JP5733503B2 - Measuring device, measuring method, and measuring program - Google Patents

Description

  The present invention relates to a measurement apparatus, a measurement method, and a measurement program.

  The 5-year survival rate of elderly people who can not walk due to fractured femoral neck is 50%. The decline in gait function greatly affects the life expectancy of the elderly. Patent Document 1 discloses a pedometer that displays health management indices such as walking distance and calorie consumption based on the number of steps information measured by a number of steps sensor.

Japanese Patent Laid-Open No. 10-258042

  However, since the pedometer of Patent Document 1 uses the magnitude of the amount of exercise such as walking distance as an index, for example, when the amount of exercise is originally low, such as when the person does not leave the house all day due to cold winter, the walking function is degraded. There is a problem that cannot be evaluated accurately.

  The present invention has been made in view of such problems, and an object of the present invention is to provide a measuring device, a measuring method, and a measuring program for acquiring information for accurately evaluating a decrease in walking function.

  In order to achieve the above object, a measuring apparatus according to the first aspect of the present invention comprises:
  A sensor output acquisition means for acquiring an output from a sensor that is installed in a human body and measures acceleration or pressure applied to the human body;
  1 walking cycle time acquisition means for acquiring the time required for 1 walking cycle based on the sensor output;
  Based on sensor output, it takes from the heel contact of one foot to the toe-off of the other foot during walking Per walking cycleBoth feet contact time measuring means for measuring both feet contact time and,
  Based on the time required for one walking cycle and the contact time of both feet per one walking cycle Calculating means for calculating the ratio of the time for both feet to touch;
  A discriminating means for discriminating whether or not the ratio of both foot contact time is equal to or greater than a predetermined threshold;
  ThePrepare
  It is characterized by that.

The sensor output acquisition means includes
Means for acquiring measurement outputs of accelerations in two or more directions,
The both foot contact time measuring means,
There may be provided means for measuring both foot contact time based on acceleration in two or more directions.

The sensor output acquisition means includes
Means for obtaining a measurement output of longitudinal acceleration which is acceleration in the traveling direction;
Means for obtaining a measurement output of vertical acceleration, which is acceleration in the vertical direction,
The both foot contact time measuring means,
Means for discriminating when the heel-contact is based on the timing at which the longitudinal acceleration decreases from increase or decreases to increase;
Means for discriminating the toe-off time based on the timing at which the vertical acceleration decreases from increase or decreases to increase;
Means for measuring the time required from the heel-contact to the toe-off immediately after the heel-contact.

The sensor output acquisition means includes
Means for obtaining a measurement output of longitudinal acceleration, which is acceleration in the traveling direction,
The both foot contact time measuring means,
Means for obtaining a combined acceleration by vector-synthesizing accelerations in two or more directions;
Means for discriminating when the heel-contact is based on the timing at which the longitudinal acceleration decreases from increase or decreases to increase;
Means for discriminating the toe-off time based on the timing at which the resultant acceleration changes from increasing to decreasing;
Means for measuring the time required from the heel-contact to the toe-off immediately after the heel-contact may be provided.

The sensor output acquisition means includes
Means for acquiring a measurement output of lateral acceleration that is acceleration in the lateral direction,
1 walk cycle time acquisition means,
There may be provided means for acquiring a time required for one walking cycle based on the measurement output of the lateral acceleration.

Information input means for inputting information on the age, sex, height, weight, or stride of the pedestrian,
Threshold information acquisition means for acquiring the threshold value based on the information input to the information input means.

In order to achieve the above object, a measurement method according to the second aspect of the present invention includes:
A sensor output acquisition step for acquiring an output from a sensor that is installed on the human body and measures acceleration or pressure applied to the human body;
1 walk cycle time acquisition step of acquiring time required for 1 walk cycle based on the sensor output ;
Based on the sensor output, a both-foot contact time acquisition step of acquiring a both-foot contact time per one walking cycle, which is a time required from the heel contact of one foot to the toe-off of the other foot during walking ;
Based on the time required for 1 walking period and the two-footed contact time per gait cycle, a calculation step of calculating the ratio of which accounts footed contact time 1 walking cycle,
A determination step of determining whether or not the ratio of both feet contact time is equal to or greater than a predetermined threshold;
Having
It is characterized by that.

