JP2013013567A - Bone sound velocity measuring wearing implement, bone sound velocity measurement device, and bone velocity measurement method - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a bone sound velocity measuring wearing implement, a bone sound velocity measurement device, and a bone sound velocity measurement method using those, capable of stably measuring a constant place of a bone without depending on a measurer when measuring a bone sound velocity of a tibia.SOLUTION: This bone sound velocity measuring wearing implement includes: a first fixing mechanism 20 positionably fixed on the basis of a tibial tuberosity part, and having an opening 21 fitted on the tibial tuberosity part in a distal abutment part 128 on the tibial tuberosity part; a second fixing mechanism 30 positionably fixed on the basis of a medial malleolus part of the tibia, and having an opening 31 fitted on the medial malleolus part in a proximal abutment part 132 on the medial malleolus part; a connection mechanism 10 connecting the first fixing mechanism 20 and the second fixing mechanism 30, capable of expanding/contracting an interval between the first fixing mechanism 20 and the second fixing mechanism 30; and a probe holding mechanism 40 installed to the connection mechanism 10, and holding a probe 51 transmitting/receiving an ultrasonic wave abuttably on a prescribed region of the tibia.

Description

  The present invention relates to a bone sound speed measuring device and a bone sound speed measuring device for measuring bone sound speed by transmitting and receiving ultrasonic waves to and from the surface of the tibia, and a bone sound speed measuring method using them.

  2. Description of the Related Art Conventionally, an apparatus and a method for measuring cortical bone sound velocity in a load direction of a long bone portion such as a tibia using ultrasonic waves are known. By the way, as shown in FIG. 4A, the tibia has a triangular bone cross section and is divided into three ridgelines, an anterior edge, an interosseous edge, and an inner edge. Among these, the site | part which can be measured with an ultrasonic wave from the outside of a body is restricted to the site | part of the inner surface from the front edge vicinity to an inner edge. In the conventional method, the sound velocity of the bone is measured by transmitting and receiving ultrasonic waves while scanning the inner surface of the inner surface in a direction parallel to the axis of the bone and analyzing the signal.

  In addition, Patent Documents 1 to 4 disclose methods of measuring bone sound speed by transmitting and receiving ultrasonic waves in a circumferential direction orthogonal to the load direction of the long bones. And it becomes possible to measure bone strength from the bone sound velocity measurement in the load direction and circumferential direction of these long bones.

JP 2010-57520 A JP 2010-29240 A JP 2010-29241 A JP 2010-246692 A

  FIG. 5 is a cross-sectional view of the tibia. Healthy tibias are dense bones other than the bone marrow 204, but the tibia with reduced bone mass due to osteoporosis or the like becomes porous at the site A close to the leading edge 206, and the overall bone mass decreases and cancellous bone (sea surface) Bone 202). On the other hand, in the region B near the inner edge 208 of the inner surface 207, the cortical bone 203 becomes thin while maintaining a dense bone state. Thus, the change tendency of the bone microstructure differs depending on the site of the tibia 201, and accordingly, the bone sound velocity measurement measured by the ultrasonic wave also differs depending on the site. Therefore, in the measurement on the inner surface 207 of the tibia 201, one or both of the two portions A and B are measured. For example, with respect to the direction parallel to the bone axis, the probe is brought into contact with the soft tissue so as to be parallel to the tibia 201, and a bone strength index such as bone sound speed is measured. A bone strength index such as bone sound speed may be measured by bringing the probe into contact with the soft tissue so as to be orthogonal to the tibia 201.

  However, between these two parts A and B, the measurement value of the bone sound speed changes depending on the position. Therefore, when a hand-held probe is scanned, the result varies greatly depending on the deviation of the measurement position, and the reproducibility. There was a problem of getting worse. That is, in the measurement method in which the probe is scanned by hand, the measurement result greatly depends on the technique of the measurer. Also, the bone strength measuring methods disclosed in Patent Documents 1 to 4 only disclose that the bone sound velocity is measured by bringing the probe into contact with soft tissue, and when the probe is scanned by the operator's hand, The measurement location is not constant and the reproducibility is deteriorated.

  In the conventional measurement method, the measurement location is determined in advance by marking the skin directly. In this case, the skin is easy to move with respect to the bone, and the skin moves while palpating the shape of the bone, so that accurate positioning is difficult. Also, with such a marking method, it takes time to prepare for measurement, which is troublesome. Although the front edge 206 and the inner edge 208 of the tibia 201 can be found by palpation and positioned, it may be difficult for some subjects to find, for example, it is difficult for women to find compared to men. Furthermore, since there are individual differences depending on the measurer who palpates, an error occurs only by palpation.

