MOTION ASSISTING DEVICE

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to a motion assisting device for assisting a walking motion of a creature by applying to the creature an assisting force which assists a leg in moving with respect to a body.

2. Description of the Related Art

According to a first prior art (refer to Japanese Patent Laid-open No. 2004-073649), a periodical walking motion of a creature, such as a human whose body such as a lower limb or the like is suffering from hypofunction, is assisted by applying a periodically varying force to the creature. According to a second prior art (refer to Japanese Patent Laid-open No. 2007-061217), a periodical motion of a human can be assisted by adjusting a force applied to the human according to a second model (spring model) representing a behavior feature of a virtual elastic element so as to match a motion scale of the human to a desired motion scale thereof. According to the first and the second prior arts, the periodical motion of a creature can be assisted so as to match a motion rhythm of the creature to a desired motion rhythm thereof. Particularly, according to the second prior art adopting the spring model, the periodical motion of the creature can be assisted so as to match the motion scale of the creature to the desired motion scale thereof.

However, the first prior art and the second prior art can be further modified from the viewpoint of conducting a smooth motion of a plurality of legs of the creature.

SUMMARY OF THE INVENTION

The present invention has been accomplished in view of the aforementioned problems, and it is therefore an object of the present invention to provide a motion assisting device capable of assisting a periodical walking motion of a creature so as to conduct a smooth motion of a plurality of legs thereof.

A first aspect of the present invention provides a motion assisting device which assists a walking motion of a creature by applying to the creature an assisting force which assists a leg in moving with respect to a body comprises: a controlling device configured to control the assisting force according to an auxiliary coefficient, wherein the controlling device includes a first processing element configured to determine whether the leg is at an on-ground state or at an off-ground state, and a posture of the leg with respect to the body; and a second processing element configured to adjust the auxiliary coefficient so as to make the auxiliary coefficient in a reinforcement duration containing a part or a total of a second duration in which the leg is performing a stretch motion at an on-ground state as a second reinforcement duration greater than the auxiliary coefficient in a duration other than the reinforcement duration, on the basis of a determination result by the first processing element.

According to the motion assisting device of the first aspect of the present invention, the assisting force applied to the creature is reinforced only by an increment in the auxiliary coefficient increased in the reinforcement duration containing the second reinforcement duration. Note that it is not limited that the reinforced assisting force is stronger than the assisting force in the duration other than the reinforcement duration. The second reinforcement duration is referred to as a part or a total of the second duration in which the leg is performing a stretch motion (backward motion) at the on-ground state. Accordingly, the stretch motion of the leg at the on-ground state is assisted by a relatively stronger assisting force, and resultantly, the leg is subjected to a relatively stronger floor reaction force. The floor reaction force is transmitted to the body through the leg at the on-ground state to conduct the body to translate forward. When the leg is stretched by the assisting force at the on-ground state, there occurs a reflex (stretch reflex) to the stretch motion of the leg. As a result, the flexion motion (forward motion) of the leg at a subsequent off-ground state is induced by the stretch reflex at the previous on-ground state. According thereto, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state.

A second aspect of the motion assisting device of the present invention is dependent on the first aspect of the present invention, wherein the second processing element is configured to adjust the auxiliary coefficient so as to make the auxiliary coefficient in the reinforcement duration further containing a part or a total of a first duration in which the leg is moved from the flexion motion at the off-ground state to the stretch motion to step on the ground as a first reinforcement duration greater than the auxiliary coefficient in the duration other than the reinforcement duration.

According to the motion assisting device of the second aspect of the present invention, the assisting force applied to the creature is controlled to be stronger in the reinforcement duration containing the first reinforcement duration and the second reinforcement duration than that in the duration other than the reinforcement duration. The first reinforcement duration is referred to as a part or a total of the first duration in which the leg is moved from the flexion motion at the off-ground state to the stretch motion to step on the ground. Accordingly, the stretch motion of the leg immediately before the leg steps on the ground is assisted by a relatively stronger assisting force. When the leg is landed on the ground, it is subjected to a relatively stronger floor reaction force. As above mentioned, the floor reaction force is transmitted to the body through the leg at the on-ground state to conduct the body to translate forward and the leg to perform the flexion motion at the off-ground state. According thereto, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state.

A third aspect of the motion assisting device of the present invention is dependent on the first aspect of the present invention, wherein the controlling device includes a motion oscillator determination element configured to determine a second motion oscillator which periodically varies according to the walking motion of the creature; and a second oscillator generation element configured to generate a second oscillator as an output oscillation signal from a second model by inputting the second motion oscillator determined by the motion oscillator determination element to the second model as an input oscillation signal, in which the second model is configured to generate an output oscillation signal which periodically varies at an angular velocity defined according to a second intrinsic angular velocity on the basis of an input oscillation signal; and the controlling device controls the assisting force so that the assisting force periodically varies according to an amplitude determined according to the auxiliary coefficient and an angular velocity of the second oscillator generated by the second oscillator generation element.

According to the motion assisting device of the third aspect of the present invention, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state. Furthermore, the periodical operation of the motion assisting device can be controlled so as to maintain stable an amplitude relationship and a phase relationship between the periodical walking motion of the creature and the periodical operation of the motion assisting device.

A fourth aspect of the motion assisting device of the present invention is dependent on the third aspect of the present invention, wherein the controlling device includes a motion variable determination element configured to determine a motion variable representing a scale of the walking motion performed by the creature; the second model is defined by a simultaneous differential equation having a plurality of state variables representing a behavior state of the creature; and the second oscillator generation element corrects the second model by correcting a constant or a coefficient contained in the simultaneous differential equation so as to approximate a determination value of the motion variable obtained from the motion variable determination element to a desired value and generates the second oscillator on the basis of the state variables obtained by solving the simultaneous differential equation.

According to the motion assisting device of the fourth aspect of the present invention, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state. Furthermore, the periodical walking motion can be assisted so as to approximate the motion variable representing the scale of the walking motion performed by the creature to a desired value.

A fifth aspect of the motion assisting device of the present invention is dependent on the third aspect of the present invention and further includes an adjusting device, wherein the second model is defined by a simultaneous differential equation having a plurality of state variables representing a behavior state of the creature; the adjusting device is capable of manually adjusting a constant or a coefficient in the simultaneous differential equation; and the second oscillator generation element generates the second oscillator on the basis of the state variables obtained by solving the simultaneous differential equation.

According to the motion assisting device of the fifth aspect of the present invention, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state. Furthermore, the operation mode of the motion assisting device can be manually adjusted through the adjusting device so as to maintain stable an amplitude relationship and a phase relationship between the periodical walking motion of the creature and the periodical operation of the motion assisting device.

A sixth aspect of the motion assisting device of the present invention is dependent on the fourth aspect of the present invention, wherein the constant or the coefficient in the simultaneous differential equation adjusted by the second processing element serves as the auxiliary coefficient.

According to the motion assisting device of the sixth aspect of the present invention, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state. Furthermore, by adjusting the auxiliary coefficient for defining the assisting force applied to the creature, the motion variable representing the scale of the periodical walking motion of the creature can be made to approximate to the desired value, or the operation mode of the motion assisting device can be manually adjusted through the adjusting device to maintain stable an amplitude relationship and a phase relationship between the periodical walking motion of the creature and the periodical operation of the motion assisting device.

A seventh aspect of the motion assisting device of the present invention is dependent on the third aspect of the present invention, wherein the controlling device includes a motion variable determination element configured to determine a motion variable representing a scale of the walking motion performed by the creature; and the controlling device controls the assisting force so that the assisting force periodically varies according to an amplitude determined according to an elastic coefficient of a virtual elastic element serving as the auxiliary coefficient and an angular velocity of the second oscillator generated by the second oscillator generation element, both of which are used to approximate a determination value of the motion variable obtained from the motion variable determination element to a desired value.

