CN111632361B - Foot pronation detection method and device based on sole pressure - Google Patents
Foot pronation detection method and device based on sole pressure Download PDFInfo
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Abstract
The embodiment of the invention provides a method and a device for detecting pronation of feet based on plantar pressure, wherein the method comprises the following steps: acquiring real-time pressure signals of each area of the foot in a preset time period, wherein each area of the foot comprises a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot and a fifth metatarsal joint area of the foot; determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; and if the proportion is higher than the first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation. The method and the device provided by the embodiment of the invention realize the balance between the cost and the precision of the excessive pronation detection.
Description
Technical Field
The invention relates to the technical field of pronation detection, in particular to a pronation detection method and device based on plantar pressure.
Background
With the improvement of living standard, people increasingly pay attention to the health problem, and sports become an indispensable part of daily life of people. In recent years, many intelligent wearable products are on the market to record people's amount of motion. For the general public, the wearable devices provide certain exercise health data information feedback by detecting the walking steps, routes and calorie consumption of the human body, but the traditional wearable devices cannot completely meet the requirements of the crowd with higher requirements on health data.
For people who need more accurate analysis and research on exercise health, such as frequent sports runners and postoperative rehabilitation patients, irregular gaits can seriously affect human health, and if the gaits are not corrected, serious injury can be caused to knees. Incorrect foot posture can be reflected by the distribution of plantar pressure. Pronation refers to the outward turning, abduction, and dorsiflexion of the foot, which mainly occurs in the subtalar joint. When pronation occurs, the calcaneus turns outward, the talus adducts and the driver bends. Pronation occurs during the entire period from heel strike to mid-support in one gait cycle to reduce shock from the ground. However, if the pronation time exceeds 25% of the whole support period, excessive pronation will occur, which will affect the force lines of tibia and knee joint, further cause related muscle and ligament strain injury, and finally cause chronic pain such as foot pain and knee pain. Therefore, the pressure sensor is scientifically installed on the sole of the foot, the health of the foot is detected in real time, and reasonable advice guidance is provided for the running posture of the user and potential problems of the foot.
The following are currently studied about the plantar pressure distribution measuring technique:
1. the most advanced state at present is to arrange sensors in shoes or insoles, such as the American Fcan system and the Belgian RScan system, and although the gait analysis systems have high precision and complete functions, the gait analysis systems are expensive and hard to bear by ordinary people, and are difficult to popularize and apply particularly when medical resources are in short supply.
2. Some low-cost, small-sized and portable plantar pressure analysis systems exist in the market, but most of the plantar pressure analysis systems utilize a threshold method for analysis, and the stability of the result is difficult to guarantee. In addition, the existing analysis method is only suitable for specific people, the phase sequence of human gait is preset according to experience, and the internal difference of individual gait cannot be fully considered.
3. In the domestic market, a mature finished product for detecting pronation is not available for a while, and the finished product is still in a laboratory stage at present.
Therefore, how to avoid the problem that the high precision, complete functions and cost of the existing method for detecting pronation of feet are difficult to balance, and it is difficult to provide a method for detecting pronation of feet with suitable precision and cost for average people remains a problem to be solved urgently by the technical staff in the field.
Disclosure of Invention
The embodiment of the invention provides a method and a device for detecting pronation of feet based on plantar pressure, which are used for solving the problem that the existing method for detecting pronation of feet is high in precision, complete in function and difficult in cost balance.
In a first aspect, an embodiment of the present invention provides a method for detecting pronation based on plantar pressure, including:
acquiring real-time pressure signals of each area of the foot in a preset time period, wherein each area of the foot comprises a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot and a fifth metatarsal joint area of the foot;
determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot;
and if the proportion is higher than the first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation.
Preferably, in the method, the determining a ratio of a pronation duration to a support duration in any one of the foot support periods based on the real-time pressure signals of the respective areas of the foot specifically includes:
determining the supporting early stage starting time, the supporting middle stage ending time and the supporting late stage ending time in any supporting period of the foot based on the real-time pressure signals of all areas of the foot;
and determining the proportion of the pronation time length of the foot supporting period to the supporting time length based on the supporting early-stage starting time, the supporting middle-stage ending time and the supporting later-stage ending time.
