201004606 九、發明說明： 【發明所屬之技術領域】 本發明是有關於一種測量裝置，特別是指一種手持气 肌肉痙攣測量裝置。 【先前技術】 腦性麻痒病患的下肢肌肉張力增強（稱為痙攣， spasticity)，常造成步行的阻礙，是臨床治療（手術、藥物） 的一個標的。目前臨床上評估痙攣使用的是非量化的方式 ，常見的如測試者牽拉肢體，憑阻力感覺給予〇 5分六種 等級；或者以不同的速度牽拉肢體，目測或以量角器量測 受限角度差異，以判斷神經反射的影響程度。對於臨床人 員（例如醫師、治療師），若需在治療前後或長時間觀察痙 攣變化ί更又限於量表式臨床評估方式無法提供足夠準確 的量化數據，故近二十年來，各國臨床研究單位皆嘗試著 發展標準化的量化方式，可惜目前尚無統一標準。 過去量化痙攣之技術手段，主要是採用馬達牵拉系統 (Motor-based system)，並配合扭力感測器記錄阻力，其優 點在於控制及量測精確，但缺點則是體積龐大、造價昂貴 ，無法靈活應用於臨床，實用性並不佳，進而無法普及化 〇 【發明内容】 因此，本發明之目的，即在提供—種體積小、重量輕 、臨床實用性高的下肢肌肉痙攣測量裝置。 於疋，本發明之下肢肌肉癌擎測量裝置，是供臨床人 5 201004606 員使用並測量患者下肢肌肉的痙攣狀況，該下肢肌肉痙攣 - 測量裝置包含：一座體單元、一力感測元件，及一速度感 測元件。 該座體單元具有一頂抵於該患者下肢的底座，及一可 相對於該底座運動並設置於該底座上且提供給臨床人員予 以施力的施力座。 該力感測元件是夾設於該底座及該施力座之間，並感 應該臨床人員對該施力座施力以連動該底座推抵該患者下 ® 肢，配合患者下肢所產生之反饋力量相配合地在該施力座 及該底座之間所形成的壓迫力。 該速度感測元件是設置於該底座上，並偵測該底座受 力而移動時之角速度。 本發明之功效在於，臨床人員可施力推抵該施力座以 使該底座頂抵於患者下肢之欲測量部位，並藉由該力感測 元件測量形成於該施力座及該底座之間的壓迫力，以紀錄 患者下肢在臨床人員牵拉過程中的阻力變化，再配合該速 ® 度感測元件測量該患者下肢在受到該臨床人員牽拉過程的 角速度’進而推算出患者下肢之阻力及角度受限程度等量 化數據。 【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一個較佳實施例的詳細說明中，將可 清楚的呈現。 參閱圖1、2’本發明下肢肌肉痙攣測量裴置之較佳實 6 201004606 施例’是供臨床人員100握持使用並測量患者下肢肌肉的 痙攣狀況，該下肢肌肉痙攣測量裝置包含：一座體單元1、 一力感測元件2、一資料傳輸埠5，及一速度感測元件3。 該座體單元1具有一頂抵於該患者下肢的底座U、複 數連接件4,及一可相對於該底座η運動並設置於該底座 11上且提供給臨床人員1〇〇予以施力的施力座12«該底座 11具有一本體111，及一與該本體111相連接的頂抵部112 ，該等連接件4是相間隔並可滑動地穿伸設置於該底座i j 之本體111上，並與該施力座12相連接以將該施力座12可 活動地撐立於該底座11上’該頂抵部112是頂抵於該患者 之腳掌200底部。在本實施例中，該底座丨丨是由硬質塑鋼 所製成，而該施力座12則為金屬，且該座體單元1之整體 體積約為5x5.5x3.5公分，另外，該施力座12上更形成有 一凹陷部121，以方便該臨床人員100以拇指扶持抵於腳掌 ，並透過施力座12進行牽拉。 該力感測元件2是設置於該底座丨丨之本體U1上並 夾設於該底座11之本體111及該施力座12之間，以感應該 臨床人員100對該施力座12施力後及患者下肢阻力形成於 該她力座12及§亥底座11之間的壓迫力，一般來說，該臨床 人員100會將手部之拇指推抵於該施力座12之凹陷部121 以對其施力，以使該施力座12是朝該底座n之本體lu以 及該患者之腳掌200方向推擠，並壓迫該力感測元件2，且 在施力的同時，該施力座12即會帶動該底座u之本體m 與頂抵部112朝該患者之腳掌200處推去，而該患者之腳掌 7 201004606 200在接受到此一牵拉時，患者處於痙攣狀態之小腿後側肌 肉會因為牵拉產生一股反饋力量，也同時被該力感測元件2 記錄下來。 參閱圖3、4，在此要注意的是，該等連接件4是搭載 該施力座12在相對於該底座π的一自由位置與一壓迫位置 間移動，當該施力座12是位於自由位置時，即不會壓迫到 該力感測元件2’且該施力座12與該底座11之本體之 間形成有一間隙，而當該施力座12是位於壓迫位置時，即 會緊靠於該本體111並對該力感測元件2形成壓迫。此外， 由於該施力座12之整體面積較大’又是藉由該等連接件4 來撐立於該底座11上’因此，當該臨床人員1〇〇藉由拇指 施力於該施力座12來連動其壓迫該力感測元件2時，也可 藉由該等連接件4將該施力座12垂直導向該力感測元件2 ’使該力感測元件2可感受到均勻之正向力量值，進而提 升力量感測的靈敏度與正確性。 在本實施例中所使用的力感測元件2為一用於感測正 向力之感應元件’而此種力感應元件2應為所屬技術領域 中具有通常知識者所熟悉的’在此即不對其細部結構以及 工作原理進行介紹。 回顧圖1，該速度感測元件3是設置於該底座11之本 體111上並偵測該底座11受力後所產生的角速度（angular velocity) ’本實施例是採用一微型速度感測元件3(如咖 Chip Yaw Rate Gyro)來進行角速度的偵測。 該資料傳輸埠5則是設置於該底座11之本體π!上， 8 201004606 並與一外界裝置300電連接（例如―雪腿 m 、_ 電腦’圖中未顯示），以 進行資料數據的傳輸，而該資料傕於 寸得輸埠5同時是與該速度 感測元件3及該力感糾件2電連接，以將該速度感測元 件3及該力感測元件2所偵測到之資料傳輸至該外界裝置 300進行處理。 四頻圖 1、2201004606 IX. Description of the Invention: [Technical Field] The present invention relates to a measuring device, and more particularly to a hand-held muscle muscle spasm measuring device. [Prior Art] The increased muscle tone of the lower extremities (called spasticity) in cerebral palsy patients often causes obstacles to walking and is a target for clinical treatment (surgery, drugs). At present, the clinical evaluation of sputum is a non-quantitative method. Commonly, if the tester pulls the limb, he or she will give 〇5 points and six grades according to the resistance feeling; or pull the limb at different speeds, visually measure or limit the angle by a protractor. Differences to determine the extent of the effects of neural reflexes. For clinical staff (such as physicians, therapists), if you need to observe the changes before and after treatment, or if