Anatomie Knie… sehr anschaulich https://www.youtube.com/watch?v=_q-Jxj5sT0g

Measurement of invivo anterior cruciate ligament strain during dynamic jump landing 2011 .A. Taylor a, M.E.Terry c, G.M.Utturkar a, C.E.Spritzer b, R.M.Queen c, L.A.Irribarra Abstract Despite recent attention in the literature, anterior cruciate ligament (ACL) injury mechanisms are controversial and incidence rates remain high. One explanation is limited data on in vivo ACL strain during high-risk, dynamic movements. The objective of this study was to quantify ACL strain during jump landing. Marker-based motion analysis techniques were integrated with fluoroscopic and magnetic resonance (MR) imaging techniques to measure dynamic ACL strain non-invasively. https://ajs.sagepub.com/content/43/2/482.full

Abstract First, eight subjects’ knees were imaged using MR. From these images, the cortical bone and ACL attachment sites of the tibia and femur were outlined to create 3D models. Subjects underwent motion analysis while jump landing using reflective markers placed directly on the skin around the knee. Next, biplanar fluoroscopic images were taken with the markers in place so that the relative positions of each marker to the underlying bone could be quantified. Numerical optimization allowed jumping kinematics to be superimposed on the knee model, thus reproducing the dynamic in vivo joint motion. ACL length, knee flexion, and ground reaction force were measured. During jump landing, average ACL strain peaked 55 +/- 14 ms (mean and 95% confidence interval) prior to ground impact, when knee flexion angles were lowest.

1. Introduction Over 200,000 anterior cruciate ligament (ACL) injuries occur in the United States every year, half of which are experienced by young athletes between 15 and 25 years of age (Miyasaka et al., 1991; AAOS, 2008). The consequences of ACL deficiency incurred from ACL injury include pain, instability, damage to the menisci, and early-onset osteoarthritis (OA) (Fairclough et al., 1990; Roos et al., 1995; Fithian et al., 2002; Hill et al., 2005). For these reasons, between 100,000 and 175,000 patients elect to undergo ACL reconstruction annually (Koh, 2005; Griffin et al., 2006). Although surgical intervention provides good short-term outcomes, long-term results are less consistent (Asano et al., 2002; Wolf and Lemak, 2002; Lohmander et al., 2004; von Porat et al., 2004; Grossman et al., 2005).

1. Introduction Some studies have suggested that current reconstructive techniques do not decrease the probability of developing OA when compared to non-operative treatment (Fink et al., 2001; Lohmander et al., 2004; von Porat et al., 2004; Lohmander et al., 2007; Butler et al., 2009). Kreuzbandimplantate helfen nicht bei der Verringerung der Wahrscheinlichkeit von Osteoarthritis im Vergleich zu nicht operierten Kreuzbandbehandlungen Because ACL injury affects such a young population (Roos et al., 1995; Beynnon et al., 2005) and surgery has mixed results in preventing early-onset OA (Fithian et al., 2002; Lohmander et al., 2007), there has been great interest in developing ACL injury prevention programs (Hewett et al., 1999; Heidt et al., 2000; Myklebust et al., 2003; Gilchrist et al., 2008).

Introduction However, the levels of success achieved by current prevention programs have shown varied efficacy (Hewett et al., 1999; Soderman et al., 2000; Myklebust et al., 2003; Mandelbaum et al., 2005; Pfeiffer et al., 2006; Barber- Westin et al., 2009) and despite their implementation, high rates of non-contact ACL injuries persist (Agel et al., 2005). Trainingsprogramme sind nicht unbedingt wirksam -die hohe Anzahl an „Nicht-Kontakt“ ACL Verletzungen bleibt