Preferably, in the method, the determining a support early stage starting time, a support middle stage ending time and a support late stage ending time in any support period of the foot based on the real-time pressure signals of each region of the foot specifically includes:
marking the real-time pressure signals of all areas of the foot as high pressure or low pressure based on a second threshold value;
determining a moment when a last heel area of the foot is high in pressure and a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal area of the foot and a fifth metatarsal area of the foot are all low in pressure for the first occurrence in any one foot support period as a support early period starting moment in the foot support period;
determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the third metatarsal area, the fifth metatarsal area and the first metatarsal joint area of the foot in the foot supporting period are all the first pressure as the end moment of the middle supporting period in the foot supporting period;
and determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the first-toe metatarsal joint area, the second-toe metatarsal joint area, the third metatarsal area and the fifth metatarsal area of the foot are all low in voltage and the first metatarsal area of the foot is high in voltage in the last occurrence of the foot supporting period as the end moment of the supporting later period in the foot supporting period.
Preferably, in the method, the determining a ratio of the pronation duration to the support duration in the foot support period based on the support earlier-stage starting time, the support middle-stage ending time, and the support later-stage ending time specifically includes:
the ratio of pronation time to support time of the foot support period
Wherein, T1For the support earlier stage starting time, T2Is the end time of the support middle period, T3And the later support end time is obtained.
Preferably, the method further comprises:
and determining the ratio of the number of gait cycles which are determined to be excessive pronation to the total number of gait cycles as an abnormal cycle ratio, and outputting the abnormal cycle ratio.
Preferably, in the method, the first threshold is 25%.
In a second aspect, an embodiment of the present invention provides a device for detecting pronation based on plantar pressure, including:
the pressure sensor module is used for acquiring real-time pressure signals of all areas of the foot in a preset time period, wherein all areas of the foot comprise a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area, a first metatarsal joint area, a second metatarsal joint area, a third metatarsal joint area and a fifth metatarsal joint area;
the algorithm analysis module is used for determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; if the proportion is higher than a first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation;
and the wireless communication module is used for sending the result of whether each gait cycle is judged to be excessive pronation to the receiving end.
Preferably, in the device, the determining a ratio of a pronation duration to a support duration in any one of the foot support periods based on the real-time pressure signals of the regions of the foot specifically includes:
determining the supporting early stage starting time, the supporting middle stage ending time and the supporting late stage ending time in any supporting period of the foot based on the real-time pressure signals of all areas of the foot;
and determining the proportion of the pronation time length of the foot supporting period to the supporting time length based on the supporting early-stage starting time, the supporting middle-stage ending time and the supporting later-stage ending time.
In a third aspect, an embodiment of the present invention provides an electronic device, which includes a memory, a processor, and a computer program stored in the memory and executable on the processor, and the processor executes the program to implement the steps of the plantar pressure based foot pronation detection method according to the first aspect.
In a fourth aspect, embodiments of the present invention provide a non-transitory computer-readable storage medium, on which a computer program is stored, the computer program, when executed by a processor, implementing the steps of the plantar pressure based foot pronation detection method as provided in the first aspect.
According to the method and the device provided by the embodiment of the invention, real-time pressure signals of all areas of the foot are collected within a preset time period, wherein all areas of the foot comprise a last heel area, a second-heel area, a left heel area, a second-heel area, a first phalanx area, a first metatarsal joint area, a second metatarsal joint area, a third metatarsal joint area and a fifth metatarsal joint area; determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; if the proportion is higher than the first threshold value, the gait cycle corresponding to the foot support period is judged to be excessive foot pronation, the pronation duration and the support duration in the same foot support period are determined according to the change condition of real-time pressure of each area of the foot, and then whether the gait cycle corresponding to the foot support period is excessive foot pronation is judged based on the proportion of the pronation duration to the support duration. Therefore, the method and the device provided by the embodiment of the invention realize the balance between the cost and the precision of the excessive pronation detection.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, a brief description will be given below of the drawings required for the embodiments or the technical solutions in the prior art, and it is obvious that the drawings in the following description are some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to these drawings without creative efforts.
