WO1987001574A1 - Evaluation des phases de la marche - Google Patents

Evaluation des phases de la marche Download PDF

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Publication number
WO1987001574A1
WO1987001574A1 PCT/IT1986/000070 IT8600070W WO8701574A1 WO 1987001574 A1 WO1987001574 A1 WO 1987001574A1 IT 8600070 W IT8600070 W IT 8600070W WO 8701574 A1 WO8701574 A1 WO 8701574A1
Authority
WO
WIPO (PCT)
Prior art keywords
pressure
layer
conductive paths
lines
matrix
Prior art date
Application number
PCT/IT1986/000070
Other languages
English (en)
Inventor
Massimiliano Bugarini
Pietro Chistolini
Luciano Da Cas
Velio Macellari
Original Assignee
Istituto Superiore di Sanità
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 Istituto Superiore di Sanità filed Critical Istituto Superiore di Sanità
Publication of WO1987001574A1 publication Critical patent/WO1987001574A1/fr

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Classifications

    • 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
    • A61B5/1036—Measuring load distribution, e.g. podologic studies
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR 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
    • G06F3/03—Arrangements for converting the position or the displacement of a member into a coded form
    • G06F3/041—Digitisers, e.g. for touch screens or touch pads, characterised by the transducing means
    • G06F3/0414—Digitisers, e.g. for touch screens or touch pads, characterised by the transducing means using force sensing means to determine a position
    • G06F3/04146—Digitisers, e.g. for touch screens or touch pads, characterised by the transducing means using force sensing means to determine a position using pressure sensitive conductive elements delivering a boolean signal and located between crossing sensing lines, e.g. located between X and Y sensing line layers