These findings suggest that there is an incomplete understanding of the underlying injury mechanisms. Specifically, there are limited in vivo data on ACL strain, a critical parameter for predicting ACL failure. Numerous studies have investigated ACL injury mechanisms using videographic and motion analyses (Chappell et al., 2002; Chappell et al., 2007; Krosshaug et al., 2007a, 2007b; Boden et al., 2009; Hewett et al., 2009; Nagano et al., 2009). These studies provide important kinematic data, but do not directly measure ACL strain. Many previous studies have examined ACL loading in cadavers (Draganich and Vahey, 1990; Markolf et al., 1990; Woo et al., 1991; Li et al., 1999; Kanamori et al., 2000; DeMorat et al., 2004). Although these data give valuable information on ACL function, their application to in vivo environments are restricted by an inability to recreate complex multi-planar loading conditions experienced during dynamic jumping and cutting activities.

Using implantable strain gauges, some in vivo measurements of ACL strain have also been reported (Beynnon and Fleming, 1998; Fleming et al., 1999; Cerulli et al., 2003; Fleming and Beynnon, 2004). Beynnon and Fleming et al. (Beynnon et al., 1997; Fleming et al., 1998; Fleming et al., 1999) ran a series of in vivo strain studies to understand how an ACL graft would be loaded during common post-surgical rehabilitation exercises and daily tasks. These data were the basis for many pertinent clinical rehabilitation guidelines. However, there are limited data on ACL strains during sport-specific dynamic movements. Dynamic ACL strain data are needed to accurately predict what motions predispose the ACL to injury. The objective of this study was to measure in vivo ACL strain non-invasively during a dynamic jumping activity using a novel method developed by our laboratory.

All subjects were imaged with a 3Tmagnet (Trio Tim, Siemens Medical Solutions USA, Malvern, PA). Coronal, sagittal, and axial images were taken with the patient supine and the knee in a relaxed position. Coronal…Frontalebene (blau) Axilaebene…Transversalebene (gelb) Sagittalebene (rosa) From these images, the outer margins of the cortical bone and ACL attachment site were outlined using solid- modeling software. These tracings were compiled to create subject-specific 3D models of each tested knee. The location of the ACL was confirmed using orthogonal image sets. This methodology accurately measures the location of the ACL footprint center to within 0.3 mm, as described previously (Abebe et al., 2009). Subjects next underwent a 3D motion analysis using an eight camera motion capture system with a sampling rate of 240 Hz (Motion Analysis Corporation, Santa Rosa, CA). Also, centered within the capture volume were four embedded force plates (AMTI, Boston, MA, USA) with a sampling rate of 2400 Hz

Additionally, non- symmetric clusters of markers were also placed on the thigh and shank until a total of 28 markers were positioned on the leg (Fig. 1). The primary goal of this complex marker set was to over-constrain each anatomical segment (thigh, shank) so that the effects of skin motion could be minimized via numerical optimization, as demon- strated by previous investigators (Andriacchi et al., 1998; Alexander and Andriacchi, 2001; Ngai et al., 2009; Ngai and Wimmer, 2009). Marker data were captured initially during a static standing trial with the subject’s feet shoulder width apart for one second. Next, subjects performed five successful trials of a jump landing task. Starting from a platform 0.47 m off of the ground and half their standing height away from the force plate’s edge, subjects were asked to jump from the platform onto two force plates, then immediately jump straight up with maximal effort and land back on the same force plates again.

….subjects were imaged with the markers still in the same positions using biplanar fluoroscopy (DeFrate et al., 2004; Caputo et al., 2009) …the 3D joint model was imported into the environment and viewed from two orthogonal directions corresponding to the location of the image sources of each fluoroscope. Next, the position and orientation of the model were manipulated manually in six degrees-of-freedom (6DoF) until their projections, as viewed from the two orthogonal directions, matched the outlines on the fluoroscopic images (Fig. 2).

3. Results 3.1. Validation study Linear regression demonstrated that the two techniques had excellent correlation,with a coefficient of determination of 0.92. Root mean square error between the measurements was 0.5 mm. These results indicate that the combined methodology accurately measures ACL deformation up to 45° of flexion during a quasi-static lunge.