Fig. 1 is a schematic flow chart of a method for detecting pronation based on plantar pressure according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a configuration of pressure sensor distribution in various regions of a foot according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of a complete gait cycle provided by an embodiment of the invention;
fig. 4 is a schematic structural diagram of a device for detecting pronation based on plantar pressure according to an embodiment of the present invention;
fig. 5 is a schematic physical structure diagram of an electronic device according to an embodiment of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, but not all, embodiments of the present invention. All other embodiments, which can be obtained by a person skilled in the art without inventive effort based on the embodiments of the present invention, are within the scope of the present invention.
The existing method for detecting pronation of foot generally has the problems of high precision, complete functions and high cost which are difficult to balance. In view of the above, the embodiment of the invention provides a method for detecting pronation based on plantar pressure. Fig. 1 is a schematic flow chart of a method for detecting pronation based on plantar pressure according to an embodiment of the present invention, as shown in fig. 1, the method includes:
Specifically, fig. 2 is a schematic structural diagram of the distribution of pressure sensors in various regions of the foot according to an embodiment of the present invention, as shown in fig. 2, GRF pressure sensors placed at the GRF1 of the foot are used to acquire pressure in the heel area of the foot, GRF pressure sensors placed at foot GRF2 are used to acquire pressure in the left heel area of the foot, GRF pressure sensors placed at foot GRF3 are used to acquire pressure in the right heel area of the foot, a GRF pressure sensor placed at the GRF4 of the foot is used to acquire pressure in the third metatarsal region of the foot, a GRF pressure sensor placed at foot GRF5 is used to acquire pressure in the fifth metatarsal region of the foot, a GRF pressure sensor placed at the GRF6 of the foot is used to acquire pressure at the metatarsophalangeal joint area of the second digit of the foot, a GRF pressure sensor placed at the GRF7 of the foot is used to acquire pressure at the first metatarsal joint area of the foot, a GRF pressure sensor placed at the GRF8 of the foot is used to acquire pressure in the first phalangeal region of the foot. Therefore, the real-time pressure signals of the foot regions are collected within a preset time period, wherein the preset time period can be any preset time period, such as a time period of normal activities of the detected person with the feet rotating forwards, for example, 8 to 9 hours of morning work or morning exercise; the real-time pressure signals of all areas of the foot are acquired in real time through pressure sensors arranged in all areas of the sole.
And 120, determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot.
Specifically, the change condition of the pressure of each region of the foot in a preset time period can be obtained based on the real-time pressure signals of each region of the foot, each foot supporting region can be divided according to the change condition, and then the pronation time length and the supporting time length of the foot supporting period are divided for any foot supporting period according to the change condition, so that the proportion of the pronation time length in any foot supporting period to the supporting time length can be calculated. Therefore, all that is needed in this step is to divide each foot supporting area, i.e. to realize the gait cycle division, and fig. 3 is a schematic diagram of a complete gait cycle provided by the embodiment of the present invention. As shown in fig. 3, a complete gait cycle is divided into two parts: a support period and a swing period; a complete gait cycle is defined as starting from the initial contact of one side foot with the ground and ending to the next initial contact of the side foot with the ground, wherein the support period is defined as the whole process of the contact of the foot and the ground in one gait cycle, starting from the initial contact of the foot and the ground and ending at the toe-off state, the swing period is defined as the whole process of the stage that the foot is not in contact with the ground, the whole process starts at the toe-off state and ends at the next contact of the foot and the ground, and the support period and the swing period jointly form the complete gait cycle.
And step 130, if the ratio is higher than the first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation.
Specifically, the excessive pronation is determined by the fact that the ratio of the pronation time to the total support period time exceeds a certain threshold, and usually, the threshold takes a value of 25%.
