, templates adapted to the 3D model will allow different heights of osteotomy gaps and with oblique osteotomy planes they will allow multidimensional changes. Variously shaped wedges also offer a wide range of correction possibilities for open-wedge osteotomies.
First in vivo results also showed similar advantages in accuracy with PSI for femoral osteotomies [43]. In addition to improving accuracy, 3D printed PSIs could reduce intraoperative fluoroscopy time and surgical time [44, 45].
An important point of this study is the execution of the essential steps in the planning and analysis process by orthopedic surgeons. An uninfluenced analysis of these new promising possibilities of PSI, independent of the manufacturing companies, is necessary for a critical scientific discussion.
Conclusion
With 3D printed PSIs and spacers, 3D planning of HTO can be realized with high accuracy. Only minor deviations were recorded in the surgical procedures using relatively small 3D printed PSIs. Some deviations in the 3D angle measurement are due to the manual nature of these measurements and can soon be improved by automation. False color analysis can reveal deviations from the 3D plans and helps to improve the procedure. Based on the present results, 3D cutting templates appear to be a promising tool for optimizing and simplifying HTOs, but further studies on 3D printed wedges and the required size of the cutting blocks are warranted.
References
Ozel O, Yucel B, Mutlu S, Orman O, Mutlu H. Changes in posterior tibial slope angle in patients undergoing open-wedge high tibial osteotomy for varus gonarthrosis. Knee Surg Sports Traumatol Arthrosc. 2017;25(1):314–8.
Marti CB, Gautier E, Wachtl SW, Jakob RP. Accuracy of frontal and sagittal plane correction in open-wedge high tibial osteotomy. Arthroscopy. 2004;20(4):366–72.
Keppler P, Gebhard F, Grutzner PA, Wang G, Zheng G, Hufner T, et al. Computer aided high tibial open wedge osteotomy. Injury. 2004;35 Suppl 1:S-A68-78.
Kim JH, Kim JR, Lee DH, Bang JY, Hong IT. Combined medial open-wedge high tibial osteotomy and modified Maquet procedure for medial compartmental osteoarthritis and patellofemoral arthritis of the knee. Eur J Orthop Surg Traumatol. 2013;23(6):679–83.
Niemeyer P, Stohr A, Kohne M, Hochrein A. Medial opening wedge high tibial osteotomy. Oper Orthop Traumatol. 2017;29(4):294–305.
Kim JH, Kim HJ, Lee DH. Survival of opening versus closing wedge high tibial osteotomy: a meta-analysis. Sci Rep. 2017;7(1):7296.
Giffin JR, Vogrin TM, Zantop T, Woo SL, Harner CD. Effects of increasing tibial slope on the biomechanics of the knee. Am J Sports Med. 2004;32(2):376–82.
Kim GB, Kim KI, Song SJ, Lee SH. Increased posterior tibial slope after medial open-wedge high tibial osteotomy may result in degenerative changes in anterior cruciate ligament. J Arthroplasty. 2019;34(9):1922–8.
Cantivalli A, Rosso F, Bonasia DE, Rossi R. High tibial osteotomy and anterior cruciate ligament reconstruction/revision. Clin Sports Med. 2019;38(3):417–33.
Schroter S, Gunzel J, Freude T, Ateschrang A, Stockle U, Albrecht D. Precision in the planning of open wedge HTO. Z Orthop Unfall. 2012;150(4):368–73.
Paley D. Principles of deformity correction. Springer Science & Business Media; 2002.
Jacobi M, Villa V, Reischl N, Demey G, Goy D, Neyret P, et al. Factors influencing posterior tibial slope and tibial rotation in opening wedge high tibial osteotomy. Knee Surg Sports Traumatol Arthrosc. 2015;23(9):2762–8.
Hinterwimmer S, Feucht MJ, Paul J, Kirchhoff C, Sauerschnig M, Imhoff AB, et al. Analysis of the effects of high tibial osteotomy on tibial rotation. Int Orthop. 2016;40(9):1849–54.
Jang KM, Lee JH, Park HJ, Kim JL, Han SB. Unintended rotational changes of the distal tibia after biplane medial open-wedge high tibial osteotomy. J Arthroplasty. 2016;31(1):59–63.
Munier M, Donnez M, Ollivier M, Flecher X, Chabrand P, Argenson JN, et al. Can three-dimensional patient-specific cutting guides be used to achieve optimal correction for high tibial osteotomy? Pilot study Orthop Traumatol Surg Res. 2017;103(2):245–50.
