Functional insole for inducing proper gait and preventing ankle sprain

Abstract

The present invention relates to a functional insole capable of preventing ankle sprains while simultaneously supporting the transverse arch, medial longitudinal arch, and lateral longitudinal arch of the forefoot. The insole of the present invention comprises a forefoot portion, a posterior insole portion, and a protrusion formed between them, wherein the protrusion has a structure that protrudes upward and sinks downward. Accordingly, during walking, it supports the transverse arch of the forefoot during the swing phase and absorbs shock by elastically deforming under load during the stance phase. In addition, the protrusion is formed in an asymmetrical shape to induce weight transfer, and the lateral wing portion supports the fifth metatarsal region to suppress excessive rotation of the ankle joint. Accordingly, walking stability is improved and the likelihood of ankle sprains is reduced.

Description

Technology Field

[0001] The present invention relates to an insole for shoes, and more specifically, to a functional insole that structurally supports the transverse arch, medial longitudinal arch, and lateral longitudinal arch of the forefoot, while simultaneously preventing ankle sprains caused by excessive rotation of the ankle joint during walking. Background Technology

[0002] The human foot performs the function of supporting body weight and absorbing shock transmitted from the ground during the process of walking and maintaining an upright posture. To this end, multiple arches are formed on the soles of the feet, and these arch structures play an important role in maintaining foot stability and walking efficiency.

[0004] The structure of the foot arch can generally be divided into the forefoot transverse arch (AB), medial longitudinal arch (AC), and lateral longitudinal arch (BC), as shown in Fig. 5.

[0005] The forefoot transverse arch (AB) is an arch structure formed over the section from the first metatarsal to the fifth metatarsal (rectangular dotted line) as shown in Fig. 6, and performs the function of distributing body weight and generating propulsion in the front part of the foot.

[0006] The medial longitudinal arch (AC) is an arch structure formed in the section extending from the first metatarsal bone through the navicular bone to the anterior part of the calcaneus; it functions as the primary cushioning structure of the foot, absorbing body weight and providing rebound force during walking.

[0007] The lateral longitudinal arch (BC) is an arch structure formed in the section extending from the fifth metatarsal bone through the cuboid bone to the anterior part of the calcaneus, and it plays a role in maintaining lateral stability of the foot and assisting in balance during walking.

[0008] Here, the calcaneus is a bone that makes up the sole of the foot and is the part that first comes into contact with the ground when walking.

[0010] These forefoot transverse arch (AB), medial longitudinal arch (AC), and lateral longitudinal arch (BC) are interconnected to form a three-dimensional arch structure of the entire sole of the foot, and play a role in distributing body weight, cushioning impact transmitted from the ground, and stably inducing the movement of the body's center of gravity.

[0012] However, if the arch structure is degraded or collapses due to congenital factors, insufficient muscle development during the growth process, overweight, prolonged standing, incorrect walking habits, or shoe-wearing habits, it can progress to a flat foot condition where the entire sole of the foot contacts the ground. In such cases, the impact from body weight is concentrated on the forefoot, midfoot, and hindfoot, causing a rapid increase in foot fatigue and increasing the likelihood of various foot diseases such as plantar fasciitis, hallux valgus, interdigital neuralgia, corns, and ankle joint diseases.

[0014] In particular, when the transverse arch (AB) of the forefoot is degraded, the transverse arch structure formed in the first to fifth metatarsals collapses, causing localized pressure concentration in the forefoot, which can reduce the propulsion efficiency of the foot during walking and induce pain. In addition, an imbalance between the medial longitudinal arch (AC) and the lateral longitudinal arch (BC) can disrupt the alignment of the ankle joint, causing the ankle to tilt excessively in the inversion or eversion direction, which increases the risk of ankle sprains.

[0016] To address these issues, various functional insoles have been proposed in the past to support the arch of the foot. Conventional functional insoles are generally configured to support the sole of the foot by protruding the medial longitudinal arch region upward, or by attaching pads to the forefoot or hindfoot. However, these conventional technologies have focused primarily on unidirectional arch support, which has limited structural design that simultaneously considers the transverse arch of the forefoot, the medial longitudinal arch, and the lateral longitudinal arch.

[0018] Furthermore, conventional protruding insole structures often feature a shape that simply protrudes from the upper surface, raising concerns that load may be concentrated on the protrusions during walking, potentially causing a foreign body sensation or tenderness on the wearer's soles. Moreover, in structures with a flat lower surface, there is insufficient space for the protrusions to deform under load, resulting in limited shock absorption performance. Prior art literature

[0019] Korean Registered Patent Publication No. 10-2238244 The problem to be solved

[0020] Generally, the foot is formed with a transverse arch, medial longitudinal arch, and lateral longitudinal arch, and these arches play a role in distributing body weight, absorbing shock, and maintaining body balance during walking. However, if the arch structure deteriorates or collapses due to overweight, prolonged walking or standing, incorrect walking habits and footwear, or decreased muscle strength, body weight becomes concentrated on the entire sole of the foot, increasing foot fatigue and raising the likelihood of various foot conditions such as plantar fasciitis, hallux valgus, and interdigital neuralgia.

