WO2018110622A1 - Foot region abnormality analysis device and method - Google Patents

Abstract

The purpose of the present invention is to provide a foot region abnormality analysis device and method that make it possible to analyze foot region abnormalities that cannot be assessed from a foot pressure distribution alone. This foot region abnormality analysis device (100) has: a member (10: for example, an insole, a shoe) that contacts the sole of a foot; sensors (1–7: shear force sensors, pressure sensors) that measure the force (the shear force, the pressure) that acts at prescribed locations on the member (10); and a control device that functions to assess the presence of abnormalities on the basis of output from the sensors (1)–(7). The control device functions: to determine a center-of-gravity point for the foot, a center-of-gravity line, an arch, and a bone axis for the foot; and to assess the presence of abnormalities by comparing the determined center-of-gravity point for the foot, center-of-gravity line, arch, and bone axis for the foot with normal data.

Description

Foot abnormality analysis apparatus and method

The present invention relates to a system and method for analyzing an abnormality in a human foot and leg (referred to herein as “foot”).

By measuring the pressure acting on a specific part of the human foot and identifying the so-called “foot pressure distribution”, the position where the most load is applied on the sole is estimated, and knee osteoarthritis and hallux valgus Risk assessment.
Here, there are various types of abnormalities of legs and legs other than knee osteoarthritis and hallux valgus. However, in the prior art, abnormalities that cannot be determined only by foot pressure distribution such as knee osteoarthritis and hallux valgus cannot be determined.
Parameters other than the foot pressure distribution are necessary to determine such an abnormality (an abnormality that cannot be determined only by the foot pressure distribution), but such a parameter has not been proposed in the past.
As another conventional technique, there is a technique for evaluating walking ability using a seat-type pressure sensor (see Patent Document 1). However, the related art (Patent Document 1) requires a large area for installing the seat type pressure sensor, and cannot be applied to a technique for determining various diseases.

JP 2014-94070 A

The present invention has been proposed in view of the above-described problems of the prior art, and is a foot abnormality analyzer that can analyze an abnormality of a foot that cannot be determined only by a foot pressure distribution. And to provide a method.

The foot abnormality analysis apparatus (100) of the present invention includes a member (10: for example, an insole or a shoe) with which the sole of the foot contacts, and a predetermined position (L (1), R (1 in FIG. 1) of the member (10). ), L (2), R (2)... L (7), R (7): Sensors for measuring forces (shearing force, pressure) acting on (1) to (7) in FIG. (1-7: shear force sensor, pressure sensor) and a control device (20) having a function of determining the presence or absence of abnormality based on the output from the sensors ((1)-(7)). It is a feature.
In the present invention, the control device (20) is determined to have a function of determining a center of gravity point, a center of gravity line, an arch, and a bone axis of the foot based on outputs from the sensors (1) to (7). It is preferable that the center of gravity of the foot, the center of gravity line, the arch, and the bone axis of the foot are compared with normal data to determine whether or not there is an abnormality.

According to the foot abnormality analysis method of the present invention, a predetermined position (L (1), R (1), L (2), R (2) in FIG. )... L (7), R (7): a step of measuring the force (shear force, pressure) acting on (1) to (7) in FIG. 2 with a sensor (shear force sensor, pressure sensor) When,
It has the process of determining the presence or absence of abnormality based on the output from the said sensor.
In the present invention, based on the output from the sensor, determining the center of gravity of the foot, the center of gravity line, the arch, the bone axis of the foot;
It is preferable to include a step of comparing the determined foot center of gravity point, center of gravity line, arch, and foot bone axis with normal data to determine whether there is an abnormality.

In the present invention, the sensor includes a rib raised portion (position 1), a cubic bone (position 2), a fifth metatarsal head (position 3) of a member (10: for example, insole, shoe) with which the sole of the foot contacts. The first metatarsal head (position 5), the intermediate wedge bone (position 6), and the lateral foot arch center (position 7) are preferably provided.

In the present invention, it is preferable that the sensor is also provided on the thumb contact surface (position 4).
In the present invention, the rib raised portion (position 1), the cubic bone (position 2), the fifth metatarsal head (position 3), the thumb contact surface (position 4), the first metatarsal head (position 5), the middle The sensors 1 to 7 provided at positions corresponding to the wedge bone (position 6) and the lateral foot arch center (position 7) preferably have a function of wirelessly transmitting the output to the control device.

In carrying out the present invention, the position rib ridge (position 1), the cubic bone (position 2), the fifth metatarsal head (position 3), the first metatarsal head (position 5), the lateral foot arch center (position 7). ) Is preferably a shear force sensor.

According to the foot abnormality analyzing apparatus (100) and the foot abnormality analyzing method of the present invention having the above-described configuration, the center of gravity point of the foot, the arch, and the bone axis of the foot are determined, and the locus of the center of gravity point of the foot is determined. By obtaining a certain “foot barycentric line” and comparing it with normal data, it is possible to determine whether there are various abnormalities (abnormalities other than knee osteoarthritis and hallux phalanges) that cannot be determined by the foot pressure distribution alone. Can be judged. Then, it is possible to propose a device or exercise that corrects or suppresses the abnormality. In particular, at the stage of growth like elementary school students and junior high school students, there is a high possibility that various abnormalities will be resolved and the normal state will be obtained by the exercise and equipment described above.
In other words, according to the present invention, as parameters for determining various abnormalities other than knee osteoarthritis and hallux valgus, parameters other than the foot pressure distribution such as the center of gravity line of the foot, the arch, and the bone axis of the foot are used. Yes.

In the present invention, the sensor includes the rib raised portion (position 1), the cubic bone (position 2), the fifth metatarsal head (position 3), the first metatarsal head (position 5), and the intermediate wedge bone (position 6). If provided at a position corresponding to the center of the lateral foot arch (position 7), the center of gravity of the foot, the arch, and the bone axis of the foot can be accurately determined.
Then, the “foot barycentric line” that is the trajectory of the barycentric point can be easily obtained.

