JPH10217157A - Muscle electric signal generating device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To use a functional electric signal as an input signal of stimulation, an electric stimulation signal for rehabilitation, etc., by finding false tensile force by estimating a track of a body portion and a muscle electric signal by an valuation standard using an acceleration estimation model. SOLUTION: A muscle electric signal is detected from a human arm 1 of a healthy person and amplified by a muscle electric signal amplifier 2. The amplified muscle electric signal is filtered by a filter 3, and false tensile force is extracted. Tensile force is estimated by a muscle tensile force estimation circuit 4 from the extracted false tensile force, joint torque is estimated by a joint torque estimation circuit 5 in accordance with the tensile force, and a motion track is formed by an equation of motion 6. A body model is constituted by the filter 3, the muscle tensile force estimation circuit 4, the joint torque estimation circuit 5 and the equation of motion 6. A terminal end condition at a starting point and a terminal point is satisfied by using this body model, and a track to minimize an evaluation function of the false tensile force is computed by repeating computation.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a myoelectric signal generator, and more particularly, to functional electrical stimulation, rehabilitation,
The present invention relates to a myoelectric signal generation device for estimating an input signal of a control target such as a robot having redundant degrees of freedom such as motor learning and muscles.

[0002]

2. Description of the Related Art When the brain function is impaired due to a stroke or the like, arms and legs may be paralyzed. In this case, the muscles of the arms and legs are normal, and a myoelectric signal for moving the muscles is transmitted from the brain. Not transmitted to muscles, resulting in motor paralysis. If such a myoelectric signal can be generated, motor paralysis can be overcome.

[0003]

Conventionally, in order to generate a myoelectric signal, a myoelectric signal pattern of a healthy person when a certain exercise pattern is previously performed is measured, and an electromyographic analysis is performed. Based on the results, the signal was normalized to match the myoelectric signal of the patient and used as stimulus data. Therefore, for example, in the case of an operation in which the hand is brought from the state where the hand is extended to the mouth, the pattern of the myoelectric signal for the target operation is measured by measuring a myoelectric signal pattern at the time of bending the elbow of a healthy person. I had to remember it. Because it is difficult to create data for all movement patterns, it was necessary to save a certain number of patterns and apply them to patients.

[0004] Therefore, a main object of the present invention is to create a model for estimating joint torque from pseudo-tension, and based on the model, to estimate a trajectory and a pseudo-tension by an evaluation function for minimizing pseudo-tension change. A signal generation device.

[0005]

The invention according to claim 1 is
A myoelectric signal generating apparatus for generating an electromyographic signal, which estimates a trajectory and a myoelectric signal of a body part based on an evaluation criterion of a minimum myoelectric signal change processed by using a body model realized by an acceleration model. .

According to the second aspect of the present invention, the body part model of the first aspect measures an arm movement and a myoelectric signal at the same time by a subject and determines a model for converting the measured myoelectric signal into a joint torque in advance. The function relation between the measurement data is reproduced using the algorithm.

In the invention according to claim 3, in the body model according to claim 1, joint torque is given as teacher data, and parameters thereof are determined using a predetermined algorithm.

In the invention according to claim 4, the joint torque is determined based on the measurement data of the trajectory, and the physical parameters such as the length and weight of the body part are determined from the shape of the body part.

According to the fifth aspect of the present invention, the optimal trajectory and the optimal trajectory are determined based on an evaluation criterion that makes the pseudo tension as smooth as possible by using the mapping relation from the pseudo tension obtained by the body model and the physical parameters to the joint torque. Calculate the pseudo tension that satisfies the evaluation criteria.

[0010]

DESCRIPTION OF THE PREFERRED EMBODIMENTS FIG. 1 is a diagram showing a flow from when a joint torque is generated from a myoelectric signal to when a trajectory is generated in an embodiment of the present invention.

In FIG. 1, a myoelectric signal is detected from a human arm 1 of a healthy person and amplified by a myoelectric signal amplifier 2.
The amplified myoelectric signal is filtered by the filter 3, and the pseudo tension is extracted. A muscle tension estimating circuit 4 estimates a tension from the extracted pseudo tension, a joint torque is estimated by a joint torque estimating circuit 5 based on the tension, and a motion trajectory is generated from a motion equation 6.