[0022] In particular, when the transverse arch of the forefoot is lowered, local pressure tends to concentrate on the second or third metatarsal bone, and imbalance in the medial or lateral longitudinal arch causes the ankle joint to be excessively inverted or eversed during walking, increasing the risk of ankle sprains.

[0024] Conventional functional insoles are mostly designed to support the medial longitudinal arch or to place cushioning material across the entire sole of the foot, and thus have limitations in structurally supporting the transverse arch, medial longitudinal arch, and lateral longitudinal arch of the forefoot simultaneously. In addition, insoles in the form of simple pads with a protruding upper surface may cause a foreign body sensation or tenderness when worn, and when a load is applied during walking, localized pressure concentration occurs, leading to a decrease in comfort.

[0026] Furthermore, conventional insole structures have problems in that they cannot actively respond to changes in load on the sole of the foot during the walking phase (swing and stance phases), resulting in insufficient arch support during the swing phase or reduced shock absorption during the stance phase. Consequently, there is a need for a structural means that can prevent ankle sprains while stably maintaining the arch structure of the foot.

[0028] The present invention is proposed to solve the problems of the prior art as described above, and its objective is to provide a functional insole that can prevent ankle sprains by providing a structure capable of simultaneously supporting the transverse arch, medial longitudinal arch, and lateral longitudinal arch of the forefoot, and by controlling the weight transfer path during walking to suppress excessive rotation of the ankle joint.

[0030] In addition, another objective of the present invention is to provide a functional insole that simultaneously satisfies comfort and functionality by providing a structure that supports the transverse arch of the forefoot during the swing phase and absorbs shock by elastically deforming according to the load during the stance phase through the upper protrusion and lower depression structure of the protrusion.

[0032] In addition, another objective of the present invention is to provide a functional insole that prevents localized concentration of load in the transverse arch region of the forefoot, distributes the load across the entire foot to reduce foot fatigue, and improves walking stability. means of solving the problem

[0033] A functional insole for guiding proper walking and preventing ankle sprains according to the present invention comprises: a front insole portion; a rear insole portion; and a protrusion located between the front insole portion and the rear insole portion; wherein the protrusion is formed in the forefoot region of the foot, protrudes toward the upper surface of the insole, and is simultaneously formed to be sunken in a concave shape toward the lower surface of the insole.

[0034] In addition, the protrusion of the functional insole for guiding proper walking and preventing ankle sprains according to the present invention includes a apex (P1), an outer end in the width direction, and an inner end in the width direction, and the height of the inner end in the width direction is formed to be higher than the height of the outer end in the width direction.

[0035] In addition, the functional insole for guiding proper walking and preventing ankle sprains according to the present invention is characterized in that the apex of the protrusion is located within the transverse arch of the forefoot formed by the first to fifth metatarsals of the user's foot when worn.

[0036] In addition, the apex of the protrusion of the functional insole for guiding proper walking and preventing ankle sprains according to the present invention is positioned near the third metatarsal bone of the user's foot when worn.

[0037] In addition, the protrusion of the functional insole for guiding proper walking and preventing ankle sprains according to the present invention is characterized by being formed to support the sole of the foot upward during the swing phase of walking and to deform downward due to the load during the stance phase.

[0038] In addition, the protrusion of the functional insole for guiding proper walking and preventing ankle sprains according to the present invention is characterized by being formed to be continuous with the inner wing portion and the outer wing portion.

[0039] In addition, the outer wing portion of the functional insole for guiding proper walking and preventing ankle sprains according to the present invention is characterized by being positioned to support the fifth metatarsal portion of the user's foot when worn. Effects of the invention

[0040] According to the present invention, the forefoot transverse arch, medial longitudinal arch, and lateral longitudinal arch can be structurally supported simultaneously by a structure comprising a forefoot insole, a posterior insole, and a protrusion formed between them. Accordingly, the arch structure of the foot is stably maintained during walking, thereby alleviating localized pressure concentration caused by the collapse of the forefoot transverse arch and providing the effect of reducing foot fatigue.

[0042] In addition, the protrusion according to the present invention is formed to protrude from the upper surface of the insole and simultaneously is concavely sunken from the lower surface to form a hollow portion, so that it supports the transverse arch of the forefoot upward during the swing phase and elastically deforms downward due to the load during the stance phase to absorb shock. Accordingly, different functions are implemented depending on the walking phase, thereby providing the effect of simultaneously satisfying the functions of supporting the transverse arch of the forefoot and absorbing shock.

[0044] In addition, due to the asymmetrical structure in which the heights of the inner and outer ends in the width direction of the protrusion are formed differently, body weight is induced to naturally shift from the outer side to the inner side of the foot during walking. Accordingly, the phenomenon of excessive eversion or inversion of the ankle joint is suppressed, thereby providing the effect of reducing the likelihood of ankle sprains.

[0046] In addition, due to a structure in which the lengths of the longitudinal anterior and posterior ends of the protrusion are formed differently, the load is transferred stepwise from the posterior region to the anterior region during walking. Accordingly, the phenomenon of body weight being rapidly concentrated in the transverse arch region of the forefoot is prevented, and as the load is distributed and transferred over time, it provides the effect of reducing localized tenderness and fatigue accumulation occurring in the forefoot and midfoot.

