Dynamic Analysis and Performance Verification of a Novel Hip Prosthetic Mechanism

To assist an amputee in regaining his or her daily quality of life, based on analysis of the motion characteristics of the human hip, a 2-UPR/URR parallel mechanism with a passive limb was designed. The inverse kinematics of this mechanism was analyzed based on a closed-loop vector method. The constrained Jacobian matrix and kinematic Jacobian matrix of each limb were then analyzed, and a 6 × 6 fully Jacobian matrix was constructed. Based on this, kinematic performances were analyzed and summarized. Finally, the dynamic model of the mechanism was constructed based on the virtual work principle, and its theoretical solution was compared with the numerical results, which were obtained in a simulation environment. Results showed that the prosthetic mechanism had a larger rotating workspace and better mechanical performance, which accorded a range of motion and bearing capacity similar to that of the human hip in multiple gait modes. Moreover, the validity of the dynamic model and inverse kinematics were verified by comparing the theoretical and simulation results. Furthermore, with flexion and extension, the torque change in the hip prosthetic mechanism was similar to that of the human hip, which demonstrated the feasibility of the hip prosthetic mechanism and its good dynamic performance.


Introduction
The main purpose of prosthetic mechanisms is to restore the functional motion of amputees in daily life, which can effectively compensate for the lost limbs of the amputee. With the rise in living standards, traditional prostheses that serve only as auxiliary support can no longer meet the requirements for movement of amputees. With the widespread application of robots in recent years, robotic prostheses [1,2] have been extensively studied, especially for prosthetic mechanisms. Nelson et al. [3] designed a prosthesis, named Helix 3D, for amputees with hip dissociation, which is a serial mechanism that can only realize a single degree-of-freedom (DOF). Maja et al. [4] synthesized a hip prosthesis and conducted its periodic gait experiment by using wireless sensors. Hanz et al. [5] designed a hip prosthetic mechanism that has two DOFs in the sagittal plane. The control strategy was built and implemented to test its motion performance. However, the stiffness of these prosthetic mechanisms was comparatively low owing to the open-loop structure, and the limited DOF could not meet the movement requirements of the human hip. In order to achieve the motion characteristics of the human hip and improve its stiffness, Gu [6] designed a multi-DOF humanoid robot with a serial structure similar to the lower limbs of the human body, although it is rather complicated and heavy due to its excessive components. Hence, it is essential to design a hip prosthesis with multi-DOFs, good kinematics, and dynamic performance.
To achieve multi-DOFs and increase structural stiffness, parallel mechanisms have been applied in the design of the hip prosthesis. Its performance analyses have also been carried out by the designers. Cheng et al. [7] designed a 3-SPS/PS hip parallel mechanism with its singularity analyzed using Grassmann line geometry. Due to the existence of the spherical joints, its stability would become poor when loaded. Sellaouti et al. [8] designed a bipedal walking robot with a 3-DOF parallel mechanism, which was a planar mechanism. The stability of the robot worsens during walking. Wang et al. [9] designed a 3R1T bionic parallel mechanism at the hip, and the kinematics and statics were analyzed. However, the presence of more actuators made it unfavorable for analysis of the dynamics and implementation of a control strategy for the mechanism.
In this paper, motion characteristics of the human hip were tested and analyzed via motion capture device, and a novel 2-DOF purely rotational parallel mechanism with a passive limb was synthesized by applying screw theory. The proposed mechanism acted as a hip prosthesis to fulfill the movement function of the human hip. The introduced passive limb not only enhanced the stiffness and stability of the prosthetic mechanism, but also reduced the control difficulty due to the employment of fewer motors. This paper is organized as follows: Configuration syntheses of active and passive limbs are illustrated in Section 2 based on the proposed design principles. From among the results, a parallel mechanism was selected as our hip prosthesis. In Section 3, inverse kinematics of the proposed mechanism are derived. The method of building the fully Jacobian matrix is presented in Section 4. In Section 5, its workspace, stiffness, bearing capacity, and dexterity are analyzed. The dynamic modeling process is shown in Section 6. The numerical and theoretical results are compared in Section 7. Finally, conclusions are drawn in Section 8.