  The present invention has been made in view of the above problems, and when measuring the bone sound speed of the tibia, a bone sound speed measuring device capable of stably measuring a certain position of the bone without depending on the measurer, and It is an object of the present invention to provide a bone sound speed measuring device and a bone sound speed measuring method using them.

  The bone sound velocity measuring device of the present invention is fixed so as to be able to be positioned on the basis of the characteristic bone portion that can be specified from the body surface proximal to the tibia, and the characteristic bone portion fits in a contact portion with the characteristic bone portion. A first fixing mechanism having an opening and a feature bone portion that can be specified from the body surface distal to the tibia are fixed so as to be positioned as a reference, and the feature bone portion fits in a contact portion with the feature bone portion A second fixing mechanism having an opening; a connecting mechanism that connects the first fixing mechanism and the second fixing mechanism; and a space between the first fixing mechanism and the second fixing mechanism; A probe holding mechanism that is attached to the mechanism and holds a probe that transmits and receives ultrasonic waves so as to be able to contact a predetermined portion of the tibia.

  According to said structure, a 1st fixing mechanism and a 2nd fixing mechanism are the space | interval of both on the basis of the characteristic bone part of a proximal side and a distal side, respectively, in the state connected with the connection mechanism. Is fixed by scaling. Thereby, the positional relationship between the first fixing mechanism and the second fixing mechanism is fixed by the connecting mechanism. Furthermore, since the probe is held by a probe holding mechanism attached to the coupling mechanism, the position of the probe during measurement can be stabilized. As a result, the reproducibility of the measurement location and the stability of the measurement can be improved.

  Further, in the bone sound speed measuring device of the present invention, the first fixing mechanism has an opening in which the characteristic bone portion fits in a proximal contact portion with the characteristic bone portion, and the second fixing mechanism You may be set as the structure which has the opening which this characteristic bone part fits in the distal contact part with a characteristic bone part.

  According to said structure, since the 1st fixing mechanism and the 2nd fixing mechanism have opening in the contact part with each characteristic bone part, the protrusion part of each characteristic bone part in this opening Fits. As a result, the position of the bone sound velocity measuring device relative to the tibia is stabilized, and whether the characteristic bone portion is confirmed from the respective openings of the first fixing mechanism and the second fixing mechanism can be correctly mounted even after the device is mounted. Can be confirmed. As a result, the reproducibility of the measurement location and the stability of the measurement can be further improved.

  In the bone sound speed measurement device of the present invention, the first fixing mechanism and the second fixing mechanism may be moved back and forth in a symmetrical direction around the probe holding mechanism by the connecting mechanism. Good.

  According to said structure, when the distance of a 1st fixing mechanism and a 2nd fixing mechanism expands / contracts by a connection mechanism, a 1st fixing mechanism and a 2nd fixing mechanism advance / retreat to the symmetrical direction centering on a probe holding mechanism. Moving. As a result, even when the distance between the first fixing mechanism and the second fixing mechanism is increased or decreased in accordance with the length of the tibia, the probe held by the probe holding mechanism is always in contact with a predetermined predetermined portion of the tibia. Become. Therefore, the transmission / reception site of the ultrasonic wave by the probe with respect to the tibia is determined at a certain location, and the bone sound speed can be measured at the certain location.

  In the bone sound speed measurement device according to the present invention, the probe holding mechanism may be attached so that an attachment angle with respect to the coupling mechanism can be changed.

  According to said structure, the attachment angle of a probe holding mechanism can be made into a desired angle. As a result, the probe holding mechanism can be brought into close contact with the soft tissue, and a desired location can be measured with the probe.

  In the bone sound velocity measuring device of the present invention, the probe holding mechanism may further include a parallel guide groove capable of holding the probe in a direction parallel to the axis of the tibia.

  According to the above configuration, the bone sound velocity can be measured by the probe along the direction parallel to the axis of the tibia.

  In the bone sound velocity measuring device of the present invention, the probe holding mechanism may further include an orthogonal guide groove capable of holding the probe in a direction orthogonal to the axis of the tibia.

  According to the above configuration, the bone sound velocity can be measured by the probe along the direction orthogonal to the axis of the tibia.