A body model is constituted by the filter 3, the muscle tension estimating circuit 4, the joint torque estimating circuit 5, and the equation of motion 6 shown in FIG.

Using this body model, a trajectory that satisfies the termination conditions at the start point and the end point and further minimizes the evaluation function of the expression (1) is calculated by iterative calculation.

[0014]

(Equation 1)

Here, u _j represents the j-th pseudo tension. Further, t _f represents the time at the end point. Hereinafter, each step will be described more specifically.

In the filter 3 shown in FIG. 1, pseudo tension is extracted from the myoelectric signal. The surface myoelectric signal is a signal in which the excitation potential of the membrane is temporally and spatially superimposed. The signal output using a low-pass filter as the filter 3 is expected to reflect the firing frequency of the α motor neuron. Also, this signal is called pseudo tension because it is considered to be quite close to true tension. This low pass filter is 2
It is known that the secondary system is sufficient, and the input EMG, output T
^If it is realized by an FIR filter as ^* , it is expressed by equation (2).

[0017]

(Equation 2)

Here, EMG is a myoelectric signal, and T ^* is a pseudo tension. There is a non-linear property between the tension generated by the muscle and the motion command as described below. The tension generated by the muscle increases as the muscle length increases, even with the same exercise command. This manner of change is non-linear and is referred to as a length-tension curve. Also, even with the same exercise command,
As the speed of shortening the muscle length increases, the tension decreases. The manner of this change is also non-linear, and is called a shortening speed-tension curve. This time, in order to estimate the position during attitude control,
The shortening speed-tension curve need not be taken into account.

FIG. 2 is a diagram showing a calculation model of the trajectory.
In FIG. 2, acceleration estimation models 11, 12,.
For example, it is constituted by a neural circuit, and the pseudo tension, the joint angle, and the joint angular velocity at the time T _i are input as inputs, and the output is the change in the joint angular velocity and the joint angle one unit time later.

Here, the joint torque is determined by the product of the tension and the moment arm. The distance between the rotation axis of the joint and the line of action of the muscle is the moment arm. When you bend and stretch your joints, your muscles are bent by your skin and bones,
This distance is not constant, and the relationship between torque and tension depends nonlinearly on the joint angle. That is, the joint torque is generated by the difference between the torque generated by the extensor and the flexor, and is determined depending on the tension and the moment arm. These relationships can be formulated as the following equation (3).

[0021]

(Equation 3)

Where τ_m= (Τ₁, Τ_Two,…, Τ_n)^t θ = (θ₁, Θ_Two,…, Θ_n)^t α_i(Θ) = (α_i1(Θ), α_i2(Θ),…, α
_in(Θ))^t Where τ_jIs the j-th joint torque, and θ_jIs the jth
Eye joint angle, α _ij(Θ) is the i-th muscle mode.
Ment arm (for joints that are not involved
0) and T_iIs the muscle tension of the ith muscle, T^*
_iRepresents the pseudo tension of the i-th muscle. Subscript t with upper right
Means transposition. However, there are n joints (1 ≦ j
≦ n) and k muscles (1 ≦ i ≦ k).

FIG. 3 shows a model 2 of a human forearm and upper arm.
It is a figure showing a manipulator of a link. In the manipulator shown in FIG. 3, if the length of the upper arm of the right arm of the human M is L1 and the length of the forearm is L2, the following equation of motion is established.

[0024]

(Equation 4)

Here, τ _i is a driving torque of each joint, θ _i is a joint angle, θ _i1 is a joint angular velocity, and θ _i1 is a joint angular velocity.
_i2 represents the joint angular acceleration. M _i is the mass of each link, L _i is the length, L _gi is the length from the joint to the center of mass, I _i is the moment of inertia around the joint, and b _i is the viscous drag Represents the coefficient of

In order to describe the relationship between the trajectory and the joint torque by the equation of motion, it is necessary to know physical parameters of the arm such as an accurate moment of inertia. Therefore, as an example, the parameters of the arm are calculated from the shape of the arm, but another method may be used. First, Cyberwar
e Measure the three-dimensional shape of the arm using a Laser Range Scanner. Then, assuming that the substance is a uniform substance having a specific gravity of 1, the length, the center of mass, and the moment of inertia are calculated from the volume. Table 1 shows the arm parameters thus obtained.