Design Demand Analysis Based on Kinematics of the Human Body
Based on the human musculoskeletal anatomy and human rehabilitation kinematics [10], the motion characteristics of the human hip, which has three spatial rotational DOFs around the horizontal, sagittal, and vertical axes, were analyzed as shown in Figure 1. However, the main locomotor expression [11] of a hip in daily life is characterized by flexion, extension, abduction, and adduction, as shown in Figure 2(a) and 2(b); intorsion and extorsion can be neglected. Therefore, a hip prosthetic mechanism is designed to assist the amputee to restore the lost motion functions of flexion, extension, abduction, and adduction of the hip.
MotionAnalysis was used to test the gait data of inverse kinematics of the subjects, whose height and mass were 1.76 m and 80 kg, respectively, as shown in Figure 3. The ultimate rotational angles of the hip in multiple gait modes were tested, as shown in Table 1.
Parallel mechanisms have advantages such as multiple DOFs and high bearing capacity. The designed hip prosthetic parallel mechanism should have a rotational ability around the lateral and sagittal axes, where the minimum range of rotational angles should be, respectively, − 22° to approximately 33° and − 7° to approximately 6°. Meanwhile, it should also have sufficient stiffness and bearing capacity, which can give it good stability when supporting the human body. Although the maximum angles of intorsion and extorsion of the hip can be up to 45°, this is only in a special state. However, the motion performances of the intorsion and extorsion are not active during the normal gait, as mentioned above; thus, the motion performances of intorsion and extorsion were not considered in the design of the hip prosthetic mechanism in this paper.

Configuration Synthesis
As shown in Section 2.1, to design a hip prosthetic parallel mechanism, five design guidelines should be followed: 1) In order to simplify the mechanism and ensure its effective motion characteristics, the designed hip prosthetic parallel mechanism consists of a passive limb and two actuating limbs. 2) Since the thigh is similar to a fixed-length binary rod, the function of the passive limb is to restrict its movement along the limb, i.e., there is no prismatic pair in the passive limb. In addition, the length of the passive limb is equal to the size of the human thigh. Moreover, spherical and universal joints cannot be the middle pair of each limb. 3) Configurations of the actuating limbs are the same, and they are distributed symmetrically to the plane where the passive limb is located.

4)
To better mimic the contraction and extension of related muscles, the middle kinematic pair in each actuating limb sets as the prismatic pair. 5) To achieve the rotational angles of the hip, two revolute pairs that parallel to lateral and sagittal axes should be connected with the fixed base.
Based on this, the connectivity of the mechanism can be solved by the modified enumeration methodology: where C k is the connectivity of the kth limb, F D is the DOFs of the mechanism, d is the mechanism order, L is the number of closed-loop mechanisms, and η is the number of redundant DOFs of the mechanism. Then, in terms of Eq. (1), the classifications of connectivity of each limb are: (C 1 , C 2 , C 3 ) = (6, 3, 3) = (4, 4, 4) = (2,5,5).
It was assumed that the available types of joints were R (Revolute), P (Prismatic), U (Universal), C (Cylinder), and S (Spherical). Based on connectivity, the synthesis of the actuating and passive limbs are shown in Tables 2, 3. (1)    In Tables 2 and 3, (·) ⊥ indicates that the axes of two kinematic pairs in parentheses were orthogonal, and they were installed together on the fixed base and served as a joint. ⊥ Denotes that the axis of kinematic pair was orthogonal with the plane on which the fixed base was located. * Denotes the axis of kinematic pairs in parentheses along the limb.
According to the configurations of the limbs, a parallel mechanism was designed that met the motion characteristics of the human hip following these two steps: 1) The terminals of the passive or actuating limb had least two spatial rotational DOFs. 2) A parallel mechanism with two spatial rotational DOFs was synthesized based on the mathematical intersection operation [12].
Generally, for good stability and better motion characteristics, each limb of the parallel mechanism was consistently arranged with three joints. By analysis and comparison for the configuration of limbs under design guidelines, the configuration of UR ⊥ R was selected as the passive limb, and the configuration of UPR was selected as the actuating limb. Therefore, the hip parallel prosthetic mechanism designed in this paper was called a 2-UPR/URR parallel mechanism, as shown in Figure 4, which had the motions of flexion, extension, abduction, and adduction.
The schematic diagram is shown in Figure 5. The prosthesis can rotate around both the X-axis and the Y-axis.
Our prosthetic consisted of a fixed base, a moving platform, a passive limb, and two actuating limbs, and the driving limbs were arranged symmetrically along the X-Z plane. The universal and revolute pairs were connected to the fixed base and the moving platform, respectively, in each limb, and the axis of revolute was parallel to the outboard axis of the universal one. The upper and lower rods in the passive limb were connected by a revolute, and the axis was collinear with the direction of the passive limb. The cylinder and piston in the actuating limb were connected by a prismatic, whose moving direction was along the direction of the actuating limb, and it also served as an actuator.
In Figure 5, the fixed base ∆A 1 A 2 A 3 and the moving platform ∆B 1 B 2 B 3 are equilateral triangles and their side lengths are 2a and 2b, respectively; the origin O of the fixed frame O-XYZ is located at the center of A 2 A 3 , the direction of X and Y axis is along OA 1 and OA 2 , and the direction of Z is obtained by the right-hand rule. The origin o of the moving frame o-xyz is located at the center of B 2 B 3 , the direction of x-and y-axes are along oB 1 and oB 2 , respectively, and the direction of z is obtained by the right-hand rule.

