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WO2013073677A1 - Capteur capacitif - Google Patents

Capteur capacitif Download PDF

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Publication number
WO2013073677A1
WO2013073677A1 PCT/JP2012/079822 JP2012079822W WO2013073677A1 WO 2013073677 A1 WO2013073677 A1 WO 2013073677A1 JP 2012079822 W JP2012079822 W JP 2012079822W WO 2013073677 A1 WO2013073677 A1 WO 2013073677A1
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WO
WIPO (PCT)
Prior art keywords
muscle
electrode
support member
belt
sensor
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/JP2012/079822
Other languages
English (en)
Japanese (ja)
Inventor
俊司 諸麥
隆和 石松
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Tomei Brace Co Ltd
Nagasaki University NUC
Original Assignee
Tomei Brace Co Ltd
Nagasaki University NUC
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 Tomei Brace Co Ltd, Nagasaki University NUC filed Critical Tomei Brace Co Ltd
Publication of WO2013073677A1 publication Critical patent/WO2013073677A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
    • G01L1/00—Measuring force or stress, in general
    • G01L1/14—Measuring force or stress, in general by measuring variations in capacitance or inductance of electrical elements, e.g. by measuring variations of frequency of electrical oscillators
    • G01L1/142—Measuring force or stress, in general by measuring variations in capacitance or inductance of electrical elements, e.g. by measuring variations of frequency of electrical oscillators using capacitors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring 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 or mobility of a limb
    • A61B5/1107—Measuring contraction of parts of the body, e.g. organ or muscle
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A61B5/6803—Head-worn items, e.g. helmets, masks, headphones or goggles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F4/00—Methods or devices enabling patients or disabled persons to operate an apparatus or a device not forming part of the body
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06F—ELECTRIC DIGITAL DATA PROCESSING
    • G06F3/00—Input arrangements for transferring data to be processed into a form capable of being handled by the computer; Output arrangements for transferring data from processing unit to output unit, e.g. interface arrangements
    • G06F3/01—Input arrangements or combined input and output arrangements for interaction between user and computer
    • G06F3/011—Arrangements for interaction with the human body, e.g. for user immersion in virtual reality
    • G06F3/015—Input arrangements based on nervous system activity detection, e.g. brain waves [EEG] detection, electromyograms [EMG] detection, electrodermal response detection
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0209—Special features of electrodes classified in A61B5/24, A61B5/25, A61B5/283, A61B5/291, A61B5/296, A61B5/053
    • A61B2562/0214—Capacitive electrodes

Definitions

  • the present invention relates to a capacitive sensor that detects the movement of muscles in a predetermined part of the human body.
  • An electric power glove is a powered glove that realizes a free gripping operation with a paralyzed finger.
  • the gripping device (glove part) worn on the user's hand and the gripping device are driven via a transmission mechanism.
  • a push button switch attached to the glove is pressed against a desk, or a surface myoelectric potential to detect a weak electric signal accompanying muscle activity from an electrode attached to the body surface.
  • BCI Brain-Computer Interface
  • the push button type is limited to the operation of grasping and releasing the object placed on the table, and in the surface EMG measurement, the hair such as the head is shaved or a special gel is applied. Such a complicated treatment was necessary.
  • the BCI method has problems such as low recognition rate, long training time, and troublesome wearing as in the case of myoelectric potential measurement, and has not been widely used as a means for daily device operation. Therefore, as an operation input means for solving the problems of these methods, an interface used for extracting an activity amount of the head voluntary muscle by detecting a partial change in the shape of the head and using it as an operation input of the grasping device is attracting attention. Yes.
  • a belt provided with a capacitive sensor is wound around a predetermined part of the human body, the movement of the muscles at this part is detected by the sensor, the motor is driven, and the gripping device is operated via the transmission mechanism. It is.
  • capacitance-type sensors are used as capacitive sensors, but the dielectric provided between the electrodes has a bubble structure that can be expanded or contracted so that it can be accurately contacted and attached to a soft part.
  • a capacitive pressure sensor has been proposed and used (see Patent Document 1).