In order to achieve the above object, a measurement program according to the third aspect of the present invention includes:
A sensor output acquisition step for acquiring an output from a sensor that is installed on the human body and measures acceleration or pressure applied to the human body;
1 walk cycle time acquisition step of acquiring time required for 1 walk cycle based on the sensor output ;
Based on the sensor output, a both-foot contact time acquisition step of acquiring a both-foot contact time per one walking cycle, which is a time required from the heel contact of one foot to the toe-off of the other foot during walking ;
Based on the time required for 1 walking period and the two-footed contact time per gait cycle, a calculation step of calculating the ratio of which accounts footed contact time 1 walking cycle,
A determination step of determining whether or not the ratio of both feet contact time is equal to or greater than a predetermined threshold;
To run on a computer,
It is characterized by that.

  It is possible to provide a measurement device, a measurement method, and a measurement program that acquire information for accurately evaluating a decrease in walking function.

It is a figure which shows a mode that the measuring apparatus which concerns on Embodiment 1 was attached to the person, (A) is the figure which looked at the person who attached the measuring apparatus from the back surface, and (B) is the person who attached the measuring apparatus on the right side. It is the figure seen from the surface. It is a figure for demonstrating a walk cycle and both leg | foot contact time. 2 is a block diagram illustrating a configuration of a measurement apparatus according to Embodiments 1 and 2. FIG. It is a figure which shows the acceleration signal produced | generated by removing noise from the electrical signal output from the sensor of a measuring apparatus, (A) is an acceleration signal which shows left-right acceleration, (B) is an acceleration signal which shows longitudinal acceleration, ( C) is an acceleration signal indicating vertical acceleration. It is a figure which shows the digital data (acceleration data) produced | generated by sampling an acceleration signal with a predetermined period. 4 is a flowchart for explaining a walking function determination process according to the first embodiment. It is a figure which shows the process start time preservation | save queue for preserve | saving the start time of a walk function discrimination | determination process, and the acceleration data preserve | saved at the memory | storage part. It is a figure for demonstrating the S-shaped waveform which appears in left-right acceleration in the vicinity of the timing when the turning direction of the pelvis changes. When it is determined that the user is not walking, the display indicating that the user is not walking is displayed on the display unit of the measurement apparatus. It is a figure which shows a mode that the S-shaped waveform which shows the change of the turning direction of a pelvis appears twice in one walk cycle. It is a figure for demonstrating a mode which distinguishes at the time of "heel contact" and "toe take off" from the longitudinal acceleration and the vertical acceleration, (A) is from front to back when the longitudinal acceleration is "heel contact" It is a figure for demonstrating showing an inflection point, (B) is a figure for demonstrating showing the inflection point from an upward direction to a downward direction when vertical acceleration is "toe toe-off". It is a figure which shows a mode that the both-legs ground contact time which occupies for one walk cycle is calculated by making the time from the "longitudinal inflection point" of the longitudinal acceleration to the "vertical inflection point" of the vertical acceleration into the time required for the both foot support period, respectively. It is a figure which shows the discrimination | determination result displayed on the display part, (A) is a figure which shows a mode that the user's walk function has fallen, (B) is a user's walk function normal It is a figure which shows a mode that it was displayed that it is. It is a figure which shows a mode that it discriminate | determines from the up-and-down inflection point of a vertical acceleration to the next inflection point from the downward direction to an upward direction as a both-foot support period. It is a figure which shows a mode that it is discriminate | determined from the back-and-front inflection point of the back-and-forth acceleration to the inflection point from the next back direction to the front direction as a both foot support period. It is a figure which shows a mode that it discriminate | determines from the first inflection point of the S-shaped waveform of left-right acceleration to the next inflection point as a both-foot support period. Vector synthesis of a vector (a) indicating the magnitude and direction of lateral acceleration at a certain point in time of walking, a vector (b) indicating the magnitude and direction of longitudinal acceleration, and a vector (c) indicating the magnitude and direction of vertical acceleration. It is a figure for demonstrating synthetic | combination acceleration (d) produced | generated in this way. It is the figure which added the data of the synthetic acceleration with respect to each data of the acceleration data shown in FIG. It is a figure which shows the menu screen for setting the age and sex of a pedestrian to a measuring apparatus. It is a figure for demonstrating the threshold value setting matrix for setting the threshold value for discriminating the fall of a walking function based on the information of a pedestrian's age and sex. It is a figure which shows a mode that the pressure sensor was attached to the heel and toe of both feet, and they were connected with the main body of the measuring apparatus with the signal wire | line. 10 is a flowchart for explaining walking function determination processing according to the second embodiment.

