WO2018110621A1 - Sole measurement device - Google Patents

Sole measurement device Download PDF

Info

Publication number
WO2018110621A1
WO2018110621A1 PCT/JP2017/044821 JP2017044821W WO2018110621A1 WO 2018110621 A1 WO2018110621 A1 WO 2018110621A1 JP 2017044821 W JP2017044821 W JP 2017044821W WO 2018110621 A1 WO2018110621 A1 WO 2018110621A1
Authority
WO
WIPO (PCT)
Prior art keywords
arch
foot
bone
sensor
center
Prior art date
Application number
PCT/JP2017/044821
Other languages
French (fr)
Japanese (ja)
Inventor
山下　和彦
英治 榎本
真澄 篠原
Original Assignee
Ａｏｆ株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Ａｏｆ株式会社 filed Critical Ａｏｆ株式会社
Publication of WO2018110621A1 publication Critical patent/WO2018110621A1/en

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/107—Measuring physical dimensions, e.g. size of the entire body or parts thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb

Definitions

  • the present invention relates to an apparatus for measuring a force (for example, pressure, shearing force) acting on a specific part of a human foot sole.
  • a force for example, pressure, shearing force
  • Patent Document 1 there is a technique for evaluating walking ability using a seat-type pressure sensor (see Patent Document 1).
  • Patent Document 1 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.
  • the present invention has been proposed in view of the above-described problems of the prior art, and has a function of reducing the size of a measuring device and acting on a specific part of a human foot sole while in motion (for example, while walking).
  • An object of the present invention is to provide a sole measuring device that can measure a force (for example, pressure, shearing force) to be performed and can determine parameters other than a foot pressure distribution.
  • the sole measuring device (100) of the present invention includes a rib raised portion (position 1), a cubic bone (position 2), and a fifth metatarsal head (10 Position 3), first metatarsal head (position 5), intermediate wedge bone (position 6), positions corresponding to the lateral foot arch center (position 7) (L (1), R (1), L ( 2), R (2)... L (7), R (7): (1) to (7) in FIG. 2 are provided with sensors (shear force sensors, pressure sensors). .
  • the outputs of the sensors 1 to 7 provided at the positions corresponding to the wedge bone (position 6) and the lateral foot arch center (position 7) are preferably transmitted wirelessly to the analysis device (20).
  • 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.
  • the sole measuring device (100) of the present invention having the above-described configuration, it can be configured only by providing a sensor on a member that comes into contact with the sole of the shoe or sole (10). It can be downsized. Therefore, it does not give extra stress to the person being measured like a large-sized device, and therefore accurate measurement is possible.
  • 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.
  • the sensor output is wirelessly transmitted to the analysis device (20) in the present invention, analysis of movement during exercise is easily performed.
  • the sensor is provided at a position corresponding to the center of the foot arch (position 7), the center of gravity of the foot, the arch, and the bone axis of the foot can be determined. Then, the “foot barycentric line” that is the trajectory of the barycentric point can be easily obtained.
  • the pressure value on the thumb contact surface (position 4) 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. 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 (the distance between the toe and the contact surface during walking) is also large. It will be big. Therefore, walking is stable and there is little risk of falls during walking.
  • the walking function is determined from the measurement result of the sensor (position 4), and the possibility of falling during walking can be determined.
  • FIG. 1 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
  • FIG. 1 shows an overview of an embodiment of the present invention.
  • the sole measuring device 100 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, an analysis device 20, and a display.
  • the apparatus 30 and the determination apparatus 40 are included.
  • 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.
  • 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 obtained by the sensors R1 to R7 and L1 to L7 are transmitted to the analysis device 20 by radio.
  • arrows SR ⁇ b> 1 and SL ⁇ b> 1 indicate how the measurement results are wirelessly transmitted from the sensors R ⁇ b> 1 and L ⁇ b> 1 to the analysis device 20. It should be noted that, when the respective measurement results are transmitted from the sensors R1 to R7 and L1 to L7 to the analysis device 20, they may be performed by wire.
  • the analysis result by the analysis device 20 is transmitted to the display device 30 via the information signal line IL9. Further, the result (analysis result) processed by the analysis 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 analysis device 20 and the image data of the display device 30.
  • 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 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 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 is a position corresponding to the fifth metatarsal head.
  • the fifth metatarsal head which is the root of the fifth metatarsal, is a “location where weight is applied during walking”.
  • the force acting on “the place where weight is applied during walking” is measured. There is no problem because it can be done.
  • 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 is a region that reaches the ground when walking on the thumb contact surface, that is, the tip of the thumb. This is because the force acting on the position (4) needs to be measured in order to obtain the kicking strength during walking.
  • 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 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 L ⁇ connecting the second finger (index finger) from the position (1) where the sensor 1 is arranged and a straight line L ⁇ 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.
  • it is inconvenient to install the sensor 6 because the region closer to the thumb than the straight line L ⁇ connecting the position (1) and the second finger (index finger) may become an arch.
  • the arrangement position of the sensor 6 is determined as described above.
  • a 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
  • 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
  • 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.
  • 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).
  • the position where the sensor 7 is disposed 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).
  • the barycentric line passes along a line (line L ⁇ in FIG. 2) connecting the heel and the second finger.
  • 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.
  • 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 understood by measuring the forces acting on the positions (1) to (7) and analyzing them by the analysis device 20 are exemplified below (in addition to specifying the type of the arch).
  • Items that can be understood by measuring the forces acting on the positions (1) to (7) and analyzing them by the analysis device 20 are exemplified below (in addition to specifying the type of the arch).
  • the flexibility of the arch can be understood.
  • a “high arch” when standing still may result in a “flat foot” when walking (when the arch is soft).
  • the center of gravity (the pressure center of the sole at the moment) and the arch shape are appropriately I understand.
  • 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.
  • 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.
  • the lateral arch AR3 can be specified based on the measurement results at the positions (3), (7), and (5).
  • the measurement result of the position (7) is indispensable for determining the lateral arch AR3.
  • 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).
  • the sensors 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.
  • 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.
  • 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).
  • 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).
  • 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.
  • 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.
  • 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.
  • 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).
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • the measurement result of the position (4) is used for determining the walking function and determining the possibility of falling during walking.
  • the analysis apparatus 20 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.
  • Reference numerals 20I and 20O in FIG. 6 indicate an input side interface and an output side interface, respectively.
  • the analysis device 20 is connected to the display device 30 and the determination device 40 through 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.
  • 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.
  • COP center-of-gravity point
  • 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.
  • COP barycentric point
  • 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.
  • 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.
  • 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. .
  • 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.
  • 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.
  • 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 of determining how abnormal the arch is when the arch is not normal (how much the arch is deformed from the normal arch) (see steps S2 and S3 in FIG. 7). 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.
  • 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.
  • 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.
  • the data is transmitted to the determination device 40 via the output side interface 20O and the information signal line IL10.
  • 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.
  • 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 analysis 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.
  • the display device 30 uses the determination result of the analysis device 20 (determination block 20E) as “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 analysis 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, it includes 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 analysis device 20 or the display device 30.
  • the determination result of the determination device 40 is fed back to the analysis device 20 through the information signal line IL40.
  • 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.
  • 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.
  • 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.
  • 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).
  • 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).
  • 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.
  • 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
  • FIG. 8 shows control (processing) for determination using such a relationship.
  • 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.
  • 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.
  • 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.
  • 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.
  • step S12 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).
  • 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).
  • 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.
  • step S15 it is determined that the subject's arch corresponds to the “high arch”, and the control is terminated.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • the foot bone axis is easily moved inward or the foot bone axis is outside.
  • the movement of the heel can be limited and brought close to a normal center of gravity line. Therefore, knee pain is also reduced.
  • 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.
  • 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.
  • 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.
  • step S31 the shear force acting on the position (1) is measured by the sensor 1. Then, the process proceeds to step S32.
  • 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.
  • 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.
  • the heel 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.
  • 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.
  • the embodiment of the illustrated embodiment can improve the hallux valgus.
  • 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.
  • the detection unit is configured by providing the sensors 1 to 7 on the member that comes into contact with the sole of the insole 10 (or shoes). Can be Therefore, the measurement subject is not subjected to excessive stress unlike a large-sized device, and accurate measurement is possible. Moreover, since it is a miniaturized device, it is possible to exercise with the sole measuring device 100 worn or worn. Therefore, it is possible to directly measure the force (shearing force or pressure) acting on the positions (1) to (7) (sensors 1 to 7 are arranged) while exercising (eg during walking). . Therefore, unlike the prior art, there is no need 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 wirelessly transmitted to the analysis device 20, so that the subject is exercising (for example, walking) compared to the case where the measurement result is transmitted by wire. ) Is easy to transmit the measurement results.
  • the rib ridge position 1
  • the cubic bone position 2)
  • the fifth metatarsal head position 3
  • the first metatarsal head position 5
  • the intermediate wedge bone position 6
  • the sensor is provided at a position corresponding to the center of the lateral foot arch (position 7)
  • the center of gravity of the foot the arch (the vertical arch AR1, the outer arch AR2, the lateral arch AR3), and the bone of the foot from the measured values of each sensor Axis can be determined.
  • the “foot barycentric line” that is the trajectory of the barycentric point can be easily obtained.
  • the pressure value on the thumb contact surface (position 4) 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. 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 (the distance between the toe and the contact surface during walking) is also large. It will be big. Therefore, walking is stable and there is little risk of falls during walking.
  • the sensor 4 since the sensor 4 is provided on the thumb contact surface (position 4), the walking function is determined from the measurement result of the sensor 4 (position 4), and the possibility of falling down during walking is determined. I can do it.
  • FIG. 5 shows the case of valgus, but the present invention can also deal with varus.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Veterinary Medicine (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Public Health (AREA)
  • Physics & Mathematics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Physiology (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Measuring And Recording Apparatus For Diagnosis (AREA)