[0048] In addition, the protrusion is formed to be continuous with the medial wing portion and the lateral wing portion, and the lateral wing portion is positioned to support the fifth metatarsal portion, thereby stably supporting the lateral longitudinal arch. Accordingly, the phenomenon of the lateral side of the foot descending excessively or the ankle joint tilting sharply outward is suppressed, thereby improving walking stability and further increasing the effect of preventing ankle sprains.

[0050] Furthermore, plantar pressure analysis of the insole according to the present invention revealed a tendency for the contact area to increase and the maximum average pressure to decrease, confirming the effect of distributing the load across the entire sole of the foot. Accordingly, the average pressure level transmitted to the sole of the foot during walking is reduced, thereby improving comfort and providing the effect of alleviating the burden on the foot even during prolonged walking or standing.

[0052] Accordingly, according to the present invention, by simultaneously supporting the transverse arch, medial longitudinal arch, and lateral longitudinal arch of the forefoot, distributing and redistributing the load during walking, and suppressing abnormal rotation of the ankle joint, it provides the effect of simultaneously achieving prevention of ankle sprains, improvement of walking stability, and reduction of foot fatigue. Brief explanation of the drawing

[0053] FIG. 1 is a perspective view of a functional insole for guiding proper walking and preventing ankle sprains according to the present invention. FIG. 2 is a front view of a functional insole according to the present invention. FIG. 3 is a drawing of a functional insole according to the present invention viewed from the bottom. FIG. 4 is a diagram illustrating a functional insole according to the present invention from the side and schematically showing the state of contact with the sole of the foot. Figures 5 and 6 are drawings illustrating the transverse arch, medial longitudinal arch, and lateral longitudinal arch of the forefoot. FIG. 7 is a diagram illustrating the performance evaluation items of a functional insole according to the present invention. FIG. 8 is a drawing comparing a functional insole (Type A) and a control insole (Type B) according to the present invention. Figure 9 is a diagram illustrating the information of the experiment participants. Figure 10 is a diagram illustrating an example of plantar pressure analysis. Figure 11 is a diagram illustrating the plantar pressure distribution analysis elements and analysis areas. Figure 12 is a drawing illustrating a plantar pressure measuring device. Figure 13 is a photograph illustrating the actual performance of a plantar pressure measurement experiment. Figure 14 is a graph showing the analysis results for the contact area. Figure 15 is a graph showing the analysis results for the maximum force. Figure 16 is a graph showing the analysis results for peak pressure. Figure 17 is a graph showing the analysis results for Maximum Mean Pressure. Specific details for implementing the invention

[0054] The following description merely illustrates the principles of the present invention. Therefore, a person skilled in the art may invent various devices that embody the principles of the present invention and are included within the concept and scope of the present invention, even though they are not explicitly described or illustrated in this specification. Furthermore, all conditional terms and embodiments listed in this specification are, in principle, explicitly intended only for the purpose of understanding the concept of the present invention and should be understood not as being limited to the embodiments and conditions specifically listed as such.

[0055] Furthermore, it should be understood that all detailed descriptions enumerating specific embodiments, as well as the principles, aspects, and embodiments of the present invention, are intended to include structural and functional equivalents thereof. In addition, it should be understood that such equivalents include not only currently known equivalents but also equivalents to be developed in the future, that is, all elements invented to perform the same function regardless of structure.

[0056] The aforementioned objectives, features, and advantages will become clearer through the following detailed description in conjunction with the attached drawings, and accordingly, a person skilled in the art to which the present invention pertains will be able to easily implement the technical concept of the present invention. Furthermore, in describing the present invention, if it is determined that a detailed description of known technology related to the present invention may unnecessarily obscure the essence of the present invention, such detailed description will be omitted.

[0057] Hereinafter, various embodiments of the present invention will be described in detail with reference to the attached drawings. FIG. 1 is a perspective view of a functional insole of the present invention, FIG. 2 is a drawing showing the insole from the front, FIG. 3 is a drawing showing the insole from the bottom, and FIG. 4 is a drawing showing the insole from the side and conceptually illustrating the state of contact with the sole of the foot.

[0059] The present invention relates to a functional insole capable of preventing ankle sprains while simultaneously structurally supporting the transverse arch, medial longitudinal arch, and lateral longitudinal arch of the forefoot. The functional insole of the present invention comprises a front insole portion (100), a rear insole portion (200), and a protrusion (300) located between the front insole portion (100) and the rear insole portion (200).

[0061] The above-mentioned front insole (100) is positioned in an area corresponding to the front part of the user's foot and is formed to support the transverse arch area of ​​the forefoot formed by the first to fifth metatarsals. The above-mentioned front insole (100) may be formed with a curved structure corresponding to the shape of the sole of the foot and is configured to distribute the load applied to the forefoot during walking so that the propulsion motion of the foot is performed smoothly. In addition, the above-mentioned front insole (100) is formed to be continuous with the protrusion (300) so that the load of the transverse arch area of ​​the forefoot supported by the protrusion (300) is naturally transferred to the front part.

[0063] The rear insole (200) is positioned in an area corresponding to the rear part of the user's foot and is formed so that the calcaneus rests thereon. The rear insole (200) may have a concave curved structure corresponding to the bottom shape of the calcaneus and is configured to absorb the impact applied to the calcaneus portion that first contacts the ground during walking. In addition, the rear insole (200) is formed to be continuous with the front insole (100) so that the load is gradually transferred during the process of weight transfer from the heel contact through the midfoot to the forefoot.