Definitions

  • the present invention relates to a computer controlled platform responsive to the pressure of the foot sole of a walking subject.
  • the lenght of this platform has to be such as to allow at least a complete gait cycle (double step) to be analyzed.
  • the system has to provide firstly information concerning the geometry of the footprints as a function of the time and the relative location of the footprints of both feet and secondly a point by point information .-.bout the intensity of the pressure exerted by the sole of a feet on the platform.
  • the platforms have limited size of the order of 30 cm x 30 so as to provide the pressure distribution of one foot at a time and then insufficient for the analysis of the double step.
  • the platforms of the prior art would give impaired results.
  • the walking subject attempting to trample exactly on the centre of the small platform would be disposed to toddle before the latter, thus altering his normal gait with the result that the pressure distribution of the foot in the sole valid footing on the platform would be unnatural.
  • the limited size of the already known platforms is intrinsically due to the tecniques used for manufacturing the sensors. Such tecniques do not allow for different reasons much larger platforms to be manufactured at non-prohibitive price.
  • the man's gait dynamics has for physiological reasons significant spectral components higher than 20 Hz, * whereby it is necessary a sampling frequency not lower than 50 Hz in order to analyze these phenomena.
  • Most of the above mentioned systems operate at a lower sampling frequency. In those systems with capacitive sensors in which an adequate sampling frequency can be reached, this facility is limited to a minimun number of sensors which is not sufficient to analyze the double step.
  • the systems based on piezoelectric sensors besides being much more expensive are not provided with a matrix (lines and columns) but have at least a wire for each sensor, thus providing insurmountable wiring difficulties as the number of sensors increases.
  • the system based on capacitive sensors operate at scanning frequencies higher than 1 MHz and therefore are subject to noise caused by stray capacities between adjacent sensors. Such a circumstance sets bounds to both the sensor reading speed and the density of the sensors itself.
  • the platform according to this invention can have a size such as to provide digital pressure information, temporal phases and geometrical data of the whole double step such as the times between two footings, the delays, the distance between footings and the inclination of the feet with respect to the walking direction.
  • the whole system of the present patent application consists of following four main blocks:
  • a host computer retrieving data from the storing system, processing them and displaying the results.
  • the sensing mat consists of three rectangular layers laid one upon the other.
  • the lower layer is formed of a rigid or flexible printed board provided 'on the upper surface, with conductive paths equally spaced and parallel to one another and to one side of the sensing mat.
  • the upper layer is formed of a flexible printed board provided on the lower surface, with conductive paths equally spaced and parallel to one another and orthogonal to the paths of the lower layer.
  • the middle layer is formed of a conductive rubber sheet the electric resistance of which varies point by point only in the direction of the thickness of the layer as a function of the pressure exerted between a point of the upper surface and the corresponding point of the lower surface of the rubber sheet.
  • a resistive contact matrix is thus provided.
  • the size and the resolving capability of such a matrix depend upon the number and the spacing of the conductive paths of the upper and lower layers.
  • the resistance of each contact point is inversely proportional to the pressure applied by the sole of the foot.
  • the use of resistive contacts and the way to take the information allow the points on which a pressure is applied to be detected without ambiguity and mistakes. It should be noted that problems are avoided that might ensure, for exa ble, by using a decoding similar to that of the computer keyboards (phanton key problem) when more than one key at a time are pressed. Such an aspect will be now better illustrated.
  • the conductive rubber can be schematically represented as a matrix of variable resistances connected among lines and columns of the matrix.
  • the lines are supplied one after the other with a d.c. voltage Vg and the columns are connected to the input of an operational amplifier acting as current-voltage converter. Due to this configuration each column is connected to the virtual ground of the corresponding operational amplifier. In this way adjacent columns are at the same potential.
  • Such e.n expedient along with the use of resistive contacts would prevent that an undesired current flows in the lines which are not supplied with the voltage Vg r said current being capable to cause errors of detecting the points on which a pressure has been applied.
  • each operational amplifier varies as a function of the resistance between the column to which the amplifier is connected and the line selected at that time, i.e. as a function of the pressure applied on that cross point.
  • the use of resistive and non-capacitive contact points avoids a trigger signal at high frequency to be used, thus providing a lower sensitivity to noise caused by stray capacities and a higher measuring rate.
  • data can be supplied by a great number of sensors at a sampling frequency of at least 50 Hz.
  • the structural simplicity and the low cost allow a sensing mat to be built having a size such as to analyze a double step. This analysis can involve also particular gait conditions such as the running and the walk with a walking-stick or on crutches.
  • Fig. 1 shows a schematic diagram of the sensing mat with its three layers
  • Fig. 2 shows the equivalent electric diagram of the sensing mat with the annexed electronics for detecting signals generated by the application of the pressure on the sensing mat and
  • Fig. 3 shows a block diagram of the whole apparatus for the evaluation of the support pressures according to the present invention.
  • Fig. 1 shows the sensing mat according to the present invention which is generally designed by 1.
  • Sensing mat 1 according to a preferred embodiment has size 2.6m x 0.5m and consists of an upper layer 2, a middle layer 3 and a lower layer 4, which are laid one upon the other, and of support means.
  • Upper layer 2 consists of a flexible printed board on the lower surface of which conductive paths 5 spaced apart from (for instance 5 mm)
  • Middle layer 3 consists of a conductive rubber sheet, for example, of the type available under the name VELOSTAT of the firm 3M Italia S.p.A.