  In the bone acoustic velocity measurement device of the present invention, the probe holding mechanism may further include a plurality of the parallel guide grooves at a predetermined distance.

  According to said structure, the several location along a parallel direction with respect to a tibia can be measured with a probe.

  In the bone acoustic velocity measurement device of the present invention, the probe holding mechanism may further include a plurality of the orthogonal guide grooves at a predetermined distance.

  According to said structure, the several location along a direction orthogonal to the axis | shaft of a tibia can be measured with a probe.

  Further, in the bone acoustic velocity measurement device of the present invention, the probe holding mechanism further includes an opening region into which a pressing member that presses the tibia is fitted, and the pressing member presses the front edge of the tibia. The probe holding mechanism may be positioned at a predetermined position with respect to the front edge when fitted in the opening region in a state.

  According to the above configuration, by pressing the front edge of the tibia with the pressing member, the position of the front edge can be known more accurately than when searching for the front edge only by palpation, for example. By fitting the member into the probe holding mechanism, the probe holding mechanism can be positioned at a predetermined location with respect to the front edge. As a result, the measurement location of the probe mounted on the probe holding mechanism becomes constant with respect to the leading edge.For example, even if the measurer changes or the measurement is performed several times, the same measurement location can be measured with high reproducibility. can do.

  In the device for measuring bone sound speed according to the present invention, the characteristic bone of the characteristic bone portion with which the proximal contact portion abuts may be a tibial rough surface, a medial condyle, or a patella.

  Further, in the bone sound speed measuring device of the present invention, the characteristic bone of the characteristic bone portion with which the distal abutting portion abuts may be an inner fruit, an outer fruit, or a rib.

  The bone sound speed measuring device of the present invention includes the above-described bone sound speed measuring device and the probe that can be attached to the probe holding mechanism.

  According to said structure, the measurement place of a probe can be defined in the fixed place of an inner surface by the bone sound speed measurement apparatus. Thereby, for example, even when the measurer changes or the measurement is performed several times, the same measurement place can be measured with high reproducibility.

  In the bone sound velocity measuring method of the present invention, the pressing member is pressed against the front edge of the tibia, and the pressing member is fitted into the opening region of the probe holding mechanism to fix the position of the probe holding mechanism. In this state, the bone sound speed is measured by the probe.

  According to the above method, the probe holding mechanism is fixed at a predetermined position based on the front edge by fitting the pressing member into the probe holding mechanism in a state where the front edge of the tibia is pressed by the pressing member. Can do. As a result, the measurement location of the probe mounted on the probe holding mechanism becomes constant with respect to the leading edge.For example, even if the measurer changes or the measurement is performed several times, the same measurement location can be measured with high reproducibility. can do.

  According to the bone sound velocity measuring device of the present invention, the ultrasonic wave transmission / reception site for the tibia is determined at a certain location, and the bone sound velocity can be measured at the certain location. Therefore, for example, even when the measurer changes or the measurement is performed several times, the same measurement place can be measured with high reproducibility.

It is a perspective view which shows the state which mounted | wore the leg | foot part with the bone sound speed measuring device which concerns on this embodiment. It is a perspective view which shows the bone sound speed measuring device and probe unit which concern on this embodiment. (A) It is a perspective view which shows the pressing member which concerns on this embodiment. (B) It is a figure which shows the state which fitted the pressing member which concerns on this embodiment in the opening area | region of the probe holding mechanism. (A) It is sectional drawing of a tibia. (B) Side view of the tibia. It is explanatory drawing explaining sectional drawing of the tibia in which the bone mass fell.

  Hereinafter, preferred embodiments of the present invention will be described with reference to the drawings.

(Outline of bone sound velocity measuring device and bone sound velocity measuring device)
The bone sound velocity measuring apparatus 100 according to the present embodiment measures the bone sound velocity of the cortical bone 203 of a long tubular bone such as the tibia 201 as shown in FIG. However, the measurement target is not limited to this. Bone is generally covered with soft tissues such as muscle and fat, and bone marrow 204 is contained inside cortical bone 203. The bone sound speed measuring apparatus 100 according to the present embodiment transmits and receives ultrasonic waves to and from the cortical bone 203 from the outside of the soft tissue using the probe 51, and measures the sound speed (bone sound speed) in the cortical bone 203. Sound speed can be measured. Further, the bone sound velocity measuring apparatus 100 according to the present embodiment, when measuring the bone sound velocity of the bone (particularly the tibia 201) as described above, is worn according to the foot portion 90, thereby fixing the bone sound velocity for fixing the tibia 201. A measuring device 1 is provided. By using this bone sound velocity measuring device 1, the tibia 201 can be fixed and the probe 51 can be held in accordance with a predetermined part of the tibia 201.