[0065] The protrusion (300) is formed in the forefoot region of the foot and is positioned within the forefoot transverse arch region formed particularly by the first to fifth metatarsals.

[0067] The above-mentioned protrusion (300) is formed to protrude from the upper surface of the insole to support the sole of the foot, and at the same time, on the lower surface of the insole, an area corresponding to the above-mentioned protrusion (300) is formed to be sunken in a concave shape. Accordingly, the above-mentioned protrusion (300) forms a hollow structure that has a convex shape on the upper surface (310) and a concave shape on the lower surface (320), and a hollow portion (301) is formed inside the protrusion (300) by the above-mentioned hollow structure. Due to this structure, when a load is applied to the protrusion (300) during walking, elastic deformation occurs toward the above-mentioned hollow portion (301), thereby absorbing the impact caused by body weight.

[0069] Referring to FIG. 2, the protrusion (300) is formed to include a apex (P1), an inner end (P2) in the width direction, and an outer end (P3) in the width direction. At this time, with respect to a reference line (G) based on the bottom surface of the insole, the height (h2) of the inner end (P2) in the width direction is formed to be greater than the height (h3) of the outer end (P3) in the width direction. That is, the protrusion (300) has an asymmetric cross-sectional structure that gradually becomes higher as it moves inward along the width direction.

[0071] Due to this structure, when the sole of the foot comes into contact with the protrusion (300) during walking, the inner end (P2), which is formed relatively high, first supports the transverse arch area of ​​the forefoot of the sole, and the load is gradually transferred from the outer end (P3), which is formed relatively low. As a result, body weight naturally moves from the outer side of the foot toward the inner side, and the sole of the foot rests stably according to the sloped shape of the protrusion (300).

[0073] In particular, the normal walking pattern in which body weight is first transferred to the outer forefoot and then to the inner forefoot during the process of the foot landing on the ground is assisted by the asymmetric height structure of the protrusion (300), thereby suppressing the phenomenon of the ankle joint tilting abruptly to the outer or inner side. Accordingly, excessive rotation of the ankle joint in the eversion or inversion direction is prevented, and the phenomenon of a large load being concentrated on the ankle ligament at once is alleviated.

[0075] In addition, the asymmetrical structure in the width direction of the protrusion (300) acts to maintain the left-right balance of the forefoot transverse arch, thereby preventing the forefoot transverse arch from collapsing to one side. As a result, the pressure generated in the forefoot during walking is distributed over a wider area, and the pressure concentrated locally on specific metatarsal bones is reduced.

[0077] Accordingly, the height difference between the inner end (P2) and the outer end (P3) in the width direction of the protrusion (300) is not merely a difference in shape, but functions as a structural means to control the weight transfer path, and provides the effect of reducing the possibility of ankle sprains by maintaining the alignment of the ankle joint along with stable support of the transverse arch of the forefoot.

[0079] Referring to FIG. 3, the protrusion (300) is formed to include a longitudinal front end (P4) and a longitudinal rear end (P5). When the length from the vertex (P1) to the front end (P4) is denoted as l1 and the length from the vertex (P1) to the rear end (P5) is denoted as l2, the l2 is formed to be longer than the l1. That is, the protrusion (300) has an asymmetrical shape in which the rear region along the longitudinal direction is formed to be relatively longer than the front region.

[0081] Due to this shape, when the weight is transferred from the heel to the ground during walking, through the midfoot to the forefoot, the rear region of the protrusion (300) first supports the load, and then the load is gradually transferred to the front region. That is, the weight is transferred sequentially from the rear end (P5) of the protrusion (300), through the apex (P1), to the front end (P4).

[0083] In particular, since the rear region of the protrusion (300) is formed long, the rear region cushions and supports the lower part of the forefoot transverse arch during the initial landing, and the load gradually moves to the front region as walking progresses. Accordingly, the sudden concentration of body weight on the forefoot transverse arch region is prevented, and the body weight is distributed and transmitted over time.

[0085] In addition, the longitudinal asymmetric structure of the protrusion (300) serves to guide the path of pressure generated in the forefoot during walking, thereby alleviating the phenomenon where a large amount of pressure is momentarily concentrated in a specific metatarsal area. As a result, localized tenderness or fatigue accumulation that is prone to occur in the second or third metatarsal area can be reduced.

[0087] Accordingly, a structure in which the length (l1) to the front end (P4) and the length (l2) to the rear end (P5) are formed differently from the apex (P1) of the protrusion (300) performs the function of distributing the load acting on the forefoot transverse arch region in stages, and serves to simultaneously improve the shock absorption effect and the forefoot transverse arch support effect during walking.

[0089] The apex (P1) of the protrusion (300) is a key positional and shape element that determines the function of the present invention, and is set to be located within the forefoot transverse arch area formed by the first to fifth metatarsals in the user's foot when worn. The forefoot transverse arch is an arch structure formed in the section from the first metatarsal to the fifth metatarsal, and since it is involved in dispersing the load applied to the forefoot during walking and generating propulsion, it is preferable that the position of the apex (P1) is not merely limited to the highest point of the protrusion (300), but is set to a point that can substantially provide structural support for the forefoot transverse arch. In the present invention, the apex (P1) is configured to be located particularly near the third metatarsal within the forefoot transverse arch area, thereby providing support for the center (central part) of the forefoot transverse arch and simultaneously stabilizing the left-right balance and front-back load transfer of the forefoot.

