201238563 六、發明說明： 【發明所屬之技術領域】 本發明是有關於一種量測裝置及量测方法，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及量測方法。 【先前技術】 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。 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KT1〇〇〇量測儀器，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勤帶量 測系統以及美國專利第4,969,471號專利案所揭露之膝關節 動帶量測裝置及其使用方法所研發。然而，前述ΚΤ1000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β再者，量測儀器只能 201238563 對前、後十字Μ進行量測評估，而無法對側㈣進行量 測評估，故使用上有其侷限性。 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’ Α卜咖公司所生產的Rolimeter量測 儀^只能做最大施力測試，並且只能對前、後十字動帶進 仃ϊ測5平估。Sport Tech公司所生產❾LigMaster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。GeN〇uR〇b公司所生產的 GNRB ：!:測儀器則只能對前十字㈣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。 【發明内容】 ㈢本’X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 内翻與外翻的程度，以評估前'後十字㈣以及内、外側 韌帶受傷的程度。 本發明之另-目的，在於提供一種膝關節勒帶鬆他度 量測裝置’其操作容易，且可方便地對前、後十字韌帶以 内外側勒帶進行1測，且量測可靠度及準確性高量 測數據重現性佳。 旦本發月之又-目的，在於提供一種膝關節勒帶鬆他度 1測裝置’具有優良的數據顯示介面與使用者介面。 本發明的目的及解決先前技術問題是採用以下技術手 5 201238563 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-大腿及一與大腿相連接的小腿上。膝 關節勃帶鬆他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。 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 第二侧面。帛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 向刖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侧面 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。 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 内、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。 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： (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； 201238563 (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 (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。 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： (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； (B) 感測施加於左右向施力桿件上的力量並產生一力量 感測訊被’以及感測小腿套接機構的翻轉量並產生·—位移 感測訊號；及 (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。 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： (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； (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 201238563 位移感測訊號；及 (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。 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、後十字動帶 的受傷程度；藉由第二量測機構的設計，能量測脛骨内翻 量以及脛骨外翻量，以得知内、外侧勃帶的受傷程度；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。 【實施方式】 有關本發明之前述及其他技術内容、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。 在本發明被詳細描述之前，要注意的是，在以下的說 明内谷中’類似的元件是以相同的編號來表示。此外，在 以下的說明内容中’「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 才曰方向為從人體膝蓋往小腿沿伸的方向。 如圖1所示，是一般人體腿部的示意圖。大腿11的一 201238563 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的内側之間 連接有一内侧韌帶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 十字勃帶13、14或者是内、外侧韌帶15、16受傷。前、 灸十子動帶13、14受傷會造成脛骨前向位移（Anterior tmnslatl〇n )以及脛骨後向位移（Posterior translation )， 内、外側韌帶15、16受傷時則會造成脛骨内翻（Varus angulation )以及脛骨外翻（vaigus anguiati〇n )。 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2〇〇 適於女裝在患者的一大腿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 測腔jg則向位移、脛骨後向位移、脛骨内翻，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。 如圖3、圖4及圖5所示，膝關節韌帶鬆弛度量測裝置 2〇〇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; 第一套设21呈倒U形並包含一前壁211及二分別由前壁 211左、右％朝後凸伸的侧壁212 ;前壁211及侧壁212共 同界疋一空間供大腿11及一髌骨17 (即膝蓋骨，如圖 £ 9 201238563 不）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内側，用以抵接於大腿u上迫 緊板223外側凸設有—穿出側壁212的-穿孔213的螺桿 224，螺桿224可螺接於旋鈕222的一螺孔225内，旋鈕 222樞設於各侧壁212外側，透過旋轉兩旋鈕222轉動以帶 動兩迫緊# 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u左、右兩 側，以避免第一套殼21相對於大腿u產生晃動。 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，各固緊帶乃 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u上❶ 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# 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m 刖壁311及側壁312共同界定—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-旋紐322，追緊件321的一迫緊板323位於各 側壁312内側’用以抵接於小腿12上，迫緊板323外側凸 10 201238563 設有一穿出侧壁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内，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此緊选地貼覆在小腿12左、右兩側，以避免第二套 殼31相對於小腿12產生晃動。 另外’小腿套接機構3還包括一連接於前壁311的一第 一則端面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π 34 n又置於延伸架33上，其包括一連接於延伸架33的 第一帶體341，及—連接於延伸架33且可拆卸地黏扣於第 :帶體34i上的第二帶體342,其中，第一帶體341例如為 毛面▼體第一帶體342例如為一鉤面帶體。透過各固 緊帶34的第—帶體342黏扣於第—帶體34 j上，使得第二 套殼31能固緊於小腿12上。 mi 〇 ^ 及圖7所示’第-量測機構4用以量測腔 月121 (如圖1所不）受一向前或向後方向的力量施加後的201238563 VI. Description of the Invention: [Technical Field] The present invention relates to a measuring device and a measuring method, and more particularly to a method for measuring the amount of movement of a tibia relative to a femur by applying an external force. A knee joint ligament relaxation measuring device and a measuring method for applying a relative change relationship between external forces. [Prior Art] 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 a merger. Other factors such as injury, to consider the way to treat. When the doctor makes a diagnosis, the patient's knee ligament laxity (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 the correct patient injury information, so that the doctor can diagnose the condition and give the patient the best and immediate medical treatment. At present, most of the knee ligament relaxation measuring devices used by the medical community are KT1 〇〇〇 measuring instruments produced by MEDmetric, which is based on the knee joints disclosed in U.S. Patent No. 4,583,555. The test system and the knee joint moving band measuring device disclosed in U.S. Patent No. 4,969,471, and the method of use thereof are developed. However, the main disadvantage of the aforementioned ΚΤ1000 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 are affected, thereby misleading the doctor's diagnosis. In addition, the measuring instrument can only measure the front and rear crossbows of 201238563, but cannot measure the side (4), so there are limitations in its use. On the other hand, other existing knee ligament relaxation measuring instruments also have their disadvantages. For example, the Rolimeter measuring instrument produced by the company can only do the maximum force test, and can only be used for the front and back cross motions. The operation steps of the TechLigMaster measuring instrument (developed based on 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 posture to measure ligaments at different positions. The GNRB:!: instrument produced by GeN〇uR〇b can only be used for the measurement of the front cross (four). Therefore, how to conceive a structural design that overcomes the shortcomings of the current measuring instruments has become a subject of further improvement of the present invention. [Summary of the Invention] (3) The main purpose of this 'X Ming' is to provide a knee ligament relaxation measuring device, which measures the forward and backward displacement of the tibia of the lower leg, and the degree of varus and valgus before evaluation. 'After the cross (four) and the extent of injury to the medial and lateral ligaments. Another object of the present invention is to provide a knee joint strapping measuring device which is easy to operate, and can conveniently perform 1 measurement on the inner and outer strips of the anterior and posterior cruciate ligaments, and the measurement reliability and accuracy are accurate. High reproducibility data is reproducible. The purpose of this month is to provide a knee joint with a degree of relaxation. The device has an excellent data display interface and a user interface. The object of the present invention and to solve the prior art problems are achieved by the following technical hand 5 201238563. A 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 joint belt measuring device includes a one-leg socket mechanism, a calf socket mechanism, a first measuring mechanism, and a second measuring mechanism. 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 the force in the longitudinal direction or the backward direction. The second measuring mechanism is coupled 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. 