According to the motion assisting device of the seventh aspect of the present invention, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state. Furthermore, the periodical walking motion can be assisted so as to approximate the motion variable representing the scale of the walking motion performed by the creature to the desired value.

An eighth aspect of the motion assisting device of the present invention is dependent on the third aspect of the present invention, wherein the motion oscillator determination element determines a first motion oscillator which periodically varies according to the walking motion of the creature; the controlling device includes a first oscillator generation element and an intrinsic angular velocity setting element, in which the first motion oscillator generation element is configured to generate a first oscillator as an output oscillation signal from a first model by inputting the first motion oscillator determined by the motion oscillator determination element to the first model as an input oscillation signal, in which the first model is configured to generate an output oscillation signal which varies at an angular velocity defined according to a first intrinsic angular velocity by entraining to an input oscillation signal; and the intrinsic angular velocity setting element is configured to set an angular velocity of a second virtual oscillator as the second intrinsic angular velocity according to a virtual model on the basis of a first phase difference between the first motion oscillator determined by the motion oscillator determination element and the first oscillator generated by the first oscillator generation element so as to approximate a second phase difference to a desired phase difference, in which the virtual model is expressed by a first virtual oscillator and the second virtual oscillator which vary periodically with the second phase difference while interacting mutually.

According to the motion assisting device of the eighth aspect of the present invention, the periodical walking motion of the creature can be assisted to conduct not only a stretch motion (backward motion) of the leg of the creature at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state. Furthermore, the periodical operation of the motion assisting device can be controlled so as to approximate the phase relationship between the periodical walking motion of the creature and the periodical operation of the motion assisting device to the desired phase relationship expressed by the desired phase difference.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an explanatory diagram schematically illustrating a motion assisting device according to a first embodiment of the present invention;

FIG. 2 is an explanatory diagram schematically illustrating a controlling device of the motion assisting device according to the first embodiment;

FIG. 3 is a flow chart illustrating a motion assist method according to the first embodiment;

FIG. 4 is an explanatory diagram illustrating an operation of the motion assisting device;

FIG. 5 is an explanatory diagram illustrating a walking motion of a human;

FIG. 6 is an explanatory diagram schematically illustrating a motion assisting device according to a second embodiment of the present invention;

FIG. 7 is an explanatory diagram schematically illustrating a controlling device of the motion assisting device according to the second embodiment;

FIG. 8 is a flow chart illustrating a motion assist method according to the second embodiment;

FIG. 9 is an explanatory diagram illustrating a walk training method (part 1);

FIG. 10 is an explanatory diagram illustrating a walk training method (part 2).

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

An embodiment of a motion assisting device according to the present invention will be described with reference to the drawings. Hereinafter, symbols “L” and “R” are used to differentiate a left leg and a right leg or the like. However, the symbols may be omitted if there is not necessary to differentiate a left part and a right part or a vector having both of left and right components is mentioned. Moreover, symbols “+” and “−” are used to differentiate a flexion motion (forward motion) and a stretch motion (backward motion) of the leg (in particular, a thigh).

First, descriptions will be performed on a first embodiment of the present invention. FIG. 1 illustrates a motion assisting device 10 which assists a human P in walking motion according to the first embodiment of the present invention. The motion assisting device 10 includes a first orthosis 1100 attached to a waist (a first body part) of the human P, a second orthosis 1200 attached to a thigh (a second body part) of the human P, a hip joint angle sensor 11, an actuator 15, a controlling device 100, and a battery 1000.

The first orthosis 1100 includes a first supporter 1110 and a first link member 1120. The first supporter 1110 is made from a combination of a rigid material such as a rigid resin and a flexible material such as a fiber and is mounted on the waist backward. The first link member 1120 is made of a rigid resin, and is fixed at the first supporter 1110 in such a way that when the first supporter 1110 is attached to the waist, the first link member 1120 is located at both sides of the waist laterally. The second orthosis 1200 includes a second supporter 1210 and a second link member 1220. Similar to the first supporter 1110, the second supporter 1210 is also made from a combination of a rigid material and a flexible material and is mounted on a front side and a back side of the thigh, respectively. The second link member 1220 is made of a rigid resin, extending vertically along outside of the thigh and formed as being forked into two downwardly and is connected to an output shaft of the actuator 15 and the second supporter 1210. Note that it is acceptable to mount a third orthosis to the human P. The third orthosis is comprised of a third supporter and a third link member. The third supporter is formed to have a shape of a slipper or a shoe which is mounted to a foot of the human P. The third link member is configured to extend vertically along the crus so as to connect the third supporter and a lower end portion of the second link member 1220 in a movable manner.

The hip joint angle sensor 11 is comprised of a rotary encoder disposed on a transverse side of the waist of the human P and outputs a signal according to the hip joint angle. The actuator 15 is comprised of a motor, including either one or both of a reduction gear and a compliance mechanism where appropriate. The battery 1000 is housed in the first orthosis 1100 (for example, fixed in multiple sheets of cloth constituting the first supporter 1110), which supplies electrical power to the actuator 15, the controlling device 100 and the like. Note that it is acceptable to attach or house the controlling device 100 and the battery 1000 in the second orthosis 1200; it is also acceptable to dispose them separately from the motion assisting device 10.

The controlling device 100 includes a computer housed in the first orthosis 1100 and a software stored in a memory or a storing device in the computer. The controlling device 100 controls an operation or an output torque T of the actuator 15 by adjusting the electrical power supplied from the battery 1000 to the actuator 15. The magnitude of an output from the actuator 15 is controlled according to the value of an auxiliary coefficient which will be described hereinafter. The controlling device 100 illustrated in FIG. 2 is provided with a first processing element 101, a second processing element 102, a motion variable determination element 108, a motion oscillator determination element 110, a first oscillator generation element 120, an intrinsic angular velocity setting element 130, a second oscillator generation element 140, and an auxiliary oscillator generation element 150. Each element may be constituted from a mutually different CPU, or a universal CPU or the like.

The first processing element 101 determines whether each leg of the human P is on the ground or has been raised from the ground and a posture of each with respect to the body. The second processing element 102 adjusts the auxiliary coefficient so as to make the auxiliary coefficient in a reinforcement duration greater than the auxiliary coefficient in a duration other than the reinforcement duration on the basis of the determination result by the first processing element 101.

The motion variable determination element 108 determines the value of a motion variable 4 which represents a scale of a periodical motion of the human P. The motion oscillator determination element 110 determines an angular velocity of each hip joint as a first motion oscillator φ₁and an angle thereof as a second motion oscillator φ₂on the basis of an output from the hip joint angle sensor 11. Each of the first motion oscillator φ₁and the second motion oscillator φ₂varies periodically according to the periodical motion of the human P, and a variation pattern thereof is defined by an amplitude and a phase (or an angular velocity which is a first order differentiation of the phase by time). Determination of an oscillator means to determine a periodical variation pattern of the oscillator. The first oscillator generation element 120 generates a first oscillator ζ₁as an output oscillation signal from a first model by inputting the first motion oscillator φ₁determined by the motion oscillator determination element 110 as an input oscillation signal to the first model. Generation of an oscillator means to define a periodical variation pattern for the oscillator. The “first model” is a model configured to generate an output oscillation signal which varies at an angular velocity defined according to a first intrinsic angular velocity ω₁by entraining to an input oscillation signal.