(Bone sound velocity measurement equipment)
The bone sound velocity measuring device 1 according to the present embodiment will be specifically described.

  As shown in FIGS. 1 and 2, the bone acoustic velocity measuring device 1 according to the present embodiment is fixed so that it can be positioned with reference to a characteristic bone (rough surface of the tibial bone) that can be identified from the body surface proximal to the tibia 201. A first fixing mechanism 20 having an opening 21 into which the feature bone portion fits in a proximal contact portion 132 with the feature bone portion, and a feature bone (endothelium) that can be identified from a body surface distal to the tibia A second fixing mechanism 30 which is fixed to be positionable with respect to the portion and has an opening 31 into which the characteristic bone portion fits at a distal contact portion with the characteristic bone portion; a first fixing mechanism 20; and a second fixing mechanism 30 and a connecting mechanism 10 capable of expanding and reducing the distance between the first fixing mechanism 20 and the second fixing mechanism 30, and a probe 51 attached to the connecting mechanism 10 for transmitting and receiving ultrasonic waves to a predetermined part of the tibia 201. And a probe holding mechanism 40 that holds the contactable portion.The rough surface of the tibia is a portion located above the tibia 201, and it can be seen that this portion protrudes when touched from the surface of the soft tissue 205. In addition, as shown in FIG. 4B, the endometrium is a portion located below the tibia 201 and corresponds to a so-called ankle.

  Here, “proximal” indicates a side near the trunk in the extremities, and “distal” indicates a side far from the trunk in the extremities. Note that “proximal to the tibia” and “distal to the tibia” may include the tibia. That is, the “characteristic bone that can be identified from the body surface proximal to the tibia” may be a rough tibial surface or a medial condyle proximal to the tibia or a patella. In addition, “characteristic bones that can be identified from the body surface distal to the tibia” are the internal caucasian distal to the tibia, the external caucasian distal to the tibia adjacent to the tibia, and the ribs. Also good.

  The “characteristic bone portion” refers to a protruding portion including the characteristic bone as described above and soft tissue on the body surface. Hereinafter, the characteristic bone portion of the tibial rough surface is referred to as the tibial rough surface portion, and the characteristic bone portion of the endothelium is referred to as the endothelium.

  In the present embodiment, the first fixing mechanism 20 is fixed in a state where the rough tibial surface is in contact with the opening 21 of the proximal contact portion 132. On the other hand, the second fixing mechanism 30 is fixed in a state where the endophysis portion of the tibia 201 is in contact with the opening 31 of the distal contact portion 128. The first fixing mechanism 20 and the second fixing mechanism 30 are connected by the connecting mechanism 10, and the slide parts 111 and 117 of the connecting mechanism 10 move forward and backward in a symmetric direction, whereby the first fixing mechanism 20 and the second fixing mechanism 30 are connected to each other. The space | interval with 2 fixing mechanism 30 expands / contracts. As a result, the bone sound speed measuring device 1 can be mounted in accordance with the length of the tibia 201.

  In addition, when the bone sound velocity measuring device 1 is mounted in accordance with the length of the tibia 201, the probe holding mechanism 40 attached to the coupling mechanism 10 is always located at a half position of the tibia 201. ing. Further, the probe holding mechanism 40 can change the attachment angle around the attachment pin 155 that is an attachment location with the coupling mechanism 10. Accordingly, the probe holding mechanism 40 can be fixed along the inner surface 207 of the tibia 201, and the measurement location of the probe 51 attached to the probe holding mechanism 40 can be adjusted to a desired position. ing.

  Hereinafter, each member which comprises the bone sound speed measuring device 1 is demonstrated.

