- Open Access
An extended OpenSim knee model for analysis of strains of connective tissues
© The Author(s) 2018
- Received: 17 January 2018
- Accepted: 12 April 2018
- Published: 17 April 2018
OpenSim musculoskeletal models provide an accurate simulation environment that eases limitations of in vivo and in vitro studies. In this work, a biomechanical knee model was formulated with femoral articular cartilages and menisci along with 25 connective tissue bundles representing ligaments and capsules. The strain patterns of the connective tissues in the presence of femoral articular cartilage and menisci in the OpenSim knee model was probed in a first of its kind study.
The effect of knee flexion (0°–120°), knee rotation (− 40° to 30°) and knee adduction (− 15° to 15°) on the anterior cruciate, posterior cruciate, medial collateral, lateral collateral ligaments and other connective tissues were studied by passive simulation. Further, a new parameter for assessment of strain namely, the differential inter-bundle strain of the connective tissues were analyzed to provide new insights for injury kinematics.
ACL, PCL, LCL and PL was observed to follow a parabolic strain pattern during flexion while MCL represented linear strain patterns. All connective tissues showed non-symmetric parabolic strain variation during rotation. During adduction, the strain variation was linear for the knee bundles except for FL, PFL and TL.
Strains higher than 0.1 were observed in most of the bundles during lateral rotation followed by abduction, medial rotation and adduction. In the case of flexion, highest strains were observed in aACL and aPCL. A combination of strains at a flexion of 0° with medial rotation of 30° or a flexion of 80° with rotation of 30° are evaluated as rupture-prone kinematics.
- Musculoskeletal model
- Differential intra-bundle strain
The human knee is a critical load bearing joint that experiences 200–300% of the body weight during various kinetic activities such as standing up, sitting down, standing on one foot, level walking, ascending stairs, descending stairs etc., [1–3]. Multiple ligaments and tendons hold the complex knee joint together. Studies suggest that the rate of ligament injuries are considerably higher in athletes (~ 54%) compared to general day-to-day activities (~ 36%) and trauma (< 12%) [4–7]. Of the several ligaments in the knee joint, anterior cruciate ligament (ACL) encounters the highest frequency of injuries during dynamic events and therefore the study of ACL injury in sports is a well-researched topic of interest . Majority of the published studies on ACL injuries have explored the diagnosis and surgical treatment, post-surgical rehabilitation programs, procedures to facilitate speedy recovery and post-injury biomechanics [9–12]. A handful number of cadaveric studies were reported on mechanical and structural properties of knee ligaments [13, 14]. Though the information provided by these studies are quite valuable, there are limitations such as differences in sources of cadaveric tissues, preservation modes of tissues, in vitro conditions, experimental design and loading parameters etc., . However, the mechanical behaviour of ACL and other ligaments in-line with real-life kinematics and loading conditions shall help us in a better understanding of the stress–strain relationship, injury mechanisms etc.
In the past, various methods were employed to study the strain behaviour of the ligaments and tendons. The use of surface electromyogram (sEMG) during dynamic sports activities was one of the approaches. However, dynamic motion during sports offers jerk over the sensor results in spatial re-orientation of the sensor. Further, sEMG sensors create hindrance towards the natural motion of the subject during sports activities [16–19]. Studies involving in vivo testing using surgically implanted measurement devices have also been used to estimate ACL tension during human walking and other activities [13, 15, 20]. However, such an approach is invasive and introduces additional complexities. The study of strain on cadaveric ligaments and tendons is an alternate method for assessment of strain, however, factors such as availability of samples, ethical clearances etc., limit the kinematic studies [19, 21–25]. Hence, in order to understand strains of the connective tissue, there is a need for musculoskeletal models in simulation-based studies.