the scale-based clinical evaluation method can not provide accurate and accurate quantitative data, in recent 20 years, clinical research units in various countries All attempts to develop standardized quantitative methods, but unfortunately there is no uniform standard. In the past, the technical means of quantifying 痉挛 was mainly to use a motor-based system and to record the resistance with a torque sensor. The advantage is that the control and measurement are accurate, but the disadvantage is that it is bulky and expensive. The invention is applicable to clinical use, and is not practical enough to be popularized. [Explanation] Therefore, an object of the present invention is to provide a lower limb muscle spasm measuring device which is small in size, light in weight, and highly clinically practical. Yu Yu, the lower limb muscle cancer measuring device of the present invention is used by a clinical person 5 201004606 to measure the paralysis condition of the lower limb muscle of the patient, the lower limb muscle spasm - measuring device comprises: a body unit, a force sensing element, and A speed sensing element. The base unit has a base that abuts against the lower limb of the patient, and a force-applying seat that is movable relative to the base and disposed on the base and provides a force to the clinical staff. The force sensing component is sandwiched between the base and the force applying seat, and senses that the clinical staff applies a force to the force applying seat to interlock the base to push the lower limb of the patient, and cooperates with the feedback force generated by the lower limb of the patient. Cooperatingly forming a pressing force between the force applying seat and the base. The speed sensing component is disposed on the base and detects an angular velocity when the base is forced to move. The effect of the present invention is that the clinical staff can push the urging seat to push the base against the intended part of the patient's lower limb, and measure the force formed between the urging seat and the base by the force sensing component. Compressive force to record the resistance change of the patient's lower limb during the pulling of the clinical staff, and then use the speed sensory component to measure the angular velocity of the lower limb in the patient's pulling process, and then calculate the resistance of the lower limb of the patient and Quantitative data such as the degree of angle limitation. 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. Referring to Figures 1, 2', the preferred embodiment of the lower extremity muscle spasm measurement device of the present invention is as follows: 201004606 The application example is for the clinical staff 100 to use and measure the paralysis condition of the lower limb muscle of the patient. The lower limb muscle spasm measurement device comprises: a body The unit 1, a force sensing element 2, a data transmission port 5, and a speed sensing element 3. The base unit 1 has a base U that abuts against the lower limb of the patient, a plurality of connecting members 4, and a movable base relative to the base η and disposed on the base 11 and provided to the clinical staff for exerting force. The base 11 has a body 111 and a top abutting portion 112 connected to the body 111. The connecting members 