According to the method provided by the embodiment of the invention, real-time pressure signals of all areas of the foot are collected within a preset time period, wherein all areas of the foot comprise a last heel area, a left heel area after the last foot, a right heel area after the last foot, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot and a fifth metatarsal joint area of the foot; determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; if the proportion is higher than the first threshold value, the gait cycle corresponding to the foot support period is judged to be excessive foot pronation, the pronation duration and the support duration in the same foot support period are determined according to the change condition of real-time pressure of each area of the foot, and then whether the gait cycle corresponding to the foot support period is excessive foot pronation is judged based on the proportion of the pronation duration to the support duration. Therefore, the method provided by the embodiment of the invention realizes the balance between the cost and the precision of the excessive pronation detection.
Based on the above embodiment, in the method, the determining, based on the real-time pressure signals of the various regions of the foot, a ratio of a pronation time length to a support time length in any one of the foot support periods specifically includes:
determining the supporting early stage starting time, the supporting middle stage ending time and the supporting late stage ending time in any supporting period of the foot based on the real-time pressure signals of all areas of the foot;
and determining the proportion of the pronation time length of the foot supporting period to the supporting time length based on the supporting early-stage starting time, the supporting middle-stage ending time and the supporting later-stage ending time.
Specifically, the support period in each gait cycle can be divided based on the change condition of the real-time pressure signals of each area of the foot in a preset time period, then the support early-stage starting time, the support middle-stage ending time and the support later-stage ending time of any support period can be detected according to the real-time pressure values of each area of the foot, and the support early-stage starting time to the support middle-stage ending time are the pronation time of the foot support period, while the support early-stage starting time to the support later-stage ending time are the support time of the foot support period, so that the proportion of the pronation time of the foot support period to the support time can be obtained.
Based on any one of the above embodiments, in the method, the determining a support early stage starting time, a support middle stage ending time, and a support late stage ending time in any one of the support periods of the foot based on the real-time pressure signals of the regions of the foot specifically includes:
marking the real-time pressure signals of all areas of the foot as high pressure or low pressure based on a second threshold value;
determining a moment when a last heel area of the foot is high in pressure and a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal area of the foot and a fifth metatarsal area of the foot are all low in pressure for the first occurrence in any one foot support period as a support early period starting moment in the foot support period;
determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the third metatarsal area, the fifth metatarsal area and the first metatarsal joint area of the foot in the foot supporting period are all the first pressure as the end moment of the middle supporting period in the foot supporting period;
and determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the first-toe metatarsal joint area, the second-toe metatarsal joint area, the third metatarsal area and the fifth metatarsal area of the foot are all low in voltage and the first metatarsal area of the foot is high in voltage in the last occurrence of the foot supporting period as the end moment of the supporting later period in the foot supporting period.
Specifically, the real-time pressure signals of each area of the foot are acquired by voltage film pressure sensors arranged in each area of the sole, the sensors generally acquire resistance values, and the pressure values are obtained through conversion from the resistance values to the voltage values. For example, for a GRF sensor, the resistance value signal collected by the sensor has a value range of [0,4096 ]]Using the formula
Converting the resistance value into a voltage value, here, 3.3V is only an example of an operating voltage, and for other voltage values, still falls within the scope of the present invention. The voltage values here represent the pressure values of the various regions of the foot. Then, fuzzification processing is carried out on the pressure values of all areas of the foot, namely all the pressure values are divided into two types: the high pressure and the low pressure are classified by a second threshold value, and a pressure value higher than the second threshold value is set as the high pressure, and a pressure value not higher than the second threshold value is set as the low pressure.
The support early stage, the support middle stage and the support later stage are explained as follows:
1. front Support (FS): force is measured from the last heel area, the second left heel area and the second right heel area of the heel, the outer side of the heel begins to contact the ground, and the third metatarsal bone area and the fifth metatarsal bone area of the foot begin to measure force.