Among various musculoskeletal models, a finite element knee model offers accurate analyses. However, the analysis is complex and computationally time-consuming . OpenSim provides discrete element models that offer a balance of low computational time and a relatively complex anatomically correct model [10, 27]. Predicting muscle and soft tissue behaviour during gait using musculoskeletal models has been an area of research interest for the past few years [13, 27, 28]. Xu et al.  developed an OpenSim Gait model that includes four knee ligaments with 6 degrees of freedom (DOF) to the knee joint. Schmitz et al.  further developed Xu’s model to include articular cartilage, tibial plateaus and 18 bundles of connecting tissues. The authors substantiated the findings with cadaveric studies on specimens for structural properties . However, menisci were absent in both the models. Menisci is a soft tissue that plays an important role in modifying the point contact of femoral cartilage with tibia into a uniform surface contact by facilitating a larger area of contact that decreases the contact pressure . The inclusion of menisci leads to realistic strains in the connective tissues. In summary, the development of an OpenSim musculoskeletal gait model with a serial joint knee comprising all ligaments, capsules, menisci and femoral articular cartilages to an anatomically correct system is presented here. The strains in the connective tissue bundles are evaluated under three rotational kinematics of the knee.
Tibio-femoral geometry and connective tissues
Passive simulations of the knee under flexion, rotation and adduction
Maximum strain of connective tissue bundles
− 0.004 (0°)
− 0.044 (30°)
− 0.040 (− 15°)
0.228 (− 15°)
0.139 (− 40°)
0.188 (− 40°)
0.138 (− 40°)
0.184 (− 15°)
0.148 (− 40°)
0.195 (− 15°)
0.099 (− 40°)
0.141 (− 15°)
0.357 (− 40°)
0.309 (− 15°)
0.275 (− 40°)
0.240 (− 15°)
− 0.009 (0°)
0.097 (− 15°)
− 0.004 (0°)
0.136 (− 40°)
0.143 (− 40°)
0.154 (− 40°)
0.185 (− 15°)
0.092 (− 15°)
− 0.085 (120°)
0.383 (− 40°)
− 0.031 (15°)
− 0.010 (− 15°)
− 0.046 (constant)
− 0.046 (constant)
Maximum DIBS of connective tissue
0.19 (− 15°)
0.04 (0°) (aDMCL–pDMCL)
0.08 (− 40°) (aDMCL–pDMCL)
0.07 (− 15°) (aDMCL–pDMCL)
0.075 (100°) (cPT–lPT)
0.08 (cPT–lPT) constant
The importance of realistic knee model is necessary for the study of ligament kinematics and dynamics. The model can serve as an alternative to cadaveric studies due to complexities involved, for example, low availability of samples, storage requirements and extensive time for preparation etc., [34, 35]. A finite element model eludes the complexities associated with cadaveric studies however, it suffers in mimicking the complex organic geometries of the human anatomical structure. In order to understand the complex mechanism of connective tissue injury, a more pragmatic model is desired. Discrete element OpenSim models are a bridge between both the extremes and hence was chosen for the present study. The proposed model includes all 25 connecting bundles, femoral articular cartilages and menisci to facilitate a realistic model of the knee joint. The model was passively simulated in the three independent rotations to study the strains on individual connective tissues. Mechanism of sports injuries [8, 21, 22, 36] and injuries in elderly [5, 15, 28] are lucidly credible with the help of the proposed model.
Strains in the connective tissues
In the case of flexion, most bundles are not strained above 0.1 except for aACL, aPCL and lPFL. The highest number of the knee bundles for which strains exceeded 0.1 (Table 1) occurred during lateral rotation followed by abduction, medial rotation and adduction. These kinematics wherein the bundles strained over 0.1 can be quite dangerous leading to rupture of the bundle eventually. During lateral rotation, the bundles that were highly strained during are LCL, PL, MCL (all five bundles), CAPl, CAPo, CAPm and mPFL. These bundles are either placed anatomically in vertical orientation or at perfectly horizontal orientation resisting the rotation (Fig. 3b, c). Hence, high strains were observed. In addition, the strain pattern of these bundles were observed to be parabolic in nature.
In the case of adduction, the strains were found to linearly vary as a function of angle. However, high strains were observed in both abduction and adduction. It was noted that the bundles attached at the posterior part and medial part of the knee shows maximum strains at 15° of lateral rotation except for CAPl, CAPo, CAPm and lPFL. It is to note that the absolute values of a strain of the connective tissue depend upon the initial values of resting strains considered from the references. The values of the strains are bound to change depending upon the resting strains. However, the strain pattern with respect to the angle of flexion, rotation and adduction will remain unchanged at different resting strains.