The study showed that the peak ACL strain occurred 55+/-14 ms prior to impact when ACL length was 12 +/- 7% longer than an MRI based reference length. In the future, this system will be used to examine kinematic parameters that elevate ACL strain. After ground contact, the ACL length initially spiked to a local maximum, but quickly decreased as the knee bent. The post impact local maximum in the ACL length demonstrated local maximum in the ACL length demonstrated 5% less relative strain than the absolute maximum prior to impact. In the current study, we detected peak ACL strains 55 ms prior strains 55 ms prior to impact, when flexion angles were their lowest. This is consistent with the finding that non-contact ACL injuries most commonly occur with the knee in less than 30° of flexion. Moreover, videographic analyses of real time sports injuries have determined that a significant number of non-contact injuries are associated with a perturbation prior to contact with the ground (Olsen et al., 2004; Krosshaug et al., 2007a, 2007b; Boden et al., 2009), a time when we observed higher ACL lengths. …15–19% ultimate strain threshold range reported by Butler et al.

One limitation of the combined method is that it was unable to be validated dynamically. A second limitation is that the presented technique was only validated to measure ACL deformations accurately up to 45° of flexion. However, because most injuries occur at flexion angles less than30° (Chaudhari …. Finally, strain was approximated by normalizing ACL length to the reference length measured in a relaxed position during MR imaging, where the fibers of the ACL appeared taut. It is difficult to know precisely the reference length of the ACL in vivo since it cannot support axial compression. These data will provide valuable information for developing prevention programs aimed at reducing the incidence of ACL injury.

Perspective article Hip extension, knee flexion paradox: A new mechanism for non-contact ACL injury Javad Hashemi a,b,n, Ryan Breighner a, Naveen Chandrashekar c, Daniel M. Hardy b,g, AjitM. Chaudhari d, Sandra J. Shultz e, James R. Slauterbeck f, Bruce D. Beynnon 2010 Abstract …To date, numerous non-contact ACL injury mechanisms have been proposed, but none provides a detailed picture of sequence of events leading to injury and the exact cause of this injury remains elusive. In this perspective article, we propose a new conception of non-contact ACL injury mechanism that comprehensively integrates risk factors inside and outside the knee joint. The proposed mechanism is robust in the sense that it is biomechanically justifiable and addresses a number of confounding issues related to ACL injury In diesem Perspektive Artikel wird ein neues Konzept des Nichtkontakts ACL Verletzungsmechanismus vorgestellt, der umfassend Risikofaktoren innerhalb und außerhalb des Kniegelenks integriert. Der vorgeschlagene Mechanismus ist in jenem Sinne robust, dass er biomechanisch zu rechtfertigen ist. Zusätzlich behandelt er einige verwirrende Fragen bezogen auf ACL Verletzungen.

In der Literatur bisher angeführte Verletzungsvorgänge ACL anterior shear force mechanisms - major contributor to the anterior shear force is the contraction of quadriceps muscles resulting in significant anterior tibial translation at low knee flexion angles axial compressive load mechanism hyperextension mechanism valgus collapse mechanism — owing either to pure abduction of the distal tibia relative to the femur or to tibiofemoral internal/external rotations internal rotation of the tibia combined valgus and anterior shear combined valgus and internal tibial torque valgus and external tibial torque valgus, anterior tibial shear, and axial torque about the long axis of the tibia

The mechanical and/or structural properties of the ACL are not considered important in these mechanisms partly because it is presumed, perhaps precipitately, that little can be done to alter ACL size and strength. In almost all of the ACL injury mechanism literature (with the exception of Ireland, 1999), sagittal plane hip kinematics are ignored as a direct contributor to ACL loading. It is also frequently assumed that excessive muscle-generated forces or torques cause ACL injury, but never the opposite. A lack of adequately protective co-contraction of both knee and hip muscles is seldom considered as a cause of ACL injury, despite being more plausible. Es wird auch häufig angenommen, dass hohe, durch Muskeln erzeugte, Kräfte oder Drehmomente ACL Verletzungen verursachen, jedoch nie das Gegenteil. Ein Mangel an ausreichendem Schutz durch Co-Kontraktion sowohl der Knie- als auch Hüftmuskulatur wird selten als Ursache der ACL-Verletzung angesehen, obwohl dies mehr plausibel wäre.