And according to this invention, since the sensor is provided in the member (10) which contacts the soles, such as shoes or soles which contact a test subject's leg | foot, the structure which contacts a test subject can be reduced in size.
Therefore, it does not give extra stress to the person being measured like a large-sized device, and therefore accurate measurement is possible. In addition, if the device is downsized, it is possible to directly measure the force (shearing force or pressure) acting on the above-described position while exercising (for example, during walking). Unlike the prior art, it is not necessary to estimate the sole pressure during walking from the sole pressure in a stationary state.
In particular, if the sensor output is wirelessly transmitted to the control device (20) in the present invention, analysis of movement during exercise is easily performed.

Here, when the pressure value on the thumb contact surface (position 4) is large, it means that the toes are used effectively during walking and the force to kick the ground is large. That is, if the pressure value on the thumb contact surface (position 4) is large, it means that the toes are used effectively during walking and the force to kick the ground is large. Therefore, if other conditions are the same, when the pressure value on the thumb contact surface (position 4) is large, the stride is large, the walking speed is fast, and the clearance (distance between the toe and the contact surface) is also large. Become. Therefore, walking is stable and there is little risk of falls during walking.
In the present invention, if a sensor is provided on the thumb contact surface (position 4), it is possible to determine the walking function in addition to the abnormality of the foot and determine the possibility of falling during walking.

It is an explanation top view of a sole measuring device concerning an embodiment of the present invention. It is a figure which shows the skeleton of a human foot part. It is explanatory drawing which shows the arch of a leg | foot. It is explanatory drawing which shows the reason for using a shear force sensor. It is a figure which shows an example which the bone | frame above the collar is deform | transforming. It is a block diagram which shows an example of the control apparatus used by embodiment of this invention. It is a flowchart which shows an example of the process in 1st Embodiment of this invention. It is a flowchart which shows an example of the process in 2nd Embodiment of this invention. It is a flowchart which shows an example of the process in 3rd Embodiment of this invention. It is a flowchart which shows an example of the process in 4th Embodiment of this invention.

Embodiments of the present invention will be described below with reference to the accompanying drawings.
FIG. 1 shows an overview of an embodiment of the present invention.
The analysis apparatus of the present invention according to the embodiment is generally indicated by reference numeral 100 in FIG. 1, and includes an insole 10 (or shoes) that is a member that contacts the sole of the foot, a control device 20, a display device 30, And a determination device 40.
The insole 10 (or shoes) is composed of an insole 10R for the right foot and an insole 10L for the left foot, and in each of the insole 10R, 10L, seven predetermined positions (R1) to (R7), (L1) to (L7). ) Are provided with sensors R1 to R7 and L1 to L7. In FIG. 1, the “predetermined position” or the “sensor” installed at the predetermined position is represented by the same reference numeral, and is indicated by reference numerals (R1) to (R7) and (L1) to (L7), respectively. ing.

The measurement results by the sensors R1 to R7 and L1 to L7 are transmitted to the control device 20 by radio. In FIG. 1, on behalf of each sensor, an aspect in which measurement results are wirelessly transmitted from the sensors R1 and L1 to the control device 20 is indicated by arrows SR1 and SL1 (wireless signal lines).
It should be noted that when the respective measurement results are transmitted from the sensors R1 to R7 and L1 to L7 to the control device 20, it is also possible to use a wired connection.

The analysis result by the control device 20 is transmitted to the display device 30 via the information signal line IL9.
The result (analysis result) processed by the control device 20 is transmitted to the determination device 40 via the information signal line IL10, and the image data of the display device 30 is also transmitted to the determination device 40 via the information signal line IL12. .
The determination device 40 determines and presents the necessary countermeasure content based on the analysis result of the control device 20 and the image data of the display device 30.

Next, the installation positions of the sensors R1 to R7 and L1 to L7 will be described with reference to FIG.
FIG. 2 shows the right foot (the position of the sensors (1) to (7) in the insole 10R for the right foot or the shoe), but the position of the sensor in the insole 10L (or the shoe) for the left foot or the left foot is shown in FIG. It is a position symmetrical to the position indicated by.
The positions of the sensors 1 to 7 (sensors R1 to R7, which are hereinafter referred to as “sensors 1 to 7” for the sake of simplicity) are defined from the skeleton structure of the side of the human foot. Therefore, FIG. 2 shows the skeleton of the right foot.

The position where the sensor 1 is disposed (indicated by reference numeral (1) in FIG. 2) is the rib bulge. More preferably, position (1) is the center of the heel bone.
In determining the position (1), when the rib bulge is displaced outward (the fifth metatarsal side, that is, the little finger side in FIG. 2), the amount (the amount displaced outward) is measured. The position is set as possible. Normally, if the rib bulge is displaced, it is on the outside of the foot (the little finger side) and does not come off the inside of the foot (the first metatarsal side, that is, the thumb side in FIG. 2).
The position where the sensor 2 is arranged (the position indicated by the reference numeral (2) in FIG. 2) is a position corresponding to the cubic bone. However, it may be slightly outside the center of the cubic bone (the little finger side: the region of the fifth metatarsal bone).

The position where the sensor 3 is disposed (indicated by reference numeral (3) in FIG. 2) is a position corresponding to the fifth metatarsal head.
In order to analyze the state at the time of walking, it is necessary to measure the force acting on the “location where weight is applied during walking”. The fifth metatarsal head, which is the root of the fifth metatarsal, is a “location where weight is applied during walking”.
Here, even if the position where the sensor 3 is arranged is shifted to about ３ of the length of the fifth metatarsal head and to the side opposite to the toes, the force acting on “the place where weight is applied during walking” can be measured. So there is no problem.
However, since the fifth peripheral bone (toe side bone) does not bear weight, it is inconvenient to attach the sensor to a position shifted to the fifth peripheral bone side (toe side) from the fifth metatarsal head.