  • Lower layer 4 consists of a rigid printed board on the upper surface of which conductive paths 6 spaced apart from (for istance.5 mm) and parallel to one another, are applied, said paths being transversal to the conductive paths 5 of the upper layer 2.
  • conductive paths 6 are orthogonal to conductive paths 5.
  • On the whole a crossing path matrix is provided, consisting of 512 lines and 96 columns in case a sensing mat having the above mentioned size is built. If it is used a conductive rubber sheet the surface resistance of which (Fig.
  • the surface resistance R' t between two columns of the matrix does not considerably impair the sensing of the pressure signal as the columns are connected to a virtual ground.
  • the surface resistance R" t between lines can give rise to tolerable errors in many applications, but if it is not negligible to reach the desired precision, it has to be interrupeted by means of a little modification.
  • the conductive rubber sheet is stuck on the lower layer of the sensing mat consisting of conductive paths (the lines of the matrix) by applying the adhesive in the insulating spaces between the- aths.
  • Fig. 2 shows the equivalent circuit diagram of sensing mat 1 consisting of the matrix having lines 6 and columns 5. Schematically shown between lines 6 and columns 5 are the equivalent resistances (R; , T . 2' R 21' 22. " ) of the middle conductive rubber sheet 3 at the cross points between lines and columns, said resistances depending upon the pressure applied on those points.
  • Voltage generator V s supplies lines 6 through the solid state analogue switch 7 in a cyclic sequence, i.e. one after the other as shown by the arrows in switch 7.
  • a voltage signal V TH is applied to the invertent input of the operational amplifiers 8. It determines the threshold level of the operational amplifiers 8.
  • Generator Vg' i n ' case no pressure is applied on the sensing mat, is practically a no-load generator as it is connected to the very high resistances of the conductive rubber sheet 3 connecting the cross points of the conductive path matrix (5,6).
  • the voltage Vg supplied, for example, to line r 2 generates a current only in those columns over which a pressure is applied on the sensing mat, as this pressure causes the variation, i.e. the decreasing, of the resistances between those columns and lines r 2 selected by analogue switch 7.
  • All points of a line over which no pressure is applied are represented by resistance R shown in phantom, the value of that resistance being practically infinite so that a current cannot be generated, i.e. no or non- valuable pressure is applied on the sensing mat.
  • Each line is selected by a solid state analogue switch 7 that applies the voltage Vg to the lines according to a cyclic sequence.
  • Switch 7 (Fig. 3) is in turn addressed by the output of line counter 9. The same output is fed through port 11 to the output data bus 12 for being stored into RAM 13 connected by parallel interface 14 to computer 15.
  • the whole scanning of the lines is carried out at a " frequency of 50 Hz. Such a value of frequency corresponds to the maximum sampling frequency at which the pressure applied by the sole of the feet on the whole sensing mat is sensed.
  • each sampling phase is enabled by an outer clock signal S supplied to line counter 9 from computer 15 through interface 14. Such a signal defines the sampling frequency.
  • Line counter 9 is increased by line clock C rq generated by unit 10.
  • Designated by 19 is a clock generator C s ⁇ the output signal of which is fed to column counter 20 and controller 21.
  • Column counter addresses each column through analogue multiplexer 16 and is connected to bus 12 through port 15.
  • Operational amplifiers 8 are connected to analogue multiplexer 16, the output of which is connected to analogue-digital converte block 17.
  • the output of converter 17 is connected to store register 22.
  • Digital comparator 18 checks that data contained in register 22 is different from zero. Only if this is true comparator 18 supplies signal E 0 to controller 21.
  • E Q controller 21 On receiving E Q controller 21 supplies signals E ⁇ , E 2 , E3 to ports 11, 15, 23, respectively. On receiving said signals E lf E 2 , E 3 , said ports enable storing of line and column addresses and the content of register 22 into memory 13 through bus 12. Data are then available through interface 14 to computer 15 processing and displaying them on a video and/or graphic terminal.
  • the scanning of the sensing mat is enabled by a sampling signal S having a frequency of 50 Hz as a maximum.
  • Vg is applied in a cyclic sequence to each line via the solid state analogue switch 7 which in turn is addressed by line counter 9.
  • Line counter 9 after signal S being fed, is increased by clock signal C RG generated by block 10.
  • clock signal C RG generated by block 10.
  • Column counter 20 addresses sequentially the outputs of operational amplifiers 8 which are connected to analogue-digital convertor 17 through multiplexer 16. Data at the output of convertor 17 is stored into register 17.
  • Comparator 18 determines if data of register 21 is different from zero. If so, a pressure has been applied on the point addresses by the column and the line selected at that time. In such a case comparator 18 enables controller 21 which in turn enables sequentially gates 11, 15 and 23, thus allowing line address, column address and the value of the pressure to be stored into memory 13. The content of memory 13 is then transferred through interface 14 into computer 15.
  • Operational amplifiers 8 act as voltage comparator. In this way the output of operational amplifiers 8 is already coded in digital form, the voltage V TH being constant, so that the multiplexer 16 is of digital type and the analogue- digital converter 17 can be omitted. Therefore the addresses of the points of the sensing mat, on which a pressure greater or equal than that corresponding to the threshold voltage V TH has been applied, are stored into memory 13.
  • analogue-digital conversion block 18 is formed of more analogue-digital
  • Scanning of the columns has not to be carried out a column at a time but a group of more columns (for example, 8) are scanned at a time, so that each column is connected to one converter of the block 17.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Theoretical Computer Science (AREA)
  • General Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Medical Informatics (AREA)
  • Animal Behavior & Ethology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Biophysics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Pathology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Human Computer Interaction (AREA)
  • General Physics & Mathematics (AREA)
  • Dentistry (AREA)
  • Force Measurement Appropriate To Specific Purposes (AREA)