The intrinsic angular velocity setting element 130 includes a first phase difference setting element 131, a second phase difference setting element 132, a correlation coefficient setting element 133, a first angular velocity setting element 134, and a second angular velocity setting element 135. The intrinsic angular velocity setting element 130 sets a second intrinsic angular velocity ω₂so as to approximate a second phase difference δθ₂to a desired phase difference δθ₀according to a virtual model on the basis of a first phase difference δθ₁. The first phase difference δθ₁is a phase difference between the first motion oscillator φ₁determined by the motion oscillator determination element 110 and the first oscillator ζ₁generated by the first oscillator generation element 120. The virtual model represents a periodical motion of the human P with a periodical variation of a first virtual oscillator φ₁, a periodical operation of the motion assisting device 10 with a periodical variation of a second virtual oscillator φ₂, and a phase difference between the periodical motion of the human P and the periodical operation of the motion assisting device 10 with a phase difference between the first virtual oscillator φ₁and the second virtual oscillator φ₂, namely, the second phase difference δθ₂, respectively.

The second oscillator generation element 140 generates a second oscillator ζ₂as an output oscillation signal from a second model by inputting the second motion oscillator φ₂determined by the motion oscillator determination element 110 as an input oscillation signal to the second model. The “second model” is a model which generates an output oscillation signal varying at an angular velocity defined according to the second intrinsic angular velocity ω₂defined by the intrinsic angular velocity setting element 130 on the basis of an input oscillation signal.

The auxiliary oscillator generation element 150, on the basis of the second oscillator ζ₂generated by the second oscillator generation element 140, generates an auxiliary oscillator η. The auxiliary oscillator η is used to define a variation pattern of the torque applied to the thigh by the actuator 15 in the motion assisting device 10.

Hereinafter, the operation of the motion assisting device 10 having the configuration mentioned in the first embodiment of the present invention will be described. The motion variable determination element 108, on the basis of the output signal from the hip joint angle sensor 11, determines the left hip joint angle and the right hip joint angle at the respective finished timing of the flexion motion and the finished timing of the stretch motion of the thigh for each walking cycle (FIG. 3/S002) (in detail, the left hip joint angle at the finished timing of the flexion motion, the left hip joint angle at the finished timing of the stretch motion, the right hip joint angle at the finished timing of the flexion motion and the right hip joint angle at the finished timing of the stretch motion of the thigh) as the motion variable ζ={ζ_i|i=L+, L−, R+, R−}. Note that it is acceptable to determine a footstep of the human P as the motion variable ζ. The footstep, for example, may be determined on the basis of a correlation among the hip joint angle of the human P which is determined according to the output signal from the hip joint angle sensor 11, the hip joint angle of the human P stored in memory and the foot position in the anteroposterior direction. Herein, it is possible to determine a step rate (numbers of steps every unit time) and a walking velocity of the human P, and thereafter determine the footstep on the basis of the step rate and the walking velocity. The step rate may be determined on the basis of an output signal from an acceleration sensor attached to the human P, which outputs the output signal according to an acceleration of the human P in the vertical direction. The walking velocity may be determined on the basis of an output signal from a velocity sensor disposed in a treadmill 30, which outputs the output signal according to the speed of an endless belt 32. Moreover, it is also acceptable to determine the value of a function, namely the motion variable A, having multiple variables containing at least one of the walking rate (=footstep/step rate), the footstep, the left hip joint angle at the finished timing of the flexion motion and the left hip joint angle at the finished timing of the stretch motion, the right hip joint angle at the finished timing of the flexion motion and the right hip joint angle at the finished timing of the stretch motion of the thigh for each walking cycle.

Further, the motion oscillator determination element 110 determines the angular velocity of each of the left and right hip joints of the human P as the first motion oscillator φ₁=(φ+_1L, φ_1R) on the basis of the output from the hip joint angle sensor 11 (FIG. 3/S011). Furthermore, the motion oscillator determination element 110 determines the left hip joint angle and the right joint angle of the human P as the second motion oscillator φ₂=(φ_2L, φ_2R) on the basis of the output from the hip joint angle sensor 11 (FIG. 3/S012).

Note that it is acceptable to determine an arbitrary variable varying periodically according to the periodical motion of the human P by using an appropriate sensor as the first motion oscillator φ₁and the second motion oscillator φ₂, respectively. For example, an angle or angular velocity of an arbitrary joint, such as the hip joint, knee joint, ankle joint, shoulder joint, elbow joint and the like, and a position of the thigh, foot, upper arm and waist (the position or the like in the anteroposterior direction or the vertical direction with the center-of-gravity of the human P as a reference), and a variation pattern of velocity or acceleration may be determined as the motion oscillator. The variation patterns of various parameters varying at a rhythm in conjunction with the walking motion rhythm, such as a sound generated when the left or right leg steps on the ground, a breathing sound, a deliberate phonation or the like, may be determined as one or both of the first motion oscillator φ₁and the second motion oscillator φ₂. Moreover, it is acceptable to determine variables representing the periodical motion state of the same body part, such as the angle and the angular velocity or the like of the same joint, as the first motion oscillator φ₁and the second motion oscillator φ₂, respectively; it is also acceptable to determine variables representing the periodical motion state of different body parts, such as the respective angles and the angular velocities or the like of different joints, as the first motion oscillator φ₁and the second motion oscillator φ₂, respectively.

Thereafter, the first oscillator generation element 120 generates the first oscillator ζ₁as an output oscillation signal from the first model by inputting the first motion oscillator φ₁determined by the motion oscillator determination element 110 as an input oscillation signal to the first model (FIG. 3/S011). The first model represents the correlation between a plurality of first elements, such as the left and right feet or the like, and generates the output oscillation signal which varies at the angular velocity defined according to the first intrinsic angular velocity ω₁=(ω_1L, ω_1R) by entraining to the input oscillation signal as described above. The first model, for example, may be defined by the Van der Pol equation expressed by the equation (10). Moreover, it is possible that the first oscillator generation element 120 sequentially updates the first model by adopting an updated second intrinsic angular velocity ω₂set by the intrinsic angular velocity setting element 130 as an updated first intrinsic angular velocity ω₁, and generates a subsequent first oscillator ζ₁as the output oscillation signal by inputting a subsequent first motion oscillator φ₁as the input oscillation signal into the updated first model.

(d²φ_1L/dt²)=A(1−ζ_1L²)(dζ_1L/dt)−ω_1L²ζ_1L+g(ζ_1L−ζ_1R)+K₁φ_1L,

(d²φ_1R/dt²)=A(1−ζ_1R²)(dζ_1R/dt)−ω_1R²ζ_1R+g(ζ_1R−ζ_1L)+K₁φ_1R (10)

Wherein:

A: a positive coefficient set in such a way that a stable limit cycle may be drawn from the first oscillator ζ₁and the first order temporal differential (dζ₁/dt) thereof in a plane of “ζ₁−(ζ₁/dt)”;

g: a first correlation coefficient for reflecting the correlation of different body parts, such as the left and right feet of the human P or the like, with the correlation of each of the left and right components of the first oscillator ζ₁(correlation of the output oscillation signals among the plurality of first elements); and

K₁: a feedback coefficient with respect to the first motion oscillator φ₁.

The first oscillator ζ₁=(ζ_1L, ζ_1R) is calculated or generated according to the Runge-Kutta method. The angular velocity of each of the components ζ_1Land ζ_1Rof the first oscillator ζ₁represents a virtual rhythm which assists the motion of the left leg and the right leg, respectively. Further, the first oscillator ζ₁has a feature to vary or oscillate periodically with an autonomous angular velocity or rhythm defined on the basis of the first intrinsic angular velocity ω₁while harmonizing with the rhythm of the first motion oscillator φ₁varying at an angular velocity or rhythm substantially the same as a rhythm of the actual walking motion, according to the “mutual entrainment” (harmonization effect) which is one of the properties of the Van del Pol equation.

In addition, the first model may be expressed by the Van der Pol equation having a different expression from that of the equation (10), or by a certain equation which generates the output oscillation signal varying periodically at the angular velocity defined on the basis of the first intrinsic angular velocity ω₁, accompanied by the mutual entrainment to the input oscillation signal. Moreover, it is acceptable to increase the numbers of the first motion oscillator φ₁, namely the determination object. The more numbers of the first motion oscillators φ₁are input to the first model, the motion will be more elaborately assisted by considering the motions of various body parts of the human P through the adjustment of the correlation coefficients, although the correlation members in a non-linear differential equation corresponding to the first oscillator ζ₁generated by the Van der Pol equation for defining the first model will become more accordingly.