The position at which the sensor 4 is disposed (indicated by reference numeral (4) in FIG. 2) is a region that reaches the ground when walking on the thumb contact surface, that is, the tip of the thumb. The reason for arranging the sensor 4 at the position (4) is that it is necessary to measure the force acting on the position (4) in order to obtain the kicking strength during walking.
Here, there is an individual difference as to which part of the thumb of the toe the bone (first talus bone) extends. Therefore, the position (4) is not specified by the name of the bone, but is specified as the “finger ground contact surface” as described above.
If the position of the sensor 4 deviates from the thumb contact surface, it is inconvenient because the strength of kicking out during walking cannot be measured.
As will be described later, the measurement results of the sensor 4 arranged at the position (4) are not used to specify (determine) the “foot bone axis”, “arch”, and “center of gravity”.

The position where the sensor 5 is disposed (indicated by reference numeral (5) in FIG. 2) is a position corresponding to the first metatarsal head.
It is the so-called “thumb ball” part of the first metatarsal side that weighs during walking. For this reason, it is necessary to prevent the sensor 5 from being attached to the “finger ball”. This is because the ball ball takes weight.

The position where the sensor 6 is disposed (the position indicated by reference numeral (6) in FIG. 2) is a position corresponding to the intermediate wedge bone.
The position where the sensor 6 is arranged is sandwiched between a straight line Lα connecting the second finger (index finger) from the position (1) where the sensor 1 is arranged and a straight line Lβ connecting the fourth finger (ring finger) from the position (1). What is necessary is just the area of three wedge-shaped bones in the area.
Here, it is inconvenient to install the sensor 6 because the region closer to the thumb than the straight line Lα connecting the position (1) and the second finger (index finger) may become an arch. On the other hand, since the region on the little finger side of the straight line Lβ connecting the position (1) and the fourth finger (ringing finger) may overlap with the position (2), it is also inconvenient to install the sensor 6. It is. For these reasons, the arrangement position of the sensor 6 is determined as described above.

As shown in FIG. 3, there are three types of foot arches: a longitudinal arch AR1, an outer arch AR2, and a lateral arch AR3. The longitudinal arch AR1 extends from the vicinity of the position (1) representing the rib bulge in FIG. 2 to the vicinity of the position (5) representing the first metatarsal head, and the outer arch AR2 is the heel in FIG. It extends from the vicinity of the position (1) representing the bone protuberance to the vicinity of the position (3) representing the fifth metatarsal head. Further, the lateral arch AR3 extends from the vicinity of the position (5) representing the first metatarsal head in FIG. 2 to the vicinity of the position (3) representing the fifth metatarsal head. The arches AR1 to AR3 can absorb the impact on the sole when walking.
In order to specify the foot arch, it is necessary to refer to the measurement results at positions other than the positions (2) and (6) (for example, the positions (1) and (3)).
Also, from the measurement results of position (6) and position (2) (and other measurement results of positions (1), (3), etc.), the center of gravity (the pressure center of the sole at the moment: the center of gravity of the center of gravity) The trajectory can be specified (determined).

From the measurement result of the force (pressure, shear force) acting on the position (6) measured by the sensor 6 and the measurement result of the force (pressure, shear force) acting on the position (2) measured by the sensor 2, Three types of “flat feet”, “normal”, and “high arch” can be determined.
Measurement results of force (pressure or shear force) acting at position (6) and force (pressure or shear force) acting at position (2) in each of “flat foot”, “normal”, and “high arch” The magnitude relationship of the results is different. That is,
Flat feet: force acting on position (2) ≒ force acting on position (6), or
Force acting on position (2) ≦ force acting on position (6) Normal: force acting on position (2)> force acting on position (6) High arch: force acting on position (2), position (6 The force acting on) is not detected.
This will be described later with reference to FIG.

In FIG. 2, the position where the sensor 7 is disposed (indicated by (7) in FIG. 2) is the second metatarsal head (the base portion of the second finger (index finger)) and the third metatarsal head (the third finger ( It is located in the area between the base part of the middle finger).
Here, the barycentric line passes along a line (line Lα in FIG. 2) connecting the heel and the second finger. For this reason, it is inconvenient to provide the sensor 7 in a region closer to the first finger (thumb side) than the second finger.
On the other hand, the region closer to the little finger than the third finger (middle finger) deviates from the barycentric line, so it is inconvenient to provide the sensor 7. Since the weight is on the inner side of the center line of the foot, if the position (7) of the sensor 7 is on the outer side of the center line of the foot, the weighted state cannot be detected.

According to the illustrated embodiment, the sensors 1 to 7 arranged at the positions (1) to (7) described above are used to measure the force acting on the position, thereby standing in a predetermined position of the measuring device. Not only measurement but also walking measurement.
Items that can be found by measuring the forces acting on the positions (1) to (7) and analyzing them by the control device 20 are exemplified below (in addition to specifying the type of arch).
First, since there are individual differences in foot flexibility, there are also individual differences in the flexibility of the arch shown in FIG.
By analyzing the measurement results at the positions (2), (6), and (7), the flexibility of the arch can be understood. Depending on the flexibility of the arch, a “high arch” when standing still may result in a “flat foot” when walking (when the arch is soft). Alternatively, there is a case of “normal” when standing and stationary, but a “high arch” when walking (when the arch is hard).

As will be described later with reference to FIG. 7, by analyzing the measurement results at positions (2), (6), and (7), the center of gravity (the pressure center of the sole at the moment) and the arch shape are appropriately I understand.
Here, when the force acting on the positions (2), (6), (7) is not measured, for example, when only the force acting on the positions (1), (3), (5) is measured, It is impossible to identify the arch.
In the illustrated embodiment, by measuring the forces acting on the positions (2), (6), (7) in addition to the forces acting on the positions (1), (3), (5), It enables identification. That is, the vertical arch AR1 and the outer arch AR2 can be determined from the measurement results of the positions (2) and (6), and the state of the arch can be grasped from the vertical arch AR1. Further, the lateral arch AR3 can be specified based on the measurement results at the positions (3), (7), and (5). In other words, the measurement result of the position (7) is indispensable for determining the lateral arch AR3.