[0091] The apex (P1) forms the highest point on the upper surface (310) of the protrusion (300) and supports the apex area of ​​the forefoot transverse arch upward by directly contacting or being close to the sole of the user's foot. At the same time, since the protrusion (300) is sunken into a concave shape on the lower surface (320) to form a hollow portion (301), the apex (P1) acts as both an “upward support point” and a “downward deformation center point.” That is, when a load is transferred to the apex (P1) during walking, the hollow portion (301) provides a deformation clearance space, allowing the protrusion (300) to elastically deform downward, and as a result, localized pressure concentration occurring near the apex (P1) is alleviated and shock absorption performance can be improved. In other words, the apex (P1) provides the support force necessary to maintain the forefoot transverse arch, while also acting as a center point where elastic deformation of the protrusion (300) is induced when the load increases, thereby achieving a balance between comfort and functionality.

[0093] In addition, the apex (P1) functions as a reference point for controlling the weight transfer path during walking by combining with the left-right asymmetrical shape (P2, P3 and h2, h3) of the protrusion (300). That is, as the height (h2) of the inner end (P2) in the width direction relative to the reference line (G) is formed to be greater than the height (h3) of the outer end (P3) in the width direction, the load transmitted to the apex (P1) does not act simply in the vertical direction, but has a component that is induced from the outer side to the inner side by the asymmetrical slope of the protrusion (300). Accordingly, the weight transfer from the outer side to the inner side after landing on the outer side, which occurs during normal walking, is induced more stably, and the phenomenon of the ankle joint rapidly everting or inverting can be suppressed. In particular, left-right load imbalance in the forefoot is prone to causing abnormal rotation of the ankle joint, and the left-right asymmetrical support structure centered on the apex (P1) provides the effect of mitigating this imbalance and reducing the possibility of ankle sprains.

[0095] The apex (P1) functions as a reference point that allows the load to be distributed temporally during the walking phase, in combination with the anterior-posterior asymmetrical shape (P4, P5 and l1, l2) of the protrusion (300). That is, as the length (l2) from the apex (P1) to the rear end (P5) is formed to be longer than the length (l1) from the apex (P1) to the front end (P4), the rear region of the protrusion (300) first supports the load during the process of weight moving forward after heel contact, and then the load is gradually transferred to the front region through the apex (P1). This stepwise load transfer alleviates the phenomenon of weight being concentrated at one point in time in the transverse arch region of the forefoot and provides the effect of reducing fatigue accumulation and the occurrence of tenderness by distributing the load throughout the forefoot. In particular, the apex (P1) acts as a “reference point (pivot) for load transfer” during the process of the load moving from the rear to the front, allowing the protrusion (300) to be stably deformed and restored in the anterior-posterior direction.

[0097] In terms of the walking phase, the apex (P1) performs different functions during the swing phase and the stance phase. During the swing phase, the sole of the foot is lifted off the ground, so the apex (P1) supports the apex area of ​​the forefoot transverse arch upward to maintain the arch shape and provides structural stability to the foot during the walking preparation phase. On the other hand, during the stance phase, the sole of the foot contacts the ground and body weight is applied, so pressure may be concentrated on the apex (P1). In the present invention, elastic deformation near the apex (P1) is induced by the depression of the lower surface (320) of the protrusion (300) and the hollow portion (301), thereby absorbing shock and dispersing pressure. As a result, the apex (P1) can simultaneously perform the functions of an “arch support point” and a “shock absorption point,” thereby ensuring both the maintenance of the forefoot transverse arch and wearing comfort.

[0099] Accordingly, in the present invention, the position of the apex (P1) (within the transverse arch of the forefoot and near the third metatarsal bone), the shape (the highest point of the protrusion (300)), the structural linkage (formation of the hollow part (301) due to the sinking of the lower surface (320)), and the combination with the left-right and front-back asymmetrical shape do not each act independently, but form a three-dimensional load induction and distribution mechanism centered on the apex (P1). As a result, structural collapse of the transverse arch of the forefoot is suppressed, pressure distribution and shock absorption performance of the forefoot during walking are improved, and abnormal rotation of the ankle joint is suppressed, thereby providing an effect of increasing the prevention of ankle sprains.

[0101] In one embodiment, the apex (P1) of the protrusion (300) may be positioned at a location spaced forward in the longitudinal direction of the foot by a predetermined ratio relative to the calcaneus. Specifically, the apex (P1) may be positioned at a location corresponding to a point approximately 60% to 70%, preferably approximately 66%, forward in the longitudinal direction of the foot from the posterior end of the calcaneus. This location corresponds to the central part of the transverse arch region of the forefoot formed by the first to fifth metatarsals, and in particular corresponds to a location near the third metatarsal.

[0103] In this way, by positioning the apex (P1) at a certain ratio from the calcaneus, the protrusion (300) can be aligned at a position corresponding to the anatomical center of the forefoot transverse arch, even if the absolute length of the foot varies from user to user. That is, by setting the position of the apex (P1) based on a ratio rather than absolute length, the protrusion (300) can be positioned at a position corresponding to the apex of the forefoot transverse arch for users with various foot sizes.