[0027]

[Table 1]

FIG. 4 shows an example of a muscle model, but the present invention can be applied to other robot control devices. In FIG. 4, the muscle tension is given by the following equation (5).

T _j = k _j (u _j , l _j ) Δl _j (u _j , l _j ) −b _j (u _j , l _j , _ij ) _ij (5) where k _j (u _j , l _j ) is the elastic modulus of the muscle, b _j
(U _j , l _j , i _j ) is the viscosity coefficient, Δl _j (u _j ,
l _j ) indicates muscle elongation. U _j is an exercise command for the muscle, l _j is the length of the muscle, and i _j indicates the contraction speed. The joint torque is expressed by equation (6).

[0030]

(Equation 5)

Here, i indicates a joint, and j is a subscript indicating a muscle. The moment arm A _ij (θ) has the same absolute value as the physical moment arm A _ij (θ _i ).
Positive and negative signs for flexors.

[0032] _{A ij (θ i) = {} d j a ij (θ i)} d j = 1.0 flexor, -1.0 extensor moment arm varies nonlinearly generally depends on the joint angle . Considering the moment arm divided into a part that is constant without depending on the joint angle and another part,

[0033]

(Equation 6)

## EQU1 ## Also, k _j (u _j , l _j ), b _j
(U _j , l _j , i _j ) is also 0 for u
The linear term up to the first and the first order and the non-linear term higher than it are considered separately.

[0035]

(Equation 7)

Further, regarding Δl _j (u _j , l _j ), first, the muscle length l _j is considered as a function of the joint angle θ _i . Δl _j (u _j , l _j ) is composed of a change in muscle length due to a change in joint angle and a change in the natural length of the muscle depending on the movement command u _j by the tension generating mechanism.

The length of a muscle when the joint angle is 0 for all muscles is defined as l _j (0). When θ _i = 0, i = 1, 2,..., N, l _j = l _j (0) The moment arm is as follows.

∂l _j / ∂θ _i = -A _ij (θ _i ) The length l _j (θ) of the muscle is as follows.

[0039]

(Equation 8)

Here, since the moment arm depends on the posture,

[0041]

(Equation 9)

In the above equation, l _j ^bias is a bias term for preventing the amount of elongation of the muscle from becoming negative due to bending and stretching of the joint. It is assumed that the movable range of the shoulder joint is −20 <θ ₀ <110 degrees, and the movable range of the elbow joint is 0 <θ ₁ <140 degrees (the bending direction is positive). At this time, when the flexor of the shoulder is bent, the maximum a _0j × 1
It becomes shorter by 10 / 180π [rad], and when the extensor muscle is stretched, it becomes shorter by a maximum of a _0j × 20 / 180π [rad]. The same is true for the elbow. In addition, the flexor of the _biarticular muscle has a maximum of a _0j × 110 /
180π + a _1j × 140 / 180π [rad] is shortened, and when the extensor is stretched, the maximum a _0j × 20 / 180π + a _1j ×
0 / 180π [rad] becomes shorter.

[0043]

(Equation 10)

[0044] u elongation of muscles, represents what can be modeled by a linear in ^{_{θ, Δl * j (u j}} , θ) represents the other nonlinear terms. Eventually, the expression (6) can be expressed by the following expression when expressed by the joint angle.

[0045]

[Equation 11]

In equation (8), ψ _ij (ω _j1 , θ _i ,
u _j ) and φ _ij (ω _j2 , θ _i , θ _i1 , u _j ) are expressed by a neural network model, and have a nonlinear relationship between muscle length and tension, a nonlinear relationship between muscle shortening speed and tension, and movement commands. It is used to absorb any nonlinear relationship to increase or decrease, as well as any nonlinearities that depend on the joint angle of the moment arm.