Inverse Kinematic Analysis
For the parallel mechanism, the final location was obtained by a rotation of α about the x-axis, followed by a second rotation of β about the displaced y′-axis. The resulting rotation matrix was derived based on a Euler angle representation [13], as follows, assuming that the position vector of point o expressed in the fixed frame is p = [x p , y p , z p ]. The position vector of point A i is a 1 , a 2 , and a 3 , which can be obtained easily in Figure 5. B i with respect to the fixed frame is given by: A vector-loop equation of a Limb i can then be written as:  where s i is a unit vector pointing from A i to B i , l i is the length of the ith limb, and is a constant when i = 1. From Eqs. (3) and (4), the position vector of point o is solved:

Motion characteristics Joints Configuration of actuating limbs
Therefore, the lengths l i (i = 2, 3) of limbs 2 and 3 are solved in terms of the value of α and β as follows:

Jacobian Matrix of UPR Limb
We assumed that the actuating limb UPR was an openloop limb connecting the moving platform to the fixed base. The unit screw of the jth joint in the ith limb was expressed as $ j,i , as shown in Figure 6. In order to facilitate the analysis, the origin of the instantaneous frame was defined at point o, and its x s , y s , and z s axes were parallel to the X, Y, and Z axes, respectively. Letting be the instantaneous kinematic screw of the moving platform, which can be expressed as a linear combination of the kinematic screws in the actuating limb, we have: In Eq. (7), θ j,i is the rotational angular velocity of the jth (j = 1-4) joint in the ith (i = 2,3) limb, and q i is the linear velocity of prismatic in the ith limb.

Constraint Jacobian Matrix
There were three passive joints and an actuating joint in the actuating limb, and its joint screws were represented thusly: The actuating limb was regarded as a spherical-revolute dyad that formed a four-screw system [18], so its constraint Jacobian matrix was composed of two constraint screws, which were reciprocal with the four-screw system: Taking the dot-product of both sides of Eq. (7) with $ r1,i and $ r2,i , the constraint Jacobian matrix of the two actuating limbs were obtained: where the row vector indicates that a constraint force and a constraint couple were imposed on the moving platform by each actuating limb.

Kinematic Jacobian Matrix
The actuating limbs became a universal-revolute dyad that formed a three-screw system [18] when the prismatic joint was locked. Compared with Eq. (8), a constraint screw was added: The kinematic Jacobian matrices of the two actuating limbs were obtained by :

Jacobian Matrix of the URR Limb
The unit screw of the jth joint was expressed as $ j,1 for the passive limb URR, as shown in Figure 7.
The instantaneous kinematic characteristics of the moving platform can be expressed as a linear combination of the kinematic screws in the passive limb thusly: In Eq. (13), θ j,1 is the rotational angular velocity of the jth joint in Limb 1.
Since the passive limb had no actuator, it only contained a constraint Jacobian matrix, which acted as the constraint on the moving platform. The constraint Jacobian matrix of the passive limb could be obtained based on and : (11) In Eq. (14), the row vector indicates the constraint force on the moving platform imposed by the passive limb.