  • the capacitive sensor described in Patent Document 1 has the following problems. That is, since a highly flexible material is used for the dielectric of the capacitive sensor, if the sensor is pressed against the muscle to be measured with an elastic belt, the sensor may be deformed by the pressing force of the belt was there. Further, the belt may be completely crushed depending on the pressing force of the belt. In such a case, there is a problem that the movement of the muscle cannot be accurately detected and the user's operation intention cannot be accurately reflected on the grasping device. On the other hand, if the belt is loosened in order to avoid deformation of the sensor due to the pressing force, the sensor may be displaced from the target part during use, or the belt itself may fall, which is stable. There is a problem that muscle movement cannot be detected in the state.
  • an object of the present invention is to provide a capacitive sensor capable of detecting a muscle movement based on a user's operation intention in a stable state and accurately. It is to provide.
  • the present invention is a capacitive sensor that detects the movement of a muscle, and includes a first electrode, a second electrode, and a first electrode that are arranged to face each other. Provided between the second electrode and a dielectric made of a deformable material, and a support member made of a material harder than the dielectric provided around the dielectric.
  • the support member made of a material harder than the dielectric is provided around the dielectric, the dielectric is supported by the support member even when the capacitive sensor is pressed by the belt or the like. can do. Thereby, a deformation
  • FIG. 6 is a cross-sectional view taken along the line AA of the capacitive sensor shown in FIG. 5.
  • FIG. 6 is a sectional view taken along line BB of the capacitive sensor shown in FIG.
  • the measurement data in the case where the ear is moved backward after the right back teeth are tightened is shown, and the old sensor without a support member and the non-stretchable belt are used.
  • the measurement data when the ear is moved backward after the right back tooth biting is shown is the case where the old sensor and the elastic belt without the support member are used.
  • the measurement data in the case where the ear is moved backward after the right back tooth is tightened is shown, and the capacitance type sensor and the non-stretchable belt according to the present invention are used.
  • the measurement data in the case where the ear is moved backward after the right back teeth are tightened are shown, and the capacitance type sensor and the elastic belt according to the present invention are used. It is measurement data at the time of measuring the right temporal muscle by changing the belt tension using the capacitive sensor according to the present invention and the old sensor without a support member, respectively.
  • FIG. 1 shows an example of a schematic configuration of a power globe PG according to an embodiment of the present invention.
  • 1, 2, 3, 4 A, 4 B, 4 C, 5, 6 A, and 6 B are expanded for convenience of explanation and are different from the actual ratio.
  • the glove unit 600 only shows the thumb and index finger, but it is assumed that it is actually composed of five fingers.
  • the power globe PG includes an interface 200, a controller 300, a drive device 400, and a globe unit 600.
  • the interface 200 detects the user's operation intention from the movement of the user's muscles, and includes a stretchable belt 50 attached to the head and a plurality of capacitive sensors attached to the stretchable belt 50. 100.
  • the capacitive sensor 100 of the present invention has a soft surface that comes into contact with the skin, and a flexible sensor body. When the sensor is fixed by the elastic belt 50, the capacitive sensor 100 is curved along the curved surface of the head. Is deformed and comes into close contact with the head.
  • the bulge of the muscle according to the user's operation intention is detected, and the operation signal Sm obtained by this detection is supplied to the controller 300 via wiring or wireless communication. To do. Details of the interface 200 will be described later.
  • the controller 300 has, for example, a CPU (Central Processing Unit) and a ROM (Read Only Memory), and controls the operation of each unit such as the driving device 400 that constitutes the power globe PG. For example, the controller 300 performs a threshold determination process for the operation signal Sm supplied from the interface 200, and supplies a drive signal Sv for controlling the driving of the globe unit 600 to the drive device 400 according to the determination result of the determination process. .
  • a CPU Central Processing Unit
  • ROM Read Only Memory
  • the driving device 400 includes, for example, a motor and a movable portion 402 connected to the motor.
  • the driving device 400 drives and controls the transmission means 500 connected to the movable portion 402 by driving the motor based on the drive signal Sv supplied from the controller 300 to operate the movable portion 402.
  • the movable part 402 is composed of one set (two) on the assumption that the index finger of the glove part 600 is operated.
  • the movable part 402 is provided according to the number of fingers to be operated. Can do. The same applies to the transmission means described later.
  • the transmission unit 500 is a unit for transmitting the power generated by the driving device 400 to the globe unit 600, and includes a guide tube 502, an operation member 504, and an auxiliary support member 506.