Abstract

The purpose of the present invention is to provide a sole measurement device that is small, that can measure the force (for example, the pressure, the shear force) that acts at a specific site on the sole of a foot of a human that is exercising (for example, walking), and that can determine a parameter other than a foot pressure distribution. In this sole measurement device (100), sensors (shear force sensors, pressure sensors) are provided to a member (10: for example, an insole, a shoe) that contacts the sole of a foot. The sensors are provided at locations that correspond to the superior portion of the calcaneus (position 1), the cuboid bone (position 2), the head of the fifth metatarsal bone (position 3), the head of the first metatarsal bone (position 5), the intermediate cuneiform bone (position 6), and the center of the transverse arch (position 7).

Description

足裏計測装置Foot measuring device
　本発明は、人間の足裏の特定の部位に作用する力（例えば圧力、せん断力）を計測する装置に関する。 The present invention relates to an apparatus for measuring a force (for example, pressure, shearing force) acting on a specific part of a human foot sole.
　人間の足裏の特定の部位に作用する圧力を測定して、所謂「足圧分布」を特定することにより、足裏で最も荷重が加わる位置を推定し、変形性膝関節症や外反拇指のリスク評価を行なうことが出来る。
　しかし、従来技術では人間の足裏の特定の部位に作用する圧力を測定するのに大型な装置が必要となり、被測定者に余計なストレスを与えてしまい、正確な計測が困難になる恐れがある。
　また、足裏圧力測定は運動している中で（例えば歩行中に）計測することが必要であるが、従来の機器では歩行中の足裏圧力測定が困難である。そのため、静止した状態で足裏圧力を計測し、静止した状態の足裏圧力から歩行中の足裏圧力を推定するしかないのが実情である。 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.
However, in the prior art, a large device is required to measure the pressure acting on a specific part of the human foot, which may cause extra stress on the person being measured and may make accurate measurement difficult. is there.
In addition, although it is necessary to measure the sole pressure while exercising (for example, during walking), it is difficult to measure the sole pressure during walking with conventional devices. Therefore, the actual situation is that the sole pressure is measured in a stationary state, and the sole pressure during walking is estimated from the sole pressure in a stationary state.
　さらに足、脚の異常は、変形性膝関節症や外反拇指以外にも各種存在するが、変形性膝関節症や外反拇指以外の異常を判定するには足圧分布以外のパラメータが必要である。しかし、従来はその様なパラメータは提案されていなかった。
　その他の従来技術として、シート式の圧力センサを用いて歩行能力を評価する技術が存在する（特許文献１参照）。しかし、係る従来技術（特許文献１）では、シート式圧力センサを設置するのに大きな面積が必要であり、また、各種疾患を判定する技術に適用することが出来ない。 In addition, there are various types of abnormalities in the legs and legs other than knee osteoarthritis and hallux phalanges, but parameters other than foot pressure distribution are necessary to determine abnormalities other than knee osteoarthritis and hallux phalanges. It is. However, no such parameter has 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.
特開２０１４－９４０７０号公報JP 2014-94070 A
　本発明は上述した従来技術の問題点に鑑みて提案されたものであり、計測装置を小型化して、且つ、運動している状態（例えば歩行中）における人間の足裏の特定の部位に作用する力（例えば圧力、せん断力）を計測することが出来て、しかも、足圧分布以外のパラメータを決定することが出来る足裏計測装置の提供を目的としている。 The present invention has been proposed in view of the above-described problems of the prior art, and has a function of reducing the size of a measuring device and acting on a specific part of a human foot sole while in motion (for example, while walking). An object of the present invention is to provide a sole measuring device that can measure a force (for example, pressure, shearing force) to be performed and can determine parameters other than a foot pressure distribution.
　本発明の足裏計測装置（１００）は、足の裏が接触する部材（１０：例えばインソール、靴）の踵骨***部（位置１）、立方骨（位置２）、第五中足骨頭（位置３）、第一中足骨頭（位置５）、中間楔状骨（位置６）、横足弓中心（位置７）に対応する位置（図２のＬ（１）、Ｒ（１）、Ｌ（２）、Ｒ（２）・・・・Ｌ（７）、Ｒ（７）：図２の（１）～（７））にセンサ（せん断力センサ、圧力センサ）を設けたことを特徴としている。 The sole measuring device (100) of the present invention includes a rib raised portion (position 1), a cubic bone (position 2), and a fifth metatarsal head (10 Position 3), first metatarsal head (position 5), intermediate wedge bone (position 6), positions corresponding to the lateral foot arch center (position 7) (L (1), R (1), L ( 2), R (2)... L (7), R (7): (1) to (7) in FIG. 2 are provided with sensors (shear force sensors, pressure sensors). .
　また本発明において、拇指接地面（図１のＬ（４）、Ｒ（４）：図２の（４））にセンサを設けることが好ましい。
　そして本発明において、踵骨***部（位置１）、立方骨（位置２）、第五中足骨頭（位置３）、拇指接地面（位置４）、第一中足骨頭（位置５）、中間楔状骨（位置６）、横足弓中心（位置７）に対応する位置に設けられたセンサ１～７の出力を解析装置（２０）に対して無線で送信するのが好ましい。 In the present invention, it is preferable to provide a sensor on the thumb contact surface (L (4), R (4): FIG. 2 (4) in FIG. 1).
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 outputs of the sensors 1 to 7 provided at the positions corresponding to the wedge bone (position 6) and the lateral foot arch center (position 7) are preferably transmitted wirelessly to the analysis device (20).
　本発明の実施に際して、位置踵骨***部（位置１）、立方骨（位置２）、第五中足骨頭（位置３）、第一中足骨頭（位置５）、横足弓中心（位置７）に設けられるセンサはせん断力センサであるのが好ましい。 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.
　上述の構成を具備する本発明の足裏計測装置（１００）によれば、靴或いはソール等（１０）の足裏と接触する部材にセンサを設けるだけで構成することが出来るので、装置全体を小型化することが出来る。
　そのため、大型装置の様に被測定者に余計なストレスを与えてしまうことはなく、そのため、正確な計測が可能である。また、小型化された装置であれば、運動している中で（例えば歩行中に）、上述した位置に作用する力（せん断力或いは圧力）を直接計測することが可能になる。従来技術の様に、静止した状態の足裏圧力から歩行中の足裏圧力を推定する必要はない。
　特に、本発明においてセンサの出力を解析装置（２０）に対して無線で送信すれば、運動中における動きの解析が容易に行われる。 According to the sole measuring device (100) of the present invention having the above-described configuration, it can be configured only by providing a sensor on a member that comes into contact with the sole of the shoe or sole (10). It can be downsized.
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 analysis device (20) in the present invention, analysis of movement during exercise is easily performed.
　また本発明では、踵骨***部（位置１）、立方骨（位置２）、第五中足骨頭（位置３）、第一中足骨頭（位置５）、中間楔状骨（位置６）、横足弓中心（位置７）と対応する位置にセンサを設けているので、足の重心点、アーチ、足の骨軸を決定することが出来る。
　そして、足の重心点の軌跡である「足の重心線」も容易に求めることが出来る。
　足の重心線、アーチ（横アーチ、縦アーチ、外アーチ）、足の骨軸を決定することにより、変形性膝関節症や外反拇指以外の各種異常を判断して、当該異常を矯正或いは抑制する様な器具、運動を提案することが可能である。特に、小学生、中学生の様に成長途中の段階であれば、上述した様な運動や器具により、各種異常が解消され、正常な状態になる可能性が高い。
　そして、変形性膝関節症や外反拇指以外の各種異常を判断するパラメータとして、足の重心線、アーチ、足の骨軸という足圧分布以外のパラメータを用いることが出来る。 In the present invention, the rib raised portion (position 1), the cubic bone (position 2), the fifth metatarsal head (position 3), the first metatarsal head (position 5), the intermediate wedge bone (position 6), the lateral bone Since the sensor is provided at a position corresponding to the center of the foot arch (position 7), the center of gravity of the foot, the arch, and the bone axis of the foot can be determined.
Then, the “foot barycentric line” that is the trajectory of the barycentric point can be easily obtained.
By determining the center of gravity line of the foot, arch (lateral arch, vertical arch, external arch), and bone axis of the foot, various abnormalities other than knee osteoarthritis and hallux valgus are determined, and the abnormality is corrected or It is possible to propose a device or exercise that can be suppressed. 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.
