TWI422359B - Knee ligament laxity measuring device - Google Patents
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本發明是有關於一種量測裝置,特別是指一種透過施加外力的方式來量測脛骨相對於股骨運動,以反應出運動量與所施加外力之間的相對變化關係的膝關節韌帶鬆弛度量測裝置。The invention relates to a measuring device, in particular to a method for measuring the relaxation of the knee joint ligament by measuring the relative change relationship between the amount of movement and the applied external force by applying an external force to measure the movement of the tibia relative to the femur. Device.
膝關節韌帶受傷或斷裂是一種常見的運動傷害,醫生對於膝關節韌帶的治療通常會根據患者的年齡、是否為運動員、平常的運動方式、膝關節的穩定性,以及是否有合併其他地方傷害等因素,來考慮採用何種方式進行治療。醫生在進行診斷時,會對患者的膝關節韌帶鬆弛度(Knee ligament laxity)進行量測,以評估韌帶的受傷程度。因此,正確的膝關節韌帶鬆弛度量測結果有助於提供醫生正確的患者受傷資訊,以利於醫生診斷病情並能對患者施予最佳與即時的醫療。Injury or rupture of the knee ligament is a common type of sports injury. The doctor's treatment of the knee ligament usually depends on the patient's age, whether it is an athlete, the usual way of exercising, the stability of the knee joint, and whether there is any other injury. Factors to consider the method of treatment. When the doctor makes a diagnosis, the patient's knee ligament laxity is measured to assess the degree of ligament injury. Therefore, the correct knee ligament relaxation measurement results can help the doctor to provide correct patient injury information, so that the doctor can diagnose the disease and give the patient the best and immediate medical treatment.
目前醫界所採用的膝關節韌帶鬆弛度量測裝置大多為MEDmetric公司所生產的KT1000量測儀器,該量測儀器是基於美國專利第4,583,555號專利案所揭露之膝關節韌帶量測系統以及美國專利第4,969,471號專利案所揭露之膝關節韌帶量測裝置及其使用方法所研發。然而,前述KT1000量測儀器存在的主要缺點就是量測儀器在使用時是與操作者的操作經驗有關;因此,量測數據的可靠度與可重現性皆會受到影響,進而誤導醫生的診斷。再者,量測儀器只能對前、後十字韌帶進行量測評估,而無法對側韌帶進行量測評估,故使用上有其侷限性。At present, most of the knee ligament relaxation measuring devices used by the medical community are KT1000 measuring instruments produced by MEDmetric, which is based on the knee ligament measuring system disclosed in U.S. Patent No. 4,583,555 and the United States. The knee ligament measuring device and the method of using the same disclosed in Patent No. 4,969,471 are developed. However, the main disadvantage of the aforementioned KT1000 measuring instrument is that the measuring instrument is related to the operator's operating experience when used; therefore, the reliability and reproducibility of the measured data will be affected, thereby misleading the doctor's diagnosis. . Furthermore, the measuring instrument can only measure the anterior and posterior cruciate ligaments, but can not measure the lateral ligament, so it has its limitations.
另一方面,其他現有膝關節韌帶鬆弛度量測儀器亦都存在有其缺點。例如,Aircast公司所生產的Rolimeter量測儀器只能做最大施力測試,並且只能對前、後十字韌帶進行量測評估。Sport Tech公司所生產的LigMaster量測儀器(基於美國專利第5,724,991號專利案與美國專利第6,419,645號專利案所研發)的操作步驟複雜,患者必須變換姿勢以量測不同位置的韌帶。GeNouRob公司所生產的GNRB量測儀器則只能對前十字韌帶進行量測評估。因此,如何構思出一種能克服目前現有量測儀器缺點的結構設計,遂成為本發明要進一步改進的主題。On the other hand, other existing knee ligament relaxation measuring instruments also have their disadvantages. For example, Airline's Rolimeter measuring instruments can only perform maximum force testing and can only measure the anterior and posterior cruciate ligaments. The operation steps of the LigMaster measuring instrument (developed based on the patents of U.S. Patent No. 5,724,991 and U.S. Patent No. 6,419,645) by Sport Tech are complicated, and the patient must change his posture to measure the ligaments at different positions. The GNRB measuring instrument produced by GeNouRob can only measure the anterior cruciate ligament. Therefore, how to conceive a structural design that can overcome the shortcomings of the current measuring instruments has become the subject of further improvement of the present invention.
本發明之主要目的,在於提供一種膝關節韌帶鬆弛度量測裝置,透過量測小腿的脛骨的前向、後向位移,以及內翻與外翻的程度,以評估前、後十字韌帶以及內、外側韌帶受傷的程度。The main object of the present invention is to provide a knee ligament relaxation measuring device for measuring the anterior and posterior displacement of the tibia of the lower leg, and the degree of varus and valgus to evaluate the anterior and posterior cruciate ligaments and the inner ligament. The extent of injury to the lateral ligament.
本發明之另一目的,在於提供一種膝關節韌帶鬆弛度量測裝置,其操作容易,且可方便地對前、後十字韌帶以及內、外側韌帶進行量測,且量測可靠度及準確性高,量測數據重現性佳。Another object of the present invention is to provide a knee joint ligament relaxation measuring device, which is easy to operate, and can conveniently measure the anterior and posterior cruciate ligaments and the inner and outer ligaments, and measure reliability and accuracy. High, measurement data reproducibility is good.
本發明之又一目的,在於提供一種膝關節韌帶鬆弛度量測裝置,具有優良的數據顯示介面與使用者介面。Another object of the present invention is to provide a knee joint ligament relaxation measuring device having an excellent data display interface and a user interface.
本發明的目的及解決先前技術問題是採用以下技術手段來實現的。依據本發明所揭露的膝關節韌帶鬆弛度量測裝置,適於安裝在一大腿及一與大腿相連接的小腿上。膝關節韌帶鬆弛度量測裝置包含一大腿套接機構、一小腿套接機構、一第一量測機構,及一第二量測機構。The object of the present invention and solving the prior art problems are achieved by the following technical means. The knee ligament relaxation measuring device according to the present invention is adapted to be mounted on a thigh and a calf connected to the thigh. The knee ligament relaxation measuring device comprises a one-leg socket mechanism, a calf socket mechanism, a first measuring mechanism, and a second measuring mechanism.
大腿套接機構套接於大腿上並包括一第一前端面,及一與第一前端面相連接的第一側面。小腿套接機構套接於小腿上並包括一第二前端面,及一與第二前端面相連接的第二側面。第一量測機構連接於大腿套接機構的第一前端面與小腿套接機構的第二前端面之間,用以量測脛骨受一向前或向後方向的力量施加後的位移量。第二量測機構連接於大腿套接機構的第一側面與小腿套接機構的第二側面之間,用以量測脛骨受一向左或向右方向的力量施加後的翻轉量。The thigh socket mechanism is sleeved on the thigh and includes a first front end surface and a first side surface connected to the first front end surface. The calf socket mechanism is sleeved on the lower leg and includes a second front end surface and a second side surface connected to the second front end surface. The first measuring mechanism is connected between the first front end surface of the thigh socket mechanism and the second front end surface of the calf socket mechanism for measuring the displacement amount of the tibia after being applied by a force in a forward or backward direction. The second measuring mechanism is connected between the first side of the thigh socket mechanism and the second side of the calf socket mechanism for measuring the amount of turnover of the tibia after being applied by a force in a leftward or rightward direction.
本發明之再一目的,在於提供一種膝關節韌帶鬆弛度量測方法,操作容易且可方便地對前、後十字韌帶以及內、外側韌帶進行量測,且量測可靠度及準確性高,量測數據重現性佳。A further object of the present invention is to provide a method for measuring the relaxation of a knee joint ligament, which is easy to operate and can conveniently measure the anterior and posterior cruciate ligaments and the medial and lateral ligaments, and has high measurement reliability and accuracy. The measurement data is reproducible.
本發明的目的及解決先前技術問題是採用以下技術手段來實現的。依據本發明所揭露的膝關節韌帶鬆弛度量測方法,用以量測一小腿的一脛骨受一向前或向後方向的力量施加後的位移量,該方法包含下述步驟:The object of the present invention and solving the prior art problems are achieved by the following technical means. The knee ligament relaxation measurement method according to the present invention is for measuring a displacement amount of a tibia of a calf after being applied by a force in a forward or backward direction, the method comprising the steps of:
(A)施加一向前或向後的力量於一前後向施力桿件上,使一與前後向施力桿件相連接的伸縮連桿模組帶動一套接在小腿的小腿套接機構運動;(A) applying a forward or backward force on a forward and backward force applying member, so that a telescopic link module connected to the front and rear force applying members drives a set of the calf socket mechanism attached to the lower leg;
(B)感測施加於前後向施力桿件上的力量並產生一力量感測訊號,以及感測伸縮連桿模組的位移量並產生一位移感測訊號;及(B) sensing the force applied to the urging member and generating a force sensing signal, and sensing the displacement of the telescopic link module and generating a displacement sensing signal;
(C)利用一電腦擷取力量感測訊號及位移感測訊號以進行運算比對。(C) Using a computer to extract power sensing signals and displacement sensing signals for operational comparison.
依據本發明所揭露的膝關節韌帶鬆弛度量測方法,用以量測一小腿的一脛骨受一向左或向右方向的力量施加後的翻轉量,該方法包含下述步驟:The knee joint ligament relaxation measuring method according to the present invention is for measuring the amount of inversion of a tibia of a calf after being applied by a leftward or rightward force. The method comprises the following steps:
(A)施加一向左或向右方向的力量於一左右向施力桿件上,使一與左右向施力桿件相連接的一套接在小腿的小腿套接機構運動;(A) applying a leftward or rightward force to a left and right force applying member to move a set of calf sleeves connected to the left and right force applying members to the calf;
(B)感測施加於左右向施力桿件上的力量並產生一力量感測訊號,以及感測小腿套接機構的翻轉量並產生一位移感測訊號;及(B) sensing the force applied to the left and right force applying members and generating a force sensing signal, and sensing the amount of inversion of the calf socket mechanism and generating a displacement sensing signal;
(C)利用一電腦擷取力量感測訊號及位移感測訊號以進行運算比對。(C) Using a computer to extract power sensing signals and displacement sensing signals for operational comparison.