  • the guide tube 502 is a flexible tube having a predetermined length. One end of the guide tube 502 is connected to the driving device 400 and the other end is attached to the back of the globe unit 600.
  • the operation member 504 is composed of, for example, a wire with high tension, and is laid along the inside of the guide tube 502. One end is attached to the movable part of the driving device 400 and the other end is at the tip of the index finger of the glove part 600. It is attached.
  • An auxiliary support member 506 for fixing the operation member 504 to the finger of the glove part 600 is provided at a portion exposed from the guide tube 502 of the operation member 504.
  • the auxiliary support member 506 is composed of, for example, a belt and a tube.
  • the operation member 504 is securely fixed to the finger by two sets of auxiliary support members 506.
  • FIG. 2 shows an example of a schematic configuration of the interface 200 according to the present invention
  • FIG. 3 shows a state in which the interface 200 is mounted on the user's head.
  • the interface 200 includes an elastic belt 50 and a plurality of capacitive sensors 100.
  • the stretchable belt 50 has a width at which at least the capacitance type sensor 100 can be attached, and the capacitance type sensor 100 is stably held on the head when worn on a human head,
  • the support member 108 of the capacitive sensor 100 is constituted by a belt adjusted to a belt tension so as not to be excessively deformed.
  • the plurality of capacitive sensors 100 are fixedly attached to the inside of the elastic belt 50 so as to be positioned on the muscle to be measured on the head.
  • the electrostatic capacitance type sensor 100 is attached to the stretchable belt 50.
  • Various methods can be employed for the attachment to the elastic belt 50. For example, an attachment button or a hook-and-loop fastener may be used, or direct sewing may be performed.
  • FIGS. 4A to 4C the left temporal muscle M1, the right temporal muscle M2, and the posterior pinna muscle M3 are indicated by hatching.
  • the left temporal muscle M1 and the right temporal muscle M2 are located slightly above and behind the left and right temples of the head.
  • the left temporal muscle M1 and the right temporal muscle M2 are also active during chewing and jaw movement associated with speech, but by correctly selecting the fixed position using the capacitive sensor 100 of the present invention, It is possible to extract only the biting operation by distinguishing between utterance and biting.
  • the posterior pinna muscle M3 is located in the rear part of the ear as shown in FIG. 4C.
  • the posterior pinna muscle M3 is a muscle that can be freely moved among the muscles in the head in addition to the left temporal muscle M1 and the right temporal muscle M2. This muscle is used to move the ears, and is well developed in animals such as cats and horses.
  • Other pinna muscles include the anterior pinna muscle, the upper pinna muscle, etc., but the posterior pinna muscle M3 is particularly voluntary in humans, and it is possible to move the ear back and forth by using this muscle. There are many people who can do it. It is also known that many people can move their ears freely by training.
  • FIG. 5 shows an example of the configuration of the capacitive sensor 100.
  • 6A is a cross-sectional view taken along the line AA of the capacitive sensor 100 of FIG. 5
  • FIG. 6B is a cross-sectional view taken along the line BB of the capacitive sensor 100 of FIG.
  • the side facing the muscle to be measured by the capacitive sensor 100 is referred to as a contact surface.
  • the capacitive sensor 100 includes a first electrode 102, a second electrode 104, a dielectric 106, a support member 108, a base plate 110, an insulating layer 112, a shield layer 114, and a cover. 116.
  • the capacitance type sensor 100 has a size of, for example, 50 mm ⁇ 70 mm ⁇ 8 mm.
  • Each of the first electrode 102 and the second electrode 104 is composed of a substantially rectangular conductive member having predetermined thicknesses d1 and d2, and is disposed so as to face each other with a dielectric 106 interposed therebetween.
  • the first electrode 102 is made of, for example, a conductive cloth, and is attached to the surface on the contact surface side of the dielectric 106.
  • the second electrode 104 is made of, for example, a copper foil tape, and is attached to a surface opposite to the contact surface of the dielectric 106.
  • the dielectric 106 has a predetermined thickness d3 and is configured with substantially the same outer shape as the first electrode 102 and the like, and is disposed in a state of being sandwiched between the first electrode 102 and the second electrode 104.
  • urethane foam sponge
  • the hardness of the dielectric 106 is preferably 7 to 15 (kg / 314 cm 2 ), for example.