As parameters for determining various abnormalities other than knee osteoarthritis and hallux phalanges, parameters other than foot pressure distribution such as foot center of gravity, arch, and foot bone axis can be used.
　ここで、拇指接地面（位置４）における圧力値が大きい場合には、歩行に際して足指が有効に使われており、地面を蹴り出す力が大きいことを意味している。従って、その他の条件が同じであれば、拇指接地面（位置４）における圧力値が大きい場合には、歩幅が大きく、歩行速度が速く、クリアランス（歩行中のつま先と接地面との距離）も大きいことになる。そのため、歩行が安定しており、歩行時の転倒の危険性が少ない。
　本発明において、拇指接地面（位置４）にセンサを設けた場合には、当該センサ（位置４）の計測結果から、歩行機能が判定され、歩行時に転倒する可能性を判断することが出来る。 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. 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 (the distance between the toe and the contact surface during walking) is also large. It will be big. Therefore, walking is stable and there is little risk of falls during walking.
In the present invention, when a sensor is provided on the thumb contact surface (position 4), the walking function is determined from the measurement result of the sensor (position 4), and the possibility of falling during walking can be determined.
本発明の実施形態に係る足裏計測装置の説明平面図である。It is an explanation top view of a sole measuring device concerning an embodiment of the present invention. 人間の足部の骨格を示す図である。It is a figure which shows the skeleton of a human foot part. 足のアーチを示す説明図である。It is explanatory drawing which shows the arch of a leg | foot. せん断力センサを用いる理由を示す説明図である。It is explanatory drawing which shows the reason for using a shear force sensor. 踵の上方の骨が変形している一例を示す図である。It is a figure which shows an example which the bone | frame above the collar is deform | transforming. 本発明の実施形態で用いられる解析装置の一例を示すブロック図である。It is a block diagram which shows an example of the analyzer used by embodiment of this invention. 本発明の実施形態における処理の一例を示すフローチャートである。It is a flowchart which shows an example of the process in embodiment of this invention. 本発明の実施形態における処理の別の例を示すフローチャートである。It is a flowchart which shows another example of the process in embodiment of this invention. 本発明の実施形態における処理のその他の例を示すフローチャートである。It is a flowchart which shows the other example of the process in embodiment of this invention. 本発明の実施形態における処理のさらに別の例を示すフローチャートである。It is a flowchart which shows another example of the process in embodiment of this invention.
　以下、添付図面を参照して、本発明の実施形態について説明する。
　図１は本発明の実施形態の概要を示している。
　実施形態に係る本発明の足裏計測装置１００は、図１において全体を符号１００で示されており、足の裏が接触する部材であるインソール１０（或いは靴）と、解析装置２０と、表示装置３０、判定装置４０とを有している。
　インソール１０（或いは靴）は、右足用のインソール１０Ｒ及び左足用のインソール１０Ｌにより構成され、各々のインソール１０Ｒ、１０Ｌにおいて、７箇所の所定位置（Ｒ１）～（Ｒ７）、（Ｌ１）～（Ｌ７）にセンサＲ１～Ｒ７、Ｌ１～Ｌ７が設置されている。図１において、当該「所定位置」或いは当該所定位置に設置される「センサ」は同一の符号で表現されており、符号（Ｒ１）～（Ｒ７）、（Ｌ１）～（Ｌ７）でそれぞれ示されている。 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 sole measuring device 100 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, an analysis device 20, and a display. The apparatus 30 and the determination apparatus 40 are included.
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.
　各センサＲ１～Ｒ７、Ｌ１～Ｌ７による計測結果は、それぞれ無線により解析装置２０に送信される。図１では各センサを代表して、センサＲ１、Ｌ１から解析装置２０に計測結果が無線送信される態様を、矢印ＳＲ１、ＳＬ１（無線信号ライン）で示している。
　なお、各センサＲ１～Ｒ７、Ｌ１～Ｌ７から解析装置２０にそれぞれの計測結果を送信するに際して、有線で行うことも可能である。 The measurement results obtained by the sensors R1 to R7 and L1 to L7 are transmitted to the analysis device 20 by radio. In FIG. 1, as an example of each sensor, arrows SR <b> 1 and SL <b> 1 (wireless signal lines) indicate how the measurement results are wirelessly transmitted from the sensors R <b> 1 and L <b> 1 to the analysis device 20.
It should be noted that, when the respective measurement results are transmitted from the sensors R1 to R7 and L1 to L7 to the analysis device 20, they may be performed by wire.
　解析装置２０による解析結果は、情報信号ラインＩＬ９を介して表示装置３０に送信される。
　また、解析装置２０により処理された結果（解析結果）は情報信号ラインＩＬ１０を介して判定装置４０に送信され、表示装置３０の画像データも情報信号ラインＩＬ１２を介して判定装置４０に送信される。
　判定装置４０では、解析装置２０の解析結果や表示装置３０の画像データに基づいて、必要な対処内容を判定し提示する。 The analysis result by the analysis device 20 is transmitted to the display device 30 via the information signal line IL9.
Further, the result (analysis result) processed by the analysis 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 analysis device 20 and the image data of the display device 30.
　次に、センサＲ１～Ｒ７、Ｌ１～Ｌ７の設置位置について、図２を参照して説明する。
　図２では、右足（右足用のインソール１０Ｒ或いは靴におけるセンサ（１）～（７）の位置）について示しているが、左足或いは左足用のインソール１０Ｌ（或いは靴）におけるセンサの位置は、図２で示す位置と左右対称の位置である。
　センサ１～７（センサＲ１～Ｒ７であるが、煩雑さを避けるため、以下「センサ１～７」と記載する）は、人の足の側部の骨格構造からその位置が定義される。そのため、図２では右足の骨格を示している。 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.
　センサ１が配置される位置（図２では符号（１）で示す）は踵骨***部である。より望ましくは、位置（１）は踵の骨の中心部である。
　また、位置（１）を決定するに際しては、踵骨***部が外側（図２で第五中足骨側、すなわち小指側）にずれた際に、その量（外側にずれた量）を計測出来る様な位置に設定される。通常、踵骨***部がずれてしまうとすれば足の外側（小指側）であり、足の内側（図２で第一中足骨側、すなわち親指側）にはずれない。
　センサ２が配置される位置（図２の符号（２）で示す位置）は、立方骨に対応する位置である。但し、立方骨の中心よりもやや外側（小指側：第五中足骨の領域）であっても良い。 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).
　センサ３が配置される位置（図２では符号（３）で示す）は、第五中足骨頭に対応する位置である。
　歩行時の状態を解析するためには、「歩行時に体重が掛かる箇所」に作用する力を計測する必要がある。第五中足骨の付け根である第五中足骨頭は、「歩行時に体重が掛かる箇所」である。
　ここで、センサ３が配置される位置が第五中足骨頭の長さの１／３程度、つま先とは反対側にずれたとしても、「歩行時に体重が掛かる箇所」に作用する力を計測出来るので問題はない。
　ただし、第五末梢骨（つま先側の骨）には体重が掛からないので、第五中足骨頭よりも第五末梢骨側（つま先側）にずれた位置にセンサを取り付けることは不都合である。 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 about 1/3 of the length of the fifth metatarsal head and deviates to the side opposite to the toes, the force acting on “the place where weight is applied during walking” is measured. There is no problem because it can be done.
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.
　センサ４が配置される位置（図２では符号（４）で示す）は、拇指接地面、すなわち拇指の先端部で歩行の際に地面に着く領域である。
　歩行の際の蹴り出しの強さを求めるのに、位置（４）に作用する力を計測する必要があることによる。
　ここで、骨（第一末梢骨）が足の親指のどの部分まで伸びているのかについては、個人差がある。そのため、位置（４）は骨の名称で特定するのではなく、上述した様に「拇指接地面」として特定している。
　センサ４の位置が拇指接地面を外れてしまうと、歩行の際の蹴り出しの強さを計測できないので、不都合である。
　後述するが、「足の骨軸」、「アーチ」、「重心線」を特定（決定）するのには、位置（４）に配置したセンサ４の計測結果は用いない。 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.
This is because the force acting on the position (4) needs to be measured in order to obtain the kicking strength during walking.
Here, there are individual differences as to which part of the big toe the bone (first peripheral 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”.
　センサ５が配置される位置（図２で符号（５）で示す）は、第一中足骨頭に対応する位置である。
　歩行時に体重がかかるのが第一中足の骨頭側、いわゆる「拇指球」の部分である。そのため、センサ５の取付位置は、「拇指球」から外れないようにする必要がある。拇指球に体重が掛かるからである。 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.
　センサ６が配置される位置（図２では符号（６）で示す位置）は、中間楔状骨に対応する位置である。
　センサ６が配置される位置は、センサ１を配置した位置（１）から第二指（人差し指）を結ぶ直線Ｌαと、位置（１）から第四指（薬指）を結ぶ直線Ｌβとで挟まれた領域における３つの楔状骨の領域であれば良い。
　ここで、位置（１）と第二指（人差し指）を結ぶ直線Ｌαよりも親指側の領域は、土踏まずになってしまう可能性があるため、センサ６を設置するのは不都合である。一方、位置（１）と第四指（薬指）とを結ぶ直線Ｌβよりも小指側の領域は、位置（２）と重複してしまう可能性があるため、やはりセンサ６を設置するのは不都合である。これ等の理由により、センサ６の配置位置は上述の様に決定されている。 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.
　図３を参照して後述する様に足のアーチには縦アーチＡＲ１、外アーチＡＲ２、横アーチＡＲ３の３種類がある。縦アーチＡＲ１は、図２で踵骨***部を表す位置（１）の近傍から第一中足骨頭を表す位置（５）の近傍まで延在しており、外アーチＡＲ２は、図２で踵骨***部を表す位置（１）の近傍から第五中足骨頭を表す位置（３）の近傍まで延在している。さらに横アーチＡＲ３は、図２で第一中足骨頭を表す位置（５）の近傍から第五中足骨頭を表す位置（３）の近傍まで延在している。アーチＡＲ１～３により、歩行時などに足裏に係る衝撃を吸収することができる。
　足のアーチを特定するためには、位置（２）、（６）以外の位置（例えば、位置（１）、（３）等）における計測結果を併せて参照する必要がある。