Next, regarding the specification of the center of gravity line, conventionally, pressure sensors are installed only at the positions (1), (3), and (5), and the load distribution at the positions (1), (3), and (5) on the foot is The center of gravity point was specified on the assumption that the ratio was 3: 1: 2.
However, in the illustrated embodiment, sensors (sensors 2, 6, 7) are also installed at positions (2), (6), (7). The force (pressure, shear force) acting on the positions (2), (6), and (7) is also measured to accurately determine the center of gravity (COP), and the center of gravity line that is the locus is accurately specified. ing. This point will also be described later with reference to FIG.

Here, the “foot bone axis” will be described.
The “foot bone axis” is an axis that penetrates the position (1) representing the rib bulge and the talus, and shear force is applied to the positions (1), (2), (3), (5), and (7). By providing the sensors 1, 2, 3, 5, and 7 and analyzing the measurement result, it is possible to accurately grasp the movement in the “foot bone axis”. This will also be described later with reference to FIG.
Positions (1), (2), (3), (5), and (7) are parts that move greatly at the bottom of the foot, so when the shear force of these five parts is obtained, the movement of the “bone axis of the foot” is analyzed. easy. By analyzing the shear force at positions (1), (2), (3), (5), and (7) and analyzing the motion of the “bone axis of the foot”, the displacement of the ribs and the like while walking Speed, force (change in load), direction, twist, etc. can be evaluated.
Further, the movement of the foot bone axis depends on the flexibility of the joint of the sole.

It is preferable to arrange a “shear force sensor” in place of the pressure sensor at the positions (1), (2), (3), (5), and (7). The reason will be described with reference to FIG.
In order to measure the force acting on the positions (1), (2), (3), (5), and (7) and perform the above-described analysis, in FIG. 4 (A), the force acting axis SH1 It is necessary to measure the force indicated by the arrow AH at the lower end (including the force in the direction perpendicular to the paper surface). Therefore, it is preferable to install a shear force sensor capable of measuring such force at the positions (1), (2), (3), (5), and (7).
As shown in FIG. 4B, the pressure sensor can only measure the vertical load (reference symbol P) of the vertical axis SH2. Therefore, it is inconvenient to measure the force acting on the positions (1), (2), (3), (5), (7).

As described above, by analyzing the measurement results of the shear force acting on the positions (1), (2), (3), (5), (7), the movement of the “foot bone axis” can be accurately performed. I can grasp it. For example, it can be determined from the bone axis of the foot whether or not the bone of the heel is valgus.
For example, when the arch is hard and the bone axis of the foot does not move inward, a load is applied to the positions (2) and (3), the knee is twisted during walking (pronation moment is generated), and in the future There is a risk of complaining of knee pain in a so-called “knee rub” condition. On the other hand, in the illustrated embodiment, it is possible to determine whether or not there is a risk of knee pain by measuring whether or not a load is applied to the positions (2) and (3). This will also be described later with reference to FIG.

In FIG. 5 showing an example of the state above the heel, reference lines L5L and L5R represent the central axis (indicated by a broken line) of the leg L that is continuous with the bone axis of the foot F (indicated by a solid line). As shown by the reference lines L5L and L5R, when the heel is bent (extroverted), the heel is hard (the range of motion of the joint around the heel is limited) and bent outward (little finger side). Therefore, the value of the shear force at the position (1) is small. In the case as shown in FIG. 5 (a state where the heel is hard and does not bend outward), stress may be applied to the knee and pain may develop.
In such a case, in the shoe or insole, the movement of the heel can be restricted by adjusting the height of the outside of the shoe, the height of the inside of the shoe, or the height of the heel itself, and it can be brought close to the normal center of gravity line. . Therefore, knee pain is also reduced. This will be described later with reference to FIG.

Here, the value of the pressure at the position (4) has no relation to the specification of the arch, the bone axis of the leg, and the center of gravity line.
When the pressure value at the position (4) is large, it means that the toes are used effectively during walking and the force to kick the ground is large. In other words, if the toes are used effectively during walking, and the force to kick the ground is large, if the other conditions are the same, the stride is large, the walking speed is high, and the clearance (toe and ground contact surface during walking) The distance to the is also large. Therefore, walking is stable and there is little risk of falls during walking.
In other words, the measurement result of the position (4) is used for determining the walking function and determining the possibility of falling during walking.

The configuration and function (action) of the control device 20 shown in FIG. 1 will be described with reference to FIGS.
In FIG. 6 which shows the functional block of the control apparatus 20 preferably used in the illustrated embodiment, the control apparatus 20 (the part surrounded by a broken line) determines the center-of-gravity point determination block 20A and the center-of-gravity line which is the locus of the center-of-gravity point. A centroid line determination block 20B, an arch determination block 20C, a bone axis determination block 20D, a determination block 20E, and a storage block 20F. Reference numerals 20I and 20O in FIG. 6 indicate an input side interface and an output side interface, respectively.
As described with reference to FIG. 1, the control device 20 is connected to the display device 30 and the determination device 40 by the information signal lines IL9 and IL10.

The center-of-gravity point determination block 20A includes measurement signals (positions (1), (2), (3), (7)) from the sensors 1, 2, 3, 5, 6, and 7 via the input-side interface 20I and the information signal line IL1. 5), (6), and (7) are received (measurement results of pressure or shear force) and have a function of obtaining the center of gravity (COP).
Information on the center of gravity point (the pressure center of the sole at the moment) determined by the center of gravity point determination block 20A is transmitted to the center of gravity line determination block 20B via the information signal line IL2.
When the center-of-gravity point determination block 20A determines the center-of-gravity point (COP), it is determined on a case-by-case basis using conventionally known software technology and taking into account the characteristics of the person being measured. The same applies to the center-of-gravity line determination block 20B, the arch determination block 20C, and the bone axis determination block 20D described later.