依據本發明所揭露的膝關節韌帶鬆弛度量測方法,用以量測一小腿的一脛骨受一向前或向後方向的力量施加後的位移量,該方法包含下述步驟:The knee ligament relaxation measurement method according to the present invention is for measuring a displacement amount of a tibia of a calf after being applied by a force in a forward or backward direction, the method comprising the steps of:
(A)施加一向前或向後的力量於一前後向施力桿件上,使一與前後向施力桿件相連接且套接在小腿的小腿套接機構運動;(A) applying a forward or backward force on a forward and backward force applying member to move a calf socket mechanism connected to the front and rear force applying members and sleeved to the lower leg;
(B)感測施加於該前後向施力桿件上的力量並產生一力量感測訊號,以及感測該脛骨的一結節的位移量並產生一位移感測訊號;及(B) sensing the force applied to the urging member and generating a force sensing signal, and sensing the displacement of a nodule of the tibia and generating a displacement sensing signal;
(C)利用一電腦擷取力量感測訊號及位移感測訊號以進行運算比對。(C) Using a computer to extract power sensing signals and displacement sensing signals for operational comparison.
藉由上述技術手段,本發明膝關節韌帶鬆弛度量測裝置的優點及功效在於,藉由第一量測機構的設計,能量測脛骨前向位移以及脛骨後向位移,以得知前、後十字韌帶的受傷程度;藉由第二量測機構的設計,能量測脛骨內翻量以及脛骨外翻量,以得知內、外側韌帶的受傷程度;藉此,可供專業骨科醫生及復健人員診斷病情並對患者施予最佳與即時的醫療。According to the above technical means, the advantages and effects of the knee ligament relaxation measuring device of the present invention are that, by the design of the first measuring mechanism, the energy is measured by the forward displacement of the tibia and the posterior displacement of the tibia, so as to know the front, The degree of injury to the posterior cruciate ligament; the design of the second measuring mechanism, energy measurement of the amount of patella varus and the amount of valgus valgus, to understand the degree of injury of the medial and lateral ligaments; thereby, for professional orthopedic surgeons and Rehabilitation personnel diagnose the condition and give the patient the best and immediate medical care.
有關本發明之前述及其他技術內容、特點與功效,在以下配合參考圖式之二個較佳實施例的詳細說明中,將可清楚地呈現。透過具體實施方式的說明,當可對本發明為達成預定目的所採取的技術手段及功效得以更加深入且具體的了解,然而所附圖式只是提供參考與說明之用,並非用來對本發明加以限制。The above and other technical contents, features and advantages of the present invention will be apparent from the following detailed description of the preferred embodiments of the accompanying drawings. The technical means and functions of the present invention for achieving the intended purpose can be more deeply and specifically understood by the description of the specific embodiments. However, the drawings are only for the purpose of reference and description, and are not intended to limit the invention. .
在本發明被詳細描述之前,要注意的是,在以下的說明內容中,類似的元件是以相同的編號來表示。此外,在以下的說明內容中,「前向」所指方向為人體腿部向前行進時的方向,「後向」所指方向為「前向」之相反方向,「上方」所指方向為從人體膝蓋往大腿沿伸的方向,「下方」所指方向為從人體膝蓋往小腿沿伸的方向。Before the present invention is described in detail, it is noted that in the following description, similar elements are denoted by the same reference numerals. In addition, in the following description, the direction of "forward" refers to the direction in which the human leg moves forward, the direction of "backward" refers to the opposite direction of "forward", and the direction of "upward" refers to From the knees of the human body to the thighs, the direction of "below" refers to the direction from the knees of the human body to the lower legs.
如圖1所示,是一般人體腿部的示意圖。大腿11的一股骨111與小腿12的一脛骨121之間連接有一前十字韌帶13以及一後十字韌帶14,股骨111與脛骨121的內側之間連接有一內側韌帶15,而股骨111與脛骨121的外側之間連接有一外側韌帶16。當一般人在跑步時突然減速、迅速地改變跑步方向,或者是跳起著地時皆有可能造成前、後十字韌帶13、14或者是內、外側韌帶15、16受傷。前、後十字韌帶13、14受傷會造成脛骨前向位移(Anterior translation)以及脛骨後向位移(Posterior translation),內、外側韌帶15、16受傷時則會造成脛骨內翻(Varus angulation)以及脛骨外翻(Valgus angulation)。As shown in Figure 1, it is a schematic view of the general human leg. A anterior cruciate ligament 13 and a posterior cruciate ligament 14 are connected between a femur 111 of the thigh 11 and a tibia 121 of the calf 12. An inner ligament 15 is connected between the femur 111 and the inner side of the tibia 121, and the femur 111 and the tibia 121 are connected. An outer ligament 16 is connected between the outer sides. When the average person suddenly decels while running, quickly changes the running direction, or jumps to the ground, it is possible to cause the front and rear cruciate ligaments 13, 14 or the inner and outer ligaments 15, 16 to be injured. Injury of the anterior and posterior cruciate ligaments 13, 14 can cause Anterior translation and Posterior translation. When the medial and lateral ligaments 15 and 16 are injured, they will cause varus angulation and tibia. Valgus angulation.
如圖2及圖3所示,是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例,該膝關節韌帶鬆弛度量測裝置200適於安裝在患者的一大腿11及一與大腿11相連接的小腿12上。透過本發明的膝關節韌帶鬆弛度量測裝置200可量測脛骨前向位移、脛骨後向位移、脛骨內翻,以及脛骨外翻等四種物理量,能做為專業骨科醫生及復健人員等評估患者韌帶受傷程度與復原程度的量化數據。2 and FIG. 3, which is a first preferred embodiment of the knee ligament relaxation measuring device of the present invention, the knee ligament relaxation measuring device 200 is adapted to be mounted on a patient's thigh 11 and a The thighs 11 are connected to the lower leg 12. The knee ligament relaxation measuring device 200 of the present invention can measure four physical quantities such as anterior displacement of the tibia, posterior displacement of the tibia, varus varus, and valgus valgus, and can be used as a professional orthopedic surgeon and rehabilitation personnel. Quantitative data to assess the degree of ligament injury and recovery in patients.
如圖3、圖4及圖5所示,膝關節韌帶鬆弛度量測裝置200包含一大腿套接機構2、一小腿套接機構3,及一連接於大腿套接機構2與小腿套接機構3之間的第一量測機構4。大腿套接機構2包括一第一套殼21及二迫緊模組22;第一套殼21呈倒U形並包含一前壁211及二分別由前壁211左、右端朝後凸伸的側壁212;前壁211及側壁212共同界定一空間供大腿11及一髕骨17(即膝蓋骨,如圖1所示)容置。各迫緊模組22設置於各側壁212上,各迫緊模組22包含一迫緊件221及一旋鈕222;迫緊件221的一迫緊板223位於各側壁212內側,用以抵接於大腿11上,迫緊板223外側凸設有一穿出側壁212的一穿孔213的螺桿224,螺桿224可螺接於旋鈕222的一螺孔225內,旋鈕222樞設於各側壁212外側,透過旋轉兩旋鈕222轉動以帶動兩迫緊件221相對於側壁212左右平移,藉此,使得兩迫緊件221的迫緊板223能緊密地貼覆在大腿11左、右兩側,以避免第一套殼21相對於大腿11產生晃動。As shown in FIG. 3, FIG. 4 and FIG. 5, the knee joint ligament relaxation measuring device 200 comprises a one-leg socket mechanism 2, a calf sleeve mechanism 3, and a thigh socket mechanism 2 and a calf sleeve mechanism. The first measuring mechanism 4 between 3. The thigh sleeve mechanism 2 includes a first sleeve 21 and two pressing modules 22; the first sleeve 21 has an inverted U shape and includes a front wall 211 and two protrusions respectively protruding from the left and right ends of the front wall 211 The side wall 212; the front wall 211 and the side wall 212 together define a space for the thigh 11 and a tibia 17 (ie, the kneecap, as shown in FIG. 1). Each of the pressing modules 22 is disposed on each of the side walls 212. Each of the pressing modules 22 includes a pressing member 221 and a knob 222. A pressing plate 223 of the pressing member 221 is located inside each side wall 212 for abutting the thigh. A screw 224 is formed on the outer side of the pressing plate 223. The screw 224 is screwed into a screw hole 225 of the knob 222. The knob 222 is pivoted outside the side wall 212 and is rotated. The two knobs 222 are rotated to drive the two pressing members 221 to translate left and right relative to the side wall 212, so that the pressing plates 223 of the two pressing members 221 can be closely attached to the left and right sides of the thigh 11 to avoid the first The casing 21 is shaken relative to the thighs 11.
另外,大腿套接機構2還包括二條設置於第一套殼21的側壁212後端的固緊帶23。在本實施例中,各固緊帶23包括一連接於一側壁212的第一帶體231,及一連接於另一側壁212且可拆卸地黏扣於第一帶體231上的第二帶體232,其中,第一帶體231例如為一毛面帶體,第二帶體232例如為一鉤面帶體,透過第二帶體232黏扣於第一帶體231上,使得第一套殼21能固緊於大腿11上。In addition, the thigh socket mechanism 2 further includes two fastening straps 23 disposed at the rear end of the side wall 212 of the first casing 21. In this embodiment, each fastening strap 23 includes a first strap 231 coupled to a sidewall 212 and a second strap detachably coupled to the first strap 212 and detachably attached to the first strap 231. The first strip 231 is, for example, a matte strip body, and the second strip 232 is, for example, a hook strip body, and is adhered to the first strip 231 through the second strip 232, so that The casing 21 can be fastened to the thighs 11.