(Embodiment 1)
The measuring apparatus 100 according to the present embodiment is an apparatus for measuring acceleration applied to a human body with an acceleration sensor, and measuring both feet contact time based on the measured value. Moreover, the measuring apparatus 100 is an apparatus for discriminating whether or not the user's walking function is deteriorated based on the measured both-foot contact time. This measuring apparatus 100 is used by being attached, for example, near the third lumbar vertebra where the body center of gravity is located (for example, near the center of the back of the waist of the belt 200 as shown in FIG. 1).

  In the present embodiment, the deterioration of the walking function is determined based on the ratio of the both foot contact time in the walking cycle. This focuses on the fact that when leg strength, joint function, etc. are reduced due to aging or disability, it becomes difficult to balance with one leg, and the time required for both feet to touch naturally becomes longer during walking. The “walking cycle” is a human walking cycle. For example, as shown in FIG. 2, the right foot (or left foot) is grounded after the right foot (or left foot) is grounded. It means the period until it is done. “Both foot contact time” is the time required for both foot support periods (double support) during walking. For example, the time from the “heel contact” of the right foot to the “toe off” of the left foot immediately after ( 2 (a) shown in FIG. 2 and the time from the “heel contact” of the left foot to the “toe-off” of the right foot immediately after (left (b) shown in FIG. 2).

  Hereinafter, the configuration of the measuring apparatus 100 will be described with reference to the drawings. As shown in FIG. 3, the measuring apparatus 100 includes a sensor 110, a conversion unit 120, a storage unit 130, a control unit 140, a timer 150, a display unit 160, an operation unit 170, and a battery 180. The

  The sensor 110 is a three-axis acceleration sensor such as a MEMS (Micro Electro Mechanical Systems) sensor, and measures acceleration in the traveling direction, the left-right direction, and the vertical direction during walking. In the following description, acceleration in the traveling direction is referred to as “longitudinal acceleration”, acceleration in the left / right direction is referred to as “left / right acceleration”, and acceleration in the vertical direction is referred to as “vertical acceleration”. The measured acceleration is sequentially output to the conversion unit 120.

  The conversion unit 120 includes a noise removal filter, an A / D (Analog / Digital) converter, and the like, and removes noise from the electrical signal output from the sensor 110, as shown in FIGS. Such an “acceleration signal” is generated. Further, the conversion unit 120 samples the acceleration signal at a predetermined cycle to generate “acceleration data” as shown in FIG. The conversion unit 120 sequentially stores the generated acceleration data in the storage unit 130.

  The memory | storage part 130 is comprised from memory | storage devices, such as RAM (Random Access Memory), and memorize | stores various data, such as a program and acceleration data.

  The control unit 140 includes a processor such as a CPU (Central Processing Unit) and operates according to a program stored in the storage unit 130, and executes various operations including a “walking function determination process” described later.

  The timer 150 is composed of a timing device such as a crystal oscillator, and measures the current time and transmits it to the conversion unit 120 and the control unit 140. In addition, the timer 150 transmits an “interrupt signal” serving as a start trigger for the walking function determination process to the control unit 140 at predetermined time intervals (for example, every minute).

  The display unit 160 is composed of a display device such as a liquid crystal panel, and displays various types of information such as determination results under the control of the control unit 140.

  The operation unit 170 includes various operation switches, and includes a power switch 171 for starting driving of the measurement apparatus 100.

  The battery 180 includes a power storage device such as a lithium ion battery, and starts supplying power to each unit when the power switch 171 is pressed by a user or the like.

Next, the operation of the measuring apparatus 100 having such a configuration will be described.
When the supply of electric power from the battery 180 is started, the sensor 110 measures the vertical acceleration, the horizontal acceleration, and the longitudinal acceleration and outputs them to the conversion unit 120 as an electrical signal. The electrical signal output from the sensor 110 is converted into acceleration data by the conversion unit 120 and sequentially stored in the storage unit 130.