　また、位置（６）と位置（２）の計測結果（及びその他の位置（１）、（３）等の計測結果と併せて）から、重心点（瞬間における足裏の圧力中心：重心点の軌跡が「重心線」）が特定（決定）出来る。 As will be described later with reference to 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).
　センサ６により計測される位置（６）に作用する力（圧力、せん断力）の計測結果と、センサ２により計測される位置（２）に作用する力（圧力、せん断力）の計測結果により、「扁平足」、「正常」、「ハイアーチ」の３種類を判定することが出来る。
　「扁平足」、「正常」、「ハイアーチ」の各々において、位置（６）で作用する力（圧力或いはせん断力）の計測結果と、位置（２）に作用する力（圧力或いはせん断力）の計測結果の大小関係が異なっている。すなわち、
　扁平足：　位置（２）に作用する力≒位置（６）に作用する力、或いは、
　位置（２）に作用する力≦位置（６）に作用する力
　正常：　位置（２）に作用する力＞位置（６）に作用する力
　ハイアーチ：　位置（２）に作用する力、位置（６）に作用する力は共に検出されない。
　これについては、図８を参照して後述する。 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.
　図２において、センサ７が配置される位置（図２で（７）で示す）は、第二中足骨頭（第二指（人差し指）の付け根部分）と第三中足骨頭（第三指（中指）の付け根部分）の間の領域に位置している。
　ここで、重心線は、踵と第二指をつないだ線（図２のラインＬα）に沿って抜ける。そのため、第二指より第一指側（親指側）の領域にセンサ７を設けるのは不都合である。
　一方、第三指（中指）よりも小指側の領域は、重心線から外れてしまうので、センサ７を設けるのは不都合である。また、体重は足の中心線よりも内側に係るので、センサ７の位置（７）が足の中心線よりも外側にあると、体重が掛かった状態が検出できない。 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.
　図示の実施形態によれば、上述した位置（１）～（７）に配置したセンサ１～７により、当該位置に作用する力を計測することにより、測定装置の所定位置に立っている状態の計測のみではなく、歩いている状態の計測が出来る。
　位置（１）～（７）に作用する力を計測し、解析装置２０により解析することで分かる項目を、（前記アーチの種類の特定に加えて）以下に例示する。
　まず、足の柔軟性に個人差があることから、図３で示すアーチの柔軟性にも個人差が存在する。
　位置（２）、（６）、（７）の計測結果を解析することにより、アーチの柔軟性が分かる。アーチの柔軟性如何によっては、立って静止した状態では「ハイアーチ」でも、歩いているときには「扁平足」となる場合（アーチが柔らかい場合）がある。或いは、立って静止している状態では「正常」でも、歩いているときには「ハイアーチ」の場合（アーチが硬い場合）が存在する。 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 understood by measuring the forces acting on the positions (1) to (7) and analyzing them by the analysis device 20 are exemplified below (in addition to specifying the type of the 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).
　また、図７を参照して後述するが、位置（２）、（６）、（７）の計測結果を解析することにより、重心点（瞬間における足裏の圧力中心）とアーチ形状が適切に分かる。
　ここで、位置（２）、（６）、（７）に作用する力を計測しない場合、例えば位置（１）、（３）、（５）に作用する力のみを計測する場合には、そもそもアーチを特定することが不可能である。
　図示の実施形態では、位置（１）、（３）、（５）に作用する力に加えて、位置（２）、（６）、（７）に作用する力を計測することにより、アーチの特定を可能にしている。すなわち、位置（２）、（６）の計測結果により、縦アーチＡＲ１、外アーチＡＲ２が決定でき、縦アーチＡＲ１から土踏まずの様子が把握出来る。さらに、位置（３）、（７）、（５）の計測結果により横アーチＡＲ３の特定が可能になる。換言すれば、位置（７）の計測結果は、横アーチＡＲ３の決定に不可欠である。 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.
　次に、重心線の特定に関して、従来は位置（１）、（３）、（５）のみに圧力センサを設置し、足においては位置（１）、（３）、（５）における荷重分布が比率として３：１：２になる、という前提で重心点を特定していた。
　しかし、図示の実施形態では、位置（２）、（６）、（７）にもセンサ（センサ２、６、７）を設置している。そして、位置（２）、（６）、（７）に作用する力（圧力、せん断力）も計測して重心点（ＣＯＰ）を正確に求め、さらにその軌跡である重心線を正確に特定している。この点についても、図７を参照して後述する。 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.
　ここで、「足の骨軸」について説明する。
　「足の骨軸」は、踵骨***部を表す位置（１）と距骨とを貫く軸であり、位置（１）、（２）、（３）、（５）、（７）にせん断力センサ１、２、３、５、７を設け、計測結果を解析することにより、「足の骨軸」における動きを正確に把握することが出来る。これについても、図７を参照して後述する。
　位置（１）、（２）、（３）、（５）、（７）は足底部で大きく動く部位なので、この５箇所のせん断力を求めると、「足の骨軸」の動きを解析し易い。そして位置（１）、（２）、（３）、（５）、（７）のせん断力を解析して「足の骨軸」の動きを解析することで、歩行中の踵骨などのずれや移動の速度、力（荷重の変化）、向き、ねじれ等が評価出来る。
　また、足の骨軸の動きは、足裏の関節の柔軟性に依存する。 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.
　位置（１）、（２）、（３）、（５）、（７）には、圧力センサではなく「せん断力センサ」を配置することが好適である。その理由について、図４を参照して説明する。
　位置（１）、（２）、（３）、（５）、（７）に作用する力を計測し、上述の解析を行うためには、図４（Ａ）において、力の作用軸ＳＨ１の下端の矢印ＡＨで示す力（紙面に垂直な方向の力も含む）を計測する必要がある。そのため、係る力の計測が可能なせん断力センサを、位置（１）、（２）、（３）、（５）、（７）に設置するのが好ましい。
　図４（Ｂ）で示す様に、圧力センサは垂直軸ＳＨ２の垂直方向荷重（符号Ｐ）しか計測することが出来ない。そのため、位置（１）、（２）、（３）、（５）、（７）に作用する力を計測するには不都合である。 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).
　上述した様に、位置（１）、（２）、（３）、（５）、（７）に作用するせん断力の計測結果を解析することにより、「足の骨軸」の動きが正確に把握することが出来る。例えば、足の骨軸から、踵の骨が外反しているか否かが判断出来る。
　例えば、アーチが硬く、足の骨軸が内側に動かない場合には、位置（２）、（３）側に荷重がかかり、歩行中に膝が捻じれ（回内モーメントが発生し）、将来、いわゆる「膝がこすれる」状態になって膝の痛みを訴える恐れがある。それに対して、図示の実施形態では位置（２）、（３）側に荷重がかかっているか否かを計測して、膝の痛みを訴える恐れがあるか否かを判定することが出来る。これについても、図９を参照して後述する。 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.
　踵の上方の状態の一例を示す図５において、参考線Ｌ５Ｌ、Ｌ５Ｒは足Ｆの骨軸（実線で示す）と連続する脚部Ｌの中心軸（破線で示す）を表現している。参考線Ｌ５Ｌ、Ｌ５Ｒで示す様に、踵が曲がっている（外反している）場合には、踵が硬く（踵周辺の関節の可動域が制限されており）、外側（小指側）に曲がらないため、位置（１）におけるせん断力の数値が小さくなる。図５で示す様な場合（踵が硬く外側に曲がらない状態）では、膝にストレスが掛かり、痛みが発症する場合がある。
　その様な場合に、靴或いはインソールにおいて、靴の外側の高さ、内側の高さ或いは踵自体の高さを調節することにより、踵の動きを制限し、正常な重心線に近づけることが出来る。そのため、膝の痛みも低減する。これについては、図１０を参照して後述する。 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.
　ここで位置（４）における圧力の値は、アーチ、脚の骨軸、重心線の特定とは関係が無い。
　位置（４）における圧力値が大きい場合には、歩行に際して足指が有効に使われており、地面を蹴り出す力が大きいことを意味している。すなわち、歩行に際して足指が有効に使われており、地面を蹴り出す力が大きければ、その他の条件が同じ場合には、歩幅が大きく、歩行速度が速く、クリアランス（歩行中のつま先と接地面との距離）も大きい。そのため、歩行が安定しており、歩行時の転倒の危険性が少ない。
　換言すれば、位置（４）の計測結果は、歩行機能を判定し、歩行時の転倒の可能性を判断するのに用いられる。 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.
　図１で示す解析装置２０とその作用について、図６～図１０を参照して説明する。
　図示の実施形態で好適に用いられる解析装置２０の機能ブロックを示す図６において、解析装置２０（破線で囲まれた部分）は、重心点決定ブロック２０Ａ、重心点の軌跡である重心線を決定する重心線決定ブロック２０Ｂ、アーチ決定ブロック２０Ｃ、骨軸決定ブロック２０Ｄ、判定ブロック２０Ｅ、記憶ブロック２０Ｆを有する。図６における符号２０Ｉ、２０Ｏは、それぞれ入力側インターフェース、出力側インターフェースを示している。
　図１を参照して述べた通り、解析装置２０は、表示装置３０、判定装置４０と、情報信号ラインＩＬ９、ＩＬ１０により接続されている。 The analysis apparatus 20 shown in FIG. 1 and its operation will be described with reference to FIGS.
In FIG. 6 which shows the functional blocks of the analysis apparatus 20 preferably used in the illustrated embodiment, the analysis 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 analysis device 20 is connected to the display device 30 and the determination device 40 through information signal lines IL9 and IL10.
　重心点決定ブロック２０Ａは、入力側インターフェース２０Ｉ及び情報信号ラインＩＬ１を介してセンサ１、２、３、５、６、７からの計測信号（位置（１）、（２）、（３）、（５）、（６）、（７）に作用する圧力或いはせん断力の計測結果）を受信し、重心点（ＣＯＰ）を求める機能を有している。
　重心点決定ブロック２０Ａで決定された重心点（瞬間における足裏の圧力中心）の情報は、情報信号ラインＩＬ２を介して重心線決定ブロック２０Ｂに送信される。
　重心点決定ブロック２０Ａにおいて重心点（ＣＯＰ）を決定する際には、従来公知のソフトウェア技術を用いて、測定対象者の特質等を考慮して、ケース・バイ・ケースで決定する。後述する重心線決定ブロック２０Ｂ、アーチ決定ブロック２０Ｃ、骨軸決定ブロック２０Ｄにおいても同様である。 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.
　重心線決定ブロック２０Ｂは、情報信号ラインＩＬ２を介して重心点決定ブロック２０Ａから重心点（ＣＯＰ）の情報を受信し、重心点の軌跡である重心線を決定する機能を有している。
　重心線決定ブロック２０Ｂで決定された重心線の情報は、情報信号ラインＩＬ３を介して判定ブロック２０Ｅに送信される。 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.
　アーチ決定ブロック２０Ｃは、入力側インターフェース２０Ｉ及び情報信号ラインＩＬ４を介して、センサ１、２、３、５、６、７からの計測信号（位置（１）、（２）、（３）、（５）、（６）、（７）に作用する圧力、せん断力の計測値）を受信し、それに基づいてアーチを決定する機能を有している。
　アーチ決定ブロック２０Ｃでは、アーチを構成する縦アーチＡＲ１、外アーチＡＲ２、横アーチＡＲ３のそれぞれの位置や形状を特定し、アーチが決定される。
　アーチ決定ブロック２０Ｃで決定された縦アーチＡＲ１、外アーチＡＲ２、横アーチＡＲ３の情報は、情報信号ラインＩＬ５を介して判定ブロック２０Ｅに送信される。 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.
　骨軸決定ブロック２０Ｄは、入力側インターフェース２０Ｉ及び情報信号ラインＩＬ６を介してセンサ１、２、３、５、７からの計測信号（位置（１）、（２）、（３）、（５）、（７）に作用する圧力、せん断力の測定値）を受信し、足の骨軸の動きを把握して、足の骨軸を決定する機能を有している。
　骨軸決定ブロック２０Ｄで決定された足の骨軸の情報は、情報信号ラインＩＬ７を介して判定ブロック２０Ｅに送信される。 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.
　記憶ブロック２０Ｆには、重心点、重心線、アーチ、足の骨軸について、いわゆる「正常」と考えられる場合のデータ（正常値）が記憶されており、当該正常値データは情報信号ラインＩＬ８を介して判定ブロック２０Ｅに送信され、判定ブロック２０Ｅによる判定の際に参照される。
　記憶ブロック２０Ｆには、前記正常値データの他に、位置（２）、（３）側に作用する荷重のしきい値、位置（１）にかかるせん断力のしきい値等が記憶されている。
　ここで、位置（２）、（３）側に作用する荷重のしきい値は、判定ブロック２０Ｅにおいて、アーチの硬さ（柔軟性）を判断するために用いられる。そして、位置（１）にかかるせん断力のしきい値は、判定ブロック２０Ｅにおいて、踵が外反しているか否かを判断するために用いられる。 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.
　判定ブロック２０Ｅは、重心線の正常値データ（記憶ブロック２０Ｆから受信）と比較して、重心線決定ブロック２０Ｂで決定された重心線が正常か否かを判定する機能と、重心線が正常でない場合にどの程度異常であるか（正常な状態からどの程度偏奇しているか）を判定する機能とを有している（図７のステップＳ２、Ｓ３参照）。
　判定ブロック２０Ｅの前記判定結果は、出力側インターフェース２０Ｏ及び情報信号ラインＩＬ９を介して、表示装置３０に送信される。それと共に、出力側インターフェース２０Ｏ及び情報信号ラインＩＬ１０を介して、判定装置４０に送信される。 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.