(Coupling mechanism)
As described above, the coupling mechanism 10 includes the slide portions 111 and 117. Although not shown, the slide portions 111 and 117 are provided with damper guides on opposite sides, and a spool gear that meshes with these is held. As a result, the slide portions 111 and 117 move back and forth in symmetrical directions. In other words, the coupling mechanism 10 enables the first fixing mechanism 20 and the second fixing mechanism 30 provided in the slide portions 111 and 117 to move forward and backward in a symmetric direction around the probe holding mechanism 40. . Thus, by allowing the first fixing mechanism 20 and the second fixing mechanism 30 to move back and forth in the symmetric direction with the probe holding mechanism 40 as the center, the first fixing mechanism 20 and the second fixing mechanism 30 can be moved. The position of the probe holding mechanism is uniquely determined with respect to the distance between them. In the present embodiment, the first fixing mechanism 20 and the second fixing mechanism 30 move forward and backward in symmetrical directions. However, the present invention is not limited to this, and between the first fixing mechanism 20 and the second fixing mechanism 30. As long as the position of the probe holding mechanism 40 is uniquely determined with respect to this distance, any configuration may be used. For example, the first fixing mechanism 20 and the second fixing mechanism 30 may move forward and backward independently. That is, the probe holding mechanism 40 may be located at any position between the first fixing mechanism 20 and the second fixing mechanism 30. Further, for example, the probe holding mechanism 40 may be configured to be movable to a position having a predetermined offset from the coupling mechanism 10 that connects the first fixing mechanism 20 and the second fixing mechanism 30 by a gear, a slide, or the like. Good.

  The coupling mechanism 10 has a support holder 153 that supports the probe holding mechanism 40. The support holder 153 is formed in a refracted step shape. Although not shown, the coupling mechanism 10 includes a slide rail that allows the support holder 153 to move up and down. Thereby, the position of the probe holding mechanism 40 in the vertical direction (direction perpendicular to the tibia) can be adjusted. In addition, a hole 156 for fitting a mounting pin 155 that rotatably holds the probe holding mechanism 40 is formed at the tip of the support holder 153.

(First fixing mechanism)
As shown in FIG. 2, the first fixing mechanism 20 includes a long knee holder 131, a knee base 133 formed to be inclined to the knee holder 131, and a knee pad 134 formed on the knee base 133. Composed. The knee holder 131 is formed with a proximal contact portion 132 that contacts the rough tibial surface. The proximal contact portion 132 is formed with an opening 21 penetrating in the vertical direction. The knee pad 134 is attached to the slide portion 111 of the coupling mechanism 10. In addition, it is preferable that the member that directly touches the human body such as the proximal contact portion 132 is formed of a soft and clean resin.

(Second fixing mechanism)
The second fixing mechanism 30 includes an ankle holder part 124 and an ankle base part 121. The ankle holder part 124 is L-shaped, and a projection (not shown) is formed on the longitudinal surface thereof. On the short surface of the ankle holder portion 124, a hole-shaped distal abutting portion 128 is formed in accordance with the average size of the inner capsule. The ankle base portion 121 has an L-shape, and a mini slide rail (not shown) is attached to the longitudinal surface of the ankle base portion 121. On this mini slide rail, the protruding portion of the ankle holder portion 124 is attached so as to be movable in the sliding direction. Further, the slide portion 117 of the coupling mechanism 10 is attached to the short surface of the ankle base portion 121. In addition, it is preferable that the member that directly touches the human body, such as the distal contact portion 128, is formed of resin.

(Probe holding mechanism)
As shown in FIG. 2, the probe holding mechanism 40 has a wide cross shape, and the left and right end portions are rotatably supported by a support holder 153. Specifically, the probe holding mechanism 40 is attached to the support holder 153 via the attachment pin 155 at the front center position of the coupling mechanism 10 and is rotatable about the attachment pin 155 as a rotation axis. As a result, when the tibia 201 is fixed by the first fixing mechanism 20 and the second fixing mechanism 30, the probe holding mechanism 40 is always located at a half position of the tibia 201, and the mounting angle thereof is changed. By changing, for example, the probe holding mechanism 40 can be fixed in accordance with the angle of the inner surface 207.