  On the other hand, when the supply of power from the battery 180 is started, the timer 150 starts transmitting an interrupt signal to the control unit 140. Each time the control unit 140 receives an interrupt signal from the timer 150, the control unit 140 executes a “walking function determination process” shown in FIG. Hereinafter, the “walking function determination process” will be described with reference to the flowchart of FIG. 6.

  When the process is started, the control unit 140 acquires the current time from the timer 150 and stores it in the process start time storage queue 131 (step S101). The processing start time storage queue 131 is a storage area in the FIFO (First In First Out) format reserved in the storage unit 130. As shown in FIG. And “previous processing start time”).

  The control unit 140 acquires the process start time recorded in the previous interrupt process from the process start time storage queue 131. Then, based on the acquired time and the processing start time acquired in step S101, acceleration data accumulated in the storage unit 130 from the previous interrupt processing to the current interrupt processing (hereinafter referred to as “unprocessed acceleration”). (Referred to as “data”) (step S102). For example, the time recorded in the previous interrupt process is “12:35:56” (FIG. 7 (c)), and the current process start time is “12:36:56” 78 (FIG. 7). 7 (b)), the acceleration data from (12: 35: 56: 79) to “12: 36: 56: 78” ((d) shown in FIG. 7) is “unprocessed acceleration data”. Is.

  Next, based on the identified “unprocessed acceleration data”, the control unit 140 determines whether or not the user has walked during the unprocessed period (step S103). For example, as shown in FIGS. 8A and 8B, the lateral acceleration shows a sine waveform near the timing when the pelvic turning direction changes, so that the control unit 140 has a sine waveform having a predetermined amplitude or more. A case where a waveform (hereinafter referred to as “S-shaped waveform”) appears a certain number or more (for example, four or more determined to be steady walking) is determined to be “with walking” (step S103: Yes). On the other hand, the case where the S-shaped waveform is less than a certain number is determined as “no walking” (step S103: No).

  When it is determined that “no walking” (step S103: No), as shown in FIG. 9, the control unit 140 displays that it is not walking on the display unit 160 (step S104), and ends the process. On the other hand, if it is determined that “there is walking” (step S103: Yes), the process proceeds to step S105.

The control unit 140 calculates an average time T _wc per one walking cycle based on the left and right acceleration data (step S105). For example, since the change in the turning direction of the pelvis appears twice in one walking cycle as shown in FIG. 10, the control unit 140 determines the interval of “S-shaped waveform” indicating the change in the turning direction (t _{w1 to} t _wn ) is obtained, and a value obtained by averaging them twice is calculated as an average time _Twc per one walking cycle (the following (formula 1)).

Next, the control unit 140 obtains the time required for the both-foot support period, that is, the time from the heel contact of one foot to the toe separation of the other foot (step S106). For example, since the center of gravity of the body during walking decelerates due to the ground contact of the heel, the longitudinal acceleration is from the front to the rear during the “heel contact” as shown in FIGS. 11 (A) and 11 (c). Inflection points (hereinafter referred to as “front and rear inflection points”). Also, since the center of gravity of the body during walking rises by kicking the ground with the toes, the vertical acceleration increases at the time of “toe off” as shown in (b) and (d) of FIG. An inflection point from the direction to the downward direction (hereinafter referred to as “upper and lower inflection points”) is shown. Therefore, as shown in FIG. 12, the controller 140 takes the time (t _{d1 to} t _d) required for the both foot support period from the “front / back inflection point” of the longitudinal acceleration to the “vertical inflection point” of the immediately following vertical acceleration. _dn ).

Next, the control unit 140 calculates both feet contact time T _ds per one walking cycle from the time (t _{d1 to} t _dn ) required for the both feet support period (step S107). For example, since the both-leg support period appears twice in one walking cycle, the control unit 140 averages twice the time (t _{d1 to} t _dn ) required for the both-leg support period, It is calculated as the contact time T _ds (the following (formula 2)).