  • the base plate 110 is made of, for example, a sheet-like insulating member such as plastic that is harder than the material of the support member 108, and has an outer shape that is slightly larger than that of the second electrode 104.
  • the second electrode 104 is attached to the surface on the contact surface side of the base plate 110.
  • the second electrode 104 is affixed on the base plate 110 such that a space (projecting portion) S having a predetermined width is provided at the peripheral edge of the base plate 110.
  • a space S protruding from the second electrode 104 is a region for arranging a support member 108 described later.
  • one end of the shield cable 118 is fixed.
  • the other end of the shielded cable 118 is connected to the controller 300 (see FIG. 1).
  • Two core wires 120 and a shield wire 121 are drawn from one end of the shield cable 118, the core wires 120 are routed to the first electrode 102 and the second electrode 104, respectively, and the shield wire 121 is further routed to the shield layer 114. Connected.
  • the support member 108 is pasted on the space S of the base plate 110 so as to border the entire periphery of the dielectric 106, the first electrode 102, and the second electrode 104 (see FIG. 5). At this time, the support member 108 is attached to the dielectric 106, the first electrode 102, and the second electrode 104 with a slight gap therebetween, and is not in contact with the dielectric 106 or the like. For example, when a part of the skin rises with the activity of the muscle to be measured, the support member 108 surrounds the outer peripheral edge in correspondence with a region on the raised skin (hereinafter referred to as a measurement target site). You may form as follows. For example, as shown in FIG.
  • the deformation region of the left temporal muscle M1 is a region T surrounded by a dotted line as a measurement target
  • the deformation of the muscle to be measured is placed inside the outer frame formed of the support member 108.
  • the support member 108 is formed so that the region T is accommodated. This makes it possible to accurately detect local muscle uplift.
  • the end surface on the contact surface side of the support member 108 may be molded along the surface shape of the measurement target site.
  • the thickness d4 of the support member 108 is preferably selected to be equal to or less than the total thickness d1 + d2 + d3 obtained by adding the thickness d1 of the first electrode 102, the thickness d2 of the second electrode 104, and the thickness d3 of the dielectric 106, respectively. This is to ensure that the dielectric 106 is deformed along its shape when the contact surface of the capacitive sensor 100 comes into contact with the measurement target site. Of course, even if it is larger than the thickness d1 + d2 + d3, it can be measured depending on the shape of the measurement target part.
  • the support member 108 is deformed moderately and conforms to the shape of the measurement target portion.
  • a material having such a hardness that the thickness of the dielectric 106 can be kept almost constant without being largely crushed is used.
  • the support member 108 a material having higher hardness (lower flexibility) than the dielectric 106 in the center is used, and for example, polyethylene foam is preferably used.
  • the hardness of the support member 108 is preferably, for example, 35 or more and 70 or less as measured by a durometer hardness meter C type.
  • the reason for the above hardness is that when the hardness is less than 35, the center dielectric or the like is deformed due to belt tension or the like, and when the hardness is more than 70, the sensor forms the shape of the measurement target part at the time of measurement. It is because it does not follow.
  • any material other than polyethylene foam can be used as long as the material has a hardness within the above range. If the area to be measured is small or close to a flat surface and does not need to be deformed according to the shape of the area to be measured, a plastic is provided after considering that there is no pain by providing an appropriate cushion on the contact surface side. It is also possible to form the support member 108 with a hard material having a hardness higher than the above hardness range, such as aluminum or aluminum.
  • the insulating layer 112 is selected to have substantially the same outer shape as the base plate 110 and is attached to the upper surfaces of the first electrode 102 and the support member 108.
  • the insulating layer 112 is made of a thin and flexible material, and is made of a material such as a rubber material or a cloth.
  • a shield layer 114 is wound around the outer periphery of the base plate 110, the support member 108, and the insulating layer 112 so as to cover all of them.
  • the shield layer 114 is made of, for example, a conductive cloth and has a function of shielding the entire capacitive sensor 100 from the outside.
  • the shield layer 114 is attached to the outer surface side of the base plate 110 with an adhesive or the like.
  • the outer peripheral portion of the shield layer 114 is further covered with a cloth cover 116, so that the entire capacitive sensor 100 is protected by the cover 116.