The phase difference between the periodical motion of the human P and the periodical operation of the motion assisting device 10 defines the motion behavior of the human P with respect to the operation of the motion assisting device 10. For example, when the phase difference is positive, the human P can move in a way of leading the motion assisting device 10. On the other hand, when the phase difference is negative, the human P can move in a way of being led by the motion assisting device 10. Therefore, when the phase difference (the first phase difference) δθ₁of the first oscillator ζ₁with respect to the first motion oscillator φ₁deviates from the desired phase difference δθ₀, it is very possible for the motion behavior of the human P to become unstable. Consequently, there is a high probability that the motion rhythm of the human P whose relative motions between the waist and the thigh assisted by the torque T varying periodically at an angular velocity corresponding to the auxiliary oscillator r would deviate from the desired motion rhythm.

Therefore, from the viewpoint of matching the motion rhythm of the human P with the desired motion rhythm while maintaining the mutual harmony between the first motion oscillator φ₁and the first oscillator ζ₁, an appropriate second intrinsic angular velocity ω₂for defining the second oscillator ω₂is set by the intrinsic angular velocity setting element 130. In other words, an appropriate second intrinsic angular velocity ω₂is set from the viewpoint of realizing an appropriate phase difference between an assisting rhythm of the motion assisting device 10 and the motion rhythm of the human P so that the motion rhythm of the human P is in accordance with the desired motion rhythm while harmonizing the assisting rhythm of the motion assisting device 10 with the motion rhythm of the human P.

Specifically, the first phase difference setting element 131 sets a phase difference between the first motion oscillator φ₁and the first oscillator ζ₁as the first phase difference δθ₁(FIG. 3/S031). The first phase difference δθ₁is calculated or set on the basis of a difference of time between, for example, a timing where φ₁=0 and (dφ₁/dt)>0 and a timing where ζ₁=0 and (dζ₁/dt)>0.

Thereafter, the second phase difference setting element 132 sets the second phase difference δθ₂on a condition that the first phase difference δθ₁over the recent three walking cycles is constant or the variation of the first phase difference δθ₁is within an allowable range (FIG. 3/S032). In detail, a phase difference between the first virtual oscillator φ₁(φ_1L, φ_1R) and the second virtual oscillator φ₂(φ_2L, φ_2R) which are defined in the virtual model, which is expressed by the equations (21) and (22), is set as the second phase difference δθ₂according to the equation (23). The first virtual oscillator φ₁in the virtual model virtually represents the first motion oscillator φ₁; the second virtual oscillator φ₂in the virtual model represents the auxiliary oscillator η virtually.

dφ
_1L
/dt=ω
_1L+ε_Lsin(φ_2L−φ_1L), dφ_1R/dt=ω_1R+ε_Rsin(φ_2R−φ_1R) (21)

dφ
_2L
/dt=ω
_2L+ε_Lsin(φ_1L−φ_2L, dφ_2R/dt=ω_2R+ε_Rsin(φ_1R−φ_2R) (22)

δθ_2L=arcsin{(ω_1/L−ω_2/L)/2ε_L}, δθ_2R=arcsin{(ω_1/R−ω_2/R)/2ε_R} (23)

Wherein, each component of “ε=(ε_L, ε_R)” stands for a correlation coefficient representing the correlation between each component of the first virtual oscillator φ₁and each component of the second virtual oscillator φ₂. “ω₁/=(ω_1/L, ω_1/R)” is the angular velocity for each component of the first virtual oscillator φ₁, and “ω₂/=(ω_2/L, ω_2/R)” is the angular velocity for each component of the second virtual oscillator φ₂.

Subsequently, the correlation coefficient setting element 133 sets the correlation coefficient ε so that the deviation between the first phase difference δθ₁set by the first phase difference setting element 131 and the second phase difference 602 set by the second phase difference setting element 132 is minimum (FIG. 3/S033).

Specifically, the correlation coefficient ε(t_i) at each timing t_kwhere the first motion oscillator φ₁for each of the left and right components becomes zero is sequentially set according to the equation (24).

ε_L(t_k+1)=ε_L(t_k)−B_L{V₁L(t_k+1)−V₁L(t_k)}/{ε_L(t_k)−ε_L(t_k−1)}

ε_R(t_k+1)=ε_R(t_k)−B_R{V₁R(t_k+1)−V₁R(t_k)}/{ε_R(t_k)−ε_R(t_k−1},

V
₁
L(t_k+1)≡(1/2){δθ₁L(t_k+1)−δθ₂L(t_k)}²,

V
₁
R(t_k+1)≡(1/2){δθ₁R(t_k+1)−δθ₂R(t_k)}² (24)

Wherein, each component of “B=(B_L, B_R)” is a coefficient representing the stability of the potential V₁=(V_1L, V_1R) for approximating each component of the first phase difference δθ₁to each of the left and right components of the second phase difference δθ₂.

Next, the first angular velocity setting element 134 sets the angular velocity of the first virtual oscillator φ₁as the first angular velocity ω₁/according to the equation (25) on the basis of the correlation coefficient ε set by the correlation coefficient setting element 133 so that the deviation between the first phase difference δθ1 and the second phase difference δθ₂for each component is minimum under the condition that the angular velocity ω₂/of the second virtual oscillator φ₂is constant (FIG. 3/S034).

ω_1/L(t_k)=−α_L∫dtq₁L(t), ω_1/R(t_k)=−α_R∫dtq₁R(t)

q
₁
L(t)=(4ε_L²(t_k)−(ω₁L(t)−ω₂L(t_k)))^1/2×sin(arcsin[(ω_1/L(t)−ω_2/L(t_k−1))/2ε_L(t_k)]−δθ₂L(t_k)),

q
₁
R(t)=(4ε_L²(t_k)−(ω_1/R(t)−ω_2/R(t_k)))^1/2×sin(arcsin[(ω_1/R(t)−ω_2/R(t_k−1))/2ε_R(t_k)]−δθ₂R(t_k)) (25)

Wherein, each component of “α=(α_L, α_R)” is a coefficient representing the stability of the system.

The virtual model is constructed on a condition that the mutual harmony between the first motion oscillator φ₁and the first oscillator ζ₁is also maintained between the first virtual oscillator φ₁and the second virtual oscillator φ₂by setting the correlation coefficient ε and the angular velocity φ₁/. In other words, the virtual model is constructed so that the first virtual oscillator φ₁representing the periodical motion of the human P and the second virtual oscillator φ₂representing the periodical operation of the motion assisting device 10 vary periodically at the second phase difference δθ₂with a mutual harmonization.

Thereafter, the second angular velocity setting element 135 set the angular velocity of the second virtual oscillator φ₂as the second angular velocity ω₂/for each component on the basis of the first angular velocity ω₁/set by the first angular velocity setting element 134 (FIG. 3/S035). The second angular velocity ω₂/=(ω_2/L, ω_2/R) is set according to the equation (26) so that the second phase difference δθ₂for each of the left and right components approximates to the desired phase difference δθ₀. Subsequently, the second angular velocity ω₂/is set as the second intrinsic angular velocity ω₂(FIG. 3/S036).

ω_2/L(t_k)=β_L∫dtq₂L(t), ω_2/R(t_k)=β_R∫dtq₂R(t)

q
₂
L(t)=(4ε_L²(t_k)−(ω_1/L(t)−ω_2/L(t_k)))^1/2×sin(arcsin[(ω_1/L(t_k)−ω_2/L(t))/2ε_L(t_k)]−δθ₀),

q
₂
R(t)=(4ε_R²(t_k)−(ω_1/R(t)−ω_2/R(t_k)))^1/2×sin(arcsin[(ω_1/R(t_k)−ω_2/R(t))/2ε_R(t_k)]−δθ₀) (26)

Wherein, each component of “β=(β_L, β_R)” is a coefficient representing the stability of the system.