The control unit 140 determines the ratio R of the two-foot contact time in one walking cycle from the average time T _wc per one walking cycle calculated in step S105 and the two-foot contact time T _ds per one walking cycle calculated in step S107. (Equation 3 below) is calculated (step S108).

  The control unit 140 determines whether or not the ratio R of both foot contact time is equal to or less than a predetermined threshold (for example, 0.5) (step S109). When the ratio R exceeds the predetermined threshold value (step S109: No), as shown in FIG. 13A, the display unit 160 displays that the walking function is degraded. At this time, the ratio R of both feet contact time and the cadence K (the number of walking cycles per minute) calculated by the following (Equation 4) are also displayed on the display unit 160 so that the degree of deterioration of the walking function can be understood. (Step S110).

  On the other hand, when the ratio R is equal to or less than the predetermined threshold (step S109: Yes), the display unit 160 displays that the walking function is normal, as shown in FIG. Similarly to step S110, the ratio R of both feet contact time and cadence K are also displayed on the display unit 160 (step S111).

  When the display on the display unit 160 is completed, the control unit 140 ends the walking function determination process and waits for the interrupt signal to be transmitted from the timer 150 again. If the interrupt signal is received from the timer 150, the control part 140 will perform a walking function discrimination | determination process again from step S101.

  According to the present embodiment, since the decrease in walking function is determined based on the ratio R of both foot contact times, it is possible to accurately determine the decrease in walking function even when the amount of exercise of the user is small.

  In addition to the discrimination result, the ratio R of both feet contact time and cadence K are also displayed on the display unit 160, so that the user can easily check not only the discrimination result but also the degree of deterioration of the walking function as a numerical value. Moreover, since the patient who is rehabilitating for the improvement of the walking function can confirm the state of the improvement of the walking function as a numerical value, efficient walking training becomes possible. In particular, it is known that the cadence K that can be reasonably walked is about 100 to 130, so that it is possible to recover the early walking function by repeating walking training so that the cadence K is within the range of 100 to 130. .

  In addition, since both feet contact time is measured using acceleration, for example, when both feet contact time is measured by installing a pressure sensor on the toe and heel, both feet contact time is measured using other sensing information. Unlike the case, the sensor 110 and the control unit 140 can be provided as an integrated device. Therefore, the measuring apparatus 100 can be easily attached to the human body, and the user can be released from the troublesomeness of attaching various sensors to the human body.

  In addition, since the both-foot contact time is measured by combining the measurement results of the accelerations of a plurality of axes, higher measurement accuracy can be realized as compared with the measurement of the both-foot contact time using only one-axis acceleration. In particular, the front and rear inflection points are highly correlated with heel contact, and the upper and lower inflection points are highly correlated with tiptoe separation. Can be measured.

  In S106 of the present embodiment, the time required for the both-foot support period (that is, both-foot contact time) is measured by combining the measurement results of the accelerations of the plurality of axes, but the both-foot contact time may be measured using only one-axis acceleration. Is possible. For example, as shown in FIG. 14, the inflection point from the downward direction to the upward direction immediately after the vertical inflection point of the vertical acceleration ((a) and (c) shown in FIG. 14) ((b) shown in FIG. 14). , (D)) may be measured for both foot support periods, and as shown in FIG. 15, from the longitudinal inflection point of the longitudinal acceleration ((a), (c) shown in FIG. 15). The both-foot contact time may be measured by setting the inflection point ((b), (d) shown in FIG. 15) immediately after the rear direction to the front direction as the both-foot support period. Further, as shown in FIG. 16, the inflection point immediately after the first inflection point ((a) or (c) shown in FIG. 16) of the S-shaped waveform of the lateral acceleration ((b) or ( The contact time of both feet may be measured by d)) until both feet are supported. Since it is not necessary to use an expensive acceleration sensor capable of measuring multi-axis acceleration, the cost of the measuring apparatus 100 can be reduced.

Further, the both-foot contact time may be measured based on the magnitude of acceleration applied to the body during walking. For example, the left-right acceleration a _lr (vector (a) in FIG. 17), the longitudinal acceleration a _fb (vector (b) in FIG. 17), and the vertical acceleration a _ud (vector (c) in FIG. 17) at a certain time during walking. On the other hand, the combined acceleration A shown in FIG. 17D, which is vector-synthesized by applying the following (Formula 5), is calculated.