　また判定ブロック２０Ｅは、アーチの正常値データ（記憶ブロック２０Ｆから受信）と比較して、アーチ決定ブロック２０Ｃで決定されたアーチ（縦アーチＡＲ１、外アーチＡＲ２、横アーチＡＲ３）が正常か否かを判定する機能と、アーチが正常でない場合にどの程度異常であるか（正常なアーチとどの程度変形しているか）を判定する機能を有している（図７のステップＳ２、Ｓ３参照）。
　そして判定ブロック２０Ｅは、位置（２）、（３）側にかかる荷重の計測値を、当該荷重のしきい値（記憶ブロック２０Ｆから受信）と比較して、アーチの硬さ（柔軟性）を判定する機能を有している。この機能は、図９を参照して後述する。
　さらに判定ブロック２０Ｅは、位置（２）で作用する力の計測値と位置（６）に作用する力の計測値を比較して、アーチの種類（「扁平足」、「正常」、「ハイアーチ」）を判定する機能を有している。この機能については、図８を参照して後述する。
　判定ブロック２０Ｅによるアーチに関する前記判定結果は、出力側インターフェース２０Ｏ及び情報信号ラインＩＬ９を介して、表示装置３０に送信される。それと共に、出力側インターフェース２０Ｏ及び情報信号ラインＩＬ１０を介して、判定装置４０に送信される。 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 of determining how abnormal the arch is when the arch is not normal (how much the arch is deformed from the normal arch) (see steps S2 and S3 in FIG. 7).
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.
　判定ブロック２０Ｅは、骨軸の正常値データ（記憶ブロック２０Ｆから受信）と比較して、骨軸決定ブロック２０Ｄで決定された足の骨軸が正常か否かを判定する機能と、足の骨軸が正常でない場合に異常の程度はどれ位か（足の骨軸が正常な場合に対してどの程度変形しているのか）を判定する機能を有している（図７のステップＳ２、Ｓ３参照）。
　また、判定ブロック２０Ｅは、位置（１）にかかるせん断力の計測値を、踵が外反しているか否かを判断するための当該せん断力のしきい値（記憶ブロック２０Ｆから受信）と比較して、踵が外反しているか否かを判定する機能を有している。この機能については、図１０を参照して後述する。
　判定ブロック２０Ｅによる骨軸に関する前記判定結果は、出力側インターフェース２０Ｏ及び情報信号ラインＩＬ９を介して、表示装置３０に送信される。それと共に、出力側インターフェース２０Ｏ及び情報信号ラインＩＬ１０を介して、判定装置４０に送信される。
　図８、図９、図１０を参照して後述する制御を実行する際には、センサ１、２、３、５、６、７による計測信号は、入力側インターフェース２０Ｉ及び情報信号ラインＩＬ１１を介して、判定ブロック２０Ｅに送信される。換言すると、図８、図９、図１０を参照して後述する制御に際しては、センサ１、２、３、５、６、７による計測信号は、重心点決定ブロック２０Ａ、重心線決定ブロック２０Ｂ、アーチ決定ブロック２０Ｃ、骨軸決定ブロック２０Ｄは経由しない。 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.
　表示装置３０は、解析装置２０（判定ブロック２０Ｅ）から送信された判定結果を表示する機能を有する。
　具体的には、「被験者の重心線が正常か否か」、「重心線が正常でない場合、どの程度異常なのか」、「被験者のアーチ（縦アーチ、外アーチ、横アーチ）が正常か否か」、「アーチが正常でない場合、どの程度異常なのか」、「被験者の足の骨軸が正常か否か」、「足の骨軸が正常でない場合、どの程度異常なのか」について、画像データを含めて表示する。
　また、表示装置３０は、解析装置２０（判定ブロック２０Ｅ）の判定結果として、「アーチの硬さ（柔軟性）」、「アーチの種類（扁平足、正常、ハイアーチ）」、「踵が外反しているか否か」について、画像データを含めて表示する。
　上述した様に、表示装置３０は情報信号ラインＩＬ１２を介して、前記画像データを判定装置４０に送信する。 The display device 30 has a function of displaying the determination result transmitted from the analysis 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 uses the determination result of the analysis device 20 (determination block 20E) as “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.
　判定装置４０は、解析装置２０（判定ブロック２０Ｅ）から送信された判定結果、表示装置３０から送信された画像データを受信して、これ等に基づいて、判定結果が「正常ではない」場合に、それを改善するための運動、使用器具等を提示する機能を有する（図７～図１０参照）。
　判定装置４０による判定の際は、従来公知のソフトウェア技術を用いて、測定対象者の特質を考慮して、ケース・バイ・ケースで決定する。
　なお、判定装置４０は例えばコンピューター等の情報処理装置であるが、これに限定される訳ではない。例えば、医学的な知識を持つ専門家、オペレーターが解析装置２０や表示装置３０からの情報、データに基づいて、必要な判定や改善のための提示を行う場合も含む。
　判定装置４０の判定結果は、情報信号ラインＩＬ４０により解析装置２０にフィードバックされる。図６では情報信号ラインＩＬ４０が記憶ブロック２０Ｆに接続して表示されているが、判定装置４０の判定結果は記憶ブロック２０Ｆのみにフィードバックされる訳ではなく、解析装置２０における全ての機能ブロックに対して判定装置４０の判定結果がフィードバックされる。 The determination device 40 receives the determination result transmitted from the analysis 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, it includes 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 analysis device 20 or the display device 30.
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.
　係る解析装置２０を用いて行われる処理の一例を、主として図７を参照して説明する。
　図７のフローチャートは、位置（１）、（２）、（３）、（５）、（６）、（７）に作用する力を計測し、当該計測結果より重心点（足裏の圧力中心）、重心線、アーチ、足の骨軸を決定し当該重心線、アーチ、足の骨軸が正常か否かを判定した上、異常を抑制する運動、使用器具を設計、決定する制御を示している。
　図７において、ステップＳ１では、センサ１、２、３、５、６、７により位置（１）、（２）、（３）、（５）、（６）、（７）に作用する力を計測する。そして、ステップＳ２に進む。 An example of processing performed using the analysis apparatus 20 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.
　ステップＳ２では、重心点決定ブロック２０Ａ（図６）において、ステップＳ１の位置（１）、（２）、（３）、（５）、（６）、（７）に作用する力（圧力、せん断力）の計測結果に基づき、重心点（足裏の圧力中心）を決定し、さらに重心線決定ブロック２０Ｂ（図６）において、重心点の軌跡である重心線を決定する。
　また、ステップＳ２では、アーチ決定ブロック２０Ｃ（図６）において、ステップＳ１の位置（１）、（２）、（３）、（５）、（６）、（７）に作用する力の計測結果に基づき、アーチ（縦アーチ、外アーチ、横アーチ）を決定する
　さらに、ステップＳ２では、骨軸決定ブロック２０Ｄ（図６）において、ステップＳ１の位置（１）、（２）、（３）、（５）、（７）に作用する力の計測結果に基づき、足の骨軸を決定する。 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.
　次に、ステップＳ３では、ステップＳ２で決定した重心線、アーチ（縦アーチＡＲ１、外アーチＡＲ２、横アーチＡＲ３）、足の骨軸を、記憶ブロック２０Ｆ（図６）に格納された正常な重心線、アーチ、骨軸のデータと比較し、当該比較結果により被験者の重心線、アーチ、骨軸が正常であるか否かを判定し、異常である場合には異常の程度を判定する。
　ステップＳ４では、ステップＳ３で被験者の重心線、アーチ、骨軸の何れかが異常と判定された場合に、当該異常を抑制、改善するのに好適な運動、使用器具等を設計、決定し、提示する。そして、制御を終了する。 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.
　図６で示す解析装置２０を用いた処理の他の例を、主として図８を参照して説明する。
　図３に関連して上述した様に、位置（６）と位置（２）に作用する力の計測結果から、縦アーチＡＲ１に関連して、被験者のアーチに関する種類を「扁平足」、「正常」、「ハイアーチ」の３種類に分類することが出来る。ここで、
　位置（２）に作用する力　≒　位置（６）に作用する力、或いは、
　位置（２）に作用する力　≦　位置（６）に作用する力　であれば、被験者は扁平足であり、
　位置（２）に作用する力　＞　位置（６）に作用する力　であれば、被験者は扁平足でもハイアーチでもない「正常」な足であり、
　位置（２）に作用する力、位置（６）に作用する力が共に検出されない場合には、被験者は「ハイアーチ」に分類される。
　係る関係を用いて判断する制御（処理）が図８に記載されている。 Another example of processing using the analysis apparatus 20 shown in FIG. 6 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 position (2) ≤ the force acting on 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 the force acting on position (2) nor the 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.
　図８において、ステップＳ１１では、センサ２、センサ６により位置（２）、（６）に作用する力（例えば圧力、せん断力も可能）を計測する。そしてステップＳ１２に進む。
　ステップＳ１２では、ステップＳ１１で計測した位置（２）に作用する力と、同じく位置（６）に作用する力の大きさを比較し、位置（２）に作用する力が位置（６）に作用する力よりも大きいか否かを判断する。
　ステップＳ１２の比較の結果、位置（２）に作用する力が位置（６）に作用する力より大きい場合は（ステップＳ１２が「Ｙｅｓ」）、ステップＳ１３に進む。
　ステップＳ１３では、被験者のアーチは、扁平足やハイアーチには該当せず、「正常」と判断して、制御を終了する。 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.
　ステップＳ１２の比較の結果、位置（２）に作用する力が位置（６）に作用する力と概略等しいか、或いは、位置（２）に作用する力が位置（６）に作用する力より小さい場合（ステップＳ１２が「Ｎｏ（位置（２）≦位置（６））」の場合）は、ステップＳ１４に進む。
　ステップＳ１４では、被験者のアーチが「扁平足」に該当すると判断する。この場合には、判定装置４０（図６）において、例えばインソールにアーチを形成する等の工夫（扁平足改善用の器具の提供）を提示することが可能である。
　ステップＳ１２の比較の結果、位置（２）に作用する力及び位置（６）に作用する力が共に検出されない場合（ステップＳ１２が「Ｎｏ（位置（２）、位置（６）の力が検出されず）」の場合）は、ステップＳ１５に進む。
　ステップＳ１５では、被験者のアーチが「ハイアーチ」に該当すると判断して、制御を終了する。
　なお、図８には図示されていないが、アーチに関する各種判定においては、必要に応じて（２）、（６）以外のその他の位置（１）、（３）、（５）、（７）に作用する力（圧力、せん断力）の計測結果を併せて参照する必要がある。後述する図９、図１０の制御においても同様である。 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.
　図６で示す解析装置２０を用いた処理の別の例を、主として図９を参照して説明する。
　上述した様に、アーチが硬く、足の骨軸が内側に動かない場合には、位置（２）、（３）側に大きな荷重がかかり、歩行中に膝が捻じれ（回内モーメントが発生し）、将来、いわゆる「膝がこすれる」状態になって膝の痛みを訴える恐れがある。
　図９のフローチャートは、係る恐れの有無を判断する。そのため、位置（２）、（３）側に作用する力を計測し、計測された力が大きい場合は、「アーチが硬く歩行中に膝が捻じれる恐れがある」等の判断を行う。それと共に、「歩行中に膝が捻じれる（回内モーメントが発生する）」ことを抑制するための運動、使用器具を提示する。 Another example of processing using the analysis apparatus 20 shown in FIG. 6 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.
　図９において、ステップＳ２１では、センサ２、３により位置（２）、（３）に作用する力（圧力、せん断力）を計測する。そしてステップＳ２２に進む。
　ステップＳ２２では、ステップＳ２１で計測された位置（２）、（３）に作用する力に基づき、位置（２）、（３）側に大きな荷重がかかっているか否かを判断する。係る判断は、例えば、位置（２）、（３）に作用する力の計測結果と、歩行中に膝が捻じれる（回内モーメントが発生する）場合の各種データ及び被験者の計測データに基づいて総合的に決定されるしきい値とを比較して行われる。
　ステップＳ２２で、位置（２）、（３）側に（対処すべき）大きな荷重がかかっていると判断した場合は（ステップＳ２２が「Ｙｅｓ」）、ステップＳ２３に進む。
　一方、ステップＳ２２で、位置（２）、（３）側に（対処すべき）大きな荷重がかかっていない判断した場合は（ステップＳ２２が「Ｎｏ」）、制御を終了する。 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.
　ステップＳ２３（位置（２）、（３）側に（対処すべき）大きな荷重がかかっていると判断された場合）では、「アーチが硬く、足の骨軸が内側に移動しない（したがってＯ脚気味となり、脚が外側に曲がる）」と判断する。そしてステップＳ２４に進む。
　ステップＳ２４では、当該被験者には、現在或いは将来において、「歩行中に膝が捻じれる（回内モーメントが発生する）」と判断し、そのため、「将来、いわゆる「膝がこすれる」状態になって膝の痛みを訴える恐れがある」と判断する。
　そして、ステップＳ２５に進む。 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.