如圖3、圖4及圖6所示,小腿套接機構3的結構與大腿套接機構2的結構類似,小腿套接機構3包括一第二套殼31及二迫緊模組32;第二套殼31呈倒U形並包含一前壁311及二分別由前壁311左、右端朝後凸伸的側壁312;前壁311及側壁312共同界定一空間供小腿12容置。各迫緊模組32設置於各側壁312上,各迫緊模組32包含一迫緊件321及一旋鈕322,迫緊件321的一迫緊板323位於各側壁312內側,用以抵接於小腿12上,迫緊板323外側凸設有一穿出側壁312的一穿孔313的螺桿324,螺桿324可螺接於旋鈕322的一螺孔325內,旋鈕322樞設於各側壁312外側。透過旋轉兩旋鈕322轉動以帶動兩迫緊件321相對於側壁312左右平移,藉此,使得兩迫緊件321的迫緊板323能緊密地貼覆在小腿12左、右兩側,以避免第二套殼31相對於小腿12產生晃動。As shown in FIG. 3, FIG. 4 and FIG. 6, the structure of the calf sleeve mechanism 3 is similar to that of the thigh socket mechanism 2, and the calf sleeve mechanism 3 includes a second sleeve 31 and two pressing modules 32; The two sets of shells 31 are inverted U-shaped and include a front wall 311 and two side walls 312 respectively protruding from the left and right ends of the front wall 311. The front wall 311 and the side walls 312 together define a space for the calf 12 to be received. Each of the pressing modules 32 is disposed on each of the side walls 312. Each of the pressing modules 32 includes a pressing member 321 and a knob 322. A pressing plate 323 of the pressing member 321 is located inside each side wall 312 for abutting the lower leg. 12, a screw 324 protruding through a hole 313 of the side wall 312 is protruded from the outer side of the pressing plate 323. The screw 324 can be screwed into a screw hole 325 of the knob 322, and the knob 322 is pivoted outside the side walls 312. By rotating the two knobs 322, the two pressing members 321 are translated to the left and right with respect to the side wall 312, so that the pressing plates 323 of the two pressing members 321 can be closely attached to the left and right sides of the lower leg 12 to avoid The second set of shells 31 is swayed relative to the lower legs 12.
另外,小腿套接機構3還包括一連接於前壁311的一第二前端面314上的延伸架33,延伸架33可透過螺鎖或一體成型的方式設於第二殼套31,延伸架33可供小腿12容置。小腿套接機構3還包括二條固緊帶34,其中一條固緊帶34設置於第二套殼31的側壁312後端,其包括一連接於一側壁312的第一帶體341,及一連接於另一側壁312且可拆卸地黏扣於第一帶體341上的第二帶體342。另一條固緊帶34設置於延伸架33上,其包括一連接於延伸架33的第一帶體341,及一連接於延伸架33且可拆卸地黏扣於第一帶體341上的第二帶體342,其中,第一帶體341例如為一毛面帶體,第二帶體342例如為一鉤面帶體。透過各固緊帶34的第二帶體342黏扣於第一帶體341上,使得第二套殼31能固緊於小腿12上。In addition, the shank splicing mechanism 3 further includes an extension frame 33 connected to a second front end surface 314 of the front wall 311. The extension frame 33 can be disposed on the second casing 31 through a screw lock or an integral molding. 33 can be accommodated in the calf 12. The shank splicing mechanism 3 further includes two fastening straps 34. One of the fastening straps 34 is disposed at the rear end of the sidewall 312 of the second sleeve 31, and includes a first strap 341 connected to a sidewall 312, and a connection. The second strip 342 is detachably attached to the other side wall 312 of the first strip 341. The other fastening strap 34 is disposed on the extension frame 33 and includes a first strap body 341 connected to the extension frame 33, and a first connector attached to the extension frame 33 and detachably fastened to the first strap body 341. The second belt 342 is, for example, a rough surface belt body, and the second belt body 342 is, for example, a hook surface belt body. The second strap 342 of each of the fastening strips 34 is adhered to the first strap 341 such that the second sleeve 31 can be fastened to the lower leg 12.
如圖3、圖4及圖7所示,第一量測機構4用以量測脛骨121(如圖1所示)受一向前或向後方向的力量施加後的位移量,第一量測機構4包括一承載框架41及一伸縮連桿模組42。承載框架41透過樞接方式設置於第一套殼21的前壁211的一第一前端面214上,承載框架41包含一呈L形的架體411,及一穿設於架體411的第一軸412,第一軸412是呈左右方向延伸。伸縮連桿模組42一端樞接於承載框架41且可轉動地繞第一軸412旋轉,而其另一相反端與小腿套接機構3相連接;伸縮連桿模組42包含一第一滑接件421,及一可滑動地滑接於第一滑接件421的第二滑接件422。第一滑接件421包括一沿上下方向延伸的樞接架423,樞接架423的一上樞接端424樞接於承載框架41的第一軸412並可繞第一軸412旋轉。第一滑接件421還包括二固定地設置於樞接架423上呈長條狀的滑軌425,第二滑接件422包括一滑動架426,及二固定地設置於滑動架426上的滑塊427,各滑塊427界定有一供各滑軌425滑接的滑槽428,藉此,使得第二滑接件422可相對於第一滑接件421上下滑動。伸縮連桿模組42還包含一接合件429,接合件429透過樞接方式設置於第二套殼31的前壁311的第二前端面314上,接合件429包括一呈左右方向延伸並與第一軸412平行的第二軸430,第二滑接件422的滑動架426的一下樞接端431樞接於第二軸430並可繞第二軸430旋轉。As shown in FIG. 3, FIG. 4 and FIG. 7, the first measuring mechanism 4 is configured to measure the displacement amount of the tibia 121 (shown in FIG. 1) after being applied by a force in a forward or backward direction, and the first measuring mechanism 4 includes a carrier frame 41 and a telescopic link module 42. The carrier frame 41 is disposed on a first front end surface 214 of the front wall 211 of the first casing 21 by a pivotal connection. The carrier frame 41 includes an L-shaped frame body 411 and a first portion disposed on the frame body 411. A shaft 412 has a first shaft 412 extending in the left-right direction. One end of the telescopic link module 42 is pivotally connected to the carrying frame 41 and rotatably rotates around the first shaft 412, and the other opposite end is connected with the calf sleeve mechanism 3; the telescopic link module 42 includes a first slide The connector 421 and a second sliding member 422 slidably slidably coupled to the first sliding member 421. The first sliding member 421 includes a pivoting frame 423 extending in the up and down direction. An upper pivoting end 424 of the pivoting frame 423 is pivotally connected to the first shaft 412 of the carrying frame 41 and rotatable about the first shaft 412. The first sliding member 421 further includes two sliding rails 425 fixedly disposed on the pivoting frame 423. The second sliding member 422 includes a sliding frame 426, and two fixedly disposed on the sliding frame 426. The slider 427 defines a sliding slot 428 for sliding the sliding rails 425, so that the second sliding member 422 can slide up and down relative to the first sliding member 421. The telescopic link module 42 further includes an engaging member 429. The engaging member 429 is pivotally disposed on the second front end surface 314 of the front wall 311 of the second casing 31. The engaging member 429 includes a left-right direction and The second shaft 430 of the first shaft 412 is parallel, and the lower pivot end 431 of the carriage 426 of the second sliding member 422 is pivotally connected to the second shaft 430 and rotatable about the second shaft 430.
架體411還包括一襯套413,襯套413界定有一呈前後方向延伸的穿孔414。第一量測機構4還包括一前後向施力桿件44,前後向施力桿件44可活動地穿設於承載框架41的穿孔414並與伸縮連桿模組42相接合。在本實施例中,前後向施力桿件44包含一銷部441,及一相反於銷部441的施力部442;銷部441可穿設於第二滑接件422之滑動架426的一長形滑槽432中以使銷部441受長形滑槽432所拘束,換言之,銷部441滑動地樞接於與長形滑槽432以使兩者之間可同時產生相對滑動及相對轉動(相對滑動之方向與第一軸412垂直,相對轉動之軸向與第一軸412平行);施力部442呈T形狀用以供使用者按壓。當使用者按壓施力部442使前後向施力桿件44沿著穿孔414上下滑動的過程中,前後向施力桿件44能同時帶動伸縮連桿模組42繞第一軸412相對於承載框架41的架體411旋轉。The frame 411 further includes a bushing 413 defining a through hole 414 extending in the front-rear direction. The first measuring mechanism 4 further includes a front and rear force applying member 44. The front and rear force applying members 44 are movably disposed through the through holes 414 of the carrying frame 41 and engaged with the telescopic link module 42. In the present embodiment, the forward and backward biasing members 44 include a pin portion 441 and a biasing portion 442 opposite to the pin portion 441. The pin portion 441 can be disposed through the sliding frame 426 of the second sliding member 422. The elongated slot 432 is configured such that the pin portion 441 is restrained by the elongated slot 432. In other words, the pin portion 441 is slidably pivotally coupled to the elongated slot 432 so that relative sliding and relative can be simultaneously generated therebetween. Rotation (the direction of relative sliding is perpendicular to the first axis 412, and the direction of relative rotation is parallel to the first axis 412); the urging portion 442 is T-shaped for the user to press. When the user presses the urging portion 442 to slide the front and rear urging member 44 up and down along the through hole 414, the front and rear urging member 44 can simultaneously drive the telescopic link module 42 about the first shaft 412 relative to the bearing. The frame 411 of the frame 41 is rotated.
第一量測機構4還包括一第一力量感測元件45,第一力量感測元件45設置於前後向施力桿件44的兩隔板443之間,用以感測施加於前後向施力桿件44的施力部442上的力量。在本實施例中,第一力量感測元件45為一荷重計(Load cell),其與目前市面上的荷重計結構及作動原理相同,故在此不詳加贅述。第一量測機構4還包括一設置於承載框架41上並與伸縮連桿模組42抵接的第一位移感測元件46,用以感測伸縮連桿模組42的位移量。在本實施例中,第一位移感測元件46為一電阻式位移感測器,其包含一固定地穿設於承載框架41的架體411上的本體461,及一穿設於本體461內並可相對於本體461前後伸縮的探針462;探針462抵接於第一滑接件421的樞接架423上,藉此,當伸縮連桿模組42的第一滑接件421相對於承載框架41旋轉時,探針462會隨著第一滑接件421的旋轉帶動而相對於本體461前後伸縮。The first measuring mechanism 4 further includes a first force sensing element 45 disposed between the two partitions 443 of the front and rear force applying members 44 for sensing the application to the front and rear applications. The force on the urging portion 442 of the force member 44. In this embodiment, the first force sensing component 45 is a load cell, which is the same as the structure and operation principle of the load cell currently on the market, and therefore will not be described in detail herein. The first measuring mechanism 4 further includes a first displacement sensing component 46 disposed on the carrier frame 41 and abutting the telescopic link module 42 for sensing the displacement amount of the telescopic link module 42. In this embodiment, the first displacement sensing component 46 is a resistive displacement sensor, and includes a body 461 fixedly disposed on the frame 411 of the carrier frame 41, and is disposed in the body 461. The probe 462 can be abutted on the pivoting frame 423 of the first sliding member 421, and the first sliding member 421 of the telescopic connecting rod module 42 is opposite. When the carrier frame 41 rotates, the probe 462 is stretched back and forth with respect to the body 461 as the first sliding member 421 rotates.