In this perspective article, we propose a new non-contact mechanism of injury that is inherently different from extant mechanisms and provides a more complete picture of the events leading to injury. We propose that ACL injury occurs because of the concurrence of specific neuromuscular events, external loads due to ground contact/impact, and certain subject-specific anatomical disadvantages. The theorized mechanism is that non-contact ACL injury occurs when the following factors converge: delayed or slow co-activation of quadriceps and hamstrings muscles, a dynamic ground reaction force applied while the knee is near full extension a shallow medial tibial plateau and a steep posterior tibial slope a stiff landing due to incompatible hip and knee flexion velocities.

2.1. Delayed or slow co-activation of quadriceps and hamstring muscles It is well known that co-contraction of the quadriceps and hamstring muscles provides active protection for the knee and its passive restraints…. We suggest that a loss of active tibiofemoral stability, resulting in increased reliance on passive structures, is a necessary (but not sufficient) condition for ACL injury. We suggest that all participants, male or female, are susceptible to this delay. Wir weisen darauf hin, dass alle Teilnehmer, männlich oder weiblich, anfällig für diese Verzögerung sind.

JCF…joint compressive force QPF…quadriceps patellar force 2.2. Application of an impulsive ground reaction force while the knee is near full extension Sagitale Ebene JCF…joint compressive force QPF…quadriceps patellar force HF…hamstring force GRF…ground reaction force (could exceed 4000N) 𝐽𝐶𝐹 = 𝐺𝑅𝐹 + 𝑄𝑃𝐹 + 𝐻𝐹 Roter Pfeil ist leicht verwirrend. Exaktere Erklärung ist auf der nächsten Seite dargestellt. Annahmen: Keine Beugung im Kniegelenk Ohne Reibung muss die JCF normal zur Kontaktfläche wirken GRF wirkt senkrecht, d.h. es wirkt keine Reibungskraft am Boden Keine Muskelkraft wirkt, da die Muskeln mit Verzögerung aktiviert werden. Ebenfalls verwirrend, dass die Muskelkräfte eingezeichnet sind.

Posterior femur translation force PFTF 2.2. Application of an impulsive ground reaction force while the knee is near full extension Posterior femur translation force PFTF (Zerlegung der GRF in PFTF und JCF) PFTF Die Reibungskraft im Kniegelenk zwischen tibia und femur wird in dieser Arbeit nicht berücksichtigt. Anterior tibial translation force bewirkt eine Bewegung der Tibia Richtung anterio, bzw. die Posterior femur translation force eine Bewegung des Femur in Richtung posterior Je größer die „posterior tibial slope“ desto größer die anterior tibial translation force Vergleiche dazu Hangabwärtstreibende Kraft beim Skifahren ATTF GRF Anterior tibial translation force (Zerlegung der GRF)

2.2. Application of an impulsive ground reaction force while the knee is near full extension In the literature, there are numerous assertions that the ACL is the primary restraint against anterior tibial translation at low flexion angles. If this is true, during landing near full extension, with a delay in co-contraction of quadriceps and hamstring muscles, there is see- mingly no protective mechanism to stop anterior tibial translation other than the ACL. However, this begs the question, ‘‘If delayed co- activation of quadriceps and hamstring muscles (for instance, due to fatigue) and a dynamic ground reaction force are all that is required for injury, why are higher ACL injury rates not observed?’’ The answer to the above question is that, according to literature, there are many other mechanisms by which the ACL is protected from injury, even if a deficiency in muscular protection occurs. Several of these protective mechanisms will be discussed in later sections.