The myoelectric signal is obtained by dipole-inducing the surface myoelectric potential using a pair of silver-silver chloride surface electrodes, and sampling the differentially amplified myoelectric signal at 2 kHz and 12 bits. The diameter of the electrodes is 10 mm and the distance between the electrodes along the muscle fiber is 1 mm.
The muscles that were attached at 5 mm and measured the electromyographic signals were the extensor muscles of the shoulder joint and the flexor muscles were the anterior deltoid (DLC), upper deltoid (DLA), posterior deltoid (DLS), and pectoralis major (PM
J), great circle muscle (TEM), biceps long head (BIL), triceps extra long head (TRL) as two joint muscles of shoulder and elbow
The extensor and flexor muscles of the elbow joint are the brachial muscle (BRC), the triceps inner head (TRM), and the triceps outer head (TRA). After full-wave rectification of the myoelectric signal, an average of every 10 points is taken (EMG _ave ), and a moving average of every 5 points is taken as shown in the following equation to smooth the signal. _ma ).

[0048]

(Equation 12)

Therefore, this means that sampling was performed at 200 Hz. As a result of learning only the linear part using EMG _ma as the input signal indicated by EMG in the equation (2), the values of the parameters are as shown in Table 2.

[0050]

[Table 2]

FIG. 5 shows the DL of the six muscle models described above.
3 illustrates C, BRC, DLS, TRM, BIL, and TRL.

Next, in the torque change minimum trajectory, even if the torque for realizing the optimum motion can be calculated, there are countless combinations of muscle tensions for realizing the calculation. In the muscle-tension change minimum trajectory, the smoothest combination of muscle tensions is estimated. In addition, when creating stimulation patterns such as functional electrical stimulation, the relationship between myoelectric signals and muscle tension must be taken into account. Therefore, the minimum trajectory of the change in muscle tension that satisfies the expression (1) was calculated using a linear model of six muscles. 8 and 9 are diagrams showing the calculated generated trajectory, and FIG. 10 shows a pseudo tension satisfying the expression (1).

[0053]

As described above, according to the present invention, the trajectory and the myoelectric signal of the body part are estimated based on the evaluation criterion of the minimum change of the myoelectric signal processed using the acceleration estimation model. The pseudo-tension can be obtained from the evaluation function of the pseudo-tension change minimum, and the functional electric signal can be used as an input signal of a stimulus, an electric stimulus signal for rehabilitation, a signal for exercise learning, and the like.

[Brief description of the drawings]

FIG. 1 is a diagram showing a flow from when a joint torque is generated from a myoelectric signal to when a trajectory is generated in an embodiment of the present invention.

FIG. 2 is a diagram showing a calculation model of a trajectory.

FIG. 3 is a diagram showing a two-link manipulator that models a human forearm and upper arm.

FIG. 4 is a diagram showing a muscle model.

FIG. 5 is a diagram showing a model of six muscles.

FIG. 6 is a diagram illustrating a generated trajectory.

FIG. 7 is a diagram showing a relationship between speed and time.

FIG. 8 is a diagram showing pseudo tension.

[Explanation of symbols]

 1 human arm 2 myoelectric signal amplifier 3 filter 4 muscle tension estimation circuit 5 joint torque estimation circuit 6 equation of motion 11, 12, 1n acceleration estimation model

 ──────────────────────────────────────────────────続 き Continuing on the front page (72) Mitsuo Kawato Inventor 5 Shiratani, Inaya, Seika-cho, Soraku-gun, Kyoto Pref.

Claims (5)

[Claims] 1. A myoelectric signal generating apparatus for generating an electromyographic signal, comprising: a trajectory and a muscle of a body part based on an evaluation criterion of a minimum myoelectric signal change processed using a body model realized by an acceleration model. A myoelectric signal generating device for estimating an electric signal. 2. The body part model measures a movement of a subject's arm and a myoelectric signal simultaneously, and uses a model for converting the measured myoelectric signal into joint torque and a function between measured data using a predetermined algorithm. The myoelectric signal generation device according to claim 1, wherein the relationship is reproduced. 3. The myoelectric signal generation device according to claim 1, wherein the body model is provided with joint torque as teacher data, and parameters thereof are determined using a predetermined algorithm. 4. The muscle according to claim 2, wherein the joint torque is determined based on trajectory measurement data, and the physical parameters such as the length and weight of the body part are determined from the shape of the body part. Electric signal generator. 5. An optimal trajectory according to an evaluation criterion such that the pseudo tension is as smooth as possible by using a mapping relation from the pseudo tension obtained by the physical parameters to the joint torque, and the evaluation criterion. The myoelectric signal generation device according to claim 1, wherein a pseudo tension that satisfies is satisfied.