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. The object of the present invention and solving the prior art problems are achieved by the following technical means. According to the knee joint ligament relaxation measuring method disclosed in the present invention, the displacement amount of a tibia of a calf is applied by a force in a forward or backward direction, and the method comprises the following steps: (A) applying a direction The front or rearward force acts on the front and rear force applying members, so that a telescopic link module connected with the front and rear force applying members drives a set of calf socket mechanism connected to the lower leg; 201238563 (B) Measuring the force applied to the urging force member and generating a force sensing signal, and sensing the displacement of the telescopic link module and generating a displacement sensing signal; and (C) using a computer to extract a sense of power The test signal and the displacement sensing signal are compared for operation. According to the present invention, a knee ligament relaxation measurement method for measuring the amount of inversion of a tibia of a calf after being applied by a leftward or rightward force, the method comprising the steps of: (A) applying The force in the left or right direction is applied to the force applying member on the left and right side of the force applying member to move a set of the leg jointing mechanism connected to the left leg to the left leg. (B) The sensing is applied to the left and right sides. Applying force to the force-applying member and generating a force sense signal is 'and sensing the amount of inversion of the calf socket mechanism and generating a displacement sensing signal; and (C) using a computer to extract the force sensing signal and Displacement sensing signals are compared for operation. A method for measuring a knee ligament relaxation 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 following steps: (A) applying a direction The front or rearward force exerts a force on the front and rear force applying members to connect the front and rear force applying members to the calf socket mechanism of the lower leg; (B) the sensing applied to the front and rear force The force on the member generates a force sensing signal, and senses the displacement of a nodule of the tibia and generates a 201238563 displacement sensing signal; and (c) utilizes a computer to extract force sensing signals and displacement sensing The signal is compared for operation. 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 measures the anterior displacement of the tibia and the posterior displacement of the tibia to know the front, The degree of injury of the posterior cross-belt; the design of the second measuring mechanism, energy measurement of the amount of patella varus and the amount of valgus valgus, to know the degree of injury of the inner and outer horns; thereby, for professional orthopedic surgeons And the rehabilitation staff diagnoses the condition and gives the patient the best and immediate medical care. The above and other technical contents, features and effects of the present invention will be apparent from the following detailed description of the preferred embodiments of the invention. 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 embodiments. However, the drawings are only for the purpose of illustration and description, and are not intended to limit the invention. . Before the present invention is described in detail, it is to be noted that in the following description, like 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, and the direction indicated by "backward" is the opposite direction of "forward", and the direction of "upward" is From the knees of the human body to the thighs, the direction of the "lower" is the direction from the knees of the human body to the lower legs. As shown in Figure 1, it is a schematic view of the general human leg. A 201238563 femur 111 of the thigh 11 and a tibia 121 of the calf 12 are connected with an anterior cruciate ligament 13 and a posterior cruciate ligament 14. The femur 111 and the inside of the tibia 121 are connected with an medial ligament 15 and the femur 111 and the tibia 121. There is an outer ligament 16 connected between the outer sides. When the average person suddenly decelerates while running, and quickly changes the running direction, or when jumping to the ground, it is possible to cause the front and rear cross belts 13, 14 or the inner and outer ligaments 15, 16 to be injured. The anterior and moxibustion of the sacral spurs 13 and 14 will cause the anterior displacement of the humerus (Anterior tmnslatl〇n) and the posterior displacement of the humerus (Posterior translation). When the inner and outer ligaments 15 and 16 are injured, the humerus can be inverted (Varus). Angulation ) and patella valgus (vaigus anguiati〇n ). 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 2 is suitable for women's legs in a patient's thigh 11 And a calf 12 connected to the thigh 11 . The knee ligament relaxation measuring device 200 of the present invention can measure the physical quantity of the cavity jg to the displacement, the posterior displacement of the tibia, the patella varus, and the valgus valgus, and can be used as a professional orthopedic surgeon and rehabilitation personnel. Quantitative data for assessing the degree of ligament injury and recovery in patients. As shown in FIG. 3, FIG. 4 and FIG. 5, the knee joint ligament relaxation measuring device 2 includes a one-leg socket mechanism 2, a calf sleeve mechanism 3, and a connection to the thigh socket mechanism 2 and the calf sleeve. The first measuring mechanism 4 between the mechanisms 3 is connected. The thigh sleeve mechanism 2 includes a first sleeve 21 and two clamping modules 22; the first set 21 has an inverted U shape and includes a front wall 211 and two are respectively protruded from the front wall 211 to the left and right. 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. 9 201238563). 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. The screw 224 of the through hole 213 of the side wall 212 is protruded from the outer side of the pressing plate 223. The screw 224 is screwed into a screw hole 225 of the knob 222, and the knob 222 is pivoted outside the side wall 212. Rotating the two knobs 222 to rotate the two pressing plates 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 thighs to avoid the first A set of shells 21 is shaken relative to the thighs u. 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 includes a first strap 231 coupled to a sidewall 212 and a second strap detachably coupled to the first strap 212 and detachably bonded 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 thigh u. As shown in Fig. 3, Fig. 4 and Fig. 6, the structure of the calf socket mechanism 3 is similar to that of the thigh socket machine #2. The calf socket mechanism 3 includes a second. The sleeve 31 and the two clamping modules 32; the second sleeve 31 has an inverted u shape and includes a front wall 311 and two side walls m 311 and a side wall 312 respectively protruding from the left and right ends of the front wall 311 - Space for the calf 12 to accommodate. 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 tracking member 321 is located inside the side walls 312 for abutting On the lower leg 12, the outer side of the pressing plate 323 10201238563 is provided with a screw 324 which passes through a through hole 313 of the side wall 312. The screw 324 can be screwed into a screw hole 325 of the knob 322, and the knob 322 is pivoted on each side wall 312. Outside. 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 are closely attached to the left and right sides of the lower leg 12 to The second casing 31 is prevented from rattling relative to the lower leg 12. In addition, the calf socket mechanism 3 further includes an extension frame 33 ′ extending from a first 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 π 34 n is further disposed on the extension frame 33, and includes a first belt body 341 connected to the extension frame 33, and is connected to the extension frame 33 and detachably adhered to the first belt body 34i. The second strip 342, wherein the first strip 341 is, for example, a matte body, the first strip 342 is, for example, a hook-and-loop strip. The first belt body 342, which is passed through each of the fastening belts 34, is adhered to the first belt body 34j so that the second casing 31 can be fastened to the lower leg 12. Mi 〇 ^ and the 'first-measurement mechanism 4' shown in Fig. 7 are used to measure the force of a cavity 121 (not shown in Fig. 1) after being applied in a forward or backward direction.