[0105] In addition, due to the ratio-based positioning described above, the protrusion (300) is positioned at the center of the section where body weight is transferred from the midfoot to the forefoot during walking, so it can support the forefoot transverse arch at a key point on the load transfer path. Accordingly, the collapse of the forefoot transverse arch is effectively suppressed, and body weight is distributed throughout the forefoot, thereby alleviating the phenomenon of localized pressure concentration on specific metatarsal areas.

[0107] Furthermore, the position of the apex (P1) is combined with the front-rear asymmetric shape (P4, P5 and l1, l2) of the protrusion (300) to function as a reference point that allows the load to be transferred stepwise from the rear region to the front region with respect to the apex (P1) during the process of weight transfer after heel contact. As a result, the shock absorption and pressure distribution effects in the forefoot transverse arch region can be further enhanced.

[0109] Accordingly, in the present invention, the configuration of positioning the apex (P1) at a range of about 60% to 70% relative to the calcaneus, preferably at about 66%, serves not only as a structural means for aligning the protrusion (300) at a position corresponding to the anatomical apex of the forefoot transverse arch, but also functions as a key design element for controlling load transfer during walking and maximizing the support effect of the forefoot transverse arch.

[0111] In one embodiment, the upper surface (310) of the protrusion (300) may be formed to have a predetermined radius of curvature centered on the apex (P1). Specifically, the radius of curvature near the apex (P1) may be formed in the range of about 5 mm to 20 mm, preferably in the range of about 8 mm to 15 mm. Additionally, the radius of curvature of the central part and the front and rear regions of the upper surface (310) may be formed differently from each other. For example, the central part may be formed to have a relatively large radius of curvature, and the front and rear regions may be formed to have a radius of curvature smaller than that of the central part. Accordingly, the central part may gently support the transverse arch of the forefoot, the front region may disperse pressure during propulsion of the foot, and the rear region may perform the function of absorbing shock upon landing.

[0113] The above protrusion (300) is formed to perform different functions depending on the walking cycle. Specifically, during the swing phase when the foot is lifted off the ground while walking, the protrusion (300) supports the sole of the foot upward by protruding to the upper surface (310) of the insole, thereby acting to maintain the shape of the forefoot transverse arch. At this time, since the apex (P1) of the protrusion (300) is positioned corresponding to the apex area of ​​the forefoot transverse arch, it can structurally support the forefoot transverse arch so that it does not sag even when the sole of the foot is relaxed.

[0115] Meanwhile, during the stance phase when the sole of the foot contacts the ground and body weight is applied while walking, the protrusion (300) is formed to elastically deform downward due to the load. At this time, the protrusion (300) deforms toward the hollow portion (301) formed on the lower surface (320), absorbing the impact generated by body weight and dispersing the pressure transmitted to the transverse arch area of ​​the forefoot. Accordingly, the function of supporting the transverse arch of the forefoot is performed during the swing phase, and the shock absorption function is performed during the stance phase, thereby implementing different functions depending on the walking phase.

[0117] The above protrusion (300) may be formed to be continuous with the inner wing portion (400) and the outer wing portion (500). That is, the protrusion (300) may be formed in the central area of ​​the front insole portion (100), and the inner wing portion (400) and the outer wing portion (500) may be integrally extended on both sides in the width direction. Accordingly, the load of the forefoot transverse arch area supported by the protrusion (300) is transmitted while being distributed along the inner wing portion (400) and the outer wing portion (500).

[0119] In particular, the inner wing portion (400) may be formed to support the medial longitudinal arch region of the user's foot, and the outer wing portion (500) may be formed to support the outer longitudinal arch region of the user's foot. In this way, by forming the protrusion (300), the inner wing portion (400), and the outer wing portion (500) to form a continuous structure, a three-dimensional support structure is formed in which the forefoot transverse arch, medial longitudinal arch, and outer longitudinal arch are simultaneously supported.

[0121] The above-mentioned outer wing portion (500) is positioned to correspond to the fifth metatarsal region of the user's foot when worn. That is, the outer wing portion (500) extends along the outer edge region of the foot and is formed to support the sole of the foot upward at a position corresponding to the lower part of the fifth metatarsal. Accordingly, even when body weight shifts to the outer side of the forefoot during walking, the fifth metatarsal region is supported by the outer wing portion (500), thereby suppressing the phenomenon of the outer side of the foot descending excessively.

[0123] In addition, the fifth metatarsal region is supported by the outer wing portion (500), thereby stabilizing the outer longitudinal arch of the foot and suppressing the phenomenon of the ankle joint tilting excessively outward. As a result, the ankle joint is prevented from rotating rapidly in the eversion or inversion direction, thereby reducing the possibility of an ankle sprain.

[0125] Furthermore, the outer wing portion (500) is formed to be continuous with the outer end (P3) in the width direction of the protrusion (300), so that the weight transfer path from the outer side to the inner side induced by the protrusion (300) is assisted by the outer wing portion (500). Accordingly, the load distribution effect starting from the transverse arch area of ​​the forefoot is continuously extended to the outer longitudinal arch area, thereby forming a stable load-bearing structure over the entire foot.

