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A GLOBAL OPTIMIZATION METHOD FOR PREDICTION OF MUSCLE FORCES OF HUMAN MUSCULOSKELETAL SYSTEM + Li G; + ** Pierce JE; + Bioengineering Laboratory, Department of Orthopaedic Surgery, Massachusetts General Hospital/Harvard Medical School, Boston, MA [email protected] INTRODUCTION Quantitative data of in-vivo muscle forces, joint reaction forces and moments of human musculoskeletal joints have been pursued for decades using inverse dynamic optimization methods (1,2,3). However, the traditional formulation of the optimization method violated the joint moment equilibrium condition. The predicted muscle and joint reaction forces are coordinate system-dependent (4). This paper presented an improved optimization method, in which the instantaneous rotation center of the joint is used as an optimization variable and accurate moment equilibrium equation is formulated with respect to the joint rotation center. The new method was used to calculate muscle forces of a human elbow joint. METHODS A 3D anatomic model has been developed previously using a cadaveric human forearm specimen (female, 62 years old) (4). The model included bony geometry, insertion and origin areas of major muscles, and the action lines of the muscles (Fig. 1). The geometric center of the trochlea was chosen as the elbow joint center (1,5), and was used as the origin of the coordinate system. Six muscles were simulated: the biceps brachii (BIC), brachialis (BRA), brachioradialis (BRD), pronator teres (PRT), anconeus (ANC), and triceps brachii (TRI) (1). The model was used to simulate the equilibrium state of the elbow at 90° of flexion in the neutral forearm position under the muscle and external loads (Fig. 1). v If the actual rotation center of the joint is at the position rrot with respect to the origin of the coordinate system, then the moment equilibrium v v fiM , rrot under constraints: 6 v v v ( a) fiM ei + F Jo i n t = F i n t i= 1 6 v int v M v v f i (( ri − rr o t) × e i ) = M r o t ( b) i=1 M ( c ) 0 ≤ fi ≤ σ ⋅ Ai ∑ ∑ (2) The average mass of the lower arm is 1.36 kg. External loads include axial moments (internal-external moment) changing between ±5 Nm along the x-axis and a 50 N vertical compressive force applied at the distal end of the radius (Fig. 1). The optimization procedure predicted the muscle forces and the joint reaction forces. The results of the global optimization method were compared to those of traditional optimization method. The converged objective function values were presented as a ratio of the value predicted using traditional method. The location of the instantaneous rotation center was also presented. RESULTS The global optimization method converged to smaller objective function values (cubic muscle stress) compared to the traditional optimization method (Fig. 2a). For example, when an internal moment of 5 Nm was applied, the cubic muscle stress was only 20% of that predicted by the global optimization method. The predicted rotation center moved from medial to lateral around the geometric center of the elbow joint with the internal-external moment (Fig. 2b). As the internal moment increased (positive values), the rotation center moved almost linearly to the lateral side of the geometric center. Z Y X Medial Lateral Brachialis Brachialis Triceps Ratio of objective function value v v i= 1 is i-th muscle force and M ri on tt is the intersegamental moment calculated with respect to the actual rotation center. This treatment makes the moment equilibrium equation independent to the origin of the v coordinate sy stem. Since the joint rotation center rrot is unknown a priori, it should be calculated as an optimization variable through the optimization procedure. Therefore, a new optimization procedure can be formulated to calculate muscle forces, Minv J , (1) fi M v ∑ f iM ((ri − rr o t) × ei ) = M int r o t , where Pronator Teres Pronator Teres Brachioradialis Biceps Biceps Weight of Arm Axial Joint Reaction Force compressive Joint andReaction Moment Anconeus Anconeus load Force and Internal/external moment moment Fig. 1. An anatomic forearm model with muscle force orientations and application point. 12 1.0 a 0.8 0.6 0.4 0.2 0.0 -5 -4 -3 -2 -1 0 1 2 3 4 5 Joint rotation center location Medial Lateral 6 equation can be accurately written as The predicted muscle reaction forces were also different compared to those calculated from the traditional optimization method (Table 1). Under the ±5 Nm internal-external moment, both BIC and BRA were predicted to contract by the new optimization method while the traditional optimization method only predicted recruitment of BIC muscle under the external moment, and only BRA muscle under the internal moment. DISCUSSION In traditional optimization method, eliminating the joint reaction moment term in the moment equilibrium violates the joint equilibrium condition and is equivalent to symplify the joint as a frictionless rotational joint fixed at the origin of the coordinate system. Therefore, the optimization procedure cannot converge to the actual minimal value of the objective function. Consequently, choosing different origins will lead to different solutions of muscle forces (4). This study introduced an improved optimization method to predict the muscle and joint reaction forces, where the actual joint rotation center was treated as a variable in the optimization procedure. The moment equilibrium constraint is accurately established with respect to the actual joint rotation center. A unique minimal value for the objective function could be obtained. The predicted muscle and joint reaction forces are independent to the joint coordinate system. This method can be widely applicable to predict muscle and joint reaction forces in all other joints such as the knee, hip, and ankle joints. b 8 4 0 -4 -8 -12 -5 -4 -3 -2 -1 0 1 2 3 4 5 Internal-external moment (Nm) Internal-external moment (Nm) Fig. 2 (a) Ratio of the converged objective functions of the global to traditional optimizations; (b) Predicted rotation center location changed with external loads; Table 1. Results of of traditional and global minimizations when the forearm is under a combined load Moment (Nm) -5 Nm Optimization method TRI Muscle Forces (N) BIC BRA BRD ANC PRT Traditional 43 354 0 0 48 148 Global 84 241 246 0 0 153 Traditional 0 0 700 50 0 42 Global 0 204 313 37 30 0 5 Nm REFERENCES 1. An, J Biomech 1981. 2. Pedotti, Math Biosciences 1978. 3. Crowninshield, J Biomech 1981; 4. Pierce et al, J Biomech, 2004; 5. Morrey, J Bone Joint Surg, 1976. ** Department of Mechanical Engineering, Massachusetts Institute of Technology, Cambridge, MA 51st Annual Meeting of the Orthopaedic Research Society Poster No: 0578