Fully Jacobian Matrix
According to the constraint Jacobian matrix and the kinematic Jacobian matrix, the fully Jacobian matrix of the 2-UPR/URR parallel mechanism could be obtained:

Workspace
In order to guarantee the rotation of the 2-UPR/URR parallel mechanism around the X-axis and Y-axis, which could meet the rotational angle of the hip in multiple gait modes, its workspace [19] was analyzed.
The geometry size of the amputee's thigh was measured: Thus, the workspace of the mechanism was solved, as shown in Figure 8. Figure 8 shows that the mechanism had a large workspace and rotational angle around the X-axis and Y-axis, which exceeded the required ultimate rotational angle in multiple gait modes. The shape and position of the workspace were in accord with the movement of the human hip. When the moving platform rotated around the X-axis, α = [− 60°, 60°], the moving range of the moving platform along the Y-axis was [− 80 mm, 80 mm], as shown in Figure 8(a). When it rotated around the Y-axis, β = [− 90°, 35°], the moving range along the X-axis was [− 40 mm, 160 mm], as shown in Figure 8(b). This also indicated that the mechanism was feasible when applied as a hip prosthetic mechanism, and confirmed the correctness of the fully Jacobian matrix.

Stiffness
In order to verify the influence of a passive limb on the stiffness of the parallel mechanism, the stiffness was analyzed in this paper for the 2-UPR parallel mechanism and the 2-UPR/URR parallel mechanism with the passive limb.
Assuming that the moving platform was subjected to an external force F e = [f e , n e ] T , and the frictional force at the joints was ignored. The stiffness and structural deformation [20] could thus be solved when loaded: In Eq. (16), F e is the external force exerted on the moving platform, Δx is the deformation displacement of the moving platform under external force, K is the stiffness matrix, and k is the equivalent spring constant assuming k = 1000 N/mm via the material properties in Ref. [21].
The complete gait cycle was composed of the single and double support stages, all of which bore the weight of the trunk. Therefore, the prosthetic mechanism required sufficient stiffness. The fully Jacobian matrices of the stiffness distribution of the 2-UPR parallel mechanism and 2-UPR/URR parallel mechanism were obtained, as shown in Figure 9.
In Figure 9, the maximum stiffness of the 2-UPR parallel mechanism was about 2853 N/mm within α = − 25° to approximately 25°, β = 0° to approximately 30°, and the maximum stiffness of the 2-UPR/URR parallel mechanism was 4435 N/mm within α = − 25° to approximately 25° and β = − 90° to approximately − 60°. These results indicated that the stiffness of the parallel mechanism had been improved by introducing a passive limb. In addition, due to the presence of the passive limb, the stiffness of the 2-UPR/URR parallel mechanism was still higher at the ultimate position during flexion, as shown in Figure 9(b).
In order to verify the theoretical solution of the stiffness of the 2-UPR/URR parallel mechanism, static analysis was carried out based on the finite element method. Clearly, the hip prosthetic mechanism exerted a maximum weight when it was a supporting leg in the single support phase. The total gravity was a concentrated force, including a load of 20 kg, which was about 1000 N. It was exerted on the center of the moving platform, in a vertically downward direction. The deformation of the mechanism could then be solved by OptiStruct, as shown in Figure 10.
In Figure 10, the maximum deformation of the 2-UPR/ URR parallel mechanism was about 0.2315 mm, and the stiffness of the mechanism was 3455.72 N/mm, which could be calculated by Eq. (16b). The simulation result of the 2-UPR/URR parallel mechanism was about 979 N/ mm less than the theoretical solution when α = β = 0°. The results indicated that the mechanism had sufficient stiffness to resist maximum external load in a single support phase without a large deformation.

Buckling Analysis
Since the axial length of the parallel prosthetic mechanism was much larger than its radial length, in order to predict the maximum loading capacity and avoid the instability and collapse caused by the external load, its buckling analysis was necessary. Generally, the buckling analysis of the mechanism is based on its eigenvalue problem: In Eq. (17), K is the structural stiffness matrix, λ σ is the scale multiplier for the external load, also called the eigenvalue, K σ is the geometric stiffness matrix based on (17) (K − σ K σ )ϕ = 0. the static analysis result, and φ is the eigenvector. The eigenvalue λ σ in Eq. (17) is solved by the Lanczos method [22]. Thus, the critical load that the mechanism can bear without instability is solved: According to Eq. (17) and the static analysis result, the critical load and large deformation trend of the mechanism were obtained in a critical unstable state, as shown in Figure 11.
Furthermore, the scaling factor of the external load was λ σ ≈ 1.72, which was calculated from the buckling analysis, and the critical load for the mechanism instability was f σ = 1376 N in terms of Eq. (18). As the weight of the amputee patient, 80 kg, was less than the (18) f σ = σ f e . critical load f σ , the amputee could also bear an additional weight of 57.6 kg without instability while the 2-UPR/URR parallel mechanism served as the hip prosthetic mechanism.