Bei gebeugtem Kniegelenk und gleicher Überlegung ergibt sich: 2.3.1. Posterior slope of the tibial plateau and its orientation relative to the femur Bei gebeugtem Kniegelenk und gleicher Überlegung ergibt sich: The JCF, which is again perpendicular the plateau, will be directed posteriorly. This creates a posteriorly directed shear force shown by the red arrow which will resist anterior tibial translation. D.h bei gebeugtem Knie erzeugt die Bodenreaktionskraft GRF eine Kraft, welche die Tibia nach hinten drückt.

2.3.1. Posterior slope of the tibial plateau and its orientation relative to the femur Aufnahme von seitlich außen Aufnahme von seitlich innen

2.3 Posterior slope of the tibial plateau and its orientation relative to the femur Wilk et al. (1996) reported the generation of posteriorly directed shear forces in flexion angles ranging from 12° to 104° in squatting and 18° to 104° in leg press. The large joint compressive forces reported (6139 N in squats and 5762 N in leg press) must be directed posteriorly, as shown in Fig. 2b, to create an overall posteriorly directed shear force in the presence of anteriorly directed patellar tendon (quadriceps) forces. Lutz et al. (1993) report similar findings, showing posteriorly directed shear forces acting on the tibia in closed kinetic chain exercises at flexion angles of 30–90° . Scherkraft wirkt nach hinten bei diesen Beugewinkelbereichen. Biomechanically, it could be argued that this posteriorly directed component of the JCF plays an equal, if not greater ACL protective role than the posteriorly directed component of the hamstrings force. Subjects with mild tibial slope will benefit from this protection after very small amounts of knee flexion. On the contrary, subjects with steep tibial slopes will experience this added benefit only after moderate knee flexion.

2.3.2 Shallow medial tibial plateau depth It has also recently been shown that the depth of the medial tibial concavity may be a more critical risk factor in anterior. Those subjects with shallow or flat medial tibial plateaus, such as the one shown in Fig. 3a are at 3 times greater risk of injuring their ACLs for a 1 mm decrease in the depth of concavity. Deeper plateaus, such as the one in Fig. 3b, provide more stable seating of the medial femoral condyle on the tibial plateau.

2.4. A stiff landing due to incompatible hip and knee flexion velocities in the sagittal plane Fall1: Wenn Unter- wie Oberschenkel wie abgebildet (graue Pfeile) gedreht werden, bewegt sich das Knie einfach nach vorne und es kommt zu keiner Translation zwischen Tibia und Femur Fall 2: Wenn Unter- und Oberschenkel wie abgebildet (grauer und roter Pfeil) gedreht werden, kann dadurch eine rückwärts gerichtete Translation des Femurs gegenüber der Tibia erfolgen. Eine Drehung des OS gegen den Uhrzeigersinn kann durch eine zu starke Muskelaktivierung der Hüftstrecker erfolgen.

An in-vitro study of joint geometry and loading effects on anterior cruciate ligament strain and knee kinematics Breighner, Ryan 2012 http://repositories.tdl.org/tdl-ir/handle/2346/45231 To better understand the influence of tibial geometry on ACL strain and injury, several studies of various knee-loading conditions were conducted on cadaver knees. The knees were first imaged using MRI, and measurements of their respective tibial geometries were taken. Subsequently, the knees were installed in the simulator and muscle forces were applied. In one of these studies, hip extensor-generated joint compressive forces were also applied, followed by an impulsive ground reaction force. The results of these studies indicate that tibial slope and medial tibial depth are significant predictors of ACL strain and that prelanding joint compression is protective of the ACL under dynamic loading. Additionally, it was shown that MCL strain increases more appreciably as a result of valgus loading as compared to the ACL. This information, coupled with the material properties of the two ligaments suggest that isolated ACL injury cannot result from purely valgus loadings. In vitro: unter künstlichen Bedingungen im Labor beobachtet oder durchgeführt In vivo: im lebenden Objekt, am lebenden Organismus beobachtet oder durchgeführt