  • the support member 108 can be mounted even when the elastic belt 50 is attached to the head. Since the base plate 110 is supported, it is possible to prevent deformation such as collapse of the center dielectric 106 due to belt tension (pressing force) of the stretchable belt 50. As a result, the dielectric 106 can be held at a substantially constant thickness, and only the bulge of the muscle due to the user's intention to operate can be detected in a precise and stable state. In addition, since the dielectric 106 in the center, which is a detection unit of the muscle protrusion, is made of a highly flexible material, it can cope with various muscles having different curvatures.
  • the support member 108 is made of a material that is moderately deformed and conforms to the shape of the measurement target portion when a person wraps the elastic belt 50 with an appropriate force and fixes the capacitive sensor 100, Pain to the user's head when wearing the interface 200 can be minimized.
  • a plurality of capacitive sensors 100 when a plurality of capacitive sensors 100 are attached to the stretchable belt 50, even if the belt tension is increased by raising somewhere in the head, In the capacitive sensor 100, the effect of the belt tension can be absorbed by the action of the support member 108. Therefore, a plurality of capacitive sensors 100 can be attached to the stretchable belt 50, so that Detection of muscle uplift becomes possible.
  • the support member 108 of the capacitive sensor 100 is provided so as to surround the outer periphery of the deformation region of the muscle to be measured, a small muscle such as the posterior auricular muscle M3 or the like is provided. It is possible to accurately detect local muscle bumps. That is, conventionally, when the surrounding muscles increased, the belt tension increased accordingly, and only the bulging of the posterior pinna muscle M3 could not be detected, but by adopting the outer frame structure as in the present invention, Since only the muscle to be measured is accommodated in the outer frame (support member 108), only the muscle bulge inside the outer frame can be detected without being affected by the bulge of the surrounding muscles.
  • the interface 200 including the three capacitive sensors 100 according to the present invention is attached to the subject's head, (a) right back teeth biting, (b) left back teeth biting, (c) ears.
  • the three operations of moving the rearward are performed 100 times in order, and measurement data corresponding to each of the two operations of the measurement data is extracted as a sample.
  • the three capacitive sensors 100 were attached at positions corresponding to the left temporal muscle M1, the right temporal muscle M2, and the posterior pinna muscle M3.
  • 7A to 7C are sampled measurement results
  • FIG. 7A is a graph showing the measurement result of the right temporal muscle
  • FIG. 7B is a graph showing the measurement result of the left temporal muscle
  • FIG. It is a graph which shows the measurement result of auricular muscle.
  • 7A to 7C the vertical axis represents the capacitance, and the horizontal axis represents time.
  • FIG. 8 shows the detection results of each subject when three operations of (a) right back tooth biting, (b) left back tooth biting, and (c) moving the ear backward are performed 100 times in order. .
  • the right bite, left bite, and ear movement were detected with an accuracy of 95.2%, 92.4%, and 91.6%, respectively.
  • the overall average value is 93.1%, and it was confirmed that the interface 200 can detect three types of operation signals with high accuracy.
  • the interface 200 including the three capacitive sensors 100 according to the present invention is mounted on the subject's head, and the right back teeth, left back teeth, and ear movement are designated. Operations were performed simultaneously in combination, and whether or not the operation signals based on the respective operations could be generated independently as intended without being affected was measured.
  • FIG. 9 shows instructions such as “move the ear in the middle with the right chewing”, “move the ear in the middle with the left chewing”, and “move the ear in the middle with both the left and right back teeth tightened”. The measurement results when given in order are shown.
  • FIG. 10 shows the measurement results when the subject is instructed to perform the operations of gradually tightening the right biting and the left biting and then gradually weakening them while overlapping each other.
  • the level of the operation signal (capacitance) detected by the capacitive sensor 100 also shows the same pattern. Specifically, After gradually increasing, it gradually decreased. Similarly, when the left biting is gradually strengthened and then gradually weakened, the level of the operation signal (capacitance) detected by the capacitive sensor 100 also gradually increases and then gradually decreases. . Thus, it was confirmed that the operation signals independent from the left temporal muscle M1 and the right temporal muscle M2 can be generated while operating the strength.
  • a capacitive sensor 100 (hereinafter referred to as a new sensor) of the present invention having a frame structure for the purpose of extracting only the change in the belt tension and extracting the shape change of the muscle to be measured.
  • the following experiment was conducted to compare the influence of the elasticity of the fixed belt on the measurement results with the old sensor and the new sensor in consideration of multi-point measurement.