Donnez M, Ollivier M, Munier M, Berton P, Podgorski JP, Chabrand P, et al. Are three-dimensional patient-specific cutting guides for open wedge high tibial osteotomy accurate? An in vitro study. J Orthop Surg Res. 2018;13(1):171.
Victor J, Premanathan A. Virtual 3D planning and patient specific surgical guides for osteotomies around the knee: a feasibility and proof-of-concept study. Bone Jt J. 2013;95-B(11 Suppl A):153–8.
Yang JC, Chen CF, Luo CA, Chang MC, Lee OK, Huang Y, et al. Clinical experience using a 3d-printed patient-specific instrument for medial opening wedge high tibial osteotomy. Biomed Res Int 2018;2018:9246529.
Fürmetz J, Daniel T, Sass J, Bergsträßer M, Degen N, Suero E, et al. Three-dimensional assessment of patellofemoral anatomy: reliability and reference ranges. Knee. 2021;29:271–9.
Degen N, Sass J, Jalali J, Kovacs L, Euler E, Prall WC, et al. Three-dimensional assessment of lower limb alignment: reference values and sex-related differences. Knee. 2020;27(2):428–35.
Furmetz J, Sass J, Ferreira T, Jalali J, Kovacs L, Muck F, et al. Three-dimensional assessment of lower limb alignment: accuracy and reliability. Knee. 2019;26(1):185–93.
Bachmeier AT, Euler E, Bader R, Bocker W, Thaller PH. Novel method for determining bone dimensions relevant for longitudinal and transverse distraction osteogenesis and application in the human tibia and fibula. Ann Anat. 2021;234: 151656.
Liodakis E, Doxastaki I, Chu K, Krettek C, Gaulke R, Citak M, et al. Reliability of the assessment of lower limb torsion using computed tomography: analysis of five different techniques. Skeletal Radiol. 2012;41(3):305–11.
Fleiss JL. The design and analysis of clinical experiments. Wiley Classics Library; 1999. p. xiv (432 pages).
Cerciello S, Ollivier M, Corona K, Kaocoglu B, Seil R. CAS and PSI increase coronal alignment accuracy and reduce outliers when compared to traditional technique of medial open wedge high tibial osteotomy: a meta-analysis. Knee Surg Sports Traumatol Arthrosc. 2020;30:555–66.
Paley D, Tetsworth K. Mechanical axis deviation of the lower limbs. Preoperative planning of uniapical angular deformities of the tibia or femur. Clin Orthop Relat Res. 1992;280:48–64.
Miniaci A, Ballmer FT, Ballmer PM, Jakob RP. Proximal tibial osteotomy. A new fixation device. Clin Orthop Relat Res. 1989;246:250–9.
Dugdale TW, Noyes FR, Styer D. Preoperative planning for high tibial osteotomy. The effect of lateral tibiofemoral separation and tibiofemoral length. Clin Orthop Relat Res. 1992;274:248–64.
Mao Y, Xiong Y, Li Q, Chen G, Fu W, Tang X, et al. 3D-printed patient-specific instrumentation technique Vs. conventional technique in medial open wedge high tibial osteotomy: a prospective comparative study. Biomed Res Int 2020;2020:1923172.
Kim HJ, Park J, Shin JY, Park IH, Park KH, Kyung HS. More accurate correction can be obtained using a three-dimensional printed model in open-wedge high tibial osteotomy. Knee Surg Sports Traumatol Arthrosc. 2018;26(11):3452–8.
Liodakis E, Bruns N, Macke C, Krettek C, Omar M. 3D-printed template-assisted reduction of long bone fractures. Unfallchirurg. 2019;122(4):286–92.
Liodakis E, Krettek C. Torsion errors after fractures of long bones. Unfallchirurg. 2018;121(3):180–1.
Goleski P, Warkentine B, Lo D, Gyuricza C, Kendoff D, Pearle AD. Reliability of navigated lower limb alignment in high tibial osteotomies. Am J Sports Med. 2008;36(11):2179–86.
Stephen JM, Teitge RA, Williams A, Calder JDF, El Daou H. A validated, automated, 3-dimensional method to reliably measure tibial torsion. Am J Sports Med. 2021;49(3):747–56.
Valkering KP, van den Bekerom MP, Kappelhoff FM, Albers GH. Complications after tomofix medial opening wedge high tibial osteotomy. J Knee Surg. 2009;22(3):218–25.
van Eijnatten M, van Dijk R, Dobbe J, Streekstra G, Koivisto J, Wolff J. CT image segmentation methods for bone used in medical additive manufacturing. Med Eng Phys. 2018;51:6–16.