Dexterity
In this paper, in terms of the fully Jacobian matrix of the 2-UPR/URR parallel mechanism expressed in Eq. (15), its condition number [23][24][25] index was analyzed as follows: where κ(J ) is the condition number, σ max is the maximum eigenvalue of the Jacobian matrix, and σ min is the minimum eigenvalue of the inverse Jacobian matrix.
According to the geometry size in Section 5.1, the dexterity map of the 2-UPR/URR parallel mechanism is shown in Figure 12.
Compared with the motion characteristics of the hip in Table 1, the rotational angles of the 2-UPR/URR parallel mechanism around the X-axis and Y-axis were larger. The condition number of the 2-UPR/URR parallel mechanism as 0 to approximately 1 when the moving platform was within the range − 50° to approximately 50° around the X-axis and − 90° to approximately 40° around the Y-axis, which indicated the kinematic dexterity of the mechanism was good.
In addition, the condition number of the mechanism was close to 1 when the moving platform rotated to 45° around the X-axis or within the range of 0° to approximately 40° around the Y-axis, which indicated the position was isotropic and had an optimal kinematic performance in this area. Since no singularity occurred, relative analysis was not necessary. Results showed that the 2-UPR/URR parallel mechanism was feasible and in accord with the design requirements for a hip prosthetic mechanism.

Velocity and Acceleration of Actuating Limbs
To facilitate the inverse dynamic analysis [18,[26][27][28][29], a local coordinate system o i -x i y i z i was built in the vertex where s is the represented sine function, and c is the represented cosine function. The ith (i = 2, 3) driving limb of the mechanism consisted of a cylinder and a piston, as shown in Figure 13. Letting e i1 be the distance between A i and the center of mass of the ith cylinder, and letting e i2 be the distance between B i and the center of the mass of the ith piston, then the position vector of the centers of mass of the ith cylinder and piston could be represented thusly:

Velocity Analysis
Taking the time derivative of the right-hand side of Eq. (4), the velocity of the vertex B i , defined as v bi , is solved: where v p and ω p are, respectively, the linear velocity and angular velocity of the moving platform expressed in the fixed frame, which can be solved by Eqs. (3) and (4).
Based on A R i and Eq. (22), the velocity of the vertex B i is , which could be obtained thusly:

Acceleration Analysis
Based on the acceleration synthesis theorem [27], the acceleration of the vertex B i , i a bi , was found by differentiating Eq. (23) with respect to time: as each actuating limb cannot spin about its own axis. Dot-multiplying and cross-multiplying both sides of Eq. (26) by i s i , we obtained the linear and angular velocities of the ith actuating limb: The acceleration of the centers of mass of the ith cylinder and piston could be solved by differentiating Eq. (25) with respect to time and combining with Eq. (27):

Velocity Analysis
The passive limb of the 2-UPR/URR parallel mechanism consisted of an upper rod and a lower rod, as shown in Figure 14.
Letting e 11 be the distance between A 1 and the center of the mass of the lower rod, and letting e 12 be the distance between B 1 and the center of mass of the upper rod, as shown in Figure 14, the position vector of the centers of mass of the lower and upper rods could be represented as: (24)  As the passive limb cannot move along the z 1 axis, the linear and angular velocities of the vertex B 1 were obtained based on A R 1

and Eq. (22):
Therefore, the velocities of the center of the mass of the lower and upper rods are expressed as:

Acceleration Analysis
The acceleration of B 1 , expressed in its limb frame, was found by differentiating Eq. (31) with respect to time: Cross-multiplying both sides of Eq.(32) by 1 s 1 , the angular acceleration of the passive limb can be calculated: The acceleration of the center of mass of the lower and upper rods of the passive limb are then expressed as: (29) r 11 = a 1 + e 11 s 1 , r 12 = a 1 + (l 1 − e 12 )s 1 .