位移量’第—量測機構4包括—承載框架41及—伸縮連桿 =組42。承載框架41透過樞接方式設置於第—套殼21的 前壁2U的一第—前端面214上，承載框架41包含-呈LThe displacement amount 'the first measuring mechanism 4' includes a carrier frame 41 and a telescopic link = group 42. The carrier frame 41 is pivotally disposed on a first front end surface 214 of the front wall 2U of the first casing 21, and the carrier frame 41 includes - L
11 201238563 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且可轉動地繞第一轴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-滑接件421包括-沿上下方向延伸的梅接架 423，樞接架423的一上樞接端424樞接於承載框架41的 第一軸4丨2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^有—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， 接合件429透過樞接方式設置於第二套殼31的前壁3ιι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43〇，第二滑接件422的滑動架 426的一下樞接端431樞接於第二軸43〇並可繞第二軸43〇 旋轉。 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μ 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44卜及一相反於銷部441 的施力部442 ’·銷部441可穿設於第二滑接件422之滑動架 12 201238563 426的一長形滑槽432中以 ώ _ 使銷。卩441受長形滑槽432所拘 二1之’鎖部441滑動地柄接於與長形滑槽432以使 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，相斟絲〜 — 且相對轉動之軸向與第一軸412平 I施力施卩442呈Μ狀用以供使用者按壓。當使用者按 壓力。Η42使前後向施力桿件44沿著穿孔414上下 =程中，前後向施力桿件44能同時帶動伸縮連桿模組42 繞第一轴化相對於承載框架41的架體4ιι旋轉。 第-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的兩隔板州 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—力量感測元件Μ為―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—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-位移感測元件46為—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 -穿設於本體461内並可相對於本體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相對於承載柜架 4!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。 如圖3、圖5、圖6及圖7所示，在本實施例中，小腿 s 13 201238563 套接機構3還包括一設置於第二前端面314上的第一轴承 件35，第一軸承件35用以供接合件429的一與第二轴43〇 垂直的第二樞接轴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。 备患者因受傷因素導致小腿12相對於大腿11往内翻或往外 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上並與第一轴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u往内 翻或往外翻的程度較為嚴料，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。 ~ 如圖8、圖9、圖1〇及圖u所示，以下將針對膝關節 物帶鬆他度量測方法進行詳細說明。將膝關㈣帶鬆他度 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u及小腿12可分別透過一 支律墊（圖未示）切’使得大腿n與小腿12之間是呈 25度〜30度的f曲狀態，接著，專業骨科醫生及復健人員 14 201238563 等即可透過手動方式進行量測的操作。 圖8為㈣121 (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—前後向 施力#件44上’使—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 ’操作人員以-手握持住—設置於承載框架Μ上 的第一握把47 ’而另—手握持住前後向施力桿件44的施力 。"42 ’接者’操作人員可施加一沿箭頭ι方向所示的向前 拉力於施力部442上（如圖1〇所示），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-滑接件421沿箭頭π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u往前平移，藉此，以進行脛骨ΐ2ι前向位移 的量測。 或者’操作人員可施加一沿箭頭m方向所示的向後推 力於施力部442上（如圖U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，使得第二滑接件似 及第-滑接件421沿箭頭IV方向繞第—轴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 15 201238563 的量測。 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。 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。 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。 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的類比訊號掏取卡（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。 16 201238563 如圖、12所示’由於脛骨121 (如圖〗所示）的一位移 參考點（通常位於髂骨丨\ \ 、 賴月17下方3公分處）可能會與第一位 移感測元件4 6的探4 a ο y*· se « J秌針462位置有所差異，因此，可透過電 腦6的電腦主機63f知m 〇 a-、 C如圖2所不）經由相似三角形的幾何 關係來進行比㈣算，以得㈣位移參相时際位移量 △’其中’該位移參考點的實際位移量△是與—位移轉換公 式有關，該位移轉換公式為·· Δ = —A*«/tan ’〇 90°-tan' e-Af cos' V? 其中’ /為該位移參考點與第一轴412之轴心的偏位 量’ /。為第-位移感測元件46的—探針462之中心軸與第 了轴412之軸心的偏位量，△。為探針462的線性位移量 12為例，伸縮連桿模組42的第-滑接件42】呈水 平時的線性位移4較為零），,騎縮連桿肋Μ的第一 =件421和第一位移感測元件46的探針備的接觸點所 4^2第—轴412之轴心的偏位量，△*為伸縮連桿模組 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。 的實2^際量_4量測如圖9所示的位移參考點 的實ρ位再1測如圖10或圖11所示的位移參考點 向位移或後一+:二;，=二：11 201238563 A frame body 411, and a first shaft 412 penetrating the frame body 411, the 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 gusset 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 4 丨 2 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 has a sliding groove 428 for sliding the sliding rails 425, so that the second sliding member 422 can slide up and down with respect to the first sliding member 421. The telescopic link module 42 further includes a joint member 429 which is pivotally disposed on the second front end surface 314 of the front wall 3 ι of the second sleeve 31. The joint member 429 includes a left and right direction extending and The second shaft 43 is parallel to the shaft 412. The lower pivoting end 431 of the carriage 426 of the second sliding member 422 is pivotally connected to the second shaft 43 and rotatable about the second shaft 43. The frame body 411 further includes a bushing 413 defining a perforation extending in the front-rear direction. The first measuring mechanism 4 further includes a front and rear force applying member 44, and the front and rear force applying members 44 are movably disposed. The through hole 414 of the bearing frame μ is engaged with the telescopic link module 42. In the present embodiment, the forward and backward urging member 44 includes a pin portion 44 and a urging portion 442 ′ opposite to the pin portion 441. The pin portion 441 can be disposed through the carriage 12 of the second sliding member 422. In the elongated chute 432 of 201238563 426, the pin is made by ώ _. The 卩 441 is restrained by the elongated chute 432. The lock portion 441 is slidably coupled to the elongated chute 432 so that relative sliding and relative rotation can be simultaneously generated (the direction of the relative sliding is perpendicular to the first axis 412). The relative rotation axis is - and the axial direction of the relative rotation is the same as that of the first shaft 412. The force application 442 is in a shape for the user to press. When the user presses the pressure, the Η42 causes the front and rear force application members 44 to follow. The first and second urging members 44 can simultaneously rotate the telescopic link module 42 about the first axis to rotate relative to the frame 4 of the carrier frame 41. The first-measurement mechanism 4 further includes a first A force sensing element 45 is disposed between the two partition states of the forward and backward force applying members 44 for sensing the force applying portion 442 applied to the front and rear force applying members 44. In this embodiment, the first force sensing component is a "Load cell", which is the same as the structure and operation principle of the current load cell on the market, and therefore will not be described in detail herein. The first measuring mechanism 4 further includes a first displacement sensing disposed on the carrying frame 41 and abutting the telescopic link module 42 The component 46 is configured to sense the displacement amount of the telescopic link module 42. In the present embodiment, the 'first displacement sensing component 46 is a resistive displacement sensor, which comprises a fixedly disposed through the carrier frame 41. The body 461 of the frame body 411 and the probe 462 that is disposed in the body 461 and extendable forward and backward relative to the body 461, the probe 462 abuts on the pivot frame 423 of the first sliding member 421, Therefore, when the first sliding member 421 of the telescopic link module 42 rotates relative to the carrying frame 4!, the probe 462 is stretched back and forth with respect to the body 461 as the first sliding member 421 rotates. As shown in FIG. 3, FIG. 5, FIG. 6 and FIG. 7, in the embodiment, the calf s 13 201238563 ferrule mechanism 3 further includes a first