  This is applied to all the data of “unprocessed acceleration data” identified in step S102. Then, “acceleration data” as shown in FIG. 18, for example, is generated by adding the combined acceleration to the lateral acceleration, longitudinal acceleration, and vertical acceleration. Since the acceleration applied to the human body is the largest when the ground is kicked up, the resultant acceleration indicates a mountain inflection point (decrease from increase) at the time of “toe takeoff”. Therefore, the control unit 140 measures the both-foot contact time with the front and rear inflection points of the longitudinal acceleration and the peak inflection points of the combined acceleration as the both foot support periods. Since there is a high correlation between the acceleration applied to the human body and the toe-off, this makes it possible to measure the contact time of both feet with higher accuracy.

  As shown in FIGS. 4A to 4C, the conversion unit 120 sets the left direction, the forward direction, and the upward direction as positive (positive) directions, respectively, but the right direction, the backward direction, and the downward direction, respectively. It is good also as a plus (positive) direction. In this case, the “front and back inflection point” described in step S106 is not a point that changes from increase to decrease as shown in FIG. 11A, but a point that changes from decrease to increase. This is not a point where the increase turns to a decrease as shown in FIG. 11B, but a point where the decrease turns to an increase. In addition, the “S-shaped waveform” in FIG. 8 described in step S103 is a waveform that is upside down.

  Further, the threshold value used in step S109 for determining a decrease in walking function may be determined based on the sex, weight, etc. of the user. For example, the age and sex of the pedestrian can be input from a menu screen as shown in FIG. 19, and the control unit 140 can determine the age and sex input by the user before executing the walking function determination process. Is acquired from the storage unit 130 or the like. The storage unit 130 is a matrix as shown in FIG. 20 that pre-associates “age / gender of pedestrians” with the standard “ratio of contact time of both feet in one walking cycle R”. The control unit 140 sets a threshold value for determining a decrease in walking function before executing step S109 based on the matrix and the age / sex of the pedestrian. For example, for a 75-year-old woman, “0.37” ((a) shown in FIG. 20) is obtained from the matrix and set as a threshold value. In order not to frequently determine that “the walking machine is lowered”, 0.37 may be multiplied by a predetermined value, for example, 1.3 to set “0.48” as the threshold value. In addition to age and sex, information on height, weight, and stride may be used as information for setting a threshold. Thereby, discrimination with higher accuracy according to the age and sex of the pedestrian becomes possible.

  In step S103, the presence / absence of walking is determined using the acceleration data of the lateral acceleration. For example, whether or not the sine wave waveform (FIG. 15) appearing in the vertical acceleration is equal to or less than a predetermined number of times, similar to step S103. The presence or absence of walking may be determined by determining. Also, the presence or absence of walking may be determined by determining whether or not the sawtooth waveform (FIG. 14) appearing in the longitudinal acceleration is equal to or less than a predetermined number of times, as in step S103.

  In step S103, the presence or absence of walking is determined using sensor information from the acceleration sensor. However, the presence or absence of walking may be determined using sensor information other than the acceleration sensor. For example, a gyro sensor is provided in the measuring apparatus 100, and a change in the turning direction of the pelvis is detected based on the angular velocity detected by the gyro sensor (for example, the timing at which the detected value of the angular velocity changes from plus to minus, or from plus to minus) The change timing is detected as a change in the turning direction of the pelvis), and whether or not walking is determined by determining whether or not the change in the turning direction of the pelvis is equal to or less than a predetermined number of times, as in step S103. Good. Further, the presence or absence of walking may be determined by determining whether or not the pedestrian traveling speed detected by the magnetic sensor is equal to or lower than a predetermined walking speed by providing a magnetic sensor in the measuring apparatus 100. Even when the signal level output from the acceleration sensor is small, the presence or absence of walking can be reliably determined.

  In step S106, the both-foot contact time is measured based on the sensor information from the acceleration sensor, but the both-foot contact time may be measured based on the sensor information from the pressure sensor. For example, as shown in FIG. 21, pad-shaped pressure sensors 191 to 194 are attached to the heels and toes of both feet, and are connected to the measuring apparatus 100 by signal lines 195 and 196. Then, the control unit 140 detects whether the left toe pressure sensor 193 detects pressure until the right toe pressure sensor 192 detects pressure, or after the right toe pressure sensor 191 detects pressure. The contact time of both feet is measured until the pressure sensor 194 detects the pressure until the both feet are supported. When a highly accurate measurement result is required, such as when acquiring experimental data, it is possible to easily measure the time for both feet contact.