　ステップＳ２５では、歩行中に膝が捻じれ（回内モーメントが発生し）、将来、いわゆる「膝がこすれる」状態になって膝の痛みを訴える恐れがある場合に対する改善策或いは対処法を提示する。
　例えば、歩行中の膝の捻じれ（回内モーメントの発生）を抑制して、将来の膝の痛みを予防するため、足の骨軸が内側に移動し易い器具や、足の骨軸が外側に移動するのを抑制して、内側に移動するのを助長するための体操を提示する。例えば、靴或いはインソールにおいて、靴の外側の高さ、内側の高さ或いは踵自体の高さを調節することにより、踵の動きを制限し、正常な重心線に近づけることが出来る。そのため、膝の痛みも低減する。
　ステップＳ２５については、情報処理装置のみならず、専門家がステップＳ２３、Ｓ２４の判定結果を受けて提示を行う場合を包含する。 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.
　図６で示す解析装置２０を用いた処理のさらに別の例を、主として図１０を参照して説明する。
　図５で示す様に踵が曲がっている（外反している）場合には、踵が硬く、外側（小指側）に曲がらないため、位置（１）におけるせん断力の数値が小さくなる。
　図１０のフローチャートでは、位置（１）に作用するせん断力を計測し、当該せん断力が小さい場合は、「踵が曲がっていて（外反していて）、踵が外側に曲がらない状態」と判断して、それ抑制する体操や使用器具を提示する。 Still another example of processing using the analysis apparatus 20 shown in FIG. 6 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.
　図１０において、ステップＳ３１では、センサ１により位置（１）に作用するせん断力を計測する。そしてステップＳ３２に進む。
　ステップＳ３２では、ステップＳ３１で計測した位置（１）に作用するせん断力がしきい値Ｎ以下か否かを判断する。ここで、しきい値Ｎは、外反に関する蓄積されたデータと、被験者の計測データに基づいて、総合的に決定される。
　ステップＳ３２で、位置（１）に作用するせん断力がしきい値Ｎ以下の場合は（ステップＳ３２が「Ｙｅｓ」）、ステップＳ３３に進む。
　一方、ステップＳ３２で、位置（１）に作用するせん断力がしきい値Ｎより大きい場合は（ステップＳ３２が「Ｎｏ」）、制御を終了する。 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.
　ステップＳ３３（位置（１）に作用するせん断力がしきい値Ｎ以下の場合）は、被験者の「踵が曲がっており（外反している）、踵が硬くて外側（小指側）に曲がらない状態」と判断する。そしてステップＳ３４に進む。
　ここで、踵が硬く外側に曲がらない状態では、膝にストレスが掛かり、痛みが発症する恐れがある。そのため、ステップＳ３４では、踵が硬く外側に曲がらないため、膝にストレスが掛かり、痛みが発症する恐れがある場合の改善策或いは対処方法を提示する。
　ステップＳ３４では、例えば、踵の外側に隙間のあるインソール或いは靴を提示する。靴或いはインソールにおいて、靴の外側の高さ、内側の高さ或いは踵自体の高さを調節することにより、踵の動きを制限し、正常な重心線に近づけることが出来る。そのため、膝の痛みも低減する。 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.
　また図示はしないが、図示の実施形態であれば、外反母趾についても、それを改善することが出来る。
　外反母趾或いはその傾向がある場合には、位置（７）に大きな荷重が掛かり、位置（３）で地面を強く蹴っている。そのため、位置（５）における地面を蹴る力を抑制し、位置（７）に係る荷重が適正になる様に靴やインソール等を工夫し、器具を提案し、或いは、位置（５）における地面を蹴る力を抑制し、位置（７）に係る荷重が適正になる様な運動プログラムを提案することが出来る。 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.
　図示の実施形態に係る足裏計測装置１００によれば、インソール１０（或いは靴）の足裏と接触する部材にセンサ１～７を設けることにより検出部を構成しているので、装置全体を小型化することが出来る。
　そのため、大型装置の様に被測定者に余計なストレスを与えてしまうことはなく、正確な計測が可能である。また、小型化された装置であるので、足裏計測装置１００を着用或いは装着した状態で運動することが出来る。そのため、運動している中で（例えば歩行中に）、位置（１）～（７）（センサ１～７を配置）に作用する力（せん断力或いは圧力）を直接計測することが可能である。そのため、従来技術の様に、静止した状態の足裏圧力から歩行中の足裏圧力を推定する必要はない。
　特に、図示の実施形態では、センサ１～７の出力を解析装置２０に対して無線で送信しているので、有線で計測結果を送信する場合に比較して、被験者が運動中（例えば歩行中）における計測結果の送信が容易である。 According to the sole measuring apparatus 100 according to the illustrated embodiment, the detection unit is configured by providing the sensors 1 to 7 on the member that comes into contact with the sole of the insole 10 (or shoes). Can be
Therefore, the measurement subject is not subjected to excessive stress unlike a large-sized device, and accurate measurement is possible. Moreover, since it is a miniaturized device, it is possible to exercise with the sole measuring device 100 worn or worn. Therefore, it is possible to directly measure the force (shearing force or pressure) acting on the positions (1) to (7) (sensors 1 to 7 are arranged) while exercising (eg during walking). . Therefore, unlike the prior art, there is no need 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 wirelessly transmitted to the analysis device 20, so that the subject is exercising (for example, walking) compared to the case where the measurement result is transmitted by wire. ) Is easy to transmit the measurement results.
　また図示の実施形態では、踵骨***部（位置１）、立方骨（位置２）、第五中足骨頭（位置３）、第一中足骨頭（位置５）、中間楔状骨（位置６）、横足弓中心（位置７）と対応する位置にセンサを設けているので、各センサの計測値から足の重心点、アーチ（縦アーチＡＲ１、外アーチＡＲ２、横アーチＡＲ３）、足の骨軸を決定することが出来る。
　そして、足の重心点の軌跡である「足の重心線」も容易に求めることが出来る。
　足の重心線、アーチ（横アーチ、縦アーチ、外アーチ）、足の骨軸を決定することにより、変形性膝関節症や外反拇指以外の異常の有無を判断して、当該異常を矯正或いは抑制する様な器具、運動を提案することが可能である。
　そして、変形性膝関節症や外反拇指以外の各種異常を判断するパラメータとして、足の重心線、アーチ、足の骨軸という足圧分布以外のパラメータを用いることが出来る。 In the illustrated embodiment, the rib ridge (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). Since the sensor is provided at a position corresponding to the center of the lateral foot arch (position 7), the center of gravity of the foot, the arch (the vertical arch AR1, the outer arch AR2, the lateral arch AR3), and the bone of the foot from the measured values of each sensor Axis can be determined.
Then, the “foot barycentric line” that is the trajectory of the barycentric point can be easily obtained.
By determining the barycentric line, arch (lateral arch, vertical arch, external arch), and bone axis of the foot, it is possible to determine whether there is an abnormality other than knee osteoarthritis or a hallux phalanx and correct the abnormality. Alternatively, it is possible to propose a device or exercise that can be suppressed.
As parameters for determining various abnormalities other than knee osteoarthritis and hallux phalanges, parameters other than foot pressure distribution such as foot center of gravity, arch, and foot bone axis can be used.
　ここで、拇指接地面（位置４）における圧力値が大きい場合には、歩行に際して足指が有効に使われており、地面を蹴り出す力が大きいことを意味している。従って、その他の条件が同じであれば、拇指接地面（位置４）における圧力値が大きい場合には、歩幅が大きく、歩行速度が速く、クリアランス（歩行中のつま先と接地面との距離）も大きいことになる。そのため、歩行が安定しており、歩行時の転倒の危険性が少ない。
　図示の実施形態においては、拇指接地面（位置４）にセンサ４を設けているので、当該センサ４（位置４）の計測結果から、歩行機能が判定され、歩行時に転倒する可能性を判断することが出来る。 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. 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 (the distance between the toe and the contact surface during walking) is also large. It will be big. 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 is determined from the measurement result of the sensor 4 (position 4), and the possibility of falling down during walking is determined. I can do it.
　そして図示の実施形態では、位置（６）と位置（２）に作用する力の計測値から、被験者が「扁平足」、「正常」、「ハイアーチ」の何れに該当するのかを特定出来る。
　さらに、位置（２）、（３）側に作用する力の計測値から、「アーチが硬く歩行中に膝が捻じれる」か否かを判断することが出来て、それ抑制する運動、使用器具も併せて提示することが出来る。
　それに加えて、位置（１）に作用するせん断力の計測値から、「踵が曲がっていて（外反していて）、踵が外側に曲がらない状態」であるか否かを判断することが出来て、それ抑制する使用器具を提示することが出来る（図１０）。 In the illustrated embodiment, it is possible to specify whether the subject corresponds to “flat foot”, “normal”, or “high arch” from the measurement value of the force acting on the position (6) and the position (2).
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.
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).
　図示の実施形態はあくまでも例示であり、本発明の技術的範囲を限定する趣旨の記述ではないことを付記する。
　例えば、図５では外反の場合を示しているが、本発明では内反に対しても対応することが出来る。 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.
１～７（Ｒ１～Ｒ７、Ｌ１～Ｌ７）・・・センサ
（１）～（７）、（Ｒ１）～（Ｒ７）、（Ｌ１）～（Ｌ７）・・・センサの位置
１０、１０Ｒ、１０Ｌ・・インソール（或いは靴）
２０・・・解析装置
２０Ａ・・・重心点決定ブロック
２０Ｂ・・・重心線決定ブロック
２０Ｃ・・・アーチ決定ブロック
２０Ｄ・・・骨軸決定ブロック
２０Ｅ・・・判定ブロック
２０Ｆ・・・記憶ブロック
２０Ｉ・・・入力側インターフェース
２０Ｏ・・・出力側インターフェース
３０・・・表示装置
４０・・・判定装置
１００・・・足裏計測装置
ＡＲ１・・・縦アーチ
ＡＲ２・・・外アーチ
ＡＲ３・・・横アーチ
Ｆ・・・足
Ｌ・・・脚部
ＩＬ１～ＩＬ１２・・・情報信号ライン
ＳＲ１、ＳＬ１・・・無線信号ライン 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)
DESCRIPTION OF SYMBOLS 20 ... Analyzing device 20A ... Centroid point determination block 20B ... Centroid line 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 ... Sole measuring device AR1 ... Vertical arch AR2 ... Outer arch AR3 ... Horizontal Arch F ... Leg L ... Legs IL1-IL12 ... Information signal line SR1, SL1 ... Radio signal line