bearing member 35 disposed on the second front end surface 314, the first bearing member. The first bearing member 35 defines a first rotation center L1 extending in the front-rear direction, and the calf sleeve mechanism 3 can be pivoted. The first bearing member 35 is rotated relative to the engaging member 429 of the telescopic link module 42. The patient is caused by an injury factor to the lower leg 12 When the thigh 11 is turned inward or outward, the calf sleeve mechanism 3 can be appropriately rotated relative to the telescopic rod module 42 so that the calf sleeve mechanism 3 can be surely sleeved on the calf 12. The thigh sleeve mechanism 2 further comprising a second bearing member 24 disposed on the first front end surface 214, the second bearing member 24 for a first pivoting of the carrier frame 41 disposed on the frame body 411 and perpendicular to the first shaft 412 The 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 sleeve mechanism 2 is rotatable relative to the carrier frame 41 of the telescopic rod module 42 through the second bearing member 24. When the patient's lower leg 12 is turned inward or outward with respect to the thigh u, the calf socket mechanism 3 and the thigh socket mechanism 2 can be adjusted to rotate relative to the telescopic link module 42 at the same time, so that the calf sleeve mechanism 3 and the thigh socket mechanism 2 can be surely sleeved on the calf 12 and the thigh 11 respectively. ~ As shown in Fig. 8, Fig. 9, Fig. 1 and Fig. u, the knee joint tape measure method will be described in detail below. The thigh socket mechanism 2 and the calf socket mechanism 3 of the knee joint (4) with the loose measuring device 200 are respectively sleeved on the thigh 11 and the lower leg 12, and the thigh u and the calf 12 can respectively pass through a legal pad (Fig. The cut "shows" between the thigh n and the lower leg 12 in a f-curved state of 25 degrees to 30 degrees, and then the professional orthopedics and rehabilitation personnel 14 201238563 can perform the measurement by manual means. Figure 8 is a flow chart of the method for measuring the forward or backward displacement of (IV) 121 (shown in Figure 1). The main flow is as follows: 'Apply a forward or backward force on the front-back direction as shown in step 91. 44, the telescopic link module 42 connected to the front and rear urging member 44 drives a set of the shank splicing mechanism 3 attached to the lower leg 12, and the operator holds the hand-held frame. The first grip 47' on the crotch and the other hand hold the urging force of the urging force member 44. The operator of the '42' operator can apply a forward pulling force as shown by the direction of the arrow ι to the urging portion 442 (as shown in FIG. 1A), and the pin portion 441 of the front and rear urging member 44 is pulled. The second sliding member 422 is moved forward, so that the second sliding member 422 and the first sliding member 421 rotate around the first shaft 412 in the direction of the arrow π while being 'transmitted by the engaging member 429 and the engaging member 429 can be opposite to the second The relationship of the rotation of the sliding member 422 enables the calf socket mechanism 3 to drive the lower leg 12 to translate forward relative to the thigh u, thereby performing measurement of the forward displacement of the humerus. Or 'the operator can apply a rearward thrust shown in the direction of the arrow m to the urging portion 442 (as shown in FIG. U), and the pin portion 441 of the front and rear urging member 44 pushes the second sliding member 422. Shifting, so that the second sliding member 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. So that the calf sleeve mechanism 3 can drive the calf 12 to translate backward relative to the thigh 11 'to thereby measure the posterior displacement of the tibia 121 15 201238563. As shown in step 92, the force applied to the urging force applying member 44 is sensed and a force sensing signal is generated and the amount of displacement of the telescopic link module 42 is sensed to generate a displacement sensing signal. 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 component 45 will correspondingly generate different force sensing signals. In addition, since the probe 462 of the first displacement sensing component 46 generates a displacement sensing signal during the telescopic movement relative to the body 461, the first displacement sensing component 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 described by using an analog voltage signal as an example. As shown in step 93, a computer 6 (shown in Figure 2) is used to extract the force sensing signal and the displacement sensing signal for comparison. 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 the analog signal capture card (not shown) of a host computer 63 via a wire 62 to 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 through the host computer 63, thereby performing calculation and correlation analysis comparison. jobs. 16 201238563 As shown in Figure 12, a displacement reference point (usually located at the iliac crest \ \ , 3 cm below Laiyue 17) may be associated with the first displacement sensing element due to the patella 121 (as shown in the figure). 4 6 探 4 a ο y*· se « J 秌 462 462 position difference, therefore, through the computer 6 computer host 63f know m 〇a-, C as shown in Figure 2) through the similar triangle geometry To calculate (4), to obtain (4) displacement phase-interval displacement △ 'where 'the actual displacement △ of the displacement reference point is related to the - displacement conversion formula, which is ·· Δ = —A*« /tan '〇90°-tan' e-Af cos' V? where ' / is the amount of deviation of the displacement reference point from the axis of the first axis 412 ' /. It is the amount of deviation of the central axis of the probe 462 of the first-displacement sensing element 46 from the axis of the first axis 412, Δ. For example, for the linear displacement amount 12 of the probe 462, the linear displacement 4 of the first sliding member 42 of the telescopic link module 42 is horizontal, and the first = 421 of the rib link The amount of deviation from the axis of the contact point of the probe of the first displacement sensing element 46 is Δ*, which is the displacement of the first displacement sensing element 46 when the telescopic link module is used. The amount of displacement produced by the central axis of the needle 462. The actual 2^ quantity _4 is measured as shown in Fig. 9 and the real ρ position of the displacement reference point is measured as shown in Fig. 10 or Fig. 11 as the displacement reference point displacement or the latter +: two; :