Abstract

Appareil permettant d'évaluer les phases temporelles, les données géométriques et les forces de réaction de la voûte plantaire dans des conditions dynamiques. Cet appareil comporte essentiellement un tapis (1) constitué de trois couches (2-4). La couche supérieure (2) est constituée d'une plaquette de circuit imprimée souple possédant sur sa face inférieure des cheminements conducteurs (5) parallèles les uns aux autres, la couche intermédiaire (3) étant formée d'une feuille de caoutchouc conductrice pouvant faire varier sa résistance dans le sens de son épaisseur lorsqu'une pression est exercée dans le sens perpendiculaire aux faces de la couche , la couche inférieure (4) étant une plaquette de circuit imprimée possédant sur sa face supérieure des cheminements conducteurs (6) parallèles les uns aux autres et s'étendant dans une direction perpendiculaire par rapport aux cheminements conducteurs de la couche supérieure (3). L'appareil permet l'exploration du tapis tout entier en temps réel pendant la marche du sujet à une fréquence d'échantillonage supérieure ou égale à 50 hertz, et la détermination dans un cycle de marche complet (double pas) de la répartition des pressions de soutien exercées par la voûte plantaire.
PCT/IT1986/000070 1985-09-19 1986-09-17 Evaluation des phases de la marche WO1987001574A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
IT48574A/85 1985-09-19
IT48574/85A IT1182866B (it) 1985-09-19 1985-09-19 Apparecchiatura per la valutazione delle fasi temporali dell'andatura di un soggetto deambulante e della distribuzione istantanea delle reazioni vincolari del suolo

Publications (1)

Publication Number Publication Date
WO1987001574A1 true WO1987001574A1 (fr) 1987-03-26

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IT1986/000070 WO1987001574A1 (fr) 1985-09-19 1986-09-17 Evaluation des phases de la marche

Country Status (3)

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EP (1) EP0237544A1 (fr)
IT (1) IT1182866B (fr)
WO (1) WO1987001574A1 (fr)

Cited By (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0256799A2 (fr) * 1986-08-14 1988-02-24 The Microelectronics Applications Research Institute Ltd. Capteur sensible au toucher
EP0309946A2 (fr) * 1987-09-28 1989-04-05 Oki Electric Industry Company, Limited Appareil pour l'entrée de données sensible à la pression
EP0327824A2 (fr) * 1988-02-02 1989-08-16 Wolfgang Brunner Méthode et dispositif de stockage des données de pression
EP0459808A2 (fr) * 1990-05-31 1991-12-04 Personal Biometric Encoders Limited Convertisseur numérique
EP0471149A2 (fr) * 1990-08-01 1992-02-19 Dynapro Thin Film Products, Inc. Méthode de fabrication de membranes électriques incluant des circuits sur les films plastiques flexibles
US5408873A (en) * 1994-07-25 1995-04-25 Cleveland Medical Devices, Inc. Foot force sensor
FR2720622A1 (fr) * 1994-06-02 1995-12-08 Tambon Christian Dispositif pour la détermination du choix d'un support anti-escarres.
US5511561A (en) * 1992-11-16 1996-04-30 Wanderman; Steven M. Gait cycle force monitor
WO1997018450A1 (fr) * 1995-11-14 1997-05-22 Taylor Geoffrey L Appareil et procede piezoresistifs de mesure des pressions exercees sur un pied
EP0846441A1 (fr) * 1996-12-04 1998-06-10 Istituto Superiore Di Sanita' Appareil de télétransmission des forces d'interaction agissant entre le pied et le sol durant la marche
US5799533A (en) * 1995-05-12 1998-09-01 Director-General Of Agency Of Industrial Science And Technology Distributed pressure sensor and method for manufacturing the same
ES2120860A1 (es) * 1995-05-31 1998-11-01 Univ Zaragoza Podometro electronico.
DE10151361A1 (de) * 2001-10-22 2003-04-30 Novotec Medical Gmbh Vorrichtung zur Erfassung und Auswertung der Motorik des menschlichen Bewegungsapparates
EP2186478A1 (fr) 2008-11-14 2010-05-19 HASOMED Hard- und Software für Medizin GmbH Procédé et dispositif destinés à l'analyse d'un cycle humain
WO2012095608A2 (fr) 2011-01-13 2012-07-19 LAVARENNE, Anna Dispositif de mesure de la pression a partir d'un objet souple, pliable et/ou extensible realise a partir de matiere textile comportant un dispositif de mesure
ES2485616A1 (es) * 2013-02-12 2014-08-13 David VERDE SÁNCHEZ Dispositivo sensor de presiones
US10493350B2 (en) 2015-11-11 2019-12-03 Step And Connect, Llc Balance sensory and motor feedback mat