2. Mid support period (Mid stability, MS): the medial forefoot begins to contact the ground and the second and first metatarsal joint areas of the foot begin to measure forces, with or without the first phalanx area of the foot, depending on the gait.
3. Late Back Stage (BS): the last heel area, the left heel area and the right heel area of the heel can not measure force, but the rest points are still powerful until the pressure on the sole of the foot is completely eliminated.
The above three gait phases occur in the same support period, and the rule is designed according to the magnitude of the pressure value of each area of the foot corresponding to each gait phase, wherein the pressure value is high pressure (Large, L), the higher the possibility that the area of the foot corresponding to the pressure value touches the ground is, the lower the possibility that the area of the foot corresponding to the pressure value touches the ground is. Pressure values are collected for 8 areas of the foot, each area having 2 possible linguistic values (L and S), which may constitute 28In the embodiment of the present invention, only those rules that have the largest contribution to distinguishing possible phases are used to form a fuzzy inference rule table, which is shown in table 1:
TABLE 1 fuzzy inference rule Table
Table 1 illustrates: GRF1, GRF2, GRF3, GRF4, GRF5, GRF6, GRF7 and GRF8 respectively correspond to pressure values of a last heel area, a second-heel left heel area, a second-heel right heel area, a third metatarsal area, a fifth metatarsal area, a second-toe metatarsal joint area, a first-toe metatarsal joint area and a first-toe phalanx area of the foot, which are L or S; "/" indicates that the value can be L or S, and can be any value; FS represents the gait phase as the early stage of support, MS represents the gait phase as the late stage of support, and BS represents the gait phase as the late stage of support.
Table 1 shows 9 inference rules in which the gait phase changes from beginning to end in a support period. The combination of the pressure values of the areas of the foot represented by the inference rule 1 represents the early support period of the foot support period, and the moment when the combination of the pressure values of the areas of the foot represented by the inference rule 1 appears for the first time is the starting moment of the early support period of the foot support period; the combination of the pressure values of the areas of the foot represented by the inference rule 7 represents the middle support period of the foot support period, and the moment when the combination of the pressure values of the areas of the foot represented by the inference rule 7 occurs at the last time is the early support period end moment of the foot support period; the combination of pressure values of the regions of the foot represented by inference rule 9 represents the late support period of the foot, and the last time the combination of pressure values of the regions of the foot represented by inference rule 9 occurs is the end of the late support period of the foot. Thus, the moment when the last heel area of the foot is high and the first phalange area, the first metatarsal joint area, the second metatarsal joint area, the third metatarsal area and the fifth metatarsal area of the foot are all low in pressure for the first occurrence in any one of the foot support periods is determined as the beginning of the earlier support period in that foot support period; determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the third metatarsal area, the fifth metatarsal area and the first metatarsal joint area of the foot in the foot supporting period are all the first pressure as the end moment of the middle supporting period in the foot supporting period; and determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the first-toe metatarsal joint area, the second-toe metatarsal joint area, the third metatarsal area and the fifth metatarsal area of the foot are all low in voltage and the first metatarsal area of the foot is high in voltage in the last occurrence of the foot supporting period as the end moment of the supporting later period in the foot supporting period.
Based on any one of the embodiments, in the method, the determining, based on the support earlier-stage starting time, the support middle-stage ending time, and the support later-stage ending time, a ratio of a pronation duration to a support duration of the foot support period specifically includes:
the ratio of pronation time to support time of the foot support period
Wherein, T1For the support earlier stage starting time, T2Is the end time of the support middle period, T3And the later support end time is obtained.
Specifically, the pronation duration of the foot supporting period is from the support early period starting time to the support middle period ending time of the foot supporting period, and the support duration of the foot supporting period is from the support early period starting time to the support later period ending time of the foot supporting period, so that the pronation duration of the foot supporting period accounts for the proportion of the support duration
Wherein, T1For the support earlier stage starting time, T2Is the end time of the support middle period, T3And the later support end time is obtained.