S 17 201238563 的距離時，即可與力量感 ，以得到一位移與力量的 生及復健人員診斷病情並 脛骨121的前向位移或後向位移 測訊號轉換後的力量值進行比對 關係圖’藉此，可供專業骨科醫 對患者施予最佳與即時的醫療。 如圖5及圖6所示，小腿套接機構3還包括二樞抽座 36,各框軸座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_呈前後方向延伸的第三 轴37穿設’其中’第-軸承件35錢的第-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 -設置於延伸架33上的左右向施力捍件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。 如圖2、圖3、圖4及圖14所示，膝關節韌帶鬆弛度 里測裳置200還包含-第一量測機構5，第二量測機構$包 括二個侧伸縮連桿模組51。各侧伸縮連桿模組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 的第二侧面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包括一柩接於第一侧面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包括一枢接於第二側面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内。 如圖4、圖5、圖6及圖14所示，進一步地，大腿套 18 201238563 接機構2還包括二猶轴座25，各㈣座^可透過螺鎖方式 固定於各側壁212的-第-側面215上，各檀轴座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^ 界定的第-旋轉中心、L2與第四軸26呈共平面且互相平 行。第—連接單元511還包含一樞接於第四軸％且可轉動 地繞第四轴26旋轉的第-鉸鍊件517，第—鉸鍊件517包 括供第連接件513樞接的第一枢接軸部518，第一樞接 轴部518呈左右方向延伸，藉此，第—連接件513可透過 第-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 -樞接於第三轴37且可轉動地繞第三軸37旋轉的第二敍 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52〇，第二樞接轴部52〇呈左右方向延伸藉 此，第二連接件515可透過第二鉸鍊件519繞第三轴37旋 轉，並且可繞第二樞接轴部52〇相對於第二鉸鍊件519旋 轉。 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 括一固疋在固定板50上的本體541，及一抵接於小腿套接 19 201238563 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。 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4牛55 ’第二位移感測元# 55肖構與第一位移感測 元件46相同’第二位移感測元件透過—固定板5〇安裝 在第連接件513上，第三位移感測元件55包括一固定在 固疋板50上的本體551，及一抵接於大腿套接機構2的第 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__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。 狄如圖15、圖16、圖17及圖18所示，以下將針對膝關 即勃帶鬆弛度量測方法進行詳細說明。圖15為腔骨⑵ (如圖1所示）向外或向内翻轉量測方法的流程圖，其主 要流程為： 〃如步驟94’施加_向左或向右方向的力量於一左右向 細力柃件38上’使一與左右向施力桿件％相連接的一套 接在小腿12的小腿套接制3運動。 I先操作人員以一手握持住一設置於第一套殼21的 第月J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-沿箭 頭V方向所示的向外推力於施力部382上（如圖17所 不）’左右向施力桿件38會推動第二套殼31沿箭頭VI方 20 201238563 向相對於第-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m向外翻 轉的量測。 或者，操作人員可施加一沿箭頭νπ方向所示的向内拉 力於施力部382上（如圖18所示），左右向施力桿件^會 拉動第二套殼31沿箭頭X方向相對於第-套殼21旋轉， ㈣第二套殼31能帶動小腿12相對於大腿u向内旋轉， 藉此，以進行脛骨121向内翻轉的量測。 如步驟95所示，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3的 翻轉量並產生一位移感測訊號。 由於施加於左右向施力桿件38上的力量會使第二力量 感測兀件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Μ 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， 第一位移感測元件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 二位移感測元件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 21 201238563 二位移感測元件54、55的設計，能準確地量測脛骨121向 外或向内翻時的翻轉量。 如步驟96所示’利用一電腦如圖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。 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 能插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。 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： β ^ax+a2 α】=tan tan' -1When the distance of S 17 201238563 is used, the force sense can be used to obtain a displacement and strength of the health and rehabilitation personnel to diagnose the condition and the forward displacement of the tibia 121 or the force value after the backward displacement measurement signal is compared. 'This allows professional orthopedic doctors to give patients the best and immediate medical care. As shown in FIG. 5 and FIG. 6 , the shank shank mechanism 3 further includes two pivoting seats 36 . The frame yokes 36 can be fixed to a second side 315 of each side wall 312 by a screw locking manner. The third shaft 37 extending in the front-rear direction is disposed so that the first-rotation center L1 of the 'the-bearing member 35' is coplanar and parallel to each other. The shank splicing mechanism 3 further includes a right and left urging 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. As shown in FIG. 2, FIG. 3, FIG. 4 and FIG. 14, the knee ligament slackness measuring device 200 further includes a first measuring mechanism 5, and the second measuring mechanism $ 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 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. As shown in FIG. 4, FIG. 5, FIG. 6 and FIG. 14, further, the thigh sleeve 18 201238563 connection mechanism 2 further includes two jug bases 25, and each (four) seat can be fixed to each side wall 212 by a screw lock method. On the side 215, each of the sandal shaft seats 25 is provided for a fourth shaft 26 extending in the front-rear direction, wherein the first-rotation center defined by the second bearing member, the L2 and the fourth shaft 26 are coplanar and mutually parallel. The first connecting unit 511 further includes a first hinge member 517 pivotally connected to the fourth shaft and rotatably rotated about the fourth shaft 26, and the first hinge member 517 includes a first pivotal connection for pivoting the first connecting member 513. The first pivoting shaft portion 518 extends in the left-right direction, whereby the first connecting member 513 is rotatable through the first hinge member 517 about the fourth shaft 26 and is rotatable relative to the first pivoting shaft portion 518. The first hinge member 517 rotates. The second connecting unit 512 further includes a second chain 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 pivoting member 515. The second pivoting shaft portion 52 is extended in the left-right direction by the second pivoting shaft portion 52, and 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 The portion 52 is rotated relative to the second hinge member 519. In addition, the second measuring mechanism 5 further includes a second force sensing element 53 and a second displacement sensing element 54. The second force sensing element 53 has the same structure as the first force sensing element 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 solid body. a body 541 on the fixing plate 50, and a probe 542 abutting on the second side 315 of the shank sleeve 19 201238563 mechanism 3 and extending in the left-right direction, the probe 542 can be opposite to the second leg with the calf sleeve mechanism 3 The link 515 is rotated to expand and contract, whereby the amount of turnover of the calf socket mechanism 3 can be sensed. 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 4 牛 55 'second displacement sensing element# The fifth displacement is the same as the first displacement sensing element 46. The second displacement sensing element is transmitted through the fixing plate 5A, and the third displacement sensing element 55 is fixed to the fixing plate 50. The main body 551 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 thigh socket mechanism 2 rotating relative to the first_connection member 513, Thereby, the amount of turnover of the thigh socket mechanism 2 can be sensed. As shown in Fig. 15, Fig. 16, Fig. 17, and Fig. 18, the knee-to-belt relaxation measurement method will be described in detail below. Figure 15 is a flow chart of the method for measuring the outward or inward inversion of the cavity bone (2) (shown in Figure 1). The main flow is as follows: For example, step 94' applies a force to the left or right direction in a left-right direction. On the fine force piece 38, a set of the calf sleeves connected to the lower leg 12 is connected to the left and right force applying members. First, the operator holds the second grip 27 disposed on the first month J 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 - the outward thrust shown in the direction of the arrow V on the urging portion 382 (as shown in FIG. 17). The left and right urging member 38 pushes the second casing 31 along the arrow VI. 201238563 is rotated relative to the first sleeve 21 such that the second sleeve 31 can drive the lower leg 12 to rotate outward relative to the thigh 11 'by taking a measure of the outward rotation of the tibia m. Alternatively, the operator can apply an inward pulling force as shown by the direction of the arrow νπ to the urging portion 382 (as shown in FIG. 18), and the left and right urging members will pull the second casing 31 in the direction of the arrow X. The first sleeve 31 is rotated, and (4) the second sleeve 31 can drive the lower leg 12 to rotate inward relative to the thigh u, thereby performing measurement of the inward turning of the tibia 121. As shown in step 95, the force applied to the left and right force applying members 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. 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 second force sensing element 对应 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 first 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 socket mechanism 3 can be sensed through the arrangement of the second displacement sensing element 55. the amount. Furthermore, if the calf 12 is excessively bent relative to the thigh 11 due to an injury factor (as shown in FIG. 19), the design of the second and 21st 201238563 two displacement sensing elements 54, 55 can be accurately measured. The amount of turnover of the tibia 121 when it is turned outward or inward. As shown in step 96, 'using a computer as shown in FIG. 2', the force sensing signal and the displacement sensing signal are extracted for comparison. 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 card of 63 can insert 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. 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: β ^ax+a2 α]=tan tan' -1