Accordingly, the second angular velocity ω₂/is appropriately set from the viewpoint of approximating the phase difference between the periodical motion of the human P represented by the first virtual oscillator φ₁and the periodical operation of the motion assisting device 10 represented by the second virtual oscillator φ₂to the desired phase difference δθ₀, while the mutual harmony between the first motion oscillator φ₁and the first oscillator ζ₁is maintained between the periodical motion of the human P and the periodical operation of the motion assisting device 10.

The second oscillator generation element 140 corrects the second model by appropriately correcting a coefficient c contained in the simultaneous differential equation representing the second model according to the equation (28) (FIG. 3/S004). “c={c_i|i=L+, L−, R+, R−}” is a coefficient to be adjusted so that the motion variable ζ determined by the motion variable determination element 108 approximates to a desired value ζ₀or a deviation therebetween is minimum. The coefficient c_iis served as the “auxiliary coefficient” and is to be corrected accordingly whether or not each leg is in the reinforcement duration, which will be explained hereinafter.

c
_i(t_k+1)=c_i(t_ka)−C_i{V_i(t_k+1)−V_i(t_k)}/{c_i(t_k)−c_i(t_k−1)},

V
_i(t_k+1)≡(1/2){ζ_i(t_k+1)−ζ_i(t_k)}² (28)

Each component of “c=c_L+, c_L−, c_R+, c_R−}” is a coefficient representing the stability of a potential V₂=(V_2L+, V_2L−, V_2R+, V_2R−) for approximating each component of the determination values of the motion variable ζ to each component of the desired value ζ₀thereof. “ζ₀={ζ_0i|i=L+, L−, R+, R−}” stands for the desired value for each of the left hip joint angle and the right hip joint angle at the finished timing of the flexion motion and at the finished timing of the stretch motion of the thigh every walking cycle, respectively. The desired value ζ₀may be calculated on the basis of a desired footstep of the human P which is stored preliminarily in the memory, according to the correlation between the left hip joint angle and the right hip joint angle at the finished timing of the flexion motion and at the finished timing of the stretch motion of the thigh every walking cycle, respectively, and a footstep between the left and right feet, which is also stored in the memory.

Thereafter, the first processing element 101 determines whether each leg of the human P is at the on-ground state or at the off-ground state, and determines a posture of each leg with respect to the body (FIG. 3/S006).

The on-ground state and the off-ground state of each leg vary periodically when the human P performs the periodical walking motion. Thereby, whether each leg is at the on-ground state or at the off-ground state can be determined on the basis of an arbitrary variable which varies periodically according to the periodical walking motion of the human P. For example, whether each leg is at the on-ground state or at the off-ground state can be determined on the basis of a periodical variation pattern of an angle or angular velocity of each of the left and right hip joints, an acceleration of each leg in the vertical direction, a floor reaction force subjected to each leg of the human P or the like determined by an appropriate sensor. As a posture of each leg with respect to the body, a value of a variable which can be used to specify the phase of the hip joint angle or the like in the walking cycle (for example, the phase is zero at the time when a flexion motion is finished, the phase at the time when a subsequent stretch motion to the flexion motion is finished is π, and the phase at the time when another flexion motion after the subsequent stretch motion is finished is 2π) is determined on the basis of the output signal from the hip joint angle sensor 11. The value of a state variable (to be described hereinafter) u_i(i=L+, L−, R+, R−} for defining the second model varies periodically according to the periodical walking motion of the human P, therefore, whether each leg is at the on-ground state or at the off-ground state, or the posture of each leg with respect to the body can be determined on the basis of a periodical variation pattern of the value of the state variable u_i.

Thereafter, the second processing element 102, on the basis of the determination result by the first processing element 101, adjusts the value of the auxiliary coefficient in such a way that the auxiliary coefficient in the reinforcement duration is greater than the auxiliary coefficient in the duration other than the reinforcement duration for each leg (FIG. 3/S008). The “reinforcement duration” is referred to as a duration including a second reinforcement duration, or a duration including a first reinforcement duration and a second reinforcement duration. The “first reinforcement duration” is referred to as a part or a total of the duration in which the leg is moved from the flexion motion at the off-ground state to the stretch motion to step on the ground. The “second reinforcement duration” is referred to as a part or a total of the duration in which the leg is performing a stretch motion at the on-ground state. The first reinforcement duration and the second reinforcement duration may be alternatively continuous or discontinuous in each walking cycle. Each of the first reinforcement duration and the second reinforcement duration may be continuous or discontinuous in each walking cycle, respectively. The coefficient c_iis adjusted as the auxiliary coefficient. The coefficient c_iis used to specify the variation feature of the state variable u_ifor defining the second model. The coefficient c_ialso serves as the correction subject adjusted on the basis of the motion variable ζ. In addition to or in place of the coefficient c_i, it is also acceptable to adjust an inverse τ_1i⁻¹of the time constant as the auxiliary coefficient.

For example, when the left leg is in a normal duration other than the reinforcement duration, the left flexion coefficient c_L+ and the left stretch coefficient c_L− are maintained at their former values. On the other hand, when the left leg is in the reinforcement duration, the left flexion coefficient c_L+ is maintained at its former value, while the left stretch coefficient c_L− is increased as (1+δ) (δ>0) times as its former value. The right leg is adjusted with the same auxiliary coefficient as the left leg. Specifically, when the right leg is in the normal duration other than the reinforcement duration, the right flexion coefficient c_R+ and the right stretch coefficient c_R− are maintained at their former values. On the other hand, when the right leg is in the reinforcement duration, the right flexion coefficient c_R+ is maintained at its former value, while the right stretch coefficient c_R− is increased as (1+δ) (δ>0) times as its former value. Note that there is no limitation on the increment of the auxiliary coefficient for the left leg and the right leg.

Subsequently, the second oscillator generation element 140 generates the second oscillator ζ₂=(ζ_2L+, ζ_2L−, ζ_2R+, ζ_2R−) as an output oscillation signal from the second model, by inputting the second motion oscillator φ2 determined by the motion oscillator determination element 110 to the second model as an input oscillation signal (FIG. 3/S040). The second model represents the correlation between a plurality of second elements such as the neural elements or the like responsible for moving each leg to the flexion direction (forward direction) and the stretch direction (backward direction), and generates the output oscillation signal varying at an angular velocity defined according to the second intrinsic angular velocity φ₂set by the intrinsic angular velocity setting element 130 on the basis of the input oscillation signal as aforementioned.

The second model is defined by the simultaneous differential equation expressed by, for example, the equations (30). The simultaneous differential equation contains therein the state variable u={u_i|i=L+, L−, R+, R−} representing the behavior state (specified by an amplitude and a phase) of each thigh to the flexion direction (forward direction) and the stretch direction (backward direction), respectively, and a self-inhibition factor v={v_i|i=L+, L−, R+, R−} representing compliance of each behavior state. Moreover, the simultaneous differential equation contains therein the desired value ζ₀for each of the left hip joint angle and the right hip joint angle at the finished timing of the flexion motion and at the finished timing of the stretch motion of the thigh every walking cycle, respectively, and the coefficient c_ito be corrected as mentioned above. It is acceptable to increase the numbers of the second motion oscillator φ₂which is served as the determination object. The more numbers of the second motion oscillators φ₂are input to the second model, the more the correlation members in the simultaneous differential equation will become, however, it may allow an appropriate assist in the periodical motion of the human P through the adjustment of the correlation coefficients by considering the correlation between motion states of various body parts of the human P.