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2273257A1 (en) * 1974-05-31 1975-12-26 Anvar Sensor for surfaces of objects - has surface electrode and measurement electrodes connected to integral elastic film
DE2529475A1 (de) * 1975-07-02 1977-01-13 Klaus Dr Nicol Vorrichtung zum zeitabhaengigen messen physikalischer groessen
FR2513508A1 (fr) * 1981-09-29 1983-04-01 Agnes Michel Dispositif a usage medical et paramedical pour la mesure des pressions exercees par le corps ou parties du corps sur un support quelconque
DE3212618A1 (de) * 1982-04-05 1983-10-13 Siemens AG, 1000 Berlin und 8000 München Anordnung zur signalerzeugung
DE3248222A1 (de) * 1982-04-05 1984-06-28 Siemens AG, 1000 Berlin und 8000 München Anordnung zur signalerzeugung

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2273257A1 (en) * 1974-05-31 1975-12-26 Anvar Sensor for surfaces of objects - has surface electrode and measurement electrodes connected to integral elastic film
DE2529475A1 (de) * 1975-07-02 1977-01-13 Klaus Dr Nicol Vorrichtung zum zeitabhaengigen messen physikalischer groessen
FR2513508A1 (fr) * 1981-09-29 1983-04-01 Agnes Michel Dispositif a usage medical et paramedical pour la mesure des pressions exercees par le corps ou parties du corps sur un support quelconque
DE3212618A1 (de) * 1982-04-05 1983-10-13 Siemens AG, 1000 Berlin und 8000 München Anordnung zur signalerzeugung
DE3248222A1 (de) * 1982-04-05 1984-06-28 Siemens AG, 1000 Berlin und 8000 München Anordnung zur signalerzeugung

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
Medical and Biological Engineering and Computing, Vol. 21, No. 3, May 1983 (Stevenage, Herts, GB) M. KNIGHT et al.: "The Hollywood Gaitrack: a Method for Measuring Temporal and Distance Factors of Gait", pages 306-310, see pages 307-310, paragraph "Design"; figures 3-6 *