(Embodiment 2)
As described above, in the first embodiment, the foot contact time is measured, and the decrease in the walking function is determined based on the measured value. However, it is also possible to determine the decrease in the walking function without using the both foot contact time. Hereinafter, as an example, an apparatus for determining a decrease in walking function based on the magnitude of acceleration applied to the body of a pedestrian will be described. Note that the configuration of the measurement apparatus 100 of the present embodiment is the same as the configuration of the measurement apparatus 100 of the first embodiment shown in FIG. Hereinafter, the operation of the measuring apparatus 100 will be described.

  When the supply of electric power from the battery 180 is started, the sensor 110 measures the vertical acceleration, the horizontal acceleration, and the longitudinal acceleration and outputs them to the conversion unit 120 as an electrical signal. The electrical signal output from the sensor 110 is converted into acceleration data by the conversion unit 120 and sequentially stored in the storage unit 130. In addition, when the supply of power from the battery 180 is started, the timer 150 starts transmitting an interrupt signal to the control unit 140. Each time the control unit 140 receives an interrupt signal from the timer 150, the control unit 140 executes a “walking function determination process” shown in FIG. Hereinafter, the “walking function determination process” will be described with reference to the flowchart of FIG. 22. Note that steps S101 to S104 shown in FIG. 22 are the same as steps S101 to S104 of the first embodiment shown in FIG. Hereinafter, the description starts from step S201.

  The control unit 140 applies the above-described (Equation 5) to all the data of the “unprocessed acceleration data” specified in step S102, and calculates the combined acceleration, respectively. Then, “acceleration data” as shown in FIG. 18, for example, is generated by adding the combined acceleration calculated above to the acceleration data shown in FIG. 7 (step S201).

  Next, the control unit 140 calculates an average value of the plurality of combined accelerations calculated in step S201 (step S202). And the control part 140 discriminate | determines whether the calculated average value is below a predetermined threshold value (step S203). When the average value exceeds the predetermined threshold value (step S203: No), the display unit 160 displays that the walking function is normal (step S204). On the other hand, when the average value is equal to or less than the predetermined threshold (step S203: Yes), the display unit 160 displays that the walking function is degraded (step S205). When the display is completed, the control unit 140 ends the walking function determination process.

  When the walking function is lowered, the force of kicking the ground is weakened, and the acceleration applied to the body is reduced. Therefore, it is possible to perform the determination with higher accuracy by determining the deterioration of the walking function using the composite acceleration.

  In addition, since there is no need to match the three measurement axis directions of the acceleration sensor with the pedestrian's left / right direction, front / rear direction, and up / down direction, the user can more easily attach the measuring device 100 to the human body. Become.

  In addition, the measuring apparatus 100 of Embodiment 1 and 2 is realizable even if it uses a normal computer system instead of a dedicated system. For example, the measuring apparatus 100 may be configured by storing and distributing a program for executing the above-described operation in a computer-readable recording medium, installing the program in a computer, and executing the above-described processing. Good. Further, it may be stored in a disk device provided in a server device on a network such as the Internet so that it can be downloaded to a computer, for example. Further, the above-described functions may be realized by joint operation of the OS and application software. In this case, only the part other than the OS may be stored and distributed in a medium, or may be downloaded to a computer.

  As a recording medium for recording the program, USB memory, flexible disk, CD, DVD, Blu-ray Disc (registered trademark), MO, SD card, Memory Stick (registered trademark), magnetic disk, optical disk, magneto-optical disk Computer-readable recording media such as semiconductor memory and magnetic tape can be used. In addition, it is also possible to use a recording medium that is usually fixed to a system or apparatus, such as an HDD (hard disk) or an SSD (solid state drive).