τ_1L+(du_L+/dt)=c_L+ζ_0L+−u_L++w_L+/L−ζ_2L−+w_L+/R+ζ_2R+−λ_Lv_L++f₁(ω_2L)+f₂(ω_2L)K₂φ_2L,

τ_1L−(du_L−/dt)=c_L−ζ_0L−−u_L−+w_L−/L+ζ_2L++w_L−/R−ζ_2R−−λ_Lv_L−+f₁(ω_2L)+f₂(ω_2L)K₂φ_2L,

τ₁R+(du_R+/dt)=c_R+ζ_OR+−u_R++w_R+/L+ζ_2L++w_R+/R−ζ_2R+−λ_Rv_R++f₁(ω_2R)+f₂(ω_2R)K₂φ_2R,

τ_1R−(du_R−/dt)=c_R−ζ_OR−−u_R−+w_R−/L+ζ_2L−+w_R−/R+ζ_2R+−λ_Rv_L++f₁(ω_2R)+f₂(ω_2R)K₂φ_2R,

τ_2i(dV_i/dt)=−v_i+ζ_2i,

ζ_2i=H(u_i−u_th)=0(u_i<u_thi) or u_i(u_i≧u_thi), or

ζ_2i=fs(u_i)=u_i/(1+exp(−u_i/D)) (30)

“τ_li” is a time constant for defining the variation feature of the state variable u_i, and is expressed by a ω-dependant coefficient t_(ω)and a constant γ=(γ_L, γ_R) according to the equation (31). The time constant τ_1ivaries in dependence on the second intrinsic angular velocity ω₂. As aforementioned, “τ_1imay be also used as the auxiliary coefficient corrected by the second processing element 102.

τ_1i=(t(ω_2L)/ω_2L)−γ_L(i=L+,L−), (t(ω_2R)/ω_2R)−γ_R(i=R+, R−) (31)

“τ_2i” is a time constant for defining the variation feature of the self-inhibition factor v_i. “w_i/j” is a negative second correlation coefficient for representing the correlation between the state variables u_iand u_jwhich represent the motions of the left and right legs of the human P toward the flexion direction and the stretch direction as the correlation of each component of the second oscillator ζ₂(correlation between the output oscillation signals of the plurality of second elements). “λ_L” and “λ_R” are compliant coefficients. “κ₂” is a feedback coefficient in relation to the second motion oscillator φ₂.

“f₁” is a first order function of the second intrinsic angular velocity ω₂defined by the equation (32) with a positive coefficient c. “f₂” is a second order function of the second intrinsic angular velocity ω₂defined by the equation (33) with coefficients c₀, c₁and c₂.

f
₁(ω)≡cω (32)

f
₂(ω)≡c₀+c₁ω+c₂ω² (33)

The second oscillator ζ_2iis equal to zero when the value of the state variable u_iis smaller than a threshold value u_th; and is equal to the value of u_iwhen the value of the state variable u_iis equal to or greater than the threshold value u_th. In other words, the second oscillator ζ_2iis defined by a sigmoid function fs (refer to the equations (30)). According thereto, if the state variable u_L+ representing the behavior of the left thigh toward the forward direction increases, the amplitude of the left flexion component ζ_2L+ of the second oscillator ζ₂becomes greater than that of the left stretch component ζ_2L−; if the state variable u_R+ representing the behavior of the right thigh toward the forward direction increases, the amplitude of the right flexion component ζ_2R+ of the second oscillator ζ₂becomes greater than that of the right stretch component ζ_2R−. Further, if the state variable u_L− representing the behavior of the left thigh toward the backward direction increases, the amplitude of the left stretch component ζ_2L− of the second oscillator ζ₂becomes greater than that of the left flexion component ζ_2L+; if the state variable u_R− representing the behavior of the right thigh toward the backward direction increases, the amplitude of the right stretch component ζ_2R− of the second oscillator ζ₂becomes greater than that of the right flexion component ζ_2R+. The motion toward the forward or backward direction of the leg (thigh) is recognized by, for example, the polarity of the hip joint angular velocity. The motion toward the forward or backward direction of the leg (thigh) is recognized by, for example, the polarity of the hip joint angular velocity.

Next, the auxiliary oscillator generation element 150 sets the auxiliary oscillator η=(η_L, η_R) on the basis of the second oscillator ζ₂generated by the second oscillator generation element 140 (FIG. 3/S050). Specifically, the auxiliary oscillator q is generated according to the equation (40). In other words, the left component η_Lof the auxiliary oscillator η is calculated as a sum of a product of the left flexion component ζ_2L+ of the second oscillator ζ₂and the coefficient χ_L+, and a product of the left stretch component ζ_2L− of the second oscillator ζ₂and the coefficient “−χ_L−”. The right component η_Rof the auxiliary oscillator q is calculated as a sum of a product of the right flexion component χ_2R+ of the second oscillator δ₂and the coefficient χ_R+, and a product of the right stretch component ζ_2R− of the second oscillator ζ₂and the coefficient “−χ_R−”.

η_L=χ_L+ζ_2L+−χ_L−ζ_2L−, η_L=χ_R+ζ_2R+−χ_R−ζ_2R− (40)

Thereafter, a current I=(I_L, I_R) supplied to each of the left and right actuators 15 from the battery 1000 is adjusted by the first controller 100 on the basis of the auxiliary oscillator η. The current I is represented by, for example, I(t)=G₁*η(t) (wherein, G₁is a ratio coefficient) on the basis of the auxiliary oscillator η. Thereby, the assisting force to move each thigh (the second body part) with respect to the waist (the first body part), or the torque T=(T_L, T_R) around the hip joint which is applied to the human P by the motion assisting device 10 through the first orthosis 1100 and the second orthosis 1200 is adjusted (FIG. 3/S060). The torque T is represented by, for example, T(t)=G₂*I(t) (wherein, G₂is a ratio coefficient) on the basis of the current I. Thereafter, the series of the aforementioned processes are performed repeatedly. Note that it is acceptable to control the motion of the motion assisting device 10 irrelative to the aforementioned control method on the condition that the thigh is appropriately moved with respect to the waist in a duration from the initiation of the walking motion of the human P to the finish of the walking motion after 2 to 3 foot steps.

According to the motion assisting device 10 which exhibits the aforementioned functions as the first embodiment of the present invention, the second orthosis 1200 is actuated to move with respect to the first orthosis 1100 by the actuator 15, as illustrated in FIGS. 4(a) and 4(b). Thereby, the stretch motion and the flexion motion of the thigh with respect to the waist are assisted, and consequently, as illustrated in FIG. 5(a) to FIG. 5(e), the periodical walking motion of the human P by leaving each leg off the ground and stepping on the ground repeatedly can be assisted.

When the left leg is on the ground, the left stretch coefficient c_L− is adjusted greater (refer to FIG. 3/S008), therefore, the left stretch component u_L− of the state variable u representing the motion to the stretch direction (backward motion) of the left leg (left thigh) with respect to the body becomes greater, and the amplitude of the left stretch component ζ_2L− of the second oscillator ζ₂also becomes greater (refer to the equations 30). As a result thereof, the assisting force (torque) which assists the stretch motion of the left leg is reinforced according to amplitude of the left stretch component ζ_2L− of the second oscillator ζ₂(refer to the equation 40). In other words, the assisting force applied to the human P to assist the left leg (left thigh) in moving with respect to the body is reinforced only by an increment of the auxiliary coefficient increased in the reinforcement duration. Note that it is not limited that the reinforced assisting force is stronger than the assisting force in the duration other than the reinforcement duration. The same is applicable to the right leg.