Combinational strains in kinematics
For ACL (Fig. 5a–c), a flexion of 120° results in a strain of ~ 0.13 which is near to the ultimate strain for ACL (~ 0.15) . This kinematics imposes maximum strain in the aACL and therefore, any other kinematics accompanied with 120° of flexion may intigate failure in ACL. Abduction of 15° in pPCL (Fig. 5d–f), will result in a strain of ~ 0.23 which is equal to the ultimate strain for PCL (~ 0.23) . A medial rotation of tibia at 30° with 0° flexion adds up to a strain of ~ 0.24 in pPCL which exceeds the ultimate strain for PCL. This kinematics is commonly witnessed during sports injuries of football  and may instigate rupture. In case of LCL (Fig. 5g–i), complete adduction or complete lateral rotation of knee exceeds its ultimate strain (~ 0.10)  from cadaveric data and therefore is a failure prone kinematics for the ligament. These kinematics are commonly witnessed in sports such as American football and Indian kabaddi [8, 41]. At 20° lateral rotation, the strain in aDMCL and pDMCL (Fig. 6e) is greater than the ultimate strain for MCL i.e. ~ 0.13 . However, abduction of distant MCLs at their extremes may result in a failure-prone kinematics as it exceeds the ultimate strain for MCL . Sports actions involving physical tackle for instances English rugby or American football or Indian kabbadi causes similar kinematics, leading to rupture of MCL .
As described earlier, DIBS is a parameter to analyse the strain in the two bundles that are anatomically enclosed by a synovial membrane such as aACL and pACL . Table 2 illustrates DIBS for ACL, PCL, MCL and PT. DIBS is not applicable for MFL, PFL and CAP as the bundles are not anatomically enclosed within a membrane . As there is no experimentally defined upper limit of DIBS to be considered dangerous, a value of 0.1 is considered as the rupture-prone limit for the sake of discussion. In ACL, maximum DIBS of 0.09 was observed at 15° adduction which is close to the ultimate strain of ACL (~ 0.15)  and therefore, may induce high strain to the ligament. For PCL, the maximum DIBS of 0.19 was observed which is close to the ultimate strain of PCL (~ 0.23)  and therefore can induce high strain in the ligament. In MCL, the maximum DIBS was observed during rotation i.e. ~ 0.08 which close to the ultimate strain of MCL (~ 0.13) . This type of kinematics strains the ligament to its maximum and can instigate rupture on implication of external loading. During rotation and adduction, nearly constant strains with DIBS less than 0.1 was observed throughout the range of angles on the patellar tendons. DIBS is one of the parameters to evaluate the damage to the ligament while the other being the ultimate strain of the ligament.
During flexion, the strain variation of ACL, PL, MCL, CAP, MFL, and PFL was observed to follow a partial parabolic pattern i.e. decrease in strain initially followed by increase in strain at higher flexion angles. In the case of LCL, a non-linear decreasing strain pattern was observed. An inverse semi-parabolic strain pattern was observed in the case of aPCL. No significant change in strain was observed for FL, PT and TL.
During rotation, the strain variation in many of the bundles followed a non-symmetric parabolic contour except in the case of CAPa, CAPo, aMFL, pMFL, mPFL and lPFL, where the strain variation was linear. No change from resting strain was observed for FL, PT and TL. The parabolic pattern of strain characteristics was observed for the connective tissues that are anatomically placed in a vertical or near vertical direction between femur and tibia such as collateral ligaments and cruciate ligaments. Therefore, the maximum strain was observed at either of the two extremes of medial and lateral rotations or at both the extremes depending on the offset from the centre of rotation.
During adduction, the strain variation was linear for the knee bundles except for FL, PT and TL. Linear variation with positive slope indicates higher strains during adduction while negative slope indicates higher strains during the abduction. All connecting tissues show linear strain characteristics, again vowing to the vertical alignment.
The tissues were assumed to be linearly elastic in this study, which is a limitation. However, the tissues in real-life exhibit non-linear visco-elasticity.