/ -tan-1 l A ) \ / (A{- 1 -tan 1 l A ) V/ -tan-1 l A ) \ / (A{- 1 -tan 1 l A ) V
Si V V (^1 - )2 + 22 201238563 a2 l2 l2 -tan' -tan—Si V V (^1 - )2 + 22 201238563 a2 l2 l2 -tan' -tan—
h2 其中，如圖19为闰 _ 日 及圖20所示，夕為翻轉角度，〇 罝測機構5的側伸缩遠_ I為第一 ,, 甲縮連㈣組51與小腿套接機構3的笛一 側面化的夾角1為第二位移感測元件54的探針 線性位移量，γ為第 ，的探針542之 542 ^ 和第二位移感測元件54 針2的—凸伸端齊平的一端與第三秘37之間的垂直 距：4為第二位移感測元件54的探針％之中心軸與第 一軸37之間的垂直距離 ’、 MS與第三軸37之門t/1小腿套接機構3的第二側面 54的探針542的 距離為第二位移感測元件 的接縮Λ 小腿套接機構3的第二側面315接觸 接觸u之間的垂直距離；如圖21所示、為第二量 :伸縮連桿模組51與大腿套接機構：的第-侧 為第三位移感測元件55的探針-之線 r針55:/2為第一連接件513和第三位移感測元件55的 ^針552的-凸伸端齊平的一端與第四轴％之間的垂直距 4為第三位移感測元件55的探針切之中心轴與第四 軸％之間的垂直距離，為大腿套接機構2的第一側面 5與第四軸26之間的垂直距離，&為第三位移感測元件 的探針552的-和大腿套接機構2的第—側面215接觸 的接觸端與％之間的垂直距離。 在進行實際量測時，先量測如圓，r 尤重利如圖W所示的初始翻轉角H2, wherein, as shown in FIG. 19, the 闰_ day and FIG. 20, the eve is the flip angle, and the side telescopic distance _I of the sniffering mechanism 5 is the first, and the acetabular (four) group 51 and the calf splicing mechanism 3 The angle 1 of the flute-side is the linear displacement of the probe of the second displacement sensing element 54, the γ of the probe 542 is 542 ^, and the protrusion of the second displacement sensing element 54 of the needle 2 is flush The vertical distance between one end and the third secret 37: 4 is the vertical distance ' between the central axis of the probe % of the second displacement sensing element 54 and the first axis 37', and the gate of the MS and the third axis 37 /1 The distance of the probe 542 of the second side 54 of the calf socket mechanism 3 is the distance between the second displacement surface of the second displacement sensing element and the second side surface 315 of the calf socket mechanism 3 contacting the contact u; 21, the second amount: the telescopic link module 51 and the thigh socket mechanism: the first side is the probe of the third displacement sensing element 55 - the line r pin 55: /2 is the first connector 513 and the vertical distance 4 between the end of the convex end of the pin 552 of the third displacement sensing element 55 and the fourth axis % is the central axis of the probe of the third displacement sensing element 55 and the The vertical distance between the shaft % is the vertical distance between the first side 5 and the fourth shaft 26 of the thigh socket mechanism 2, and the probe 552 of the third displacement sensing element - and the thigh sleeve mechanism The vertical distance between the contact end of the first side 215 of 2 and %. In the actual measurement, first measure the circle, r is particularly heavy, the initial flip angle shown in Figure W
S 23 201238563 度A ’再量測如圖17、圖18或圖19所示的實際翻轉角度 々/’計算A與之差即可得到脛f 121外翻的翻轉角度或 内翻的翻轉角度，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。 如圖22及圖23所不，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 21〇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。 如圖23及圖24所示，在本實施例中，大腿套接機構 2’的侧壁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 23卜小腿套接機構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。卩381疋设置於延伸架33的侧邊，另一個固緊帶 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,的單一個侧壁312與迫緊模组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。 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 24 201238563 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41Γ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上的第二樞接轴446，桿件本體44〇透過 其一端的樞接部441’可轉動地樞接於第二轴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-傾斜角度，藉此，前後向施力桿件 44可卜與第二前端面314垂直的施力方向對小腿套接機 構3’施力。 此外，第-位移感測元件46設置於承載框架Μ，的架 體川’上，透過架體411，能相對於第一接合件416轉動到 -傾斜角度，使得第一位移感測元件4“一設置於探針 似一端的接觸板463能抵接在小腿12上並且對應於徑骨 ⑵的一結節122 (如圖27戶斤示）位置，藉此，第一位移 感測疋件46能感測脛骨121的結節122的位移量。 1如圖26、圖27、圖28、圖29及圖30所示，圖26為 （如目！所示）前向或後向位移量測方法的流程 圖’其主要流程為·· § 25 201238563 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。 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幻 方向（與第一刖端面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。 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。 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。 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。 歸納上述，兩實施例的膝關節韌帶鬆弛度量測裝置 200、21 〇 ,藉由第一量測機構4、4’的設計，能量測腔骨 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 26 201238563 «骨m内翻量以及脛骨121外翻量，以得知内、外側 物帶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。 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 範圍及發明說明内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内。 【圖式簡單說明】 圖1是一般人體腿部的示意圖； 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； * 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； 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； 圖5是本發明膝關節韌帶鬆他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； 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； 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； 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； 27 201238563 圖9是本發明膝關節韌帶鬆弛度量測裝置的第一較佳 實施例的侧視圖； 圖ίο是本發明膝關節韌帶鬆弛度量測裝置的第一較佳 實施例的侧視圖’說明前後向施力桿件往前拉小腿套接機 構； 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； 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； 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； 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； 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； 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； 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； 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内 拉； 28 201238563 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； 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； 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； 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； 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； 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； 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； 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； 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； 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； 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 圖30是本發明膝關節韌帶鬆弛度量測裝置的第二較佳 29 201238563 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。 30 201238563 【主要元件符號說明】 11............... ..大腿 111........ .股骨 12 .......... .小腿 121......... .脛骨 13 .......... .前十字韌帶 14.......... 後十字韌帶 15 .......... 内側韌帶 16 .......... 外側勤帶 17 .......... 髂骨 200'210... •膝關節韌帶鬆弛 度量測裝置 2 ' V...... 大腿套接機構 21 .......... 第一套殼 211 ' 311.... .·前壁 212、312.·.· .側壁 213 ' 313.... .穿孔 214.............. ;前端面 215.............. ·$側面 22 ' 32 ... 