Based on any one of the above embodiments, the method further includes:
and determining the ratio of the number of gait cycles which are determined to be excessive pronation to the total number of gait cycles as an abnormal cycle ratio, and outputting the abnormal cycle ratio.
Specifically, whether each obtained gait cycle is the result of excessive pronation or not is correspondingly judged, the detected person cannot be determined to have excessive pronation through a few gait cycles being excessive pronation, but the ratio of the number of the gait cycles of excessive pronation to the total number of the gait cycles within a period of time is counted to be used as the abnormal cycle ratio, and the abnormal cycle ratio is output to be used for more intuitively displaying whether excessive pronation occurs or not.
In any of the above embodiments, the method, wherein the first threshold is 25%.
In particular, in general, the value of the first threshold may be adjusted according to different medically defined criteria, for example, the criteria are moderately relaxed for young people and the labeling is moderately strict for elderly people. Generally, a recommended criterion for all age groups internationally is to have a first threshold value of 25%.
Based on any one of the embodiments, an embodiment of the present invention provides a device for detecting pronation based on plantar pressure, and fig. 4 is a schematic structural view of the device for detecting pronation based on plantar pressure according to the embodiment of the present invention. As shown in fig. 4, the apparatus includes a pressure sensor module 410, an algorithm analysis module 420, and a wireless communication module 430, wherein,
the pressure sensor module 410 is configured to acquire real-time pressure signals of each area of the foot within a preset time period, where each area of the foot includes a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot, and a fifth metatarsal joint area of the foot;
the algorithm analysis module 420 is configured to determine a ratio of a pronation duration to a support duration in any one of the foot support periods based on the real-time pressure signals of the various regions of the foot; if the proportion is higher than a first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation;
the wireless communication module 420 is configured to send a result indicating whether each gait cycle is determined to be excessive pronation to a receiving end.
According to the device provided by the embodiment of the invention, real-time pressure signals of all areas of the foot are collected within a preset time period, wherein all areas of the foot comprise a last heel area, a left heel area after the last foot, a right heel area after the last foot, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot and a fifth metatarsal joint area of the foot; determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; if the proportion is higher than the first threshold value, the gait cycle corresponding to the foot support period is judged to be excessive foot pronation, the pronation duration and the support duration in the same foot support period are determined according to the change condition of real-time pressure of each area of the foot, and then whether the gait cycle corresponding to the foot support period is excessive foot pronation is judged based on the proportion of the pronation duration to the support duration. Therefore, the device provided by the embodiment of the invention realizes the balance between the cost and the precision of the detection of the over pronation.
Based on any one of the above embodiments, in the apparatus, the determining, based on the real-time pressure signals of the regions of the foot, a ratio of a pronation duration to a support duration in any one of the foot support periods specifically includes:
determining the supporting early stage starting time, the supporting middle stage ending time and the supporting late stage ending time in any supporting period of the foot based on the real-time pressure signals of all areas of the foot;
and determining the proportion of the pronation time length of the foot supporting period to the supporting time length based on the supporting early-stage starting time, the supporting middle-stage ending time and the supporting later-stage ending time.
Based on any one of the above embodiments, in the apparatus, the determining a support early stage starting time, a support middle stage ending time, and a support late stage ending time in any one of the support periods of the foot based on the real-time pressure signals of the regions of the foot specifically includes:
marking the real-time pressure signals of all areas of the foot as high pressure or low pressure based on a second threshold value;
determining a moment when a last heel area of the foot is high in pressure and a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal area of the foot and a fifth metatarsal area of the foot are all low in pressure for the first occurrence in any one foot support period as a support early period starting moment in the foot support period;
determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the third metatarsal area, the fifth metatarsal area and the first metatarsal joint area of the foot in the foot supporting period are all the first pressure as the end moment of the middle supporting period in the foot supporting period;
and determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the first-toe metatarsal joint area, the second-toe metatarsal joint area, the third metatarsal area and the fifth metatarsal area of the foot are all low in voltage and the first metatarsal area of the foot is high in voltage in the last occurrence of the foot supporting period as the end moment of the supporting later period in the foot supporting period.