  In addition, an opening is formed in the central portion of the probe holding mechanism 40, the opening region 145a on the coupling mechanism 10 side, the opening region 145b on the first fixing mechanism 20 side, the opening region 145c on the opposite side of the coupling mechanism 10, An opening region 145d is provided on the second fixing mechanism 30 side. A plurality of parallel guide grooves 141 that can hold the probe 51 in a direction parallel to the axis of the tibia 201 are provided in the opening regions 145b and 145d at a predetermined distance. For example, in the case where three parallel guide grooves 141 are provided, the central parallel guide groove 141 is located at the position where the probe 51 hits the central portion moved from the front edge 206 of the tibia 201 by a specified distance (for example, 15 mm) and the center thereof. Parallel guide grooves 141 are provided at three locations with a specified distance (for example, ± 5 mm) centering on the portion. In addition, the opening regions 145a and 145c are provided with orthogonal guide grooves 142 that can hold the probe 51 in a direction orthogonal to the axis of the tibia 201. Although not shown, a plurality of orthogonal guide grooves 142 may be provided at a predetermined distance. The intervals between the plurality of parallel guide grooves 141 and the orthogonal guide grooves 142 can be set as appropriate. For example, if each interval is shortened, the probe 51 can measure the sound speed more finely, and the bone sound speed can be measured more accurately. Further, a probe mounting portion 53 of the probe unit 50 described later fits exactly in the parallel guide groove 141 and the orthogonal guide groove 142, and a pressing member 70 described later fits in the opening region 145a. It has become.

  Next, the probe unit 50 included in the bone sound speed measuring apparatus 100 will be described.

(Probe unit)
The probe unit 50 includes a hollow probe support portion 52, a probe 51 that fits into the central opening of the probe support portion 52, and a probe attachment portion 53 that connects the probe 51 and the probe support portion 52. doing. The probe 51 can measure the bone sound speed by transmitting and receiving ultrasonic waves. For example, an ultrasonic wave transmitted obliquely from the probe 51 to a bone such as the tibia 201 propagates while re-radiating the sound wave toward the soft tissue when propagating on the surface of the tibia 201 (leakage surface wave). By analyzing the leaky surface wave received again by the probe 51, the sound speed of the bone can be measured. The probe mounting portion 53 fixes the probe 51 to the probe support portion 52 and fits into the parallel guide groove 141 and the orthogonal guide groove 142 of the probe holding mechanism 40. That is, the claw-shaped probe attachment portion 53 is adapted to fit into the parallel guide groove 141 and the orthogonal guide groove 142. For example, the probe attachment portion 53 is placed in the opening regions 145b and 145d of the probe holding mechanism 40. By fitting into any of the paired parallel guide grooves 141 provided, the probe 51 is aligned in a direction parallel to the axis of the tibia 201 so that the bone sound velocity can be measured. Further, the probe 51 is fitted in a direction orthogonal to the axis of the tibia 201 by fitting the probe mounting portion 53 into any pair of orthogonal guide grooves 142 provided in the opening regions 145a and 145c of the probe holding mechanism 40. In addition, the bone sound velocity can be measured. Since the probe holding mechanism 40 has a plurality of grooves (parallel guide grooves 141 and orthogonal guide grooves 142) in both the parallel direction and the orthogonal direction, the probe 51 can measure a plurality of locations. Can be done.

  According to the bone sound speed measuring device 1 having the above-described configuration, the first fixing mechanism 20 fixed to the rough tibial surface of the tibia 201, and the second fixing mechanism 30 fixed to the endothelium. , The entire tibia 201 can be fixed, and the connecting mechanism 10 can expand and contract the distance between the first fixing mechanism 20 and the second fixing mechanism 30 to match the length of the tibia 201. Further, the probe 51 can be held in accordance with a predetermined part of the tibia 201 by the probe holding mechanism 40 attached to the coupling mechanism 10. Thereby, the transmission / reception site | part of the ultrasonic wave by the probe 51 with respect to the tibia 201 is defined in the fixed place, and a bone sound speed can be measured in a fixed place. Therefore, for example, even when the measurer changes or the measurement is performed several times, the same measurement place can be measured with high reproducibility.

  Further, when the distance between the first fixing mechanism 20 and the second fixing mechanism 30 is expanded or reduced by the coupling mechanism 10, the first fixing mechanism 20 and the second fixing mechanism 30 are arranged in a symmetric direction about the probe holding mechanism 40. Move forward and backward. As a result, even when the distance between the first fixing mechanism 20 and the second fixing mechanism 30 is increased or decreased in accordance with the length of the tibia 201, the probe 51 held by the probe holding mechanism 40 is always a certain predetermined amount of the tibia 201. It comes into contact with the part. Therefore, the ultrasonic wave transmission / reception part by the probe 51 with respect to the tibia 201 is determined at a certain place, and the bone sound velocity can be measured at the certain place.

  Further, the attachment angle of the probe holding mechanism 40 can be set to a desired angle. Thereby, the probe holding mechanism 40 can be brought into close contact with the soft tissue, and the probe 51 can measure a desired place.