迫緊模組 221 > 321.... •迫緊件 222'322.... .旋鈕 223、323.·.. •迫緊板 224、324··.. •螺桿 225'325.....螺孔 23、34·..·固緊帶 231、 341.....第一帶體 232、 342··.··第二帶體 24 ..........第二耗承件 25 ' 36····樞轴座 26 ..........第四· 27 ..........第二握把 3、 3 ’……小腿套接機構 31 ..........第二套殼 314 .........第二前端面 315 .........弟-—侧面 33 ..........延伸架 35 ..........第一轴承件 37 ..........第三軸 38 ..........左右向施力桿件 381 .........連接部 382 .........施力部 4、 4 ’......第一量測機構 41、41’ ..承載框架 4U、41Γ..架體 412、417...第一轴 413.........襯套S 23 201238563 degree A 're-measure the actual flip angle 々/' shown in Fig. 17, Fig. 18 or Fig. 19 to calculate the difference between A and 即可f 121 eversion flip angle or inversion flip angle, In this way, professional orthopedic surgeons and rehabilitation personnel can be used to diagnose the condition and provide the best and immediate medical treatment for the patient. 22 and FIG. 23 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 21〇 are substantially the same as those of the first embodiment. The preferred embodiment is the same except that the structural design of the thigh socket mechanism 2', the calf socket mechanism 3, and the first measuring mechanism 4' is slightly different. 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 strip 232 of each fastening strip 23 is connected to The front wall 211 can be adhered to the first belt body 23 and the calf sleeve mechanism 3, and the number of the side walls 312 and the pressing module 32 is one. The second belt 342 of the fastening belt 34 is connected to the second belt 342. The front wall 311 can be adhered to the first belt 341. Further, the connection of the right and left force applying members 38 is performed. The 卩381疋 is disposed on the side of the extension frame 33, and the first tape body 341 of the other fastening tape is coupled to the connection portion 381 and can be attached to the second tape 342. Through the single side wall 212 of the thigh socket mechanism 2' and the design of the pressing module 22, the single side wall 312 and the pressing module 32, and the single second measuring mechanism 5 The knee ligament relaxation measuring device 210 is designed to reduce the overall weight 'to reduce the burden on the patient's thigh 11 and lower leg 12 as compared to the first preferred embodiment. As shown in FIG. 24 and FIG. 25, the load-bearing frame 41 of the first measuring mechanism 4' includes an L-shaped frame body 411'' and a first joint member 416; the front and rear direction 24 201238563 force rod member 44 and The first displacement sensing element 46 is disposed on the frame 41 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 pivoting shaft 418, which is vertically and pivotally connected to the second bearing member 24, 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, and the pivoting portion of the rod body 44 through one end thereof The 441' is pivotally coupled to the second shaft 445. The frame body 411 is rotatably pivoted to the first shaft 417 such that the frame body 411 can be rotated to an oblique angle with respect to the first engaging member 416, whereby the front and rear force applying members 44 are second and second. The vertical direction of application of the front end surface 314 applies a force to the calf sleeve mechanism 3'. In addition, the first displacement sensing element 46 is disposed on the frame body of the carrier frame ,, and is transmitted through the frame body 411 to be tilted to an oblique angle with respect to the first engagement member 416 such that the first displacement sensing element 4 is “ A contact plate 463 disposed at one end of the probe can abut on the lower leg 12 and corresponding to a nodule 122 of the radial bone (2) (as shown in FIG. 27), whereby the first displacement sensing element 46 can The displacement amount of the nodule 122 of the tibia 121 is sensed. 1 As shown in FIG. 26, FIG. 27, FIG. 28, FIG. 29 and FIG. 30, FIG. 26 is a (for example, shown in FIG. Flowchart 'The main flow is § 25 201238563 As shown in step 91', a forward or backward force is applied to a forward and backward force applying member 44 to connect one to the front and rear force applying members 44. The calf sleeve mechanism 3' is slidably engaged with the calf 12. The operator holds the second grip 27 disposed on the first front end surface 214 of the thigh socket mechanism 2 with one hand while holding the other hand To the urging portion 442 of the urging member 44, the operator can then apply a direction along the arrow (with the first 刖The forward pulling force shown on the surface 314 is perpendicular to the urging portion 442 (as shown in FIG. 29), and the urging member 44 is pulled forward by the second engaging member 444 to move the shank mechanism 3' forward. Thereby, the first displacement sensing element 46 can make a measurement of the forward displacement of the tibia 121. Alternatively, the operator can apply a rearward thrust shown in the direction of the arrow A2 to the urging portion 442 (as shown in FIG. 30). The anterior-posterior urging member 44 can be pushed through the second engaging member 444 to push the calf splicing mechanism 3 to translate backwards, whereby the first displacement sensing member 46 can perform the measurement of the posterior displacement of the tibia 121. As shown in step 92', the force applied to the urging force applying 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. As shown in step 93', the power sensing signal and the displacement sensing signal are extracted by a computer 6 (as shown in FIG. 2) for comparison. The above-described knee ligament relaxation measuring device 200 of the two embodiments is summarized. 21 〇, by the design of the first measuring mechanism 4, 4' The forward displacement of the luminal bone 121 and the posterior displacement of the humerus 121 are used to know the degree of injury of the anterior and posterior cruciate ligaments 13, 14; by the design of the second measuring mechanism 5, the energy 26 201238563 «bone m inversion and the tibia 121 Turn over the amount to find out the degree of injury of the inner and outer strips 15 and 16; thereby, the professional orthopedic surgeon and the rehabilitation staff can diagnose the condition and give the patient the best and immediate medical treatment, so that the claim of the present invention can be achieved. The above is only the preferred embodiment of the present invention, and the scope of the present invention is not limited thereto, that is, the simple equivalent change according to the scope of the invention and the description of the invention. And modifications are still within the scope of the invention patent. BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 is a schematic view of a generally human leg; Fig. 2 is a perspective view of a first preferred embodiment of a knee ligament relaxation measuring device of the present invention; * Fig. 3 is a knee ligament relaxation of the present invention Figure 3 is a perspective exploded view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention; Figure 5 is a perspective view of the knee ligament of the present invention. 