[0126] By means of the asymmetric structure of the protrusion (300), the apex (P1), and the inner and outer ends (P2, P3), and the anterior-posterior asymmetric structure (P4, P5 and l1, l2), the insole of the present invention forms a load redistribution structure that not only merely reduces the plantar load during walking but also induces the load to be moved and distributed between the forefoot, midfoot, and hindfoot, and in the width direction (outer to inner). Accordingly, the phenomenon of pressure or force being locally concentrated in a specific area can be alleviated, and the distribution of pressure and force by area can be adjusted according to the user's walking pattern and weight transfer path.

[0128] In addition, the protrusion (300) of the present invention forms a hollow portion (301) by the protrusion of the upper surface (310) and the depression of the lower surface (320). Therefore, when a load is applied during walking, the protrusion (300) elastically deforms toward the hollow portion (301) to absorb the impact, and acts to disperse the pressure peak to surrounding areas rather than concentrating it at a single point. Accordingly, the effect of the present invention is not limited to “uniform reduction of all indicators” but can be implemented in the form of “dispersion by area and alleviation of perceived load due to movement.”

[0130] [Experimental Example]

[0131] The biomechanical functionality of the insole according to the present invention through plantar pressure analysis was verified through the following experiment. The performance evaluation items are as shown in Fig. 7. As shown in Fig. 8, the experiment was conducted on a total of two types of insoles: Type A, an insole according to the present invention, and Type B, a control insole without protrusions, and the insole size was 235 mm for women.

[0132] The biomechanical performance evaluation of functional insoles was conducted on 9 physically healthy female participants without neurological, musculoskeletal, or injury-prone conditions. The average age of the participants was 24.5±0.73 yrs, height was 162.2±4.15 cm, weight was 55.7±5.07 kg, and shoe size was 235.0±0.00 mm. Figure 9 shows the participant information.

[0133] Plantar pressure measurement is a measurement method for observing the contact area, maximum force, maximum pressure, and maximum average pressure of the foot when wearing a functional insole according to the present invention and a control group insole. Plantar pressure measurement is the most common experimental method for determining superiority in reducing foot impact and load through comparison between the product and the control group by measuring the contact area, generated maximum force, maximum pressure, and maximum average pressure of the product to be tested and the control group. The analysis is divided into the entire foot, forefoot, midfoot, and hindfoot. Figure 10 is an example of plantar pressure analysis.

[0135] Contact Area is an evaluation of the area where the foot and the insole come into contact with the ground; the wider the contact surface, the more the load on the foot is reduced.

[0136] Maximum Force evaluates the vertical force generated between the foot and the insole upon contact with the ground, and the smaller the maximum force, the less the load is generated on the foot.

[0137] Peak Pressure is an evaluation of the maximum pressure generated between the foot and the insole upon contact with the ground; the lower the peak pressure, the less load is placed on the foot and the greater the comfort of the foot.

[0138] Maximum Mean Pressure is an evaluation of the average value of the maximum pressure generated between the foot and the insole upon contact with the ground; the lower the maximum mean pressure, the less the load on the foot is reduced and the greater the comfort of the foot. Figure 11 relates to the plantar pressure distribution analysis elements and regions.

[0140] Changes in plantar pressure by region during gait are analyzed by dividing the foot into the forefoot, midfoot, hindfoot, and entire foot. For the forefoot, the influence on the propulsive force of pushing off and the degree of load on the forefoot can be measured and analyzed. For the midfoot, the influence of the arch shape and the degree of load on the midfoot can be measured and analyzed. For the hindfoot, the impact generated upon the initial contact between the foot and the ground can be evaluated, and the amount of impact directly transmitted to the body can be analyzed. The Pedar-X plantar pressure analysis equipment from Novel, Germany, is used. Figure 12 shows the plantar pressure measurement equipment.

[0141] The experiment participants walked on a treadmill while maintaining a constant speed (3.7 km / h). Prior to the measurement, the participants practiced sufficiently at the set speed and performed the measurement after a stable walking pattern was established. At least 20 gait cycles were measured per session, and the measurement and data collection were repeated three times to calculate the average value. To allow for adaptation to wearing insoles and to eliminate fatigue during the experiment, participants were instructed to take sufficient rest between sessions, and the order of wearing insoles was selected randomly. Sufficient adaptation time for gait stabilization was provided to ensure quantitative measurement in a stabilized walking pattern. Figure 13 is a photograph showing the actual plantar pressure measurement.

[0143] The results of the contact area analysis are shown in Fig. 14. The unit is cm. 2 am.

[0144] The results of the comparative analysis of the contact area between the functional insole Type A according to the present invention and the control insole Type B using a plantar pressure measuring device are as follows.

[0145] - Total: Type B < Type A

[0146] - Forefoot: Type B < Type A

[0147] - Midfoot: Type B < Type A

[0148] -Rear: Type B < Type A

[0150] The results of the maximum force analysis are as shown in Fig. 15. The unit is N.

[0151] The results of the comparative analysis of maximum force between functional insole Type A according to the present invention and control insole Type B using a plantar pressure measuring device are as follows.

[0152] - Total: Type A < Type B

[0153] - Forefoot: Type A < Type B

[0154] - Midfoot: Type B < Type A

[0155] -Rear: Type A < Type B

[0157] The results of the maximum pressure analysis are shown in Fig. 16. The unit is kPa.