Jacobian Matrix of the Moving Platform
In this paper, the virtual work principle was adopted to solve the dynamic solution of the mechanism. Hence, a critical step in building the dynamic equations of the mechanism was the construction of the Jacobian matrix of the moving platform and the link Jacobian matrices. Based on Eq. (24) in matrix form, the Jacobian matrix of the moving platform could be obtained: where J p = [ 2 J b2z , 3 J b3z ] T is the Jacobian matrix of the moving platform, which is expressed as the velocity mapping relationship among all actuators and the moving platform.

Link Jacobian Matrices
Combining Eqs. (24), (25), (30) and (31), the link Jacobian matrices could be obtained: where iẋ i1 and iẋ i2 are the velocities of the center of mass of the upper rod and lower rod in the passive limb when i = 1, and denotes the velocities of the center of mass of the cylinder and piston in the ith actuating limb when i = 2, 3. ẋ p denotes the velocity of the moving platform. i J i1 and i J i2 are the link Jacobian matrices, respectively, of the cylinder and piston in the ith actuating limb.

Inertia and Applied Wrenches
The vector sum of applied and inertia wrenches is denoted as F p = [f p , n p ] T , which is exerted at the center of mass of the moving platform of the 2-UPR/URR parallel mechanism: where F e = [f e , n e ] is the resultant force vector acted on the center of mass of the moving platform. m p is the mass of the moving platform, B I p is the inertia matrix of the moving platform, A I p denotes the inertia matrix of the moving platform, and Similarly, i F i1 and i F i2 are the vector sum of applied and inertia wrenches exerted at the centers of mass of the (34) iv i1 = e 11 1ω 1 × 1 s 1 + e 11 1 ω 1 × ( 1 ω 1 × 1 s 1 ), iv i2 = (l 1 − e 12 ) 1ω 1 × 1 s 1 + (l 1 − e 12 ) 1 ω 1 × ( 1 ω 1 × 1 s 1 ).
(35) l 2 where i m i1 and i m i2 are, respectively, the mass of the lower rod and upper rod when i = 1. They are the mass of the cylinder and piston when i = 2, 3. i I i1 and i I i2 denote, respectively, the inertia matrix of the lower rod and the upper rod in the ith limb.

Dynamic Equations
From the above, the dynamic model was established based on the virtual work principle [20,30] as follows: To facilitate the calculation, substituting Eqs. (37) and (38) into Eq. (39) and simplifying yields: where τ = [0, τ 2 , τ 3 ] is the vector of actuator forces, which is specified in the actuator.

Numerical Verification
The material properties of all parts of the mechanism are shown in Table 4.
The mass of each component was m p = 1.5 kg, m 11 = 0.9 kg, m 12 = 0.75 kg, m i1 = 1.2 kg, and m i2 = 0.75 kg. In terms of Ref. [21], the inertia matrix I p and i I i (i = 1, 2, 3) could be obtained: where the unit of inertia is kg/m 2 , and the gravity is g = [0, 0, − 9807] T mm/s 2 . Moreover, the joint forces were tested using the force-measuring platform in a gait cycle, which was defined as F e . It was obtained by the equivalent method: Based on these equations, the dynamic problem of the 2-UPR/URR parallel mechanism was programmed and calculated by Mathematica, which was verified by the simulation results.

Dynamic Verification
According to the gait testing in Section 2, the motion curves of the hip in four gait modes were obtained by using MotionAnalysis, as shown in Figure 15. The hip motion trajectories were all approximate during flexion and extension, though the ultimate rotational angles were different. However, the hip motion trajectories were nearly similar during abduction and adduction.
Therefore, the dynamics of the prosthetic mechanism was mainly analyzed in two gait modes based on   Furthermore, based on the human dynamic analysis, the flexion and extension of the hip prosthetic parallel mechanism in the gait cycle, as shown in Figure 16. As can be seen in Figure 16, the human gait cycle could be divided into five phases in terms of kinesiology [11].
The motions of the hip prosthetic parallel mechanism in the five phases are summarized, as shown in Table 5.
By the curve fitting method, the motion trajectory of the moving platform could be derived in the first gait mode, as shown in Eq. (42): The ith (i = 2,3) actuating forces versus time calculated by the program showed in Figure 17(a), and the simulation results based on Adams are plotted in Figure 17 Results showed that the theoretical solution was the same, owing to the symmetrical arrangement of the actuating limbs. However, the actuating forces were highly approximated in the simulation environment, and the error may have been caused by the rigid connection of the kinematic pairs. By the curve fitting method, the motion trajectory of the moving platform could be obtained in the second gait mode, as shown in Eq.   The ith (i = 2,3) actuating forces versus time calculated by the program are shown in Figure 18a, and the simulation results based on Adams are plotted in Figure 18b.
As can be known from Figure 18, the absolute changes in the theoretical solution and the simulation results were the same in the gait cycle. Due to the symmetrical arrangement of the actuating limbs in the sagittal plane, the direction was opposite.