Claims (4)

  1. 　足の裏が接触する部材の踵骨***部、立方骨、第五中足骨頭、第一中足骨頭、中間楔状骨、横足弓中心に対応する位置にセンサを設けたことを特徴とする足裏計測装置。 A sensor is provided at a position corresponding to the rib raised portion, the cubic bone, the fifth metatarsal head, the first metatarsal head, the intermediate cuneiform bone, and the lateral foot arch center of the member that contacts the sole of the foot Foot measurement device.
  2. 　拇指接地面にセンサを設けた請求項１の足裏計測装置。 The foot sole measuring device according to claim 1, wherein a sensor is provided on the ground contact surface.
  3. 　前記センサは、その出力を解析装置に対して無線で送信する請求項１、２の何れか１項の足裏計測装置。 The sole measuring device according to any one of claims 1 and 2, wherein the sensor transmits its output wirelessly to the analyzing device.
  4. 　位置踵骨***部、立方骨、第五中足骨頭、第一中足骨頭、横足弓中心に対応する位置に設けられるセンサはせん断力センサである請求項１～３の何れか１項の足裏計測装置。 4. The sensor according to claim 1, wherein the sensor provided at a position corresponding to the position of the raised rib, the cubic bone, the fifth metatarsal head, the first metatarsal head, and the lateral foot arch is a shear force sensor. Foot measurement device.
PCT/JP2017/044821 2016-12-16 2017-12-14 Sole measurement device WO2018110621A1 (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2016-244460 2016-12-16
JP2016244460A JP2018094304A (en) 2016-12-16 2016-12-16 Sole measuring instrument