[0158] The results of the comparative analysis of maximum pressure between functional insole Type A according to the present invention and control insole Type B using a plantar pressure measuring device are as follows.

[0159] - Total: Type B < Type A

[0160] - Forefoot: Type A < Type B

[0161] - Midfoot: Type A < Type B

[0162] -Rear: Type B < Type A

[0164] The results of the analysis of the maximum average pressure are shown in Fig. 17. The unit is kPa.

[0165] The results of the comparative analysis of the maximum average pressure between the functional insole Type A according to the present invention and the control insole Type B using a plantar pressure measuring device are as follows.

[0166] - Total: Type A < Type B

[0167] - Forefoot: Type A < Type B

[0168] - Midfoot: Type A < Type B

[0169] -Rear: Type A < Type B

[0171] According to the results of the above experimental example, the functional insole (Type A) according to the present invention showed a tendency for the contact area to increase in the total, forefoot, midfoot, and rearfoot regions compared to the control group (Type B). This means that the effective contact area between the sole of the foot and the insole is expanded, allowing the load to be distributed over a wider area.

[0173] In addition, the Maximum Mean Pressure is lower in Type A than in Type B across the entire range of the Total, Fore, Mid, and Rear foot, confirming a tendency for the average pressure level to decrease. This can be interpreted as a result of the elastic deformation structure due to the upper support of the protrusion (300) and the lower depression (hollow part (301)) contributing to the dispersion of pressure during walking.

[0175] Meanwhile, regarding the maximum force, a tendency was observed where Type A was greater than Type B in the midfoot; however, this can be interpreted as a result of the load being partially redistributed to the midfoot during walking, as the insole of the present invention provides structural support to the midfoot and forefoot transverse arch regions. In other words, as the support force of the midfoot increases, the load that could be concentrated on specific parts of the hindfoot or forefoot is distributed, and overall walking stability and arch maintenance effects can be secured.

[0177] Furthermore, regarding peak pressure, there may be cases where Type A appears greater than Type B in the total. However, since the "total" is an indicator that takes the peak value (maximum value) that can occur during the walking cycle as a single value, the point of peak occurrence may vary depending on the load transfer path and instantaneous contact conditions. The effect of the present invention is not limited to the single indicator of the maximum value but can be confirmed in the tendency for the load to be distributed over a wider area, such as through an increase in contact area and a decrease in maximum average pressure. Therefore, it can be confirmed that the functional insole of the present invention acts to alleviate pressure concentration and reduce the average pressure level by redistributing the plantar load to different areas during walking.

[0179] Furthermore, although preferred embodiments of the present invention have been illustrated and described above, the present invention is not limited to the specific embodiments described above. It is understood that various modifications can be made by those skilled in the art without departing from the essence of the invention as claimed in the claims, and such modifications should not be understood individually from the technical spirit or perspective of the present invention. Explanation of the symbols

[0180] 100: Anterior insole 200 : Rear insole 300 : Protrusion 301 : Ministry of Economy and Finance 310: Upper surface of the protrusion 320: Lower surface of the protrusion 400 : Inner wing section 500 : Outer wing section P1: Apex of the protrusion P2: Inner end in the width direction P3: Outer end in the width direction P4: Longitudinal front end P5: Longitudinal rear end h2 : Height of the inner end (P2) in the width direction h3: Height of the outer end (P3) in the width direction G: Reference line based on the bottom surface of the insole l1: Length from the vertex (P1) to the front end (P4) l2: Length from the vertex (P1) to the rear end (P5)

Claims

Claim 1 A functional insole for guiding proper walking and preventing ankle sprains, comprising: a front insole portion; a rear insole portion; and a protrusion located between the front insole portion and the rear insole portion; wherein the protrusion is formed in the forefoot region of the foot, protrudes toward the upper surface of the insole, and is simultaneously formed to protrude toward the lower surface of the insole in a concave shape, and the protrusion includes a apex (P1), a longitudinal front end, and a longitudinal rear end, wherein the apex (P1) is positioned at 60% to 70% of the longitudinal forward position from the posterior end of the calcaneus so as to correspond to the position of the third metatarsal among the first to fifth metatarsals in the user's foot when worn, and the length from the apex (P1) to the longitudinal rear end is formed to be longer than the length from the apex (P1) to the longitudinal front end. Claim 2 A functional insole for guiding proper walking and preventing ankle sprains, wherein, in claim 1, the protrusion includes an outer end in the width direction and an inner end in the width direction, and the height of the inner end in the width direction is formed to be higher than the height of the outer end in the width direction. Claim 3 delete Claim 4 delete Claim 5 A functional insole for guiding proper walking and preventing ankle sprains, characterized in that, in claim 1, the protrusion is formed to support the sole of the foot upward during the swing phase and to deform downward due to load during the stance phase. Claim 6 A functional insole for guiding proper walking and preventing ankle sprains, characterized in that, in claim 5, the protrusion is formed to be continuous with the inner wing portion and the outer wing portion. Claim 7 A functional insole for guiding proper walking and preventing ankle sprains, characterized in that, in claim 6, the outer wing portion is positioned to support the fifth metatarsal region of the user's foot when worn.

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