Complete characterization of the ligament failure needs consideration of both ultimate strain and DIBS. The significance of DIBS is to indicate a potential shear between anatomically connected bundles.
The application of this model lies in the study of various mechanisms of knee injury by simulating it with various sports activities. Moreover, the customizability of the model aids in the incorporation of fixtures, dampers, prosthetics and orthotic devices etc. under simulation with the prediction of various trauma mechanisms and remedies.
MM and AS has modeled and analyzed the results. AG assisted in modeling. DJ designed the work and reviewed the manuscript and DK drafted and edited the manuscript. All authors read and approved the final manuscript.
We would like to acknowledge the funding agencies for the support of the work.
The authors declare that they have no competing interests.
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The data is available on request.
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The work was partially supported by the intramural grant of the institute wide MI01420.
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- Kutzner I, Heinlein B, Graichen F, Bender A, Rohlmann A, Halder A, Beier A, Bergmann G. Loading of the knee joint during activities of daily living measured in vivo in five subjects. J Biomech. 2010;43(11):2164–73.View ArticleGoogle Scholar
- Damm P, Kutzner I, Bergmann G, Rohlmann A, Schmidt H. Comparison of in vivo measured loads in knee, hip and spinal implants during level walking. J Biomech. 2017;51:128–32.View ArticleGoogle Scholar
- Van Rossom S, Smith CR, Thelen DG, Vanwanseele B, Van Assche D, Jonkers I. Knee joint loading in healthy adults during functional exercises: implications for rehabilitation guidelines. J Orthop Sport Phys Ther. 2018;6:1–42.Google Scholar
- Stojanovic MD, Ostojic SM. Preventing ACL injuries in team-sport athletes: a systematic review of training interventions. Res Sport Med. 2012;20(3–4):223–38.Google Scholar
- Moses B, Orchard J, Orchard J. Systematic review: annual incidence of ACL injury and surgery in various populations. Res Sport Med. 2012;20(3–4):157–79.Google Scholar
- Ardern CL, Webster KE, Taylor NF, Feller JA. Return to sport following anterior cruciate ligament reconstruction surgery: a systematic review and meta-analysis of the state of play. Br J Sports Med. 2011;45(7):596–606.View ArticleGoogle Scholar
- Krosshaug T, Steffen K, Kristianslund E, Nilstad A, Mok KM, Myklebust G, Andersen TE, Holme I, Engebretsen L, Bahr R. The vertical drop jump is a poor screening test for ACL injuries in female elite soccer and handball players. Am J Sports Med. 2016;44(4):874–83.View ArticleGoogle Scholar
- John R, Dhillon MS, Syam K, Prabhakar S, Behera P, Singh H. Epidemiological profile of sports-related knee injuries in northern India: an observational study at a tertiary care centre. J Clin Orthop Trauma. 2016;7(3):1–5.View ArticleGoogle Scholar
- Roldán E, Reeves ND, Cooper G, Andrews K. Design consideration for ACL implants based on mechanical loading. Procedia CIRP. 2016;49:133–8.View ArticleGoogle Scholar
- Schmitz A, Piovesan D. Development of an open-source, discrete element knee model. IEEE Trans Biomed Eng. 2016;63(10):2056–67.View ArticleGoogle Scholar
- Schmitz A, Piovesan D. Development of an open-source cosimulation method of the knee. In: 2016 38th Annual International Conference of the IEEE Engineering in Medicine and Biology Society (EMBC), vol. 2016–October; 2016. p. 6034–7.Google Scholar
- Malaquias TM, Silveira C, Aerts W, De Groote F, Dereymaeker G, Vander Sloten J, Jonkers I. Extended foot-ankle musculoskeletal models for application in movement analysis. Comput Methods Biomech Biomed Eng. 2017;20(2):153–9.View ArticleGoogle Scholar