Cited By (28)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0256799A2 (fr) * 1986-08-14 1988-02-24 The Microelectronics Applications Research Institute Ltd. Capteur sensible au toucher
EP0256799A3 (fr) * 1986-08-14 1988-11-30 The Microelectronics Applications Research Institute Ltd. Capteur sensible au toucher
US4866412A (en) * 1986-08-14 1989-09-12 The Microelectronics Applications Research Institute Limited Tactile sensor device
EP0309946A2 (fr) * 1987-09-28 1989-04-05 Oki Electric Industry Company, Limited Appareil pour l'entrée de données sensible à la pression
EP0309946A3 (fr) * 1987-09-28 1990-05-09 Oki Electric Industry Company, Limited Appareil pour l'entrée de données sensible à la pression
EP0327824A2 (fr) * 1988-02-02 1989-08-16 Wolfgang Brunner Méthode et dispositif de stockage des données de pression
EP0327824A3 (fr) * 1988-02-02 1991-10-02 Wolfgang Brunner Méthode et dispositif de stockage des données de pression
EP0459808A3 (en) * 1990-05-31 1992-01-29 Gec-Marconi Limited Digitizers
EP0459808A2 (fr) * 1990-05-31 1991-12-04 Personal Biometric Encoders Limited Convertisseur numérique
EP0471149A2 (fr) * 1990-08-01 1992-02-19 Dynapro Thin Film Products, Inc. Méthode de fabrication de membranes électriques incluant des circuits sur les films plastiques flexibles
EP0471149A3 (en) * 1990-08-01 1992-03-04 W.H. Brady Co. Method for the manufacture of electrical membrane panels having circuits on flexible plastic films
US5511561A (en) * 1992-11-16 1996-04-30 Wanderman; Steven M. Gait cycle force monitor
FR2720622A1 (fr) * 1994-06-02 1995-12-08 Tambon Christian Dispositif pour la détermination du choix d'un support anti-escarres.
US5408873A (en) * 1994-07-25 1995-04-25 Cleveland Medical Devices, Inc. Foot force sensor
US5799533A (en) * 1995-05-12 1998-09-01 Director-General Of Agency Of Industrial Science And Technology Distributed pressure sensor and method for manufacturing the same
ES2120860A1 (es) * 1995-05-31 1998-11-01 Univ Zaragoza Podometro electronico.
WO1997018450A1 (fr) * 1995-11-14 1997-05-22 Taylor Geoffrey L Appareil et procede piezoresistifs de mesure des pressions exercees sur un pied
US6216545B1 (en) 1995-11-14 2001-04-17 Geoffrey L. Taylor Piezoresistive foot pressure measurement
EP0846441A1 (fr) * 1996-12-04 1998-06-10 Istituto Superiore Di Sanita' Appareil de télétransmission des forces d'interaction agissant entre le pied et le sol durant la marche
DE10151361A1 (de) * 2001-10-22 2003-04-30 Novotec Medical Gmbh Vorrichtung zur Erfassung und Auswertung der Motorik des menschlichen Bewegungsapparates
EP2186478A1 (fr) 2008-11-14 2010-05-19 HASOMED Hard- und Software für Medizin GmbH Procédé et dispositif destinés à l'analyse d'un cycle humain
DE102009052798A1 (de) 2008-11-14 2010-05-27 Hasomed Hard- und Software für Medizin GmbH Verfahren zur Analyse des menschlichen Gangzyklus
WO2012095608A2 (fr) 2011-01-13 2012-07-19 LAVARENNE, Anna Dispositif de mesure de la pression a partir d'un objet souple, pliable et/ou extensible realise a partir de matiere textile comportant un dispositif de mesure
FR2970566A1 (fr) * 2011-01-13 2012-07-20 Francis Cannard Dispositif de mesure de la pression a partir d'un objet souple, pliable et/ou extensible realise a partir de matiere textile comportant un dispositif de mesure
WO2012095608A3 (fr) * 2011-01-13 2012-09-13 LAVARENNE, Anna Dispositif de mesure de la pression a partir d'un objet souple, pliable et/ou extensible realise a partir de matiere textile comportant un dispositif de mesure
US9448127B2 (en) 2011-01-13 2016-09-20 Francis Cannard Device for measuring pressure from a flexible, pliable, and/or extensible object made from a textile material comprising a measurement device
ES2485616A1 (es) * 2013-02-12 2014-08-13 David VERDE SÁNCHEZ Dispositivo sensor de presiones
US10493350B2 (en) 2015-11-11 2019-12-03 Step And Connect, Llc Balance sensory and motor feedback mat

Also Published As

Publication number Publication date
EP0237544A1 (fr) 1987-09-23
IT1182866B (it) 1987-10-05
IT8548574A0 (it) 1985-09-19

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