3 is an exploded perspective view of the thigh socket mechanism of the first preferred embodiment of the measuring device; FIG. 6 is an exploded perspective view of the calf socket mechanism of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention; 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; Figure 8 is a first preferred embodiment of the knee ligament relaxation measuring device of the present invention. Flowchart of the measuring method of the example; 27 201238563 Figure 9 is a side view of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention; Figure ίο is the first of the knee ligament relaxation measuring device of the present invention Better A side view of the embodiment 'illustrating the forward and backward force applying members to pull the calf sleeve mechanism forward; FIG. 11 is a side view of the first preferred embodiment of the knee joint ligament relaxation measuring device of the present invention, illustrating the forward and backward force application Figure 12 is a partial enlarged view of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention; Figure 13 is a sectional view of the knee ligament relaxation measuring device of the present invention. Figure 14 is a perspective exploded view of the second measuring mechanism of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention; Figure 15 is a perspective view of the second measuring mechanism of the knee ligament relaxation measuring device of the present invention; Figure 16 is a plan view showing a first preferred embodiment of the knee ligament relaxation measuring device of the present invention; Figure 17 is a plan view of the first preferred embodiment of the knee ligament relaxation measuring device of the present invention; A top view of a first preferred embodiment of the joint ligament relaxation measuring device, illustrating that the left and right force applying members push the second casing outward; FIG. 18 is a first preferred embodiment of the knee ligament relaxation measuring device of the present invention. Example Figure 28 is a plan view showing the first preferred embodiment of the knee ligament relaxation measuring device of the present invention; FIG. 20 is a top view of the knee joint of the present invention; FIG. 21 is a partially enlarged view of a first preferred embodiment of the knee ligament relaxation measuring device of the present invention; FIG. 22 is a partial enlarged view of the knee joint ligament relaxation measuring device of the present invention; Figure 2 is a perspective view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention; Figure 24 is a perspective view of the knee ligament relaxation metric of the present invention; 2 is an exploded perspective view of a second preferred embodiment of the measuring device; FIG. 25 is an exploded perspective view of the first measuring mechanism of the second preferred embodiment of the knee ligament relaxation measuring device of the present invention; FIG. 27 is a side view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention; FIG. 28 is a side view of the second preferred embodiment of the knee ligament relaxation measuring device; Invention knee FIG. 29 is a side elevational view of a second preferred embodiment of the knee ligament relaxation measuring device of the present invention; FIG. 29 is a side view of the second preferred embodiment of the knee ligament relaxation measuring device of the present invention Figure 30 is a side view of a second preferred embodiment of the knee joint ligament relaxation measuring device of the present invention, in which the front and rear force applying members are pushed back to the calf sleeve mechanism. . 30 201238563 [Explanation of main component symbols] 11................. thigh 111........ Femur 12 .......... Calf 121......... .胫骨13 .......... . Anterior cruciate ligament 14.......... Posterior cruciate ligament 15 .... ... medial ligament 16 .......... lateral band 17 .......... tibia 200 '210... • knee ligament relaxation measuring device 2 ' V ... thigh socket mechanism 21 .......... first set of shells 211 '311..... front wall 212, 312...... side wall 213 '313.. .. .Perforation 214..............; front end face 215.............. $side 22 ' 32 ... forced module 221 > 321.... • Tightening member 222'322.... Knob 223, 323...... Tightening plate 224, 324··.. • Screw 225'325..... screw Hole 23, 34·..·Fixing belt 231, 341.....first belt body 232, 342····Second belt body 24 .......... second consumption Piece 25 ' 36····Pivot seat 26 ..........4·27 ..........Second grip 3, 3 '...Legs splicing mechanism 31 ..........The second set of shells 314 .........the second front end face 315 ......... brother - side 33 ... ....extension 35 .......... first bearing member 37 ..... third shaft 38 ..... left and right direction of the force member 381 ... ...connecting portion 382 ......... urging portion 4, 4 '...first measuring mechanism 41, 41'.. carrying frame 4U, 41 Γ.. Body 412, 417... first shaft 413......... bushing
S 31 201238563 414......... 穿孔 415 ' 418... ..第一樞接軸 416......... 第一接合件 42.......... 伸縮連桿模組 421......... 第一滑接件 422......... 第二滑接件 423......... 極接架 424......... 上樞接端 425......... 滑軌 426......... 滑動架 427......... 滑塊 428......... 滑槽 429......... 接合件 430、445 .. 第二轴 431......... 下樞接端 432......... 長形滑槽 433、446 .. 第二檀接轴 44 .......... ，前後向施力桿件 440......... ，桿件本體 441......... 銷部 44Γ ....... 極接部 442......... ,施力部 443......... 隔板 444......... 第二接合件 45 ..........第一力量感測元件 46 ..........第一位移感測元件 461 ...............本體 462 ...............探針 463 .........接觸板 47 ..........第一握把 5............第二量測機構 50 ..........固定板 51 ..........側伸縮連桿模組 511 .........第一連接單元 512 .........第二連接單元 513 .........第一連接件 514 .........套筒 515 .........第二連接件 516 .........導桿 517 .........第一鉸鍊件 518 .........第一樞接轴部 519 .........第二鉸鍊件 520 .........第二樞接軸部 53 ..........第二力量感測元件 54 ..........第二位移感測元件 541 .........本體 542 .........探針 55 ..........第三位移感測元件 32 201238563 551.•… ....本體 62 .. ........導線 552•.… ....探針 63 ·· ........電腦本體 6........ ....電腦 91〜 96.…步驟 61 ...... ....多通道轉接盒 91’〜93’ .步驟S 31 201238563 414......... Perforation 415 ' 418... The first pivoting shaft 416......... The first engaging member 42........ .. Telescopic connecting rod module 421......... First sliding member 422......... Second sliding member 423......... 424......... Upper pivot joint 425......... Slide rail 426......... Slider 427......... Slider 428......... Chute 429......... Engagement members 430, 445.. Second shaft 431......... Lower pivot end 432... ...... long chute 433, 446.. second tandem shaft 44 .........., front and rear force applying rods 440........., rod Piece body 441......... pin portion 44Γ....... pole portion 442........., force applying portion 443......... Plate 444......... second engagement member 45 ..... first force sensing element 46 ..... first displacement sensing element 461 ...............body 462 ...............probe 463 .........contact plate 47 ... .......the first grip 5............the second measuring mechanism 50 ..........fixing plate 51 .... ...the side telescopic link module 511 ....the first connection unit 512 ....the second connection unit 513 ......... Connector 514 ......... sleeve 515 ... ... second connector 516 ... ... guide rod 517 ......... The first hinge member 518 ... the first pivoting shaft portion 519 ... the second hinge member 520 ... ... the second pivoting shaft portion 53 .......... second force sensing element 54 ..... second displacement sensing element 541 ... ... body 542 .... .....probe 55 ..... third displacement sensing element 32 201238563 551.•.... body 62 .. ........ wire 552•. ..... Probe 63 ·· ........ Computer Body 6........ .... Computer 91~96....Step 61 ...... Multi-channel transfer box 91'~93'. Steps