Inverse Kinematic Verification
In order to verify the validity of the inverse kinematics of the hip prosthetic parallel mechanism, which was derived in Section 3. For the first gait mode, the motion trajectory of the moving platform is given in Eq. (42), and the actuating displacement along the limbs could be calculated, as shown in Figure 19.
Results showed that the changes of the actuating displacement were the same during flexion and extension of the hip. There was a displacement error between the theoretical solution and the simulation results in the heel strike phase, which was about 6 mm.
For the second gait mode, the motion trajectory of the moving platform is given in Eq. (43); the actuating displacement along the limbs could thus be solved, as shown in Figure 20.
As can be known from Figure 20, the theoretical solution and the simulation results were the same in the gait cycle. An acceptable error existed between the theoretical  solution and the simulation results, which was within 3 mm. All told, the variation trend in actuating displacements between the theoretical solution and simulation results were highly consistent in the two gait modes, which verified the validity of the inverse kinematics of the hip prosthetic parallel mechanism in Section 3. Moreover, the existence of the error was caused by the deviation between the trajectory equation and the motion curve. Another factor was the inevitable error between the joint of the prosthetic mechanism and the human hip.

Analysis of the Hip Torque
As can be seen from Figure 15, flexion and extension of the hip are the main motions, which are more important than adduction and abduction.
Hence, the joint torque during flexion and extension should be considered in the design of the hip prosthetic parallel mechanism.
Based on the human dynamic simulation of an amputee, who wears the 2-UPR/URR hip parallel prosthetic mechanism, the hip torques could be obtained in the multiple gait modes, as shown in Figure 21.
As can be seen from Figure 21, the blue solid line denotes the hip torque of the adult subject at 1.5 m/s walking speed. The magenta dashed line represents the hip torque of the amputee, who wears the prosthetic mechanism, at 1.5 m/s walking speed. The green dotdash line represents the hip torque of the amputee, who wears the prosthetic mechanism in the first gait mode.
Results showed that the variation tendency of the hip torque was consistent. It verified the feasibility of the 2-UPR/URR parallel mechanism as a hip prosthesis in multiple gait modes. Additionally, the torque changes in the prosthetic mechanism were larger than those in the adult subject in the same gait mode, which may have been caused either by the existence of the geometric error between prosthetic mechanism and the human thigh or the rigid impact between the prosthetic mechanism and the ground.

Conclusions
(1) By analysis of the motion characteristics of an adult subject's hip, a novel parallel mechanism with a passive limb, named 2-UPR/URR parallel mechanism, which can realize the movement function of the hip, was designed based on configuration synthesis and screw theory. (2) The workspace was calculated based on inverse kinematics. The stiffness and dexterity were analyzed in terms of the fully Jacobian matrix. They verified the kinematic feasibility of the 2-UPR/URR parallel mechanism as the hip prosthesis. Furthermore, a statics and buckling analysis were conducted based on the finite element method; the maximum bearing capacity was obtained when the mechanism was stable. The workspace of the proposed prosthetic mechanism was large and its rotational angles covered the requirement of the hip in the four gait modes. Additionally, the prosthesis also had enough stiffness to support the torso, and the maximum bearing capacity was 1376 N, which was greater than the weight of the human body. This indicated that the prosthesis can bear an additional load of 576 N. (3) The inverse dynamic model of the prosthetic parallel mechanism was constructed by virtual work principle, and Mathematica and Adams were adopted to solve its theoretical solution and simulated results. Moreover, the torques of the prosthetic mechanism, during flexion and extension of the hip, were evaluated based on the human dynamics and compared with the simulation results. Results showed that the actuating forces and actuating displacement were highly similar between the theoretical solution and the simulation results. This verified the validity of the dynamic model and the inverse kinematics of the proposed prosthetic mechanism. Furthermore, the variation trend was consistent between the torques of the prosthetic mechanism and the human hip, which demonstrated the feasibility of the dynamic performance of the 2-UPR/URR parallel mechanism as a hip prosthetic mechanism.