如圖3、圖5、圖6及圖7所示,在本實施例中,小腿套接機構3還包括一設置於第二前端面314上的第一軸承件35,第一軸承件35用以供接合件429的一與第二軸430垂直的第二樞接軸433樞接;第一軸承件35界定有一沿前後方向延伸的第一旋轉中心L1,小腿套接機構3可透過第一軸承件35相對於伸縮連桿模組42的接合件429旋轉。當患者因受傷因素導致小腿12相對於大腿11往內翻或往外翻時,可適當地調整小腿套接機構3相對於伸縮連桿模組42轉動,使小腿套接機構3能確實地套接在小腿12上。大腿套接機構2還包括一設置於第一前端面214上的第二軸承件24,第二軸承件24用以供承載框架41的一設置於架體411上並與第一軸412垂直的第一樞接軸415樞接;第二軸承件24界定有一沿前後方向延伸的第二旋轉中心L2,大腿套接機構2可透過第二軸承件24相對於伸縮連桿模組42的承載框架41旋轉。當患者的小腿12相對於大腿11往內翻或往外翻的程度較為嚴重時,可同時調整小腿套接機構3與大腿套接機構2相對於伸縮連桿模組42轉動,使小腿套接機構3及大腿套接機構2能分別確實地套接在小腿12與大腿11上。As shown in FIG. 3, FIG. 5, FIG. 6, and FIG. 7, in the embodiment, the calf sleeve mechanism 3 further includes a first bearing member 35 disposed on the second front end surface 314, and the first bearing member 35 is used. The second pivoting shaft 433 of the engaging member 429 perpendicular to the second shaft 430 is pivotally connected; the first bearing member 35 defines a first rotation center L1 extending in the front-rear direction, and the calf sleeve mechanism 3 is transparent to the first The bearing member 35 rotates relative to the engagement member 429 of the telescopic link module 42. When the patient turns the lower leg 12 inward or outward with respect to the thigh 11 due to the injury factor, the calf socket mechanism 3 can be appropriately rotated relative to the telescopic link module 42 so that the calf sleeve mechanism 3 can be surely nested. On the calf 12. The thigh socket mechanism 2 further includes a second bearing member 24 disposed on the first front end surface 214, and the second bearing member 24 is disposed on the frame body 411 and perpendicular to the first shaft 412. The first pivoting shaft 415 is pivotally connected; the second bearing member 24 defines a second rotation center L2 extending in the front-rear direction, and the thigh socketing mechanism 2 is permeable to the bearing frame of the second bearing member 24 relative to the telescopic link module 42. 41 rotation. When the patient's lower leg 12 is turned inward or outward with respect to the thigh 11 , the calf socket mechanism 3 and the thigh socket mechanism 2 can be simultaneously rotated relative to the telescopic link module 42 to make the calf sleeve mechanism 3 and the thigh socket mechanism 2 can be surely sleeved on the calf 12 and the thigh 11 respectively.
如圖8、圖9、圖10及圖11所示,以下將針對膝關節韌帶鬆弛度量測方法進行詳細說明。將膝關節韌帶鬆弛度量測裝置200的大腿套接機構2及小腿套接機構3分別套接在大腿11及小腿12上,大腿11及小腿12可分別透過一支撐墊(圖未示)支撐,使得大腿11與小腿12之間是呈25度~30度的彎曲狀態,接著,專業骨科醫生及復健人員等即可透過手動方式進行量測的操作。As shown in Fig. 8, Fig. 9, Fig. 10 and Fig. 11, the knee ligament relaxation measurement method will be described in detail below. The thigh socket mechanism 2 and the calf sleeve mechanism 3 of the knee ligament relaxation measuring device 200 are respectively sleeved on the thigh 11 and the lower leg 12, and the thigh 11 and the calf 12 are respectively supported by a support pad (not shown). Therefore, the thigh 11 and the lower leg 12 are bent at a degree of 25 to 30 degrees, and then, the professional orthopedist and the rehabilitation personnel can perform the measurement by manual means.
圖8為脛骨121(如圖1所示)前向或後向位移量測方法的流程圖,其主要流程為:如步驟91所示,施加一向前或向後的力量於一前後向施力桿件44上,使一與前後向施力桿件44相連接的伸縮連桿模組42帶動一套接在小腿12的小腿套接機構3運動。8 is a flow chart of a method for measuring the forward or backward displacement of the tibia 121 (shown in FIG. 1). The main flow is as follows: applying a forward or backward force to a forward and backward force bar as shown in step 91. On the member 44, a telescopic link module 42 connected to the front and rear force applying members 44 drives a set of the calf sleeve mechanism 3 attached to the lower leg 12.
首先,操作人員以一手握持住一設置於承載框架41上的第一握把47,而另一手握持住前後向施力桿件44的施力部442,接著,操作人員可施加一沿箭頭I方向所示的向前拉力於施力部442上(如圖10所示),前後向施力桿件44的銷部441會拉動第二滑接件422前移,使得第二滑接件422及第一滑接件421沿箭頭II方向繞第一軸412旋轉,同時,透過接合件429的帶動且接合件429可相對於第二滑接件422旋轉的關係,使得小腿套接機構3能帶動小腿12相對於大腿11往前平移,藉此,以進行脛骨121前向位移的量測。First, the operator holds a first grip 47 disposed on the carrying frame 41 with one hand while holding the urging portion 442 of the front and rear urging member 44 with the other hand, and then the operator can apply an edge The forward pulling force indicated by the arrow I direction is applied to the urging portion 442 (as shown in FIG. 10), and the pin portion 441 of the front and rear urging member 44 pulls the second sliding member 422 forward to make the second sliding The member 422 and the first sliding member 421 rotate around the first shaft 412 in the direction of the arrow II, and at the same time, through the engagement of the engaging member 429 and the rotating member 429 is rotatable relative to the second sliding member 422, the shank splicing mechanism 3 can drive the lower leg 12 to translate forward relative to the thigh 11 to thereby measure the forward displacement of the tibia 121.
或者,操作人員可施加一沿箭頭III方向所示的向後推力於施力部442上(如圖11所示),前後向施力桿件44的銷部441會推動第二滑接件422後移,使得第二滑接件422及第一滑接件421沿箭頭IV方向繞第一軸412旋轉,同時,透過接合件429的帶動且接合件429可相對於第二滑接件422旋轉的關係,使得小腿套接機構3能帶動小腿12相對於大腿11往後平移,藉此,以進行脛骨121後向位移的量測。Alternatively, the operator can apply a rearward thrust shown in the direction of arrow III to the urging portion 442 (as shown in FIG. 11), and the pin portion 441 of the front and rear urging member 44 pushes the second sliding member 422. Shifting, the second sliding member 422 and the first sliding member 421 are rotated around the first axis 412 in the direction of the arrow IV, while being driven by the engaging member 429 and the engaging member 429 is rotatable relative to the second sliding member 422. The relationship enables the calf splicing mechanism 3 to drive the lower leg 12 to translate rearward relative to the thigh 11, thereby performing a measurement of the posterior displacement of the tibia 121.
如步驟92所示,感測施加於前後向施力桿件44上的力量並產生一力量感測訊號,以及感測伸縮連桿模組42的位移量並產生一位移感測訊號。As shown in step 92, the force applied to the forward and backward force applying members 44 is sensed and a force sensing signal is generated, and the amount of displacement of the telescopic link module 42 is sensed and a displacement sensing signal is generated.
由於施加於前後向施力桿件44上的力量會使第一力量感測元件45對應地產生一力量感測訊號,因此,隨著施加於前後向施力桿件44上的力量不同,第一力量感測元件45會對應地產生不同的力量感測訊號。另外,由於第一位移感測元件46的探針462相對於本體461伸縮移動的過程中,會產生一位移感測訊號,因此,隨著探針462伸縮量的不同,第一位移感測元件46會對應地產生不同的位移感應訊號。在本實施例中,力量感應訊號及位移感測訊號都是以類比電壓訊號為例作說明。Since the force applied to the urging force applying member 44 causes the first force sensing element 45 to correspondingly generate a force sensing signal, the force applied to the urging force applying member 44 is different. A force sensing element 45 will correspondingly generate different force sensing signals. In addition, since the displacement sensing signal is generated during the telescopic movement of the probe 462 of the first displacement sensing element 46 relative to the body 461, the first displacement sensing element is different depending on the amount of expansion and contraction of the probe 462. 46 will correspondingly generate different displacement sensing signals. In this embodiment, the power sensing signal and the displacement sensing signal are all exemplified by analog voltage signals.
如步驟93所示,利用一電腦6(如圖2所示)擷取力量感測訊號及位移感測訊號以進行運算比對。As shown in step 93, a computer 6 (shown in FIG. 2) is used to extract the power sensing signal and the displacement sensing signal for comparison.
在本實施例中,第一力量感測元件45及第一位移感測元件46分別透過導線(圖未示)與電腦6的一多通道轉接盒61電性連接,而多通道轉接盒61是透過一導線62與一電腦主機63的類比訊號擷取卡(圖未示)電性連接,該類比訊號擷取卡可擷取第一力量感測元件45所產生的力量感測訊號,以及第一位移感測元件46所產生的位移感測訊號,透過電腦主機63將力量感測訊號及位移感測訊號分別轉換為力量值以及位移值,藉此,能進行運算及相關的分析比對工作。In this embodiment, the first power sensing component 45 and the first displacement sensing component 46 are respectively electrically connected to a multi-channel switch box 61 of the computer 6 through a wire (not shown), and the multi-channel adapter box 61 is electrically connected to an analog signal capture card (not shown) of a host computer 63 through a wire 62. The analog signal capture card can capture the power sensing signal generated by the first force sensing component 45. And the displacement sensing signal generated by the first displacement sensing component 46 converts the power sensing signal and the displacement sensing signal into a power value and a displacement value respectively through the host computer 63, thereby performing calculation and correlation analysis ratio For work.