Based on any one of the above embodiments, in the apparatus, the determining, based on the support early-stage starting time, the support middle-stage ending time, and the support later-stage ending time, a ratio of a pronation duration to a support duration of the foot support period specifically includes:
the ratio of pronation time to support time of the foot support period
Wherein, T1For the support earlier stage starting time, T2Is the end time of the support middle period, T3And the later support end time is obtained.
In the apparatus according to any of the above embodiments, the algorithm analysis module is further configured to,
and determining the ratio of the number of gait cycles judged to be excessive pronation to the total number of gait cycles as the abnormal cycle ratio.
In the apparatus according to any of the above embodiments, the first threshold is 25%.
Fig. 5 is a schematic entity structure diagram of an electronic device according to an embodiment of the present invention, and as shown in fig. 5, the electronic device may include: a processor (processor)501, a communication Interface (Communications Interface)502, a memory (memory)503, and a communication bus 504, wherein the processor 501, the communication Interface 502, and the memory 503 are configured to communicate with each other via the communication bus 504. The processor 501 may call a computer program stored on the memory 503 and executable on the processor 501 to perform the method for detecting pronation based on plantar pressure provided by the above embodiments, for example, including: acquiring real-time pressure signals of each area of the foot in a preset time period, wherein each area of the foot comprises a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot and a fifth metatarsal joint area of the foot; determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; and if the proportion is higher than the first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation.
In addition, the logic instructions in the memory 503 may be implemented in the form of software functional units and stored in a computer readable storage medium when the logic instructions are sold or used as independent products. Based on such understanding, the technical solutions of the embodiments of the present invention may be essentially implemented or make a contribution to the prior art, or may be implemented in the form of a software product stored in a storage medium and including instructions for causing a computer device (which may be a personal computer, a server, or a network device) to execute all or part of the steps of the methods described in the embodiments of the present invention. And the aforementioned storage medium includes: a U-disk, a removable hard disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a magnetic disk or an optical disk, and other various media capable of storing program codes.
Embodiments of the present invention further provide a non-transitory computer-readable storage medium, on which a computer program is stored, where the computer program is implemented to perform the method for detecting pronation based on plantar pressure provided in the foregoing embodiments when executed by a processor, for example, the method includes: acquiring real-time pressure signals of each area of the foot in a preset time period, wherein each area of the foot comprises a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot and a fifth metatarsal joint area of the foot; determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; and if the proportion is higher than the first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation.
The above-described system embodiments are merely illustrative, and the units described as separate parts may or may not be physically separate, and parts displayed as units may or may not be physical units, may be located in one place, or may be distributed on a plurality of network units. Some or all of the modules may be selected according to actual needs to achieve the purpose of the solution of the present embodiment. One of ordinary skill in the art can understand and implement it without inventive effort.
Through the above description of the embodiments, those skilled in the art will clearly understand that each embodiment can be implemented by software plus a necessary general hardware platform, and certainly can also be implemented by hardware. With this understanding in mind, the above-described technical solutions may be embodied in the form of a software product, which can be stored in a computer-readable storage medium such as ROM/RAM, magnetic disk, optical disk, etc., and includes instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to execute the methods described in the embodiments or some parts of the embodiments.
Finally, it should be noted that: the above examples are only intended to illustrate the technical solution of the present invention, but not to limit it; although the present invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some technical features may be equivalently replaced; and such modifications or substitutions do not depart from the spirit and scope of the corresponding technical solutions of the embodiments of the present invention.
Claims (8)
1. A plantar pressure-based pronation detection method is characterized by comprising the following steps:
acquiring real-time pressure signals of each area of the foot in a preset time period, wherein each area of the foot comprises a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal joint area of the foot and a fifth metatarsal joint area of the foot;
determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot;
if the proportion is higher than a first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation;
wherein, the determining the proportion of the pronation duration to the support duration in any foot support period based on the real-time pressure signals of all areas of the foot specifically comprises:
determining the supporting early stage starting time, the supporting middle stage ending time and the supporting late stage ending time in any supporting period of the foot based on the real-time pressure signals of all areas of the foot;
and determining the proportion of the pronation time length of the foot supporting period to the supporting time length based on the supporting early-stage starting time, the supporting middle-stage ending time and the supporting later-stage ending time.
