Definition of Intersegmental Moment

A moment is a vector quantity that can be considered a rotational force (lever arm x force) in the sense that it tends to produce a rotation about a specific point. Whereas moments can be calculated at any point, it is useful to use the joints between adjacent limb segments to define the moments that act on the body during walking. For example, the moment acting at the knee would be the intersegmental moment between the thigh and the shank. The external moment tending to flex or extend the joint is illustrated in Figure 6-1. The intersegmental moments are typically calculated from measurement of the foot-ground reaction forces (using a force platform) and the motion of markers placed on the limbs using an optoelectronic system for motion capture. The weight and inertial forces are often approximated by modeling the leg as a collection of rigid segments representing the thigh, shank, and foot. The reader should be aware of the assumptions used in performing these calculations.⁵ Finally, the units of a moment are force and length. Therefore, it is useful when comparing different-sized subjects to express the intersegmental moments in nondimensional units by dividing the moment by the subject’s height (ht) and body weight (bw). Thus, moments measured during gait are often expressed in units of percentage of the product of the body weight and height (% bw x ht), so that moments can be compared among subjects of different heights and weights.

Figure 6-1 The intersegmental flexion-extension moment can be visualized by considering a ground reaction force vector that passes posterior to the knee will produce an external flexion moment that is balanced by a net internal quadriceps moment. When the vector passes anterior to the knee, an external extension moment is produced that must be balanced by a net internal flexor muscle moment.

Interpretation of Intersegmental Moment

The moment can be visualized in the context of the direction of the ground reaction vector relative to the position of the knee joint center (see Fig. 6-1). If the vector passes anterior to the knee, the moment will tend to extend the knee, whereas if the vector passes posterior to the knee, the moment will tend to flex the knee. As noted previously, the direction of the moment can be used to infer the net muscular moment. Thus, an external moment tending to flex the knee will be balanced by a net quadriceps moment. Previous studies have demonstrated that the external moments measured can be interpreted in terms of the loads on muscles, passive soft tissue, and joint surfaces.³² In addition, the joint moments have been shown to be sensitive indicators of differences between normal and abnormal function.^3,10,31

It is useful to examine the assumptions used as the basis for the interpretation of the joint moments during function. Mechanical equilibrium dictates that external forces and moments must be balanced by internal forces and moments. Internal forces generated by muscle, passive soft tissue, and joint contact force create these internal moments. If muscles act only synergistically when balancing the external moments, one could directly infer the internal muscle force in synergistic muscle groups. For example, the total force in the quadriceps needed to balance an external moment tending to flex the knee joint could be determined.³² However, if antagonistic muscle activity is present, the external moment reflects the net balance between agonist and antagonist muscles. The force in the synergistic muscle group would be greater under these conditions. The external moment can, however, be used to obtain a conservative estimate or lower bound on the synergist muscle force. Throughout this chapter, external moments are described from the measurements taken in the laboratory and inferences are made in terms of the net muscular moment (see Fig. 6-1).

The Flexion-Extension Moment and the ACL-Deficient Knees

The normal temporal pattern of the flexion-extension moment during stance phase of walking can be interpreted in terms of the net quadriceps moment or net knee flexor muscle moment (hamstrings and/or gastrocnemius) during stance phase (Fig. 6-2). Typically, at heel strike, there is an external moment that tends to extend the knee joint, demanding a net knee flexor force. As the knee moves into midstance, the external moment reverses its direction, demanding a net quadriceps force. As the knee passes midstance, the moment again reverses its direction, demanding net flexor muscle force. Finally, in the pre-swing phase, the moment tends to flex the knee, demanding a net quadriceps muscle force. As previously noted, a reduction of the net quadriceps moment relative to normal is frequently seen in ACL-deficient subjects during level walking (see Fig. 6-2). Specifically, ACL-deficient subjects walk in a manner that has been interpreted as a tendency to avoid or reduce the demand on the quadriceps muscle.¹⁰ Whereas the reduction in net quadriceps moment can be interpreted as either a reduction in the quadriceps or an increase in the knee flexor muscle moment, the fact that quadriceps atrophy is a common finding after ACL injury²⁰ supports the conclusion of a reduction in quadriceps contraction during walking.

Figure 6-2 The pattern of the external flexion-extension moment during normal walking for anterior cruciate ligament (ACL)–deficient (dashed line) and normal (solid line) knees. Typically, patients with ACL-deficient knees have a reduced moment, tending to flex the knee (net quadriceps moment) during midstance. The figure of the leg indicates the position of the knee joint and the net muscular activation (shaded area) required to balance the external moment shown in the graph.

The mechanics of the knee extensor mechanism suggests a possible cause for the inhibition of quadriceps contraction during walking. As illustrated in Figure 6-3, the anterior angulation of the patellar ligament insertion angle (PLIA) causes an anterior force to be applied to the tibia when the quadriceps contracts. In the absence of the ACL, the tibia moves forward when the quadriceps contracts until the force is balanced by other secondary restraints to anterior tibial displacement, such as the medial collateral ligament, meniscus, or a hamstrings contraction. Thus, more anterior tibial translation could occur in ACL-deficient knees than in uninjured knees when the quadriceps contracts. The amount of anterior force is greatest at full extension because the PLIA has the largest anterior angle at full extension and this angle reduces as the knee flexes.^17,25 Thus, walking would produce a substantial component of anterior force owing to quadriceps contraction because the knee remains near full extension throughout stance phase, with maximum flexion angles less than 30°. A reduction in quadriceps contraction could eliminate large anterior tibial translations near full extension and prevent sensations of joint instability by the patient.

Figure 6-3 The line of action of the patellar ligament running from the posterior pole of the patella to the tibial tuberosity. The patellar ligament insertion angle (PLIA) is measured as the angle between the midshaft of the tibia and the line of action of the patellar ligament. With the knee in an extended position (as shown in the illustration), contraction of the quadriceps would transmit a relatively large anterior force (F_ant) to the proximal tibia.

Interestingly, the magnitude of the net quadriceps moment can increase by more than a factor of 5 during jogging as compared with level walking (Fig. 6-4