如圖12所示,由於脛骨121(如圖1所示)的一位移參考點(通常位於髕骨17下方3公分處)可能會與第一位移感測元件46的探針462位置有所差異,因此,可透過電腦6的電腦主機63(如圖2所示)經由相似三角形的幾何關係來進行比例換算,以得出該位移參考點的實際位移量Δ,其中,該位移參考點的實際位移量Δ是與一位移轉換公式有關,該位移轉換公式為:As shown in FIG. 12, a displacement reference point of the tibia 121 (shown in FIG. 1) (usually located 3 cm below the tibia 17) may differ from the position of the probe 462 of the first displacement sensing element 46, Therefore, the computer mainframe 63 of the computer 6 (shown in FIG. 2) can be scaled by a similar triangular geometric relationship to obtain the actual displacement amount Δ of the displacement reference point, wherein the actual displacement of the displacement reference point The amount Δ is related to a displacement conversion formula, which is:
其中,l 為該位移參考點與第一軸412之軸心的偏位量,l 0 為第一位移感測元件46的一探針462之中心軸與第一軸412之軸心的偏位量,Δ0 為探針462的線性位移量(以圖12為例,伸縮連桿模組42的第一滑接件421呈水平時的線性位移量設定為零),e 為伸縮連桿模組42的第一滑接件421和第一位移感測元件46的探針462的接觸點所在平面與第一軸412之軸心的偏位量,Δ*為伸縮連桿模組42擺動時沿第一位移感測元件46的探針462之中心軸所產生的位移量。Where l is the amount of deviation of the displacement reference point from the axis of the first axis 412, and l 0 is the deviation of the central axis of a probe 462 of the first displacement sensing element 46 from the axis of the first axis 412 The amount, Δ 0 is the linear displacement of the probe 462 (as in the case of FIG. 12 , the linear displacement amount when the first sliding member 421 of the telescopic link module 42 is horizontal is set to zero), and e is the telescopic link module. The amount of deviation between the plane of the contact point of the first sliding member 421 of the group 42 and the probe 462 of the first displacement sensing element 46 and the axis of the first shaft 412, Δ* is when the telescopic link module 42 swings The amount of displacement produced along the central axis of the probe 462 of the first displacement sensing element 46.
在進行實際量測時,先量測如圖9所示的位移參考點的實際位移量Δ i ,再量測如圖10或圖11所示的位移參考點的實際位移量Δ f ,計算Δ i 與Δ f 之差即可得到脛骨121的前向位移或後向位移。如圖13所示,當電腦主機63計算出脛骨121的前向位移或後向位移的距離時,即可與力量感測訊號轉換後的力量值進行比對,以得到一位移與力量的關係圖,藉此,可供專業骨科醫生及復健人員診斷病情並對患者施予最佳與即時的醫療。When the actual measurement is performed, the actual displacement amount Δ i of the displacement reference point shown in FIG. 9 is measured first, and then the actual displacement amount Δ f of the displacement reference point shown in FIG. 10 or FIG. 11 is measured, and Δ is calculated. The difference between i and Δ f results in a forward displacement or a backward displacement of the tibia 121. As shown in FIG. 13, when the computer host 63 calculates the distance of the forward displacement or the backward displacement of the tibia 121, it can be compared with the force value after the power sensing signal is converted to obtain a relationship between displacement and force. In this way, professional orthopedic surgeons and rehabilitation personnel can be used to diagnose the condition and give the patient the best and immediate medical treatment.
如圖5及圖6所示,小腿套接機構3還包括二樞軸座36,各樞軸座36可透過螺鎖方式固定於各側壁312的一第二側面315上,各樞軸座36可供一呈前後方向延伸的第三軸37穿設,其中,第一軸承件35界定的第一旋轉中心L1與第三軸37呈共平面且互相平行。小腿套接機構3還包括一設置於延伸架33上的左右向施力桿件38,左右向施力桿件38包含一與延伸架33相連接的連接部381,及一位於連接部381相反端可供施力的施力部382。As shown in FIG. 5 and FIG. 6 , the shank shank mechanism 3 further includes two pivot seats 36 . Each pivot seat 36 can be fixed to a second side 315 of each side wall 312 by a screw lock manner. A third shaft 37 extending in the front-rear direction is provided, wherein the first rotation center L1 defined by the first bearing member 35 and the third shaft 37 are coplanar and parallel to each other. The shank splicing mechanism 3 further includes a right and left urging lever member 38 disposed on the extension frame 33. The left and right urging member 38 includes a connecting portion 381 connected to the extension frame 33, and the opposite portion 381 is located at the connecting portion 381. The end of the force applying portion 382.
如圖2、圖3、圖4及圖14所示,膝關節韌帶鬆弛度量測裝置200還包含一第二量測機構5,第二量測機構5包括二個側伸縮連桿模組51。各側伸縮連桿模組51包括一設置於大腿套接機構2之各側壁212的一第一側面215的第一連接單元511,及一設置於小腿套接機構3之各側壁312的第二側面315且可轉動地繞第三軸37旋轉的第二連接單元512。第一連接單元511包括一樞接於第一側面215上的第一連接件513,及二分別穿設於第一連接件513的套筒514,第二連接單元512包括一樞接於第二側面315的第二連接件515,及二分別設置於第二連接件515上的導桿516,各導桿516可滑動地穿設於各套筒514內。As shown in FIG. 2, FIG. 3, FIG. 4 and FIG. 14, the knee ligament relaxation measuring device 200 further includes a second measuring mechanism 5, and the second measuring mechanism 5 includes two side telescopic link modules 51. . Each of the side telescopic link modules 51 includes a first connecting unit 511 disposed on a first side 215 of each side wall 212 of the thigh socket mechanism 2, and a second portion 312 disposed on each side wall 312 of the calf splicing mechanism 3. A side surface 315 and a second connecting unit 512 rotatably rotatable about the third shaft 37. The first connecting unit 511 includes a first connecting member 513 pivotally connected to the first side 215, and two sleeves 514 respectively disposed on the first connecting member 513. The second connecting unit 512 includes a second pivoting unit 512. The second connecting member 515 of the side surface 315 and the guiding rod 516 respectively disposed on the second connecting member 515 are slidably disposed in the sleeves 514.
如圖4、圖5、圖6及圖14所示,進一步地,大腿套接機構2還包括二樞軸座25,各樞軸座25可透過螺鎖方式固定於各側壁212的一第一側面215上,各樞軸座25可供一呈前後方向延伸的第四軸26穿設,其中,第二軸承件24界定的第一旋轉中心L2與第四軸26呈共平面且互相平行。第一連接單元511還包含一樞接於第四軸26且可轉動地繞第四軸26旋轉的第一鉸鍊件517,第一鉸鍊件517包括一供第一連接件513樞接的第一樞接軸部518,第一樞接軸部518呈左右方向延伸,藉此,第一連接件513可透過第一鉸鍊件517繞第四軸26旋轉,並且可繞第一樞接軸部518相對於第一鉸鍊件517旋轉。第二連接單元512還包含一樞接於第三軸37且可轉動地繞第三軸37旋轉的第二鉸鍊件519,第二鉸鍊件519包括一供第二連接件515樞接的第二樞接軸部520,第二樞接軸部520呈左右方向延伸,藉此,第二連接件515可透過第二鉸鍊件519繞第三軸37旋轉,並且可繞第二樞接軸部520相對於第二鉸鍊件519旋轉。As shown in FIG. 4 , FIG. 5 , FIG. 6 and FIG. 14 , the thigh sleeve mechanism 2 further includes two pivot seats 25 , and each pivot seat 25 can be fixed to each of the side walls 212 by a screw lock. On the side 215, each of the pivot seats 25 is provided for a fourth shaft 26 extending in the front-rear direction, wherein the first center of rotation L2 defined by the second bearing member 24 and the fourth shaft 26 are coplanar and parallel to each other. The first connecting unit 511 further includes a first hinge member 517 pivotally connected to the fourth shaft 26 and rotatably rotating around the fourth shaft 26, the first hinge member 517 includes a first pivotal connection for the first connecting member 513 The pivoting shaft portion 518 extends in the left-right direction, whereby the first connecting member 513 is rotatable around the fourth shaft 26 through the first hinge member 517 and is rotatable around the first pivoting shaft portion 518. Rotating relative to the first hinge member 517. The second connecting unit 512 further includes a second hinge member 519 pivotally connected to the third shaft 37 and rotatably rotating around the third shaft 37. The second hinge member 519 includes a second hinge member 515 for pivoting. The pivoting shaft portion 520 and the second pivoting shaft portion 520 extend in the left-right direction, whereby the second connecting member 515 is rotatable around the third shaft 37 through the second hinge member 519 and is rotatable around the second pivoting shaft portion 520. Rotating relative to the second hinge member 519.
另外,第二量測機構5還包括一第二力量感測元件53及一第二位移感測元件54;第二力量感測元件53結構與第一力量感測元件45相同,第二力量感測元件53設置於左右向施力桿件38的連接部381上,用以感測施加於左右向施力桿件38上的力量。第二位移感測元件54結構與第一位移感測元件46相同,第二位移感測元件54透過一固定板50安裝在第二連接件515上,第二位移感測元件54包括一固定在固定板50上的本體541,及一抵接於小腿套接機構3的第二側面315並呈左右方向延伸的探針542,探針542可隨小腿套接機構3相對於第二連接件515旋轉而伸縮,藉此,能感測小腿套接機構3的翻轉量。In addition, the second measuring mechanism 5 further includes a second force sensing component 53 and a second displacement sensing component 54. The second power sensing component 53 has the same structure as the first power sensing component 45, and the second power sense The measuring member 53 is disposed on the connecting portion 381 of the right and left biasing lever members 38 for sensing the force applied to the right and left biasing lever members 38. The second displacement sensing element 54 is identical in structure to the first displacement sensing element 46. The second displacement sensing element 54 is mounted on the second connector 515 via a mounting plate 50. The second displacement sensing element 54 includes a fixed The main body 541 of the fixing plate 50 and a probe 542 abutting against the second side surface 315 of the calf socket mechanism 3 and extending in the left-right direction, the probe 542 can be connected with the calf sleeve mechanism 3 relative to the second connecting member 515 The rotation is expanded and contracted, whereby the amount of turnover of the calf socket mechanism 3 can be sensed.
此外,為了能同時感測大腿套接機構2相對於第一連接件513旋轉的位移量,第二量測機構5還包括一第三位移感測元件55,第三位移感測元件55結構與第一位移感測元件46相同,第三位移感測元件55透過一固定板50安裝在第一連接件513上,第三位移感測元件55包括一固定在固定板50上的本體551,及一抵接於大腿套接機構2的第一側面215並呈左右方向延伸的探針552,探針552可隨大腿套接機構2相對於第一連接件513旋轉而伸縮,藉此,能感測大腿套接機構2的翻轉量。In addition, in order to simultaneously sense the displacement amount of the thigh socket mechanism 2 relative to the first connecting member 513, the second measuring mechanism 5 further includes a third displacement sensing element 55, and the third displacement sensing element 55 is configured and The first displacement sensing element 46 is identical. The third displacement sensing element 55 is mounted on the first connecting member 513 through a fixing plate 50. The third displacement sensing element 55 includes a body 551 fixed on the fixing plate 50, and a probe 552 abutting on the first side surface 215 of the thigh socket mechanism 2 and extending in the left-right direction, the probe 552 can be expanded and contracted with the rotation of the thigh socket mechanism 2 relative to the first connecting member 513, thereby being able to sense The amount of turnover of the thigh socket mechanism 2 is measured.