Clinically Relevant Injury Patterns After an Anterior Cruciate Ligament Injury Provide Insight Into Injury Mechanisms Jason W. Levine,* MD, Ata M. Kiapour,* MS, Carmen E. Quatman, Nov. 2012 Background: The functional disability and high costs of treating anterior cruciate ligament (ACL) injuries have generated a great deal of interest in understanding the mechanism of noncontact ACL injuries. Secondary bone bruises have been reported in over 80% of partial and complete ACL ruptures. Purpose: The objectives of this study were (1) to quantify ACL strain under a range of physiologically relevant loading conditions and (2) to evaluate soft tissue and bony injury patterns associated with applied loading conditions thought to be responsible for many noncontact ACL injuries. Study Design: Controlled laboratory study. Methods: Seventeen cadaveric legs (age, 45 6 7 years; 9 female and 8 male) were tested utilizing a custom-designed drop stand to simulate landing. Specimens were randomly assigned between 2 loading groups that evaluated ACL strain under either knee abduction or internal tibial rotation moments. In each group, combinations of anterior tibial shear force, and knee abduction and internal tibial rotation moments under axial impact loading were applied sequentially until failure. Specimens were tested at 25° of flexion under simulated 1200 N quadriceps and 800 N hamstring loads. A differential variable reluctance transducer was used to calculate ACL strain across the anteromedial bundle. A general linear model was used to compare peak ACL strain at failure. Correlations between simulated knee injury patterns and loading conditions were evaluated by the chi² test for independence.

Provide Insight Into Injury Mechanisms Clinically Relevant Injury Patterns After an Anterior Cruciate Ligament Injury Provide Insight Into Injury Mechanisms Jason W. Levine,* MD, Ata M. Kiapour,* MS, Carmen E. Quatman, Nov. 2012 Results: Anterior cruciate ligament failure was generated in 15 of 17 specimens (88%). A clinically relevant distribution of failure patterns was observed including medial collateral ligament tears and damage to the menisci, cartilage (Knorpel), and subchondral bone (unterhalb des Knorpels). Only abduction significantly contributed to calculated peak ACL strain at failure (P = .002). While ACL disruption patterns were independent of the loading mechanism, tibial plateau injury patterns (locations) were significantly (P = .002) dependent on the applied loading conditions. Conclusion: The current findings demonstrate the relationship between the location of the tibial plateau injury and ACL injury mechanisms. The resultant injury locations were similar to the clinically observed bone bruises across the tibial plateau during a noncontact ACL injury. These findings indicate that abduction combined with other modes of loading (multiplanar loading) may act to produce ACL injuries.

Clinically Relevant Injury Patterns After an Anterior Cruciate Ligament Injury Provide Insight Into Injury Mechanisms

Clinically Relevant Injury Patterns After an Anterior Cruciate Ligament Injury Provide Insight Into Injury Mechanisms 2012 Testing Apparatus A custom-designed testing apparatus was used to simulate landing from a jump under a wide range of loading conditions (Figure 1). Each specimen was rigidly fixed at the proximal femur to a 6-axis load cell, while the tibia was orientated vertically with the foot positioned superiorly. All specimens were tested at 25° of flexion. The load cell was suspended such that the orientation of the femur could be rotated about all 3 axes to align the tibia with the vertical loading axis. A mass pulley system was used to apply 1200 N to the quadriceps tendons and 800 N to the hamstring tendons, while maintaining the physiological line of action of each tendon. Analog data were collected at 4 kHz. Two arrays of 3 infrared light-emitting diode markers were rigidly attached to the femur and tibia to capture knee kinematics using an Optotrak 3020 (Northern Digital, Waterloo, Ontario, Canada) 3-dimensional motion capture system at 400 Hz. The ACL strain was calculated based on measurements from a differential variable reluctance transducer (DVRT) with a linear range of 3 mm that was arthroscopically placed on the anteromedial (AM) bundle of the ACL.