DESCRIPTION OF SYMBOLS 100 Measuring apparatus 110 Sensor 120 Conversion part 130 Storage part 131 Processing start time preservation | save queue 140 Control part 150 Timer 160 Display part 170 Operation part 171 Power switch 180 Battery 191-194 Pressure sensor 195, 196 Signal line 200 Belt

Claims (8)

  A sensor output acquisition means for acquiring an output from a sensor that is installed in a human body and measures acceleration or pressure applied to the human body;
  1 walking cycle time acquisition means for acquiring the time required for 1 walking cycle based on the sensor output;
  Based on sensor output, it takes from the heel contact of one foot to the toe-off of the other foot during walking Per walking cycleBoth feet contact time measuring means for measuring both feet contact time and,
  Based on the time required for one walking cycle and the contact time of both feet per one walking cycle Calculating means for calculating the ratio of the time for both feet to touch;
  A discriminating means for discriminating whether or not the ratio of both foot contact time is equal to or greater than a predetermined threshold;
  ThePrepare
  A measuring device. The sensor output acquisition means includes
Means for acquiring measurement outputs of accelerations in two or more directions,
The both foot contact time measuring means,
Means for measuring both foot contact time based on acceleration in two or more directions,
The measuring apparatus according to claim 1. The sensor output acquisition means includes
Means for obtaining a measurement output of longitudinal acceleration which is acceleration in the traveling direction;
Means for obtaining a measurement output of vertical acceleration, which is acceleration in the vertical direction,
The both foot contact time measuring means,
Means for discriminating when the heel-contact is based on the timing at which the longitudinal acceleration decreases from increase or decreases to increase;
Means for discriminating the toe-off time based on the timing at which the vertical acceleration decreases from increase or decreases to increase;
Means for measuring the time required from heel-contact to heel-off immediately after heel-contact,
The measuring apparatus according to claim 2. The sensor output acquisition means includes
Means for obtaining a measurement output of longitudinal acceleration, which is acceleration in the traveling direction,
The both foot contact time measuring means,
Means for obtaining a combined acceleration by vector-synthesizing accelerations in two or more directions;
Means for discriminating when the heel-contact is based on the timing at which the longitudinal acceleration decreases from increase or decreases to increase;
Means for discriminating the toe-off time based on the timing at which the resultant acceleration changes from increasing to decreasing;
Means for measuring the time required from heel-contact to heel-off immediately after heel-contact,
The measuring apparatus according to claim 2. The sensor output acquisition means includes
Means for acquiring a measurement output of lateral acceleration that is acceleration in the lateral direction,
1 walk cycle time acquisition means,
Based on the measurement output of the left-right acceleration, comprising means for acquiring the time taken for one walking cycle,
Measurement apparatus according to any one of claims 1 to 4, characterized in that. Information input means for inputting information on the age, sex, height, weight, or stride of the pedestrian,
Threshold acquisition means for acquiring the threshold based on the information input to the information input means,
The measuring apparatus according to claim 1, wherein A sensor output acquisition step for acquiring an output from a sensor that is installed on the human body and measures acceleration or pressure applied to the human body;
1 walk cycle time acquisition step of acquiring time required for 1 walk cycle based on the sensor output ;
Based on the sensor output, a both-foot contact time acquisition step of acquiring a both-foot contact time per one walking cycle, which is a time required from the heel contact of one foot to the toe-off of the other foot during walking ;
Based on the time required for 1 walking period and the two-footed contact time per gait cycle, a calculation step of calculating the ratio of which accounts footed contact time 1 walking cycle,
A determination step of determining whether or not the ratio of both feet contact time is equal to or greater than a predetermined threshold;
Having
A measuring method characterized by the above. A sensor output acquisition step for acquiring an output from a sensor that is installed on the human body and measures acceleration or pressure applied to the human body;
1 walk cycle time acquisition step of acquiring time required for 1 walk cycle based on the sensor output ;
Based on the sensor output, a both-foot contact time acquisition step of acquiring a both-foot contact time per one walking cycle, which is a time required from the heel contact of one foot to the toe-off of the other foot during walking ;
Based on the time required for 1 walking period and the two-footed contact time per gait cycle, a calculation step of calculating the ratio of which accounts footed contact time 1 walking cycle,
A determination step of determining whether or not the ratio of both feet contact time is equal to or greater than a predetermined threshold;
To run on a computer,
A measurement program characterized by that.

Images