如圖15、圖16、圖17及圖18所示,以下將針對膝關節韌帶鬆弛度量測方法進行詳細說明。圖15為脛骨121(如圖1所示)向外或向內翻轉量測方法的流程圖,其主要流程為:如步驟94,施加一向左或向右方向的力量於一左右向施力桿件38上,使一與左右向施力桿件38相連接的一套接在小腿12的小腿套接機構3運動。As shown in Fig. 15, Fig. 16, Fig. 17, and Fig. 18, the knee ligament relaxation measurement method will be described in detail below. 15 is a flow chart of a method for measuring the outward or inward inversion of the tibia 121 (shown in FIG. 1). The main flow is as follows: step 94, applying a leftward or rightward force to a left and right force applying rod On the piece 38, a set of the calf sleeve mechanism 3 attached to the left leg 12 is connected to the left and right force applying members 38.
首先,操作人員以一手握持住一設置於第一套殼21的第一前端面214上的第二握把27,而另一手握持住左右向施力桿件38的施力部382,接著,操作人員可施加一沿箭頭V方向所示的向外推力於施力部382上(如圖17所示),左右向施力桿件38會推動第二套殼31沿箭頭VI方向相對於第一套殼21旋轉,使得第二套殼31能帶動小腿12相對於大腿11向外旋轉,藉此,以進行脛骨121向外翻轉的量測。First, the operator holds a second grip 27 disposed on the first front end surface 214 of the first casing 21 with one hand, and the urging portion 382 of the left and right urging member 38 is held by the other hand. Then, the operator can apply an outward thrust force shown in the direction of the arrow V to the urging portion 382 (as shown in FIG. 17), and the right and left urging member 38 pushes the second casing 31 in the direction of the arrow VI. The first sleeve 21 is rotated such that the second sleeve 31 can drive the lower leg 12 to rotate outward relative to the thigh 11, thereby measuring the outward rotation of the tibia 121.
或者,操作人員可施加一沿箭頭VII方向所示的向內拉力於施力部382上(如圖18所示),左右向施力桿件38會拉動第二套殼31沿箭頭X方向相對於第一套殼21旋轉,使得第二套殼31能帶動小腿12相對於大腿11向內旋轉,藉此,以進行脛骨121向內翻轉的量測。Alternatively, the operator can apply an inward pulling force on the urging portion 382 as shown in the direction of arrow VII (as shown in FIG. 18), and the left and right urging members 38 pull the second casing 31 in the direction of the arrow X. The first set of shells 21 is rotated such that the second set of shells 31 can drive the lower legs 12 to rotate inwardly relative to the thighs 11, thereby allowing measurement of the inward turning of the tibia 121.
如步驟95所示,感測施加於左右向施力桿件38上的力量並產生一力量感測訊號,以及感測小腿套接機構3的翻轉量並產生一位移感測訊號。As shown in step 95, the force applied to the left and right force applying members 38 is sensed and a force sensing signal is generated, and the amount of inversion of the calf socket mechanism 3 is sensed and a displacement sensing signal is generated.
由於施加於左右向施力桿件38上的力量會使第二力量感測元件53對應地產生一力量感測訊號,因此,隨著施加於左右向施力桿件38上的力量不同,第二力量感測元件53會對應地產生不同的力量感測訊號。另外,由於第二位移感測元件54的探針542相對於本體541伸縮過程中,會產生一位移感測訊號,因此,隨著探針542伸縮量的不同,第二位移感測元件54會對應地產生不同的位移感應訊號。在本實施例中,力量感應訊號及位移感測訊號都是以類比電壓訊號為例作說明。特別說明的是,由於小腿套接機構3在旋轉過程中有可能同時產生平移的情況,因此,透過第三位移感測元件55的設置,能感測小腿套接機構3平移時所產生的位移量。再者,若小腿12因受傷因素而導致相對於大腿11彎曲程度過大時(如圖19所示),透過第二、第三位移感測元件54、55的設計,能準確地量測脛骨121向外或向內翻時的翻轉量。Since the force applied to the right and left urging members 38 causes the second force sensing element 53 to correspondingly generate a force sensing signal, the force applied to the right and left urging members 38 is different, The two force sensing elements 53 will correspondingly generate different force sensing signals. In addition, since the probe 542 of the second displacement sensing element 54 is stretched relative to the body 541, a displacement sensing signal is generated. Therefore, as the amount of expansion and contraction of the probe 542 is different, the second displacement sensing element 54 Correspondingly, different displacement sensing signals are generated. In this embodiment, the power sensing signal and the displacement sensing signal are all exemplified by analog voltage signals. In particular, since the calf socket mechanism 3 may simultaneously generate translation during the rotation process, the displacement generated by the translation of the calf sleeve mechanism 3 can be sensed through the arrangement of the third displacement sensing element 55. the amount. Furthermore, if the lower leg 12 is excessively bent relative to the thigh 11 due to the injury factor (as shown in FIG. 19), the design of the second and third displacement sensing members 54, 55 can accurately measure the tibia 121. The amount of flipping when turning outwards or inwards.
如步驟96所示,利用一電腦6(如圖2所示)擷取力量感測訊號及位移感測訊號以進行運算比對。As shown in step 96, a computer 6 (shown in FIG. 2) is used to extract the power sensing signal and the displacement sensing signal for comparison.
在本實施例中,第二力量感測元件53及第二、第三位移感測元件54、55分別透過導線(圖未示)與電腦6的多通道轉接盒61電性連接,電腦主機63的類比訊號擷取卡能擷取第二力量感測元件53所產生的力量感測訊號,以及第二、第三位移感測元件54、55所產生的位移感測訊號,透過電腦主機63將力量感測訊號及位移感測訊號分別轉換為力量值以及位移值,藉此,能進行運算及相關的分析比對工作。In this embodiment, the second power sensing component 53 and the second and third displacement sensing components 54 and 55 are respectively electrically connected to the multi-channel adapter box 61 of the computer 6 through a wire (not shown), and the computer host The analog signal capture signal of 63 can capture the power sensing signal generated by the second force sensing component 53 and the displacement sensing signal generated by the second and third displacement sensing components 54, 55 through the computer host 63. The power sensing signal and the displacement sensing signal are respectively converted into a power value and a displacement value, thereby performing calculation and correlation analysis work.
如圖19、圖20及圖21所示,透過電腦主機63所擷取的第二、第三位移感測元件54、55的位移感測訊號,電腦主機63可進一步地計算出脛骨121向左或向右旋轉的翻轉角度,脛骨121向左或向右的翻轉角度是與一角度轉換公式相關,該角度轉換公式為:As shown in FIG. 19, FIG. 20 and FIG. 21, the computer main body 63 can further calculate the tibia 121 to the left by the displacement sensing signals of the second and third displacement sensing elements 54, 55 captured by the host computer 63. Or the flip angle rotated to the right, the flip angle of the tibia 121 to the left or right is related to an angle conversion formula, which is:
其中,如圖19及圖20所示,β為翻轉角度,α1 為第二量測機構5的側伸縮連桿模組51與小腿套接機構3的第二側面315的夾角,Δ1 為第二位移感測元件54的探針542之線性位移量,Y 1 為第二連接件515和第二位移感測元件54的探針542的一凸伸端齊平的一端與第三軸37之間的垂直距離,L 1 為第二位移感測元件54的探針542之中心軸與第三軸37之間的垂直距離,H 1 為小腿套接機構3的第二側面315與第三軸37之間的垂直距離,S 1 為第二位移感測元件54的探針542的一和小腿套接機構3的第二側面315接觸的接觸端與H 1 之間的垂直距離;如圖21所示,α2 為第二量測機構5的側伸縮連桿模組51與大腿套接機構2的第一側面215的夾角,Δ2 為第三位移感測元件55的探針552之線性位移量,Y 2 為第一連接件513和第三位移感測元件55的探針552的一凸伸端齊平的一端與第四軸26之間的垂直距離,L 2 為第三位移感測元件55的探針552之中心軸與第四軸26之間的垂直距離,H 2 為大腿套接機構2的第一側面215與第四軸26之間的垂直距離,S 2 為第三位移感測元件55的探針552的一和大腿套接機構2的第一側面215接觸的接觸端與H 2 之間的垂直距離。As shown in FIG. 19 and FIG. 20, β is a flip angle, and α 1 is an angle between the side telescopic link module 51 of the second measuring mechanism 5 and the second side surface 315 of the calf sleeve mechanism 3, and Δ 1 is The linear displacement amount of the probe 542 of the second displacement sensing element 54 is Y 1 being the flushing end and the third axis 37 of the protruding end of the probe 542 of the second connecting member 515 and the second displacement sensing element 54. The vertical distance between them, L 1 is the vertical distance between the central axis of the probe 542 of the second displacement sensing element 54 and the third axis 37, and H 1 is the second side 315 and the third of the calf socket mechanism 3 the vertical distance between the axes 37, S 1 is a lower leg socket means and the second side 3 of the contact end 315 in contact with the vertical distance between a 1 H second displacement sensing probe 542 of the sensing element 54; FIG. 21, α 2 is the angle between the side telescopic link module 51 of the second measuring mechanism 5 and the first side surface 215 of the thigh socket mechanism 2, and Δ 2 is the probe 552 of the third displacement sensing element 55. the amount of linear displacement, Y 2 is a first connecting member 513 and the third probe displacement sensing element 55255 is a protruding end flush with the end of the vertical distance between the fourth shaft 26, L 2 The third displacement sensing element 552 of the central axis of the probe 26 and the vertical distance between the fourth shaft 55, H 2 is a side legs of the first socket means of the vertical distance between 2 215 and the fourth shaft 26, S 2 is the vertical distance between the contact end of the probe 552 of the third displacement sensing element 55 and the first side 215 of the thigh socket mechanism 2 and H 2 .