The barycentric line determination block 20B has a function of receiving the barycentric point (COP) information from the barycentric point determining block 20A via the information signal line IL2 and determining the barycentric line that is the locus of the barycentric point.
Information on the centroid line determined by the centroid line determination block 20B is transmitted to the determination block 20E via the information signal line IL3.

The arch determination block 20C receives measurement signals (positions (1), (2), (3), (7)) from the sensors 1, 2, 3, 5, 6, and 7 via the input-side interface 20I and the information signal line IL4. 5), (6), and (7) pressure and shear force measurement values) are received, and an arch is determined based thereon.
In the arch determination block 20C, the positions and shapes of the vertical arch AR1, the outer arch AR2, and the horizontal arch AR3 constituting the arch are specified, and the arch is determined.
Information on the vertical arch AR1, the outer arch AR2, and the horizontal arch AR3 determined by the arch determination block 20C is transmitted to the determination block 20E via the information signal line IL5.

The bone axis determination block 20D receives measurement signals (positions (1), (2), (3), (5)) from the sensors 1, 2, 3, 5, 7 via the input side interface 20I and the information signal line IL6. , (7) (measurement values of pressure and shear force), and the movement of the bone axis of the foot is grasped to determine the bone axis of the foot.
Information on the bone axis of the foot determined by the bone axis determination block 20D is transmitted to the determination block 20E via the information signal line IL7.

The memory block 20F stores data (normal values) when the center of gravity point, the center of gravity line, the arch, and the bone axis of the foot are considered as “normal” (normal value). The normal value data is stored in the information signal line IL8. To the determination block 20E, and is referred to in the determination by the determination block 20E.
In addition to the normal value data, the storage block 20F stores a threshold value of the load acting on the positions (2) and (3), a threshold value of the shearing force applied to the position (1), and the like. .
Here, the threshold value of the load acting on the positions (2) and (3) is used to determine the hardness (flexibility) of the arch in the determination block 20E. Then, the threshold value of the shearing force applied to the position (1) is used in the determination block 20E to determine whether or not the heel is valgus.

The determination block 20E has a function of determining whether or not the centroid line determined by the centroid line determination block 20B is normal compared to the normal value data (received from the storage block 20F) of the centroid line, and the centroid line is not normal. In this case, it has a function of determining how abnormal it is (how much it deviates from the normal state) (see steps S2 and S3 in FIG. 7).
The determination result of the determination block 20E is transmitted to the display device 30 via the output side interface 20O and the information signal line IL9. At the same time, the data is transmitted to the determination device 40 via the output side interface 20O and the information signal line IL10.

Further, the determination block 20E determines whether or not the arches (vertical arch AR1, outer arch AR2, lateral arch AR3) determined by the arch determination block 20C are normal compared to the normal value data (received from the storage block 20F) of the arch. And a function for determining how abnormal the arch is when it is not normal (how much it is deformed compared to a normal arch) (step S2, FIG. 7). (See S3).
Then, the determination block 20E compares the measured value of the load applied to the positions (2) and (3) side with the threshold value of the load (received from the storage block 20F) to determine the hardness (flexibility) of the arch. It has a function to judge. This function will be described later with reference to FIG.
Further, the determination block 20E compares the measurement value of the force acting on the position (2) with the measurement value of the force acting on the position (6) to determine the type of arch (“flat foot”, “normal”, “high arch”). It has the function to judge. This function will be described later with reference to FIG.
The determination result relating to the arch by the determination block 20E is transmitted to the display device 30 via the output side interface 20O and the information signal line IL9. At the same time, the data is transmitted to the determination device 40 via the output side interface 20O and the information signal line IL10.

The determination block 20E has a function of determining whether or not the bone axis of the foot determined by the bone axis determination block 20D is normal compared to the normal value data (received from the storage block 20F) of the bone axis, and the bone of the foot When the axis is not normal, it has a function of determining the extent of the abnormality (how much the foot bone axis is deformed compared to the normal case) (steps S2 and S3 in FIG. 7). reference).
In addition, the determination block 20E compares the measured value of the shear force applied to the position (1) with the threshold value of the shear force (received from the storage block 20F) for determining whether or not the heel is valgus. Thus, it has a function of determining whether or not the heel is valgus. This function will be described later with reference to FIG.
The determination result regarding the bone axis by the determination block 20E is transmitted to the display device 30 via the output side interface 20O and the information signal line IL9. At the same time, the data is transmitted to the determination device 40 via the output side interface 20O and the information signal line IL10.
When the control described later with reference to FIGS. 8, 9, and 10 is performed, measurement signals from the sensors 1, 2, 3, 5, 6, and 7 are transmitted via the input side interface 20I and the information signal line IL11. Is transmitted to the determination block 20E. In other words, in the control to be described later with reference to FIGS. 8, 9, and 10, the measurement signals from the sensors 1, 2, 3, 5, 6, and 7 are the center-of-gravity point determination block 20A, the center-of-gravity line determination block 20B, The arch determination block 20C and the bone axis determination block 20D are not routed.

The display device 30 has a function of displaying the determination result transmitted from the control device 20 (determination block 20E).
Specifically, “whether the subject's center of gravity is normal”, “how abnormal if the center of gravity is not normal”, “whether the subject's arch (vertical arch, outer arch, lateral arch) is normal ”,“ How abnormal is the arch when it is not normal ”,“ Is the subject's foot bone axis normal or not ”,“ How much is abnormal when the foot bone axis is not normal ” Display including data.
In addition, the display device 30 has, as the determination result of the control device 20 (determination block 20E), "arch hardness (flexibility)", "arch type (flat feet, normal, high arch)", Whether or not "is displayed including image data.
As described above, the display device 30 transmits the image data to the determination device 40 via the information signal line IL12.