2. The plantar pressure-based pronation detection method according to claim 1, wherein the determining of the support early stage starting time, the support middle stage ending time and the support late stage ending time in any one of the support periods of the foot based on the real-time pressure signals of all areas of the foot specifically comprises:
marking the real-time pressure signals of all areas of the foot as high pressure or low pressure based on a second threshold value;
determining a moment when a last heel area of the foot is high in pressure and a first phalanx area of the foot, a first metatarsal joint area of the foot, a second metatarsal joint area of the foot, a third metatarsal area of the foot and a fifth metatarsal area of the foot are all low in pressure for the first occurrence in any one foot support period as a support early period starting moment in the foot support period;
determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the third metatarsal area, the fifth metatarsal area and the first metatarsal joint area of the foot in the foot supporting period are all the first pressure as the end moment of the middle supporting period in the foot supporting period;
and determining the moment when the last heel area, the second-foot left heel area, the second-foot right heel area, the first-toe metatarsal joint area, the second-toe metatarsal joint area, the third metatarsal area and the fifth metatarsal area of the foot are all low in voltage and the first metatarsal area of the foot is high in voltage in the last occurrence of the foot supporting period as the end moment of the supporting later period in the foot supporting period.
3. The plantar pressure-based foot pronation detection method according to claim 2, wherein the step of determining the ratio of the pronation duration to the support duration of the foot support period based on the support early-stage starting time, the support middle-stage ending time and the support late-stage ending time specifically comprises the steps of:
the ratio of pronation time to support time of the foot support period
Wherein, T1For the support earlier stage starting time, T2Is the end time of the support middle period, T3And the later support end time is obtained.
4. The plantar pressure based forefoot detection method of any one of claims 1-2, further comprising:
and determining the ratio of the number of gait cycles which are determined to be excessive pronation to the total number of gait cycles as an abnormal cycle ratio, and outputting the abnormal cycle ratio.
5. The method of detecting foot pronation according to any of claims 1-2, wherein the first threshold is 25%.
6. A pronation detection device based on plantar pressure, characterized by that includes:
the pressure sensor module is used for acquiring real-time pressure signals of all areas of the foot in a preset time period, wherein all areas of the foot comprise a last heel area, a second-foot left heel area, a second-foot right heel area, a first phalanx area, a first metatarsal joint area, a second metatarsal joint area, a third metatarsal joint area and a fifth metatarsal joint area;
the algorithm analysis module is used for determining the proportion of the pronation time length to the support time length in any foot support period based on the real-time pressure signals of all areas of the foot; if the proportion is higher than a first threshold value, judging the gait cycle corresponding to the foot support period as excessive pronation;
the wireless communication module is used for sending a result of judging whether each gait cycle is excessive pronation to the receiving end;
wherein, the determining the proportion of the pronation duration to the support duration in any foot support period based on the real-time pressure signals of all areas of the foot specifically comprises:
determining the supporting early stage starting time, the supporting middle stage ending time and the supporting late stage ending time in any supporting period of the foot based on the real-time pressure signals of all areas of the foot;
and determining the proportion of the pronation time length of the foot supporting period to the supporting time length based on the supporting early-stage starting time, the supporting middle-stage ending time and the supporting later-stage ending time.
7. An electronic device comprising a memory, a processor and a computer program stored on the memory and executable on the processor, wherein the processor when executing the program implements the steps of the plantar pressure based foot pronation detection method according to any one of claims 1-4.
8. A non-transitory computer readable storage medium having a computer program stored thereon, wherein the computer program, when executed by a processor, implements the steps of the plantar pressure based pronation detection method according to any one of claims 1-4.
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