在進行實際量測時,先量測如圖16所示的初始翻轉角度β i ,再量測如圖17、圖18或圖19所示的實際翻轉角度β f ,計算β i 與β f 之差即可得到脛骨121外翻的翻轉角度或內翻的翻轉角度,藉此,可供專業骨科醫生及復健人員診斷病情並對患者施予最佳與即時的醫療。When performing the actual measurement, first measure the initial flip angle β i as shown in FIG. 16 , and then measure the actual flip angle β f as shown in FIG. 17 , FIG. 18 or FIG. 19 , and calculate β i and β f . Poor can get the flip angle of the tibia 121 eversion or the flip angle of the varus, so that professional orthopedic surgeons and rehabilitation personnel can diagnose the condition and give the patient the best and immediate medical treatment.
如圖22及圖23所示,是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例,該膝關節韌帶鬆弛度量測裝置210的整體結構與操作方式大致與第一較佳實施例相同,不同之處在於大腿套接機構2’、小腿套接機構3’,以及第一量測機構4’的結構設計略有不同。As shown in FIG. 22 and FIG. 23, it is a second preferred embodiment of the knee ligament relaxation measuring device of the present invention. The overall structure and operation mode of the knee ligament relaxation measuring device 210 are substantially the first and preferred. The embodiment is the same except that the thigh socket mechanism 2', the calf socket mechanism 3', and the first measuring mechanism 4' have slightly different structural designs.
如圖23及圖24所示,在本實施例中,大腿套接機構2’的側壁212以及迫緊模組22的數量各為一個,各固緊帶23的第二帶體232連接於前壁211上並可黏扣於第一帶體231。小腿套接機構3’的側壁312以及迫緊模組32的數量各為一個,其中一固緊帶34的第二帶體342連接於前壁311並可黏扣於第一帶體341。另外,左右向施力桿件38的連接部381是設置於延伸架33的側邊,另一個固緊帶34的第一帶體341連接於連接部381並可黏扣於第二帶體342。透過大腿套接機構2’的單一個側壁212與迫緊模組22設計、小腿套接機構3’的單一個側壁312與迫緊模組32設計,以及單一個第二量測機構5的設計,膝關節韌帶鬆弛度量測裝置210與第一較佳實施例相較下能降低整體的重量,以減輕對患者的大腿11及小腿12的負擔。As shown in FIG. 23 and FIG. 24, in the present embodiment, the number of the side walls 212 and the pressing module 22 of the thigh socket mechanism 2' is one, and the second belt 232 of each fastening belt 23 is connected to the front. The wall 211 can be attached to the first belt 231. The number of the side walls 312 of the calf splicing mechanism 3' and the pressing module 32 are each one, and the second strip 342 of a fastening strip 34 is coupled to the front wall 311 and can be affixed to the first strip 341. In addition, the connecting portion 381 of the left and right urging rods 38 is disposed on the side of the extension frame 33, and the first belt 341 of the other fastening belt 34 is coupled to the connecting portion 381 and can be affixed to the second belt 342. . Through the design of the single side wall 212 of the thigh socket mechanism 2' and the pressing module 22, the single side wall 312 of the calf splicing mechanism 3' and the pressing module 32, and the design of the single second measuring mechanism 5 The knee ligament relaxation measuring device 210 can reduce the overall weight as compared with the first preferred embodiment to reduce the burden on the patient's thigh 11 and lower leg 12.
如圖24及圖25所示,第一量測機構4’的承載框架41’包括一呈L形的架體411’,及一第一接合件416;前後向施力桿件44及第一位移感測元件46設置於承載框架41’的架體411’上。第一接合件416接合於架體411’與大腿套接機構2’的第一前端面214之間,第一接合件416包括一呈左右方向延伸的第一軸417,及一與第一軸417垂直且樞接於第二軸承件24上的第一樞接軸418,架體411’可轉動地樞接於第一軸417。前後向施力桿件44一端接合於小腿套接機構3’的第二前端面314,前後向施力桿件44包含一桿件本體440,及一第二接合件444;第二接合件444包括一呈左右方向延伸的第二軸445,及一與第二軸445垂直且樞接於第一軸承件35上的第二樞接軸446,桿件本體440透過其一端的樞接部441’可轉動地樞接於第二軸445。透過架體411’可轉動地樞接於第一軸417,使得架體411’能相對於第一接合件416轉動到一傾斜角度,藉此,前後向施力桿件44可沿一與第二前端面314垂直的施力方向對小腿套接機構3’施力。As shown in FIG. 24 and FIG. 25, the carrying frame 41' of the first measuring mechanism 4' includes an L-shaped frame 411', and a first engaging member 416; the front and rear biasing members 44 and the first The displacement sensing element 46 is disposed on the frame 411' of the carrier frame 41'. The first engaging member 416 is coupled between the frame body 411' and the first front end surface 214 of the thigh socket mechanism 2'. The first engaging member 416 includes a first shaft 417 extending in the left-right direction, and a first shaft The first pivot shaft 418 is vertically and pivotally connected to the second bearing member 24, and the frame body 411' is rotatably pivotally connected to the first shaft 417. One end of the urging force applying member 44 is coupled to the second front end surface 314 of the calf splicing mechanism 3 ′, and the front and rear urging rod member 44 includes a rod body 440 and a second engaging member 444 ; the second engaging member 444 The second shaft 445 extending in the left-right direction and the second pivot shaft 446 perpendicular to the second shaft 445 and pivotally connected to the first bearing member 35, the rod body 440 passing through the pivoting portion 441 of one end thereof 'Rotatingly pivoted to the second shaft 445. The frame body 411 ′ is rotatably pivoted to the first shaft 417 , so that the frame body 411 ′ can be rotated to an oblique angle with respect to the first joint member 416 , whereby the front and rear force applying members 44 can be along the first and the second The vertical direction of application of the front end face 314 applies a force to the calf sleeve mechanism 3'.
此外,第一位移感測元件46設置於承載框架41’的架體411’上,透過架體411’能相對於第一接合件416轉動到一傾斜角度,使得第一位移感測元件46的一設置於探針462一端的接觸板463能抵接在小腿12上並且對應於徑骨121的一結節122(如圖27所示)位置,藉此,第一位移感測元件46能感測脛骨121的結節122的位移量。In addition, the first displacement sensing component 46 is disposed on the frame 411 ′ of the carrier frame 41 ′, and the transmission frame 411 ′ is rotatable relative to the first engagement component 416 to an oblique angle, so that the first displacement sensing component 46 A contact plate 463 disposed at one end of the probe 462 can abut the lower leg 12 and correspond to a nodule 122 (shown in FIG. 27) of the radial bone 121, whereby the first displacement sensing element 46 can sense The amount of displacement of the nodule 122 of the tibia 121.
如圖26、圖27、圖28、圖29及圖30所示,圖26為脛骨121(如圖1所示)前向或後向位移量測方法的流程圖,其主要流程為:如步驟91’所示,施加一向前或向後的力量於一前後向施力桿件44上,使一與前後向施力桿件44相連接且套接在小腿12的小腿套接機構3’運動。26, FIG. 27, FIG. 28, FIG. 29 and FIG. 30, FIG. 26 is a flow chart of a method for measuring the forward or backward displacement of the tibia 121 (shown in FIG. 1). The main flow is as follows: As shown at 91', a forward or backward force is applied to a forward and backward force applying member 44 to move a calf sleeve mechanism 3' that is coupled to the front and rear force applying members 44 and that is sleeved to the lower leg 12.
操作人員以一手握持住設置於大腿套接機構2’的第一前端面214上的第二握把27,而另一手握持住前後向施力桿件44的施力部442,接著,操作人員可施加一沿箭頭A1方向(與第二前端面314垂直)所示的向前拉力於施力部442上(如圖29所示),前後向施力桿件44會透過第二接合件444拉動小腿套接機構3’往前移平移,藉此,使得第一位移感測元件46可進行脛骨121前向位移的量測。The operator holds the second grip 27 provided on the first front end face 214 of the thigh socket mechanism 2' with one hand while holding the urging portion 442 of the front and rear urging member 44 with the other hand, and then, The operator can apply a forward pulling force as shown in the direction of the arrow A1 (perpendicular to the second front end face 314) to the urging portion 442 (as shown in FIG. 29), and the front and rear urging member 44 will pass through the second engagement. The piece 444 pulls the calf socket mechanism 3' forward to translate, whereby the first displacement sensing element 46 can measure the forward displacement of the tibia 121.
或者,操作人員可施加一沿箭頭A2方向所示的向後推力於施力部442上(如圖30所示),前後向施力桿件44會透第二接合件444過推動小腿套接機構3’往後平移,藉此,使得第一位移感測元件46可進行脛骨121後向位移的量測。Alternatively, the operator can apply a rearward thrust shown in the direction of arrow A2 to the force applying portion 442 (as shown in FIG. 30), and the front and rear force applying members 44 can pass through the second engaging member 444 to push the calf socket mechanism. 3' is translated backward, whereby the first displacement sensing element 46 allows measurement of the posterior displacement of the tibia 121.
如步驟92’所示,感測施加於前後向施力桿件44上的力量並產生一力量感測訊號,以及感測脛骨121的一結節122的位移量並產生一位移感測訊號。As shown in step 92', the force applied to the urging force member 44 is sensed and a force sensing signal is generated, and the amount of displacement of a nodule 122 of the tibia 121 is sensed and a displacement sensing signal is generated.
如步驟93’所示,利用一電腦6(如圖2所示)擷取力量感測訊號及位移感測訊號以進行運算比對。As shown in step 93', a computer 6 (shown in Figure 2) is used to extract the power sensing signal and the displacement sensing signal for comparison.
歸納上述,兩實施例的膝關節韌帶鬆弛度量測裝置200、210,藉由第一量測機構4、4’的設計,能量測脛骨121前向位移以及脛骨121後向位移,以得知前、後十字韌帶13、14的受傷程度;藉由第二量測機構5的設計,能量測脛骨121內翻量以及脛骨121外翻量,以得知內、外側韌帶15、16的受傷程度;藉此,可供專業骨科醫生及復健人員診斷病情並對患者施予最佳與即時的醫療,故確實能達成本發明所訴求之目的。In summary, the knee ligament relaxation measuring devices 200 and 210 of the two embodiments are configured to measure the forward displacement of the tibia 121 and the posterior displacement of the tibia 121 by the design of the first measuring mechanism 4, 4'. The degree of injury of the anterior and posterior cruciate ligaments 13, 14 is known; by the design of the second measuring mechanism 5, the amount of inversion of the tibia 121 and the amount of valgus 121 valgus are measured by energy to know the inner and outer ligaments 15, 16 The degree of injury; whereby professional orthopedic surgeons and rehabilitation personnel can diagnose the condition and give the patient the best and immediate medical treatment, so it can achieve the purpose of the present invention.