The determination device 40 receives the determination result transmitted from the control device 20 (determination block 20E) and the image data transmitted from the display device 30, and based on these, the determination result is “not normal”. It has a function of presenting exercises, appliances, etc. for improving it (see FIGS. 7 to 10).
The determination by the determination device 40 is performed on a case-by-case basis using a conventionally known software technique in consideration of the characteristics of the person to be measured.
The determination device 40 is an information processing device such as a computer, but is not limited thereto. For example, a case where an expert or an operator who has medical knowledge makes a necessary determination or presentation for improvement based on information and data from the control device 20 or the display device 30 is also included.
The determination result of the determination device 40 is fed back to the analysis device 20 through the information signal line IL40. In FIG. 6, the information signal line IL40 is displayed connected to the storage block 20F, but the determination result of the determination device 40 is not fed back only to the storage block 20F, and for all functional blocks in the analysis device 20 Thus, the determination result of the determination device 40 is fed back.

An example of the foot abnormality analysis according to the first embodiment of the present invention will be described mainly with reference to FIG.
The flow chart of FIG. 7 measures the force acting on the positions (1), (2), (3), (5), (6), (7), and the center of gravity (the center of pressure on the sole) from the measurement result. ), Centroid line, arch, and bone axis of the foot are determined, whether the centroid line, arch, and bone axis of the foot are normal or not, exercise to suppress abnormalities, and control to design and determine the equipment used are shown ing.
In FIG. 7, in step S1, the force acting on the positions (1), (2), (3), (5), (6), (7) by the sensors 1, 2, 3, 5, 6, 7 is applied. measure. Then, the process proceeds to step S2.

In step S2, the force (pressure, shear) acting on the position (1), (2), (3), (5), (6), (7) of step S1 in the barycentric point determination block 20A (FIG. 6). Based on the measurement result of the force), the center of gravity point (center of pressure on the sole) is determined, and further, the center of gravity line that is the locus of the center of gravity point is determined in the center of gravity line determination block 20B (FIG. 6).
In step S2, the measurement result of the force acting on the position (1), (2), (3), (5), (6), (7) of step S1 in the arch determination block 20C (FIG. 6). Further, in step S2, in the bone axis determination block 20D (FIG. 6), positions (1), (2), (3), Based on the measurement results of the forces acting on (5) and (7), the bone axis of the foot is determined.

Next, in step S3, the center of gravity line, the arch (vertical arch AR1, outer arch AR2, lateral arch AR3), and the bone axis of the foot determined in step S2 are stored in the normal center of gravity stored in the storage block 20F (FIG. 6). Compared with the data of the line, arch, and bone axis, it is determined whether or not the subject's center of gravity line, arch, and bone axis are normal based on the comparison result, and if abnormal, the degree of abnormality is determined.
In step S4, if any of the subject's center of gravity line, arch, or bone axis is determined to be abnormal in step S3, design and determine a suitable exercise, equipment used, etc. to suppress and improve the abnormality, Present. And control is complete | finished.

An example of the foot abnormality analysis according to the second embodiment of the present invention will be described mainly with reference to FIG.
As described above with reference to FIG. 3, from the measurement result of the force acting on the position (6) and the position (2), the types related to the arch of the subject are “flat feet” and “normal” in relation to the vertical arch AR1. And “High Arch”. here,
Force acting on position (2) ≈force acting on position (6), or
If the force acting on the position (2) ≦ the force acting on the position (6), the subject is a flat foot,
If the force acting on position (2)> the force acting on position (6), the subject is a “normal” foot that is neither a flat foot nor a high arch,
If neither a force acting on position (2) nor a force acting on position (6) is detected, the subject is classified as “high arch”.
FIG. 8 shows control (processing) for determination using such a relationship.

In FIG. 8, in step S <b> 11, forces (for example, pressure and shear force) acting on the positions (2) and (6) are measured by the sensors 2 and 6. Then, the process proceeds to step S12.
In step S12, the force acting on the position (2) measured in step S11 is compared with the magnitude of the force acting on the position (6), and the force acting on the position (2) acts on the position (6). It is judged whether or not it is greater than the force to be applied.
As a result of the comparison in step S12, when the force acting on the position (2) is larger than the force acting on the position (6) (step S12 is “Yes”), the process proceeds to step S13.
In step S13, the subject's arch does not correspond to a flat foot or a high arch, and is determined to be “normal”, and the control is terminated.

As a result of the comparison in step S12, the force acting on the position (2) is substantially equal to the force acting on the position (6), or the force acting on the position (2) is smaller than the force acting on the position (6). In the case (when step S12 is “No (position (2) ≦ position (6))”), the process proceeds to step S14.
In step S14, it is determined that the subject's arch corresponds to a “flat foot”. In this case, in the determination apparatus 40 (FIG. 6), it is possible to present a device such as forming an arch on the insole (providing a device for improving flat feet).
As a result of the comparison in step S12, when neither the force acting on the position (2) nor the force acting on the position (6) is detected (step S12 is “No (position (2), position (6) is detected). Z) ”), the process proceeds to step S15.
In step S15, it is determined that the subject's arch corresponds to the “high arch”, and the control is terminated.
Although not shown in FIG. 8, in various determinations related to the arch, other positions (1), (3), (5), (7) other than (2) and (6) as necessary. It is necessary to refer to the measurement results of the force (pressure, shear force) acting on The same applies to the control of FIGS. 9 and 10 described later.