- Delp SL, Anderson FC, Arnold AS, Loan P, Habib A, John CT, Guendelman E, Thelen DG. OpenSim: open source to create and analyze dynamic simulations of movement. IEEE Trans Biomed Eng. 2007;54(11):1940–50.View ArticleGoogle Scholar
- Xu H, Bloswick D, Merryweather A. An improved OpenSim gait model with multiple degrees of freedom knee joint and knee ligaments. Comput Methods Biomech Biomed Eng. 2015;18(11):1217–24.View ArticleGoogle Scholar
- Arnold EM, Ward SR, Lieber RL, Delp SL. A model of the lower limb for analysis of human movement. Ann Biomed Eng. 2010;38(2):269–79.View ArticleGoogle Scholar
- Meattini R, Palli G, Melchiorri C. Experimental evaluation of a sEMG-based control for elbow wearable assistive devices during load lifting tasks. In: 2017 International Conference on Rehabilitation Robotics (ICORR); 2017. p. 140–145.Google Scholar
- Ortiz-Catalan M, Sander N, Kristoffersen MB, Håkansson B, Brånemark R. Treatment of phantom limb pain (PLP) based on augmented reality and gaming controlled by myoelectric pattern recognition: a case study of a chronic PLP patient. Front Neurosci. 2014;8(8):1–7.Google Scholar
- Radmand A, Scheme E, Englehart K. High-density force myography: a possible alternative for upper-limb prosthetic control. J Rehabil Res Dev. 2016;53(4):443–56.View ArticleGoogle Scholar
- Pizzolato C, Reggiani M, Modenese L, Lloyd DG. Real-time inverse kinematics and inverse dynamics for lower limb applications using OpenSim. Comput Methods Biomech Biomed Eng. 2017;20(4):436–45.View ArticleGoogle Scholar
- Jackson RW, Dembia CL, Delp SL, Collins SH. Muscle-tendon mechanics explain unexpected effects of exoskeleton assistance on metabolic rate during walking. J Exp Biol. 2017;220(Pt 11):2082–95.View ArticleGoogle Scholar
- Herbort M, Domnick C, Raschke MJ, Lenschow S, Förster T, Petersen W, Zantop T. Comparison of knee kinematics after single-bundle anterior cruciate ligament reconstruction via the medial portal technique with a central femoral tunnel and an eccentric femoral tunnel and after anatomic double-bundle reconstruction. Am J Sports Med. 2016;44(1):126–32.View ArticleGoogle Scholar
- Grindem H, Granan LP, Risberg MA, Engebretsen L, Snyder-Mackler L, Eitzen I. How does a combined preoperative and postoperative rehabilitation programme influence the outcome of ACL reconstruction 2 years after surgery? A comparison between patients in the Delaware-Oslo ACL cohort and the Norwegian national knee ligament registry. Br J Sports Med. 2015;49(6):385–9.View ArticleGoogle Scholar
- Hamrin Senorski E, Sundemo D, Murawski CD, Alentorn-Geli E, Musahl V, Fu F, Desai N, Stålman A, Samuelsson K. No differences in subjective knee function between surgical techniques of anterior cruciate ligament reconstruction at 2-year follow-up: a cohort study from the Swedish national knee ligament register. Knee Surg Sport Traumatol Arthrosc. 2017;25(12):1–10.View ArticleGoogle Scholar
- Wellsandt E, Khandha A, Manal K, Axe MJ, Buchanan TS, Snyder-Mackler L. Predictors of knee joint loading after anterior cruciate ligament reconstruction. J Orthop Res. 2017;35(3):651–6.View ArticleGoogle Scholar
- Nuelle C, Milles J, Pfeiffer F, Stannard J, Smith P, Kfuri M, Cook J. Biomechanical comparison of five posterior cruciate ligament reconstruction techniques. J Knee Surg. 2017;30(6):523–31.View ArticleGoogle Scholar
- Erdemir A, Sibole S. Open knee: a three-dimensional finite element representation of the knee joint. User’s guide, version 1.0; 2010.Google Scholar
- Takayama K, Matsumoto T, Muratsu H, Ishida K, Araki D, Matsushita T, Kuroda R, Kurosaka M. The influence of posterior tibial slope changes on joint gap and range of motion in unicompartmental knee arthroplasty. Knee. 2016;23(3):517–22.View ArticleGoogle Scholar