  Further, according to the bone sound speed measuring apparatus 100, the measurement location of the probe 51 can be determined at a fixed location by the bone sound speed measuring device 1. Thereby, for example, even when the measurer changes or the measurement is performed several times, the same measurement place can be measured with high reproducibility.

(Pressing member)
Next, the pressing member 70 used when measuring the bone sound speed will be described. The pressing member 70 has a convex shape as shown in FIG. 3A, and the protruding portion is fitted into the opening region 145a of the probe holding mechanism 40 as shown in FIG. 3B. Be able to. The pressing member 70 is used to confirm the front edge 206 (see FIG. 5) of the tibia 201, and is pressed against the opening region 145a of the probe holding mechanism 40 in a state where the pressing member 70 is pressed against the front edge 206 of the tibia 201. By fitting, the probe holding mechanism 40 is positioned at a predetermined location with the front edge 206 as a reference.

(Bone sound speed measurement method)
Next, the bone sound speed measuring method of the tibia 201 using the bone sound speed measuring apparatus 100 according to the present embodiment will be described.

  In the bone sound velocity measurement according to the present embodiment, first, the contact surface of the human body is wiped with gauze containing alcohol. Next, while visually recognizing the position of the rough tibial surface through the proximal contact portion 132 of the first fixing mechanism 20, the first contact mechanism 132 is aligned with the rough tibial surface to fix the first fixing mechanism 20. On the other hand, while visually recognizing the position of the inner fruit through the distal contact part 128 of the second fixing mechanism 30, the second fixing mechanism 30 is fixed by aligning the distal contact part 128 with the inner fruit. Since the openings 21 and 31 are formed in each contact portion, the characteristic bone portion can be visually confirmed and palpated during and after mounting. At this time, since the distance between the first fixing mechanism 20 and the second fixing mechanism 30 can be expanded and contracted by the connecting mechanism 10, it can be adjusted to the length of the tibia 201. When the bone sound velocity measuring device 1 is fixed to the tibia 201 in this way, the probe holding mechanism 40 is automatically positioned at a position corresponding to 1/2 of the tibia 201. The rotation axis (attachment pin 155) of the probe holding mechanism 40 attached to the support holder 153 of the coupling mechanism 10 is along the position of the front edge 206. Thereby, since the probe holding mechanism 40 can be rotated with reference to the position of the front edge 206, the probe holding mechanism 40 can be rotated and fixed at a predetermined position along the inner side surface 207. .

  Next, the position of the front edge 206 of the tibia 201 is confirmed using the pressing member 70. Specifically, the pressing member 70 is pressed against the front edge 206 slightly against the outer surface side of the front edge 206. At this time, the entire device rotates with the rough surface of the tibia as a fulcrum, so that the mini slide rail attached to the ankle base portion 121 of the second fixing mechanism 30 is slid and movable. As a result, the position of the leading edge 206 can be accurately grasped. Then, with the pressing member 70 pressed against the front edge 206, the pressing member 70 is fitted into the opening region 145a of the probe holding mechanism 40 to position the probe holding mechanism 40. FIG. 3B shows a state in which the pressing member 70 is fitted in the opening region 145a. In this way, the position of the front edge 206 can be confirmed using the pressing member 70, and the measurement location of the probe 51 can be fixed by the probe holding mechanism 40, so that palpation or direct marking on the skin as in the past, etc. Thus, the positioning can be performed more accurately than determining the measurement location.

  Next, the probe 51 is mounted in the parallel guide groove 141. Thereby, the probe 51 can be applied to the inner surface 207 in a direction parallel to the axis of the tibia 201. Thereafter, ultrasonic waves are transmitted and received by the probe 51 to measure the sound velocity, and the bone strength index of the tibia 201 is calculated. In addition, by mounting the probe 51 in the orthogonal guide groove 142, the bone sound velocity can be measured by applying the probe 51 along the orthogonal direction to the tibia 201.

  As described above, according to the bone sound velocity measurement method according to the present embodiment, the front edge of the tibia 201 is fitted into the probe holding mechanism 40 in a state where the front edge 206 of the tibia 201 is pressed by the pressing member 70. The probe holding mechanism 40 can be fixed at a predetermined location with reference to 206. As a result, the measurement location of the probe 51 attached to the probe holding mechanism 40 becomes constant with reference to the front edge 206, and the same measurement location is reproduced even when the measurer changes or the measurement is performed several times, for example. Highly measurable.