An example of the foot abnormality analysis according to the third embodiment of the present invention will be described mainly with reference to FIG.
As mentioned above, when the arch is stiff and the bone axis of the foot does not move inward, a large load is applied to the positions (2) and (3), and the knee is twisted during walking (pronation moment occurs) In the future, there is a risk of complaining of knee pain in a so-called “knee rub” condition.
The flowchart in FIG. 9 determines whether or not there is such a fear. Therefore, the force acting on the positions (2) and (3) is measured, and if the measured force is large, a determination such as “the arch is hard and the knee may be twisted during walking” is performed. At the same time, a device for exercise and use for suppressing “twisting the knee while walking (pronation moment occurs)” is presented.

In FIG. 9, in step S <b> 21, forces (pressure, shear force) acting on the positions (2) and (3) are measured by the sensors 2 and 3. Then, the process proceeds to step S22.
In step S22, it is determined whether a large load is applied to the positions (2) and (3) based on the forces acting on the positions (2) and (3) measured in step S21. Such determination is based on, for example, measurement results of forces acting on the positions (2) and (3), various data when the knee is twisted during walking (pronation moment is generated), and measurement data of the subject. This is performed by comparing with a comprehensively determined threshold value.
If it is determined in step S22 that a large load (to be dealt with) is applied to the positions (2) and (3) (step S22 is “Yes”), the process proceeds to step S23.
On the other hand, when it is determined in step S22 that a large load (which should be dealt with) is not applied to the positions (2) and (3) (step S22 is “No”), the control is terminated.

In step S23 (when it is determined that a large load (which should be dealt with) is applied to the positions (2) and (3)), “the arch is stiff and the bone axis of the foot does not move inward (therefore, the O leg It makes me feel and my legs bend outward). Then, the process proceeds to step S24.
In step S24, the subject is determined that the knee is twisted (pronunciation moment is generated during walking) at present or in the future, so that the subject is in a so-called “knee rub” state in the future. There is a risk of complaining of knee pain. "
Then, the process proceeds to step S25.

In step S25, an improvement measure or a countermeasure for the case where the knee is twisted (pronation moment occurs) during walking and there is a risk of complaining of knee pain in a so-called “knee rubbing” state in the future is presented. .
For example, in order to prevent knee torsion (occurrence of pronation moment) during walking and prevent future knee pain, the foot bone axis is easily moved inward or the foot bone axis is outside. Presenting a gymnastics to restrain the movement and encourage the movement to the inside. For example, in a shoe or an insole, by adjusting the height of the outer side of the shoe, the height of the inner side, or the height of the heel itself, the movement of the heel can be limited and brought close to a normal center of gravity line. Therefore, knee pain is also reduced.
About step S25, the case where not only an information processing apparatus but an expert receives the determination result of step S23, S24 and presents is included.

An example of the foot abnormality analysis according to the fourth embodiment of the present invention will be described mainly with reference to FIG.
As shown in FIG. 5, when the heel is bent (turned outward), the heel is hard and does not bend outward (the little finger side), so the numerical value of the shear force at the position (1) becomes small.
In the flowchart of FIG. 10, the shearing force acting on the position (1) is measured, and when the shearing force is small, it is determined that “the heel is bent (turned outward) and the heel does not bend outward”. Then, it presents gymnastics and appliances to suppress it.

In FIG. 10, in step S31, the shear force acting on the position (1) is measured by the sensor 1. Then, the process proceeds to step S32.
In step S32, it is determined whether or not the shear force acting on the position (1) measured in step S31 is equal to or less than a threshold value N. Here, the threshold value N is comprehensively determined based on accumulated data relating to hallux valgus and measurement data of the subject.
If the shear force acting on the position (1) is equal to or less than the threshold value N in step S32 (step S32 is “Yes”), the process proceeds to step S33.
On the other hand, when the shearing force acting on the position (1) is larger than the threshold value N in step S32 (step S32 is “No”), the control is terminated.

Step S33 (when the shearing force acting on the position (1) is equal to or less than the threshold value N) is “the beard is bent (reversed), the beard is hard and does not bend outward (the little finger)”. It is judged as “state”. Then, the process proceeds to step S34.
Here, when the heel is hard and does not bend outward, stress may be applied to the knee and pain may develop. Therefore, in step S34, since the heel is hard and does not bend outward, an improvement measure or a coping method when the knee is stressed and there is a risk of developing pain is presented.
In step S34, for example, an insole or a shoe with a gap on the outside of the bag is presented. In the shoe or insole, by adjusting the height of the outside of the shoe, the height of the inside of the shoe, or the height of the heel itself, the movement of the heel can be limited and brought close to the normal center of gravity line. Therefore, knee pain is also reduced.

Although not illustrated, the embodiment of the illustrated embodiment can improve the hallux valgus.
When the hallux valgus or the tendency exists, a large load is applied to the position (7), and the ground is strongly kicked at the position (3). Therefore, the force of kicking the ground at the position (5) is suppressed, the shoes and the insole are devised so that the load related to the position (7) is appropriate, the device is proposed, or the ground at the position (5) is It is possible to propose an exercise program that suppresses the kicking force and makes the load related to the position (7) appropriate.

According to the foot abnormality analysis apparatus 100 and the foot abnormality analysis method according to the illustrated embodiment, the center of gravity point of the foot, the arch, and the bone axis of the foot are determined, ”And by comparing with normal data, it is possible to determine the presence or absence of various abnormalities (abnormalities other than knee osteoarthritis and hallux phalanges) that cannot be determined only by foot pressure distribution. Then, it is possible to propose a device or exercise that corrects or suppresses the abnormality. In particular, at the stage of growth like elementary school students and junior high school students, there is a high possibility that various abnormalities will be resolved and the normal state will be obtained by the exercise and equipment described above.
In other words, according to the embodiment, as parameters for determining various abnormalities other than knee osteoarthritis and hallux valgus, parameters other than foot pressure distribution such as foot center of gravity, arch, and foot bone axis are used. Yes.