惟以上所述者,僅為本發明之較佳實施例而已,當不能以此限定本發明實施之範圍,即大凡依本發明申請專利範圍及發明說明內容所作之簡單的等效變化與修飾,皆仍屬本發明專利涵蓋之範圍內。The above is only the preferred embodiment of the present invention, and the scope of the invention is not limited thereto, that is, the simple equivalent changes and modifications made by the scope of the invention and the description of the invention are All remain within the scope of the invention patent.
11...大腿11. . . thigh
111...股骨111. . . Femur
12...小腿12. . . Calf
121...脛骨121. . . Humerus
13...前十字韌帶13. . . Anterior ligament
14...後十字韌帶14. . . Posterior ligament
15...內側韌帶15. . . Medial ligament
16...外側韌帶16. . . Lateral ligament
17...髕骨17. . . patella
200、210...膝關節韌帶鬆弛度量測裝置200, 210. . . Knee ligament relaxation measuring device
2、2’...大腿套接機構2, 2’. . . Thigh socket mechanism
21...第一套殼twenty one. . . First set of shells
211、311...前壁211, 311. . . Front wall
212、312...側壁212, 312. . . Side wall
213、313...穿孔213, 313. . . perforation
214...第一前端面214. . . First front end face
215...第一側面215. . . First side
22、32...迫緊模組22, 32. . . Tightening module
221、321...迫緊件221, 321. . . Tightening piece
222、322...旋鈕222, 322. . . Knob
223、323...迫緊板223, 323. . . Tight plate
224、324...螺桿224, 324. . . Screw
225、325...螺孔225, 325. . . Screw hole
23、34...固緊帶23, 34. . . Fastening belt
231、341...第一帶體231, 341. . . First belt
232、342...第二帶體232, 342. . . Second belt
24...第二軸承件twenty four. . . Second bearing
25、36...樞軸座25, 36. . . Pivot seat
26...第四軸26. . . Fourth axis
27...第二握把27. . . Second grip
3、3...小腿套接機構3, 3. . . Calf splicing mechanism
31...第二套殼31. . . Second set of shells
314...第二前端面314. . . Second front face
315...第二側面315. . . Second side
33...延伸架33. . . Extension frame
35...第一軸承件35. . . First bearing
37...第三軸37. . . Third axis
38...左右向施力桿件38. . . Left and right force applying rod
381...連接部381. . . Connection
382...施力部382. . . Force department
4、4’...第一量測機構4, 4’. . . First measuring mechanism
41、41’...承載框架41, 41’. . . Bearer frame
411、411’...架體411, 411’. . . Frame
412、417...第一軸412, 417. . . First axis
413...襯套413. . . bushing
414...穿孔414. . . perforation
415、418...第一樞接軸415, 418. . . First pivot axis
416...第一接合件416. . . First joint
42...伸縮連桿模組42. . . Telescopic link module
421...第一滑接件421. . . First sliding piece
422...第二滑接件422. . . Second sliding member
423...樞接架423. . . Pivot frame
424...上樞接端424. . . Upper pivot end
425...滑軌425. . . Slide rail
426...滑動架426. . . Sliding frame
427...滑塊427. . . Slider
428...滑槽428. . . Chute
429...接合件429. . . Joint piece
430、445...第二軸430, 445. . . Second axis
431...下樞接端431. . . Lower pivot end
432...長形滑槽432. . . Long chute
433、446...第二樞接軸433, 446. . . Second pivot axis
44...前後向施力桿件44. . . Front and rear force applying members
440...桿件本體440. . . Rod body
441...銷部441. . . Sales department
441’...樞接部441’. . . Pivot
442...施力部442. . . Force department
443...隔板443. . . Partition
444...第二接合件444. . . Second joint
45...第一力量感測元件45. . . First force sensing element
46...第一位移感測元件46. . . First displacement sensing element
461...本體461. . . Ontology
462...探針462. . . Probe
463...接觸板463. . . Contact plate
47...第一握把47. . . First grip
5...第二量測機構5. . . Second measuring mechanism
50...固定板50. . . Fixed plate
51...側伸縮連桿模組51. . . Side telescopic link module
511...第一連接單元511. . . First connection unit
512...第二連接單元512. . . Second connection unit
513...第一連接件513. . . First connector
514...套筒514. . . Sleeve
515...第二連接件515. . . Second connector
516...導桿516. . . Guide rod
517...第一鉸鍊件517. . . First hinge
518...第一樞接軸部518. . . First pivoting shaft
519...第二鉸鍊件519. . . Second hinge
520...第二樞接軸部520. . . Second pivoting shaft
53...第二力量感測元件53. . . Second force sensing element
54...第二位移感測元件54. . . Second displacement sensing element
541...本體541. . . Ontology
542...探針542. . . Probe
55...第三位移感測元件55. . . Third displacement sensing element
551‧‧‧本體551‧‧‧ Ontology
552‧‧‧探針552‧‧‧Probe
6‧‧‧電腦6‧‧‧ computer
61‧‧‧多通道轉接盒61‧‧‧Multi-channel transfer box
62‧‧‧導線62‧‧‧ wire
63‧‧‧電腦本體63‧‧‧ computer body
91~96‧‧‧步驟91~96‧‧‧Steps
91’~93’‧‧‧步驟91’~93’‧‧‧ steps
圖1是一般人體腿部的示意圖;Figure 1 is a schematic view of a general human leg;
圖2是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的立體圖;Figure 2 is a perspective view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖3是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的立體圖;Figure 3 is a perspective view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖4是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的立體分解圖;Figure 4 is an exploded perspective view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖5是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的大腿套接機構的立體分解圖;Figure 5 is an exploded perspective view of the thigh socket mechanism of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖6是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的小腿套接機構的立體分解圖;Figure 6 is an exploded perspective view showing the calf splicing mechanism of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖7是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的第一量測機構的立體分解圖;Figure 7 is an exploded perspective view of the first measuring mechanism of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖8是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的量測方法流程圖;Figure 8 is a flow chart showing the measurement method of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖9是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的側視圖;Figure 9 is a side elevational view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖10是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的側視圖,說明前後向施力桿件往前拉小腿套接機構;Figure 10 is a side elevational view of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention, illustrating the forward and outward force applying member to pull the calf sleeve mechanism forward;
圖11是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的側視圖,說明前後向施力桿件往後推小腿套接機構;Figure 11 is a side elevational view of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention, illustrating the forward and backward force applying members pushing the calf sleeve mechanism backward;
圖12是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的局部放大圖;Figure 12 is a partial enlarged view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖13是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的力量與位移的關係圖;Figure 13 is a graph showing the relationship between the force and the displacement of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖14是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的第二量測機構的立體分解圖;Figure 14 is an exploded perspective view showing the second measuring mechanism of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖15是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的量測方法流程圖;Figure 15 is a flow chart showing the measurement method of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖16是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的俯視圖;Figure 16 is a plan view showing a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖17是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的俯視圖,說明左右向施力桿件將第二套殼往外推;Figure 17 is a plan view showing a first preferred embodiment of the knee ligament relaxation measuring device of the present invention, illustrating that the left and right urging members push the second casing outward;
圖18是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的俯視圖,說明左右向施力桿件將第二套殼往內拉;Figure 18 is a plan view showing a first preferred embodiment of the knee ligament relaxation measuring device of the present invention, illustrating that the left and right urging members pull the second casing inward;
圖19是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的俯視圖;Figure 19 is a plan view showing a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖20是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的局部放大圖;Figure 20 is a partial enlarged view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖21是本發明膝關節韌帶鬆弛度量測裝置的第一較佳實施例的局部放大圖;Figure 21 is a partial enlarged view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖22是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的立體圖;Figure 22 is a perspective view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖23是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的立體圖;Figure 23 is a perspective view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖24是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的立體分解圖;Figure 24 is an exploded perspective view showing a second preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖25是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的第一量測機構的立體分解圖;Figure 25 is an exploded perspective view showing the first measuring mechanism of the second preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖26是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的量測方法流程圖;Figure 26 is a flow chart showing a measurement method of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖27是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的側視圖;Figure 27 is a side elevational view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖28是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的局部剖視示意圖;Figure 28 is a partial cross-sectional view showing a second preferred embodiment of the knee ligament relaxation measuring device of the present invention;
圖29是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的側視圖,說明前後向施力桿件往前拉小腿套接機構;及Figure 29 is a side elevational view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention, illustrating the forward and outward biasing members for pulling the calf sleeve mechanism forward;
圖30是本發明膝關節韌帶鬆弛度量測裝置的第二較佳實施例的側視圖,說明前後向施力桿件往後推小腿套接機構。Figure 30 is a side elevational view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention, illustrating the forward and backward force applying members pushing the calf socket mechanism back.
11‧‧‧大腿11‧‧‧Thighs
5‧‧‧第二量測機構5‧‧‧Second measuring mechanism
12‧‧‧小腿12‧‧‧ calf
51‧‧‧側伸縮連桿模組51‧‧‧ Side telescopic link module
200‧‧‧膝關節韌帶鬆弛度量測裝置200‧‧‧ Knee ligament relaxation measuring device
6‧‧‧電腦6‧‧‧ computer
61‧‧‧多通道轉接盒61‧‧‧Multi-channel transfer box
2‧‧‧大腿套接機構2‧‧‧Thigh socket mechanism
62‧‧‧導線62‧‧‧ wire
3‧‧‧小腿套接機構3‧‧‧Knee socket mechanism
63‧‧‧電腦本體63‧‧‧ computer body
4‧‧‧第一量測機構4‧‧‧First measuring mechanism
Claims (22)
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TW100111256A TWI422359B (en) | 2011-03-31 | 2011-03-31 | Knee ligament laxity measuring device |
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TW100111256A TWI422359B (en) | 2011-03-31 | 2011-03-31 | Knee ligament laxity measuring device |
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Citations (1)
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US4571834A (en) * | 1984-02-17 | 1986-02-25 | Orthotronics Limited Partnership | Knee laxity evaluator and motion module/digitizer arrangement |
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US4571834A (en) * | 1984-02-17 | 1986-02-25 | Orthotronics Limited Partnership | Knee laxity evaluator and motion module/digitizer arrangement |
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