Combined in Vivo/in Vitro Method to Study Anteriomedial Bundle Strain in the Anterior Cruciate Ligament Using a Dynamic Knee Simulator 2013 1 Introduction About 80,000 to 250,000 ACL injuries occur in North America each year [1]. These injuries result in about 2109 dollars in treatment costs [2]. About 50% of the injured are aged 15–25….. Einleitung lesen, da sie einen sehr guten Gesamtüberblick bietet. 2 Methode Motion capture of a subject landing from a jump was performed. The resulting kinematics and GRF data were input into a biomechanical model to calculate time history of muscle forces. These muscle forces and hip/ankle joint motion profiles were then applied on an instrumented cadaver knee using the dynamic knee simulator. The resulting ACL strain was then measured in real time

The dynamic knee simulator system The dynamic knee simulator system. The cadaver knee (K) is connected to the turnbuckles that are connected to surrogate hip (HI) and ankle (A) joints. The hip joint moves in the vertical direction (dark double head arrow) and the ankle moves in the horizontal direction (white double head arrow). The ankle joint also is unconstrained in the mediolateral direction (whitedouble headed dotted arrow). Three muscle force actuators (Q,H, and G) are connected to the knee, and they apply dynamic quadriceps, hamstring, and gastrocnemius muscle forces (dark single head arrows). The hip moment actuator (HM) connected to the turnbuckle below the hip applies flexor-extensor moment. The load cells connected to the actuator rod ends are not seen in this view

Weitere ACL Kadaver Untersuchung beim Laufen Sehr professionelle Lösung zur Erfassung der ACL-Kräfte bei einem Kniekadaver http://www.youtube.com/watch?v=athYrUMk2Ik&list=PLu0YtbFBcm4bmpV0gKp4E-IQyKI-Mhjsx&index=1 The knee joint is a complex structure. There are six degrees of freedom (DoF) between the tibia and the femur controlled by many muscles, tendons, and ligaments. Normal knee flexion involves translation of the tibia along the femur as well as rotation, making knee simulations computationally difficult. Analyzing the biomechanical effects of individual components in the knee can provide relevant information for developing new surgical treatments or prosthetic devices. The CORE lab uses a six DoF robot to move cadaveric knees through ranges of motion with forces up to 2,250 N and 1,000 N-m from 0 to 120 degrees of flexion. Measurement of the joint coordinate system (JCS) during passive knee flexion (i.e. with zero forces) allows us to measure the motion of the tibia relative to the femur pre- and post-surgical treatments. Muscle actuators can simulate up to 1,000 N of static loading to determine the biomechanical contribution of each muscle individually. Instrumentation of the knee with a Tekscan pressure sensor allows us to measure patellofemoral or tibiofemoral contact forces in vivo. A microstrain differential variable reluctance transducer (DVRT) can measure ligament or tendon strain with +/- 1 µm accuracy. The Orthopaedics & Sports Medicine arthroscopy room is available for performing surgical treatments on cadaveric specimens which allows us to measure the effectiveness of various types of procedures or prosthetic devices. The ability to measure the biomechanical properties of the various components within the knee in vivo while undergoing clinically relevant forces and ranges of motion can lead to new developments in several aspects of medicine. We are currently focusing on the role of the ACL in stabilization of the knee and exploring conditions under which the ACL is at risk for rupture Weitere ACL Kadaver Untersuchung beim Laufen http://p3.smpp.northwestern.edu/Project/ACL.htm Anatomievideo Knie  http://www.youtube.com/watch?v=_q-Jxj5sT0g https://ajs.sagepub.com/content/43/2/482.full Review über Präventionsprogramme https://books.google.at/books?hl=de&lr=&id=yEcwCgAAQBAJ&oi=fnd&pg=PA96&dq=acl+injuries&ots=XGzpfFVEkZ&sig=2F4GAfWdNhgisgB8wO8cNEGTZZA#v=onepage&q=acl%20injuries&f=false recht gute Zusammenfassungen über Matching Technik