  The embodiments of the present invention have been described above, but only specific examples have been illustrated, and the present invention is not particularly limited. Specific configurations and the like can be appropriately changed in design. Further, the actions and effects described in the embodiments of the present invention only list the most preferable actions and effects resulting from the present invention, and the actions and effects according to the present invention are described in the embodiments of the present invention. It is not limited to things.

  For example, in the case of the present embodiment, the pressing member 70 is a separate body from the probe holding mechanism 40, but is not necessarily limited to this. For example, the pressing member 70 may be provided in advance in the vicinity of the opening region 145c of the probe holding mechanism 40 and integrated. Moreover, the form which can be protruded or retracted from the probe holding mechanism 40 by operating with a button etc. may be sufficient.

  The present invention can be applied to an apparatus and method for diagnosing bone sound speed by transmitting and receiving ultrasonic waves to the surface of the tibia.

DESCRIPTION OF SYMBOLS 1 Bone sound speed measuring device 20 1st fixing mechanism 30 2nd fixing mechanism 40 Probe holding mechanism 51 Probe 90 Foot part 100 Bone sound speed measuring apparatus 111 Slide part 117 Slide part 128 Endothelium contact part 132 Tibial rough surface contact part

Claims (13)

A first fixing mechanism fixed so as to be able to be positioned with reference to a characteristic bone portion identifiable from a body surface proximal to the tibia;
A second fixing mechanism fixed so as to be able to be positioned with reference to a characteristic bone portion that can be identified from a body surface distal to the tibia;
A connecting mechanism that connects the first fixing mechanism and the second fixing mechanism, and is capable of expanding and contracting a distance between the first fixing mechanism and the second fixing mechanism;
A probe holding mechanism that is attached to the coupling mechanism and holds a probe that transmits and receives ultrasonic waves so as to be able to contact a predetermined part of the tibia;
A device for measuring bone sound speed, comprising: The first fixing mechanism has an opening in which the characteristic bone portion fits in a proximal contact portion with the characteristic bone portion,
The bone sound speed measuring device according to claim 1, wherein the second fixing mechanism has an opening in which the characteristic bone portion is fitted in a distal contact portion with the characteristic bone portion.   The said 1st fixing mechanism and the said 2nd fixing mechanism are enabled to move forward / backward in the symmetrical direction centering | focusing on the said probe holding mechanism with the said connection mechanism. Bone sound velocity measuring device.   The bone sound speed measuring device according to any one of claims 1 to 3, wherein the probe holding mechanism is attached so that an attachment angle with respect to the coupling mechanism can be changed.   The bone according to any one of claims 1 to 4, wherein the probe holding mechanism further includes a parallel guide groove capable of holding the probe in a direction parallel to the axis of the tibia. Equipment for measuring the speed of sound.   The bone according to any one of claims 1 to 5, wherein the probe holding mechanism further includes an orthogonal guide groove capable of holding the probe in a direction orthogonal to the axis of the tibia. Equipment for measuring the speed of sound.   The bone sound velocity measuring device according to claim 5, wherein the probe holding mechanism further includes a plurality of the parallel guide grooves at a predetermined distance.   The bone sound speed measuring device according to claim 6, wherein the probe holding mechanism further includes a plurality of the orthogonal guide grooves at a predetermined distance.   The probe holding mechanism further includes an opening region into which a pressing member that presses against the tibia is fitted, and when the pressing member is fitted into the opening region with the front edge of the tibia pressed against the opening region, The bone sound speed measuring device according to any one of claims 1 to 8, wherein the probe holding mechanism is positioned at a predetermined location with respect to the front edge.   The bone sound velocity according to any one of claims 1 to 9, wherein the characteristic bone of the characteristic bone portion with which the proximal contact portion abuts is a tibial rough surface, a medial condyle, or a patella. Measuring equipment.   The bone sound speed according to any one of claims 1 to 10, wherein the characteristic bone of the characteristic bone portion with which the distal abutting portion abuts is an inner fruit, an outer fruit or a rib. Measuring equipment. The bone sound velocity measuring device according to any one of claims 1 to 11,
The probe attachable to the probe holding mechanism;
A bone sound speed measuring device comprising:   The pressing member according to claim 9 is pressed against the front edge of the tibia, the pressing member is fitted into the opening region of the probe holding mechanism, and the position of the probe holding mechanism is fixed. A bone sound speed measuring method, characterized by measuring a sound speed.