  • An interface including two sensors fixed to positions corresponding to the right temporal muscle and right posterior pinna of the subject is attached to the subject's head, and about 2 seconds after 2 seconds from the start of the experiment to the subject.
  • the right back teeth were tightened, and the signal was measured when instructed to move the ear backward for about 2 seconds after 6 seconds.
  • the back teeth were tightened to 75 [N] and the ear movement was maximized.
  • Two types of sensors, an old sensor and a new sensor, were used.
  • the old sensor is substantially in common with the new structure except that there is no support member.
  • Two types of belts for fixing the sensor were used: a stretchable belt and a non-stretchable belt.
  • FIG. 11A shows an experimental result when an old sensor is used as a sensor and a non-stretchable belt is used as a belt.
  • FIG. 11B shows experimental results when an old sensor is used as the sensor and a stretchable belt is used as the belt.
  • FIG. 12A shows the experimental results when a new sensor is used as a sensor and a non-stretchable belt is used as a belt.
  • FIG. 12B shows the experimental results when a new sensor is used as a sensor and a stretchable belt is used as a belt.
  • the vertical axis is plotted in the range of 0.5 [pF] for the right temporal muscle and the right posterior auricular muscle.
  • the stability of the sensor with respect to the measurement target region is increased, and only the bulge of the muscle inside the support member is detected. This is thought to be due to stable and selective detection. Furthermore, since a significant change in belt tension can be suppressed by using an elastic belt, it is considered that the belt tension always remains within a range where the sensors do not interfere with each other.
  • the contraction of the right temporal muscle and the posterior pinna was detected independently only by the combination of the new sensor and the elastic belt. If the change in belt tension is too great even with the new sensor, interference may not be suppressed with the non-stretchable belt. Therefore, the new sensor employs an elastic belt for fixing.
  • FIG. 13 shows an example of the relationship between the difference in electrostatic capacity at the time of occlusion and weakness of the new sensor and the old sensor and the belt tension.
  • the vertical axis represents the difference between the capacitance at the time of occlusion and the weakness
  • the horizontal axis represents the belt tension.
  • the threshold for the amount of increase from the weakness of the electrostatic capacity at the time of occlusion is set to 0.05 [pF], for example. In this case, the tightening can be detected at a belt tension where the difference in capacitance between occlusion and weakness is 0.05 [pF] or more.
  • the range of belt tension that can be reliably measured with the conventional sensor is 1.47 to 2.45 [N]
  • the range of belt tension that can be reliably measured with the new sensor is 3.92. It was confirmed to be ⁇ 9.8 [N]. From this measurement result, the belt tension range is 0.98 [N] for the old sensor, 5.88 [N] for the new sensor, and the new sensor allows six times as much. It has been found that the range of belt tension is widened. This is because the new sensor is provided with a support member, so that even if a predetermined belt tension acts, the support member prevents the central portion from being deformed.
  • the interface 200 according to the present invention can be applied not only as the power glove PG described above but also as input operation means of various other devices because it can be easily attached and detached.
  • the stretchable belt 50 is used as the belt constituting the interface 200, a non-stretchable belt provided with a hook-and-loop fastener can also be used.
  • the support member 108 is configured by a substantially rectangular frame.
  • the support member 108 may be circular or elliptical according to the shape of the measurement target region.
  • the support member 108 is composed of a continuous frame.
  • the support member 108 may be composed of a plurality of members, and these members may be arranged along the outer peripheral portion of the dielectric 106 at a predetermined interval.
  • a total of three channels of operation signals of the left temporal muscle M1, the right temporal muscle M2, and one posterior pinna muscle M3 are output.
  • the present invention is not limited to this.