The reinforcement duration includes the second reinforcement duration, namely, a part or a total of the second duration in which the leg is performing a stretch motion (backward motion) at the on-ground state. Accordingly, the stretch motion of the leg at the on-ground state is assisted by a relatively stronger assisting force, especially when the first reinforcement duration is contained in the reinforcement duration; and resultantly, the leg is subjected to a relatively stronger floor reaction force. The floor reaction force is transmitted to the body through the leg at the on-ground state to conduct the body to translate forward. When the leg is stretched by the assisting force at the on-ground state, there occurs a reflex (stretch reflex) to the stretch motion of the leg. As a result, the flexion motion of the leg at a subsequent off-ground state is induced by the stretch reflex at the previous off-ground state (refer to FIG. 5(b) to FIG. 5(d)). According thereto, the periodical walking motion of the human P can be assisted to conduct not only a stretch motion (backward motion) of the leg (thigh) of the human P at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state.

In addition, the scale and the rhythm of the periodical walking motion of the human P are assisted so as to match the desired motion scale and the desired motion rhythm thereof, respectively.

The motion of the human P can be assisted by the motion assisting device 10 so as to match the motion rhythm of the human P to the desired motion rhythm thereof according to the following method. In detail, the second intrinsic angular velocity (2 is appropriately set from the viewpoint of approximating the phase difference between the periodical motion of the human P represented by the first virtual oscillator φ₁and the periodical operation of the motion assisting device 10 represented by the second virtual oscillator φ₂to the desired phase difference δθ₀, while the mutual harmony between the first motion oscillator φ₁and the first oscillator ζ₁is maintained between the periodical motion of the human P and the periodical operation of the motion assisting device 10 as mentioned above (refer to FIG. 3/S031 to S036). The second oscillator ζ₂varies periodically at an angular velocity defined according to the second intrinsic angular velocity ω₂and the output torque T is controlled on the basis of the second oscillator ζ₂, therefore, the output torque T varies periodically at the same angular velocity defined according to the second intrinsic angular velocity ω₂(refer to FIG. 3/S040, S050 and S060). Accordingly, by applying the torque T to the human P, the motion rhythm of the human P and the operation rhythm of the motion assisting device 10 are harmonized; as a result thereof, the periodical walking motion of the human P is assisted so as to match the motion rhythm of the human P to the desired motion rhythm thereof.

The motion of the human P can be assisted by the motion assisting device 10 so as to match the motion scale of the human P to the desired motion scale thereof according to the following method. In detail, the second model is corrected so as to approximate the motion variable ζ (the left hip joint angle and the right hip joint angle at the finished timing of the flexion motion and at the finished timing of the stretch motion of the thigh every walking cycle, respectively) representing the motion scale of the periodical walking motion of the human P to the desired value ζ₀thereof (refer to FIG. 3/S004). Thereafter, the second oscillator ζ₂is generated according to the corrected second model and the torque T applied to the human P is controlled on the basis of the generated second oscillator ω₂(refer to FIG. 3/S050 and S060). According thereto, in spite of the rhythm speed of the periodical motion of the human P, the periodical motion thereof can be assisted by applying an appropriate assisting force to the human P so as to match the motion scale (the footstep, the maximum hip joint angle or the like) of the human P to the desired motion scale thereof.

Subsequently, descriptions will be carried out on a second embodiment of the present invention. The motion assisting device 10 of the second embodiment of the present invention illustrated in FIG. 6 has substantially the same configuration as the motion assisting device 10 of the first embodiment of the present invention illustrated in FIG. 1. Therefore, the same numerals are used to refer to identical parts and descriptions thereof are omitted. The motion assisting device 10 in the second embodiment of the present invention includes an adjusting device 14 having a plurality of adjusting buttons 148 configured to adjust a value of a time constant (to be described hereinafter) or the like. Note that it is acceptable to appropriately dispose the adjusting device 14 in the motion assisting device 10 so that it is convenient to be operated by the human P or a supervisor who supervises the walking training of the human P.

As illustrated in FIG. 7, the controlling device 100 in the second embodiment of the present invention is provided with a first processing element 101, a second processing element 102, a motion oscillator determination element 110, a second oscillator generation element 140, and an auxiliary oscillator generation element 150. In other words, the controlling device 100 in the second embodiment of the present invention is configured to omit the motion variable determination element 108, the first oscillator generation element 120 and the intrinsic angular velocity setting element 130 in the controlling device 100 in the first embodiment of the present invention. Each element may be constituted from a mutually different CPU, or a universal CPU or the like.

The motion oscillator determination element 110 determines each hip joint angle as the second motion oscillator φ₂on the basis of an output from the hip joint angle sensor 11. In the second embodiment, the first motion oscillator φ₁is not determined. The second oscillator generation element 140 generates the second oscillator ζ₂as an output oscillation signal from the second model by inputting the second motion oscillator φ₂determined by the motion oscillator determination element 110 as an input oscillation signal to the second model. The second model in the second embodiment is the same as the second model in the first embodiment on a point that both of them are defined by the simultaneous differential equation (30). However, the second model in the second embodiment adjusts the coefficient c={c_i|i=L+, L−, R+, R−} of the desired value ζ₀={ζ_0i|i=L+, L−, R+, R−} of the motion variable ζ representing a motion scale of the human P and the time constant τ_1i={τ_1i=L+, L−, R+, R−} through the adjusting buttons 148 of the adjusting device 14; while the second model in the first embodiment corrects the coefficient c on the basis of a deviation between a determination value of the motion variable ζ and the desired value ζ. On this point, the second model in the second embodiment differs from the second model in the first embodiment (refer to the equation (28) and FIG. 3/S004). Moreover, the second intrinsic angular velocity ω₂contained in the second model of the second embodiment is adjusted indirectly through adjusting the time constantτ_1i(refer to the equation (31)); on this point, it differs from the second model of the first embodiment in which the second intrinsic angular velocity ω₂is set according to the virtual model. Similar to the first embodiment, the auxiliary oscillator generation element 150, on the basis of the second oscillator ζ₂generated by the second oscillator generation element 140, generates the auxiliary oscillator η. The auxiliary oscillator η is used to define a variation pattern of the torque applied to the thigh by the actuator 15 in the motion assisting device 10.

Hereinafter, the operation of the motion assisting device 10 having the configuration mentioned above in the second embodiment of the present invention will be described. The motion oscillator determination element 110 determines the left hip joint angle and the right hip joint angle of the human P as the second motion oscillator φ₂=(φ_2L, φ_2R) on the basis of the output from the hip joint angle sensor 11 (FIG. 8/S110).

Thereafter, similar to that in the first embodiment, the first processing element 101 determines whether each leg of the human P is at the on-ground state or at the off-ground state, and determines a posture of each leg with respect to the body (FIG. 8/S112). Further, similar to that in the first embodiment, the second processing element 102, on the basis of the determination result by the first processing element 101, adjusts the value of the auxiliary coefficient in such a way that the auxiliary coefficient in the reinforcement duration is greater than the auxiliary coefficient in the duration other than the reinforcement duration for each leg (FIG. 8/S114).

Subsequently, the second oscillator generation element 140 generates the second oscillator ζ₂={ζ_2i|i=L+, L−, R+, R−} as an output oscillation signal from the second model by inputting the motion oscillator determined by the motion oscillator determination element 110 as an input signal to the second model (FIG. 8/S120). As aforementioned, the time constant τ_1iand the coefficient c_irelated to the desired value ζ_0iof the motion variable ζ_iin the simultaneous differential equation (30) can be adjusted by operating the adjusting buttons 148 in the adjusting device 14. In addition to or in place of the time constant τ_1ior the coefficient c_i, the time constant τ_2i{τ_2i|i=L+, L−, R+, R−}, the correlation coefficient w_i/jor the like may be adjusted through the adjusting device 14.