Ogawa H, Matsumoto K, Ogawa T, Takeuchi K, Akiyama H. Preoperative varus laxity correlates with overcorrection in medial opening wedge high tibial osteotomy. Arch Orthop Trauma Surg. 2016;136(10):1337–42.
Lee DH, Park SC, Park HJ, Han SB. Effect of soft tissue laxity of the knee joint on limb alignment correction in open-wedge high tibial osteotomy. Knee Surg Sports Traumatol Arthrosc. 2016;24(12):3704–12.
Jud L, Furnstahl P, Vlachopoulos L, Gotschi T, Leoty LC, Fucentese SF. Malpositioning of patient-specific instruments within the possible degrees of freedom in high-tibial osteotomy has no considerable influence on mechanical leg axis correction. Knee Surg Sports Traumatol Arthrosc. 2020;28(5):1356–64.
Kim HJ, Park J, Park KH, Park IH, Jang JA, Shin JY, et al. Evaluation of accuracy of a three-dimensional printed model in open-wedge high tibial osteotomy. J Knee Surg. 2019;32(9):841–6.
Kuriyama S, Morimoto N, Shimoto T, Takemoto M, Nakamura S, Nishitani K, et al. Clinical efficacy of preoperative 3D planning for reducing surgical errors during open-wedge high tibial osteotomy. J Orthop Res. 2019;37(4):898–907.
Kyung BS, Kim JG, Jang KM, Chang M, Moon YW, Ahn JH, et al. Are navigation systems accurate enough to predict the correction angle during high tibial osteotomy? Comparison of navigation systems with 3-dimensional computed tomography and standing radiographs. Am J Sports Med. 2013;41(10):2368–74.
Jacquet C, Chan-Yu-Kin J, Sharma A, Argenson JN, Parratte S, Ollivier M. "More accurate correction using “patient-specific” cutting guides in opening wedge distal femur varization osteotomies. Int Orthop. 2019;43(10):2285–91.
Perez-Mananes R, Burro JA, Manaute JR, Rodriguez FC, Martin JV. 3D surgical printing cutting guides for open-wedge high tibial osteotomy: do it yourself. J Knee Surg. 2016;29(8):690–5.
Jacquet C, Sharma A, Fabre M, Ehlinger M, Argenson JN, Parratte S, et al. Patient-specific high-tibial osteotomy’s “cutting-guides” decrease operating time and the number of fluoroscopic images taken after a Brief Learning Curve. Knee Surg Sports Traumatol Arthrosc. 2020;28(9):2854–62.
Funding
Open Access funding enabled and organized by Projekt DEAL. This research was funded by the German Knee Society e.V. (Deutsche Kniegesellschaft e.V. (DKG)).
Author information
Authors and Affiliations
Corresponding author
Ethics declarations
Conflict of interest
The authors have no conflicts of interest to declare. OT Medizintechnik GmbH is interested in data for possible product developments.
Ethical approval
The study was approved by the Ethics Committee of the Ludwig-Maximilians-University Munich (Nr. 18–184).
Informed consent/Author contributions
All authors contributed to the study conception and design. MJ was responsible for methodology, investigation, formal analysis, data curation, writing the original draft and visualization; AMK worked on term, conceptualization, formal analysis, review & editing. MB and AB were responsible for methodology; PA, WP, CZ, ACK and WB for review & editing and supervision. JF was responsible for term, conceptualization, methodology, formal analysis, investigation, data curation, visualization, writing the original draft, supervision and project administration. All authors read and approved the final manuscript.
Rights and permissions
Open Access This article is licensed under a Creative Commons Attribution 4.0 International License, which permits use, sharing, adaptation, distribution and reproduction in any medium or format, as long as you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons licence, and indicate if changes were made. The images or other third party material in this article are included in the article's Creative Commons licence, unless indicated otherwise in a credit line to the material. If material is not included in the article's Creative Commons licence and your intended use is not permitted by statutory regulation or exceeds the permitted use, you will need to obtain permission directly from the copyright holder. To view a copy of this licence, visit http://creativecommons.org/licenses/by/4.0/.
About this article
Cite this article
Jörgens, M., Keppler, A.M., Ahrens, P. et al. 3D osteotomies—improved accuracy with patient-specific instruments (PSI). Eur J Trauma Emerg Surg 50, 3–10 (2024). https://doi.org/10.1007/s00068-022-02060-4
Received:
Accepted:
Published:
Issue Date:
DOI: https://doi.org/10.1007/s00068-022-02060-4