- Morgan KD, Donnelly CJ, Reinbolt JA. Elevated gastrocnemius forces compensate for decreased hamstrings forces during the weight-acceptance phase of single-leg jump landing: implications for anterior cruciate ligament injury risk. J Biomech. 2014;47(13):3295–302.View ArticleGoogle Scholar
- Masouros SD, McDermott ID, Amis AA, Bull AMJ. Biomechanics of the meniscus-meniscal ligament construct of the knee. Knee Surg Sport Traumatol Arthrosc. 2008;16(12):1121–32.View ArticleGoogle Scholar
- Stäubli HU, Schatzmann L, Brunner P, Rincón L, Nolte LP. Mechanical tensile properties of the quadriceps tendon and patellar ligament in young adults. Am J Sports Med. 1999;27(1):27–34.View ArticleGoogle Scholar
- Lee WC, Zhang ZJ, Masci L, Ng GYF, Fu SN. Alterations in mechanical properties of the patellar tendon is associated with pain in athletes with patellar tendinopathy. Eur J Appl Physiol. 2017;117(5):1039–45.View ArticleGoogle Scholar
- Petersen W, Zantop T. Anatomy of the anterior cruciate ligament with regard to its two bundles. Clin Orthop Relat Res. 2007;454:35–47.View ArticleGoogle Scholar
- Arliani GG, Astur DC, Moraes ER, Kaleka CC, Jalikjian W, Golano P, Cohen M. Three dimensional anatomy of the anterior cruciate ligament: a new approach in anatomical orthopedic studies and a literature review. Open Access J Sport Med. 2012;3:183–8.View ArticleGoogle Scholar
- Nessler T, Denney L, Sampley J. ACL injury prevention: what does research tell us? Curr Rev Musculoskelet Med. 2017;10(3):281–8.View ArticleGoogle Scholar
- Hettler J, Myklebust G. Avoiding the failed ACL: how to prevent ACL tears before they occur. In: Marx RG, editor. Revision ACL reconstruction. New York: Springer; 2014. p. 11–22.View ArticleGoogle Scholar
- Takahashi S, Okuwaki T. Epidemiological survey of anterior cruciate ligament injury in Japanese junior high school and high school athletes: cross-sectional study. Res Sport Med. 2017;25(3):266–76.View ArticleGoogle Scholar
- Taylor KA, Terry ME, Utturkar GM, Spritzer CE, Queen RM, Irribarra LA, Garrett WE, DeFrate LE. Measurement of in vivo anterior cruciate ligament strain during dynamic jump landing. J Biomech. 2011;44(3):365–71.View ArticleGoogle Scholar
- Baker SR, Banerjee S, Bonin K, Guthold M. Determining the mechanical properties of electrospun poly-ε-caprolactone (PCL) nanofibers using AFM and a novel fiber anchoring technique. Mater Sci Eng C. 2016;59:203–12.View ArticleGoogle Scholar
- Chandrasekaran S, Ma D, Scarvell JM, Woods KR, Smith PN. A review of the anatomical, biomechanical and kinematic findings of posterior cruciate ligament injury with respect to non-operative management. Knee. 2012;19(6):738–45.View ArticleGoogle Scholar
- Wilson WT, Deakin AH, Payne AP, Picard F, Wearing SC. Comparative analysis of the structural properties of the collateral ligaments of the human knee. J Orthop Sport Phys Ther. 2012;42(4):345–51.View ArticleGoogle Scholar
- Warren RF. Editorial commentary: knee lateral collateral ligament injury is more common than we thought. Arthrosc J Arthrosc Relat Surg. 2017;33(12):2182–3.View ArticleGoogle Scholar
- Gupta R, Khanna T, Masih GD, Malhotra A, Kapoor A, Kumar P. Acute anterior cruciate ligament injuries in multisport elite players: demography, association, and pattern in different sports. J Clin Orthop Trauma. 2016;7(3):187–92.View ArticleGoogle Scholar
- Osti M, Tschann P, Künzel KH, Benedetto KP. Anatomic characteristics and radiographic references of the anterolateral and posteromedial bundles of the posterior cruciate ligament. Am J Sports Med. 2012;40(7):1558–63.View ArticleGoogle Scholar