In the illustrated embodiment, the sensors 1 to 7 are connected to a rib ridge (position 1), a cubic bone (position 2), a fifth metatarsal head (position 3), a first metatarsal head (position 5), and an intermediate wedge shape. Since it is provided at a position corresponding to the bone (position 6) and the lateral foot arch center (position 7), the center of gravity of the foot, the arch, and the bone axis of the foot can be accurately determined.
Then, the “foot barycentric line” that is the trajectory of the barycentric point can be easily obtained.

In the illustrated embodiment, since the sensors 1 to 7 are provided on the member 10 that contacts the sole of the foot such as a shoe or sole that contacts the foot of the subject, the configuration that contacts the subject can be reduced in size.
Therefore, it does not give extra stress to the person being measured like a large-sized device, and therefore accurate measurement is possible. In addition, if the device is downsized, it is possible to directly measure the force (shearing force or pressure) acting on the above-described position while exercising (for example, during walking). Unlike the prior art, it is not necessary to estimate the sole pressure during walking from the sole pressure in a stationary state.
In particular, in the illustrated embodiment, the outputs of the sensors 1 to 7 are transmitted wirelessly to the control device 20, so that the subject is exercising (for example, walking) compared to the case where the measurement result is transmitted by wire. ) Can be easily transmitted and analyzed easily.

Here, when the pressure value on the thumb contact surface (position 4) is large, it means that the toes are used effectively during walking and the force to kick the ground is large. That is, if the pressure value on the thumb contact surface (position 4) is large, it means that the toes are used effectively during walking and the force to kick the ground is large. Therefore, if other conditions are the same, when the pressure value on the thumb contact surface (position 4) is large, the stride is large, the walking speed is fast, and the clearance (distance between the toe and the contact surface) is also large. Become. Therefore, walking is stable and there is little risk of falls during walking.
In the illustrated embodiment, since the sensor 4 is provided on the thumb contact surface (position 4), the walking function can be determined in addition to the abnormality of the foot, and the possibility of falling during walking can be determined.

In the illustrated embodiment, it is possible to specify whether the subject corresponds to “flat foot”, “normal”, or “high arch” from the measurement values of the force acting on the position (6) and the position (2) (FIG. 8). ).
Furthermore, from the measured values of the force acting on the positions (2) and (3), it is possible to determine whether or not “the knee is twisted while walking because the arch is stiff”, and the exercise and equipment used Can also be presented (Fig. 9).
In addition, from the measured value of the shear force acting on the position (1), it is possible to determine whether or not “the heel is bent (valgus) and the heel does not bend outward”. Thus, it is possible to present an appliance to be used to suppress it (FIG. 10).

It should be noted that the illustrated embodiment is merely an example, and is not a description to limit the technical scope of the present invention.
For example, FIG. 5 shows the case of valgus, but the present invention can also deal with varus.

1 to 7 (R1 to R7, L1 to L7) ... Sensors (1) to (7), (R1) to (R7), (L1) to (L7) ... Sensor positions 10, 10R, 10L ..Insole (or shoes)
20 ... Control device 20A ... Center of gravity determination block 20B ... Center of gravity determination block 20C ... Arch determination block 20D ... Bone axis determination block 20E ... Determination block 20F ... Storage block 20I ... Input side interface 20O ... Output side interface 30 ... Display device 40 ... Determination device 100 ... Analysis device AR1 ... Vertical arch AR2 ... Outer arch AR3 ... Horizontal arch F ... Leg L ... Legs IL1 to IL12 ... Information signal lines SR1, SL1 ... Radio signal lines

Claims (10)

1. A member that contacts the sole of the foot; a sensor that measures a force acting on a predetermined position of the member (10); and a control device that has a function of determining whether there is an abnormality based on an output from the sensor. A foot anomaly analyzer characterized in that
2. The control device has a function of determining the center of gravity of the foot, the center of gravity line, the arch, and the bone axis of the foot based on the output from the sensor, and the determined center of gravity of the foot, the center of gravity line, the arch, and the bone axis of the foot The foot abnormality analysis apparatus according to claim 1, which has a function of determining whether or not there is an abnormality by comparing the data with normal data.
3. The sensor is provided at a position corresponding to a rib raised portion, a cubic bone, a fifth metatarsal head, a first metatarsal head, an intermediate wedge bone, and a lateral foot arch center of a member that contacts the sole of the foot. The foot abnormality analysis apparatus according to claim 1.
4. The foot abnormality analysis device according to claim 3, wherein the sensor is also provided on a thumb contact surface.
5. Sensors provided at positions corresponding to the rib raised portion, cubic bone, fifth metatarsal head, thumb contact surface, first metatarsal head, intermediate cuneiform bone, lateral foot arch center output its output to the control device. The foot abnormality analyzer according to any one of claims 1 to 4, which has a function of transmitting wirelessly.
6. A step of measuring with a sensor a force acting on a predetermined position in a member that contacts the sole of the foot;
   A foot abnormality analysis method comprising the step of determining the presence or absence of an abnormality based on an output from the sensor.
7. Determining the center of gravity of the foot, the center of gravity line, the arch, and the bone axis of the foot based on the output from the sensor;
   The foot abnormality analysis method according to claim 6, further comprising a step of comparing the determined center of gravity point, center of gravity line, arch, and bone axis of the foot with normal data to determine whether or not there is an abnormality.
8. The sensor is provided at a position corresponding to a rib raised portion, a cubic bone, a fifth metatarsal head, a first metatarsal head, an intermediate wedge bone, and a lateral foot arch center of a member that contacts the sole of the foot. The foot abnormality analysis method according to any one of claims 6 and 7.
9. The foot abnormality analysis method according to claim 8, wherein the sensor is also provided on a thumb contact surface.
10. Sensors provided at positions corresponding to the rib raised portion, cubic bone, fifth metatarsal head, thumb contact surface, first metatarsal head, intermediate cuneiform bone, lateral foot arch center output its output to the control device. 11. The foot abnormality analysis method according to claim 6, wherein the foot abnormality analysis method has a function of transmitting wirelessly.

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