  • DESCRIPTION OF SYMBOLS 100 ... Capacitance type sensor, 102 ... 1st electrode, 104 ... 2nd electrode, 106 ... Dielectric material, 108 ... Support member, 110 ... Base plate (base member) ), 200 ... Interface, 300 ... Controller, 400 ... Drive device, 500 ... Transmission means, 600 ... Glove part, PG ... Power glove

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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

La présente invention concerne la détection stable et précise d'un mouvement musculaire sur la base d'une intention opérationnelle d'un utilisateur. Une interface placée sur la tête de l'utilisateur comprend une bande extensible et un capteur capacitif (100). Le capteur capacitif (100) comprend : une première électrode (102) et une seconde électrode (104) disposées l'une en face de l'autre ; un matériau diélectrique (106) disposé entre la première électrode (102) et la seconde électrode (104) ; et un organe de support (108) placé de façon à entourer la périphérie de la première électrode (102), de la seconde électrode (104) et du matériau diélectrique (106). L'organe de support (108) est composé d'un matériau plus dur que le matériau diélectrique (106). Ceci permet d'éviter une déformation, par exemple l'écrasement du matériau diélectrique (106) se trouvant au centre à cause de la tension (force de pression) de la bande extensible (50), même quand la bande extensible est placée sur la tête, car l'organe de support (108) supporte une plaque de base (110).
PCT/JP2012/079822 2011-11-18 2012-11-16 Capteur capacitif Ceased WO2013073677A1 (fr)

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JP2011252868 2011-11-18

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018011464A1 (fr) * 2016-07-11 2018-01-18 Forciot Oy Capteur de force et/ou de pression
JP2018175030A (ja) * 2017-04-04 2018-11-15 学校法人 中央大学 頭部筋活動検知装置
WO2021115563A1 (fr) * 2019-12-10 2021-06-17 Brainlab Ag Procédé et appareil de détermination de décalage d'organe interne

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JPS61115941U (fr) * 1984-12-28 1986-07-22
JPH04225385A (ja) * 1990-12-26 1992-08-14 Shuzo Ito 身体障害者用意志伝達方法
JPH11206740A (ja) * 1998-01-29 1999-08-03 Nagano Keiki Co Ltd 咀嚼回数計
WO2006030405A1 (fr) * 2004-09-14 2006-03-23 University Of Limerick Dispositif a transducteur pour mesurer des pressions biomedicales
JP2006129885A (ja) * 2004-11-02 2006-05-25 Yoshimichi Yonezawa 咀嚼運動検出装置
JP2010029633A (ja) * 2008-06-30 2010-02-12 Tokai Rubber Ind Ltd 筋肉動の検出方法および筋肉動検出装置

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Publication number Priority date Publication date Assignee Title
JPS61115941U (fr) * 1984-12-28 1986-07-22
JPH04225385A (ja) * 1990-12-26 1992-08-14 Shuzo Ito 身体障害者用意志伝達方法
JPH11206740A (ja) * 1998-01-29 1999-08-03 Nagano Keiki Co Ltd 咀嚼回数計
WO2006030405A1 (fr) * 2004-09-14 2006-03-23 University Of Limerick Dispositif a transducteur pour mesurer des pressions biomedicales
JP2006129885A (ja) * 2004-11-02 2006-05-25 Yoshimichi Yonezawa 咀嚼運動検出装置
JP2010029633A (ja) * 2008-06-30 2010-02-12 Tokai Rubber Ind Ltd 筋肉動の検出方法および筋肉動検出装置

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018011464A1 (fr) * 2016-07-11 2018-01-18 Forciot Oy Capteur de force et/ou de pression
JP2019522804A (ja) * 2016-07-11 2019-08-15 フォルシオット オイＦｏｒｃｉｏｔ Ｏｙ 力および／または圧力センサ
JP2020024231A (ja) * 2016-07-11 2020-02-13 フォルシオット オイＦｏｒｃｉｏｔ Ｏｙ 力および／または圧力センサ
US10591367B2 (en) 2016-07-11 2020-03-17 Forciot Oy Capacitive force and/or pressure sensor having stretchable electrodes
EP3623784A1 (fr) * 2016-07-11 2020-03-18 Forciot OY Capteur capacitif de force et/ou de pression
CN112525390A (zh) * 2016-07-11 2021-03-19 富西特有限公司 力和/或压力传感器
JP7018208B2 (ja) 2016-07-11 2022-02-10 フォルシオット オイ 力および／または圧力センサ
CN112525390B (zh) * 2016-07-11 2022-08-02 富西特有限公司 力和/或压力传感器
JP2018175030A (ja) * 2017-04-04 2018-11-15 学校法人 中央大学 頭部筋活動検知装置
WO2021115563A1 (fr) * 2019-12-10 2021-06-17 Brainlab Ag Procédé et appareil de détermination de décalage d'organe interne

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