Publications (1)

Publication Number Publication Date
WO2018110621A1 true WO2018110621A1 (en) 2018-06-21

Family

ID=62559737

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2017/044821 WO2018110621A1 (en) 2016-12-16 2017-12-14 Sole measurement device

Country Status (2)

Country Link
JP (1) JP2018094304A (en)
WO (1) WO2018110621A1 (en)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP7191658B2 (en) * 2018-11-22 2022-12-19 テルモ株式会社 Information processing device and information processing method

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140230563A1 (en) * 2013-02-13 2014-08-21 Board Of Regents, The University Of Texas System Sensor assembly, method, and device for monitoring shear force and pressure on a structure

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140230563A1 (en) * 2013-02-13 2014-08-21 Board Of Regents, The University Of Texas System Sensor assembly, method, and device for monitoring shear force and pressure on a structure

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
YAMASHITA, KAZUHIKO: "Quantitative body function measuring device'' of fall risk assessment tool, and needs for standardizing fall risk assessment tool", JOURNAL OF THE SOCIETY OF BIOMECHANISMS, vol. 38, no. 4, 2014, pages 245 - 251 *

Also Published As

Publication number Publication date
JP2018094304A (en) 2018-06-21

Similar Documents

Publication Publication Date Title
Souza An evidence-based videotaped running biomechanics analysis
US9591998B2 (en) Gait analysis system and methods
US11666244B2 (en) Foot sole pressure measurement instrument, information provision device, and information provision method
KR101447652B1 (en) Shoe insole, shoe having the same, and walking form correction system
EP1863385A2 (en) Method and appartus for displaying 3d images of a part of the skeleton
JP2015202141A (en) Method for evaluating gait
WO2018110621A1 (en) Sole measurement device
WO2018110622A1 (en) Foot region abnormality analysis device and method
JP6193847B2 (en) Orthopedic disease risk evaluation system and information processing apparatus
KR102285315B1 (en) Foot pressure analyzer
WO2014049639A1 (en) Foot pressure distribution measurement system and information processing device
JP2019150229A (en) Foot part analyzer and method
JP5956254B2 (en) Load distribution measurement system, information processing apparatus, and information processing method
KR101963624B1 (en) System and method for evaluation of exercise capacity of knee
WO2018110624A1 (en) Fall analysis system and analysis method
KR20210014232A (en) Rehabilitating method using food pressure analysis
WO2018159731A1 (en) Gait analyzing system
KR101806988B1 (en) Swing correcting apparatus
JP7031467B2 (en) Display system and display method
US20240000378A1 (en) System and method for quantifying an injury recovery state
Luczak Impact of shoe design on basketball performance and the application of soft sensors to improve dynamic fit
AU2016202577A1 (en) Gait analysis system and methods
JP6601268B2 (en) Foot load calculation device
Razak et al. Wireless Sensors Integration for Bend Angle and Distance Rate of Gait Measurement
AU2014201892A1 (en) Gait analysis system and methods

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 17880854

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 17880854

Country of ref document: EP

Kind code of ref document: A1