Next, similar to that in the first embodiment, the auxiliary oscillator η=(η_L, η_R) is set by the auxiliary oscillator generation element 150 on the basis of the second oscillator ζ₂(FIG. 8/S130). The torque T=(T_L, T_R) applied to the human P from the motion assisting device 10 through the first orthosis 1100 and the second orthosis 1200 is adjusted (FIG. 8/S140). Thereafter, the series of the aforementioned processes are performed repeatedly. Note that it is acceptable to control the motion of the motion assisting device 10 irrelative to the aforementioned control method on the condition that the thigh is appropriately moved with respect to the waist in a duration from the initiation of the walking motion of the human P to the finish of the walking motion after 2 to 3 foot steps.

Similar to the motion assisting device 10 in the first embodiment of the present invention, according to the motion assisting device 10 which exhibits the aforementioned functions in the second embodiment of the present invention, the second orthosis 1200 is actuated to move with respect to the first orthosis 1100 by the actuator 15, as illustrated in FIGS. 4(a) and 4 (b). Thereby, the stretch motion and the flexion motion of the thigh with respect to the waist are assisted, and consequently, as illustrated in FIG. 5(a) to FIG. 5(e), the periodical walking motion of the human P by leaving each leg off from the ground and stepping on the ground repeatedly can be assisted.

The assisting force applied to the human P to assist the leg (thigh) in moving with respect to the body is reinforced only by an increment of the auxiliary coefficient increased in the reinforcement duration. Note that it is not limited that the reinforced assisting force is stronger than the assisting force in the duration other than the reinforcement duration. The reinforcement duration includes the second reinforcement duration, namely, a part or a total of the second duration in which the leg is performing a stretch motion at the on-ground state. Accordingly, the stretch motion of the leg at the on-ground state is assisted by a relatively stronger assisting force, especially when the first reinforcement duration is contained in the reinforcement duration; and resultantly, the leg is subjected to a relatively stronger floor reaction force. The floor reaction force is transmitted to the body through the leg at the on-ground state to conduct the body to translate forward. When the leg is stretched by the assisting force at the on-ground state, there occurs a reflex (stretch reflex) to the stretch motion of the leg. As a result, the flexion motion of the leg at a subsequent off-ground state is induced by the stretch reflex at the previous off-ground state (refer to FIG. 5(b) to FIG. 5(d)). According thereto, the periodical walking motion of the human P can be assisted to conduct not only a stretch motion (backward motion) of the leg (thigh) of the human P at the on-ground state, but also a smooth flexion motion (forward motion) thereof at the off-ground state.

Since no other model but the second model is used, accordingly, the computation processing load needed to generate the second oscillatorζ₂by the first controlling device 100 can be reduced. Further, the time constant τ₁={τ_1i=L+, L−, R+, R−} and the coefficient c={c_i|i=L+, L−, R+, R−} contained in the simultaneous differential equation (refer to the equations (30)) for defining the second model are partially adjusted via the operations on the buttons 148 of the adjusting device 14. Thereafter, the second oscillator ζ₂is generated according to the adjusted second model and the output torque T applied to the human P is controlled to vary periodically according to the second oscillator ζ₂(refer to S130 and S140 in FIG. 8). Accordingly, the periodical motion of the human P can be assisted by applying the assisting force to the human P so as to make the motion scale and the motion rhythm of the periodical motion of the human P match the desired motion scale and the desired motion rhythm thereof, respectively, while reducing the computation processing load. Furthermore, the variation pattern of the second oscillator ζ₂(angular velocity) and the variation pattern of the output torque T from the actuator 15 are adjusted by adjusting the time constant τ_1irepresenting the variation pattern of the state variable u_i. Thereby, the periodical motion of the human P assisted by the torque T is made to approximate the motion rhythm of the human P to the desired motion rhythm thereof. Additionally, the magnitude of the second oscillator ζ₂and the magnitude of the output torque T from the actuator 15 can be adjusted by adjusting the coefficient c_irelated to the desired value ζ₀of the motion variable ζ. Thereby, the periodical motion of the human P can be assisted so as to approximate the motion scale of the periodical motion to the desired motion scale thereof.

In the aforementioned embodiment, it is described that the walking motion of the human P is assisted. However, it is also possible to assist the walking motion of an animal other than a human, such as a monkey (and/or ape), a dog, a horse, cattle or the like.

In the first embodiment, the amplitude and the phase of the periodical operation of the motion assisting device 10 represented by the auxiliary oscillator r are controlled on the basis of the amplitude and the phase of the periodical walking motion of the human P represented by the first motion oscillator φ₁and the second motion oscillator φ₂. In the second embodiment, the amplitude and the phase of the periodical operation of the motion assisting device 10 represented by the auxiliary oscillator q are controlled on the basis of the amplitude and the phase of the periodical walking motion of the human P represented by the second motion oscillator φ₂. Additionally, various algorithms can be used to control the operation of the motion assisting device 10 as long as they can apply the assisting force varying periodically so as to assist the thigh (or the leg) in moving periodically with respect to the body. For example, it is acceptable to adopt the generation method described in the first prior art or the second prior art as a generation method for the auxiliary oscillator η on the basis of the second oscillator ζ₂.

In the second prior art, the first auxiliary oscillator representing a virtual elastic force which varies periodically is generated to approximate the motion variable ζ to the desired value ζ₀and the auxiliary oscillator is generated so as to contain the first auxiliary oscillator. A spring coefficient specifying the elastic force may be adjusted as the auxiliary coefficient.

In the above embodiment, the auxiliary coefficient is adjusted on the basis whether each leg of the human P is in the reinforcement duration by adjusting the coefficient c_i(inverse τ_1i⁻¹of the time constant, in addition to or in place of the coefficient c_i) for specifying the behavior feature of the state variable u_ifor defining the second model. The magnitude of the assisted force is also adjusted according to the value of the auxiliary coefficient (refer to FIG. 3/S006 and S008, FIG. 8/S112 and S114). Additionally, the coefficient χ_iused in generating the auxiliary oscillator η may be adjusted as the auxiliary coefficient (refer to the equation (40)). For example, the coefficient χ_L− is adjusted in such a way that the coefficient χ_L− related to the left stretch component ζ_2L− of the second oscillator ζ₂is greater when the left leg is in the reinforcement duration than that when the left leg is in the normal duration. Accordingly, the assisting force to assist the left leg (left thigh) in the stretch motion is reinforced only by the increment on the auxiliary coefficient χ_L− in the reinforcement duration. Similarly, the coefficient χ_R− is adjusted in such a way that the coefficient χ_R− related to the right stretch component δ_2R− of the second oscillator ζ₂when the right leg is in the reinforcement duration is greater than that when the right leg is in the normal duration. Accordingly, the assisting force to assist the right leg (right thigh) in the stretch motion is reinforced only by the increment on the auxiliary coefficient ω_R− in the reinforcement duration.

The present invention is not merely limited to the motion assisting device 10 used in the walking training of the human P as illustrated in FIG. 9, it is also possible to include a treadmill 30 and a lifter 50 (load alleviation unit). The human P walks by advancing against the motion of an endless belt 33 moving backward, with a partial weight thereof supported by holding a handrail 32 (load alleviation unit) disposed at both sides of a base 31 of the treadmill 30 with both hands, respectively. The endless belt 33 is supported over a plurality of rollers and the speed of the endless belt 33 is controlled by controlling the rotating velocity of a part of the plurality of rollers. Additionally, a partial weight of the human P is supported by the lifter 50 through a wire 52 whose roll length is adjustable.

Furthermore, a walking machine 70 as illustrated in FIG. 10 may be used in the walking training of the human P. A partial weight of the human P is supported by holding a handrail 72 (load alleviation unit) which is disposed at both sides of a base 71 of the walking machine 70 with both hands, respectively. The base 71 can move at a rotating velocity of wheels disposed at the bottom thereof controlled according to the walking motion of the human P.

MOTION ASSISTING DEVICE

Information

Publication Number

Date Filed

Date Published

Inventors

Original Assignees

CPC

US Classifications

International Classifications

Abstract

Description

Claims

Priority Claims (1)

PCT Information