4 are spaced apart and slidably disposed on the body 111 of the base ij. And being coupled to the force-applying seat 12 to movably support the force-applying seat 12 on the base 11 'the top abutting portion 112 is abutting against the bottom of the patient's foot 200. In this embodiment, the base cymbal is made of hard plastic steel, and the urging seat 12 is made of metal, and the overall volume of the base unit 1 is about 5×5.5×3.5 cm, in addition, the urging seat A depression 121 is formed on the 12 to facilitate the clinical staff 100 to hold the thumb against the sole of the foot and pull through the force applying seat 12. The force sensing component 2 is disposed on the body U1 of the base and is interposed between the body 111 of the base 11 and the force applying seat 12 to sense the clinical staff 100 applying force to the force applying seat 12 and The patient's lower limb resistance is formed between the force of the force 12 and the base 11 of the force. Generally, the clinician 100 pushes the thumb of the hand against the depression 121 of the force-applying seat 12 to apply thereto. a force such that the force applying seat 12 pushes toward the body lu of the base n and the foot 200 of the patient, and presses the force sensing element 2, and the force applying seat 12 drives the force applying block 12 while applying the force The body m of the base u and the abutting portion 112 are pushed toward the foot 200 of the patient, and when the patient's foot 7 201004606 200 receives the pulling, the back muscle of the lower leg of the patient is in a paralyzed state due to pulling A feedback force is generated and also recorded by the force sensing component 2. Referring to Figures 3 and 4, it should be noted that the connecting members 4 are mounted with the force applying seat 12 to move between a free position relative to the base π and a pressing position, when the force applying seat 12 is in a free position. At that time, the force sensing element 2' is not pressed and a gap is formed between the force applying seat 12 and the body of the base 11, and when the force applying seat 12 is in the pressing position, it abuts against the body. 111 and the force sensing element 2 is pressed. In addition, since the overall area of the force applying seat 12 is larger, it is supported by the connecting member 4 on the base 11. Therefore, when the clinical staff 1 is biased by the thumb to the force applying seat 12 When the force sensing element 2 is pressed in conjunction with the force sensing element 2, the force applying member 12 can be vertically guided to the force sensing element 2' so that the force sensing element 2 can feel a uniform positive force. Value, which in turn increases the sensitivity and correctness of force sensing. The force sensing element 2 used in the present embodiment is an inductive element for sensing a positive force, and such a force sensing element 2 should be familiar to those of ordinary skill in the art. The detailed structure and working principle are not introduced. Referring to FIG. 1, the speed sensing component 3 is disposed on the body 111 of the base 11 and detects the angular velocity generated by the base 11 after being stressed. In this embodiment, a micro speed sensing component 3 is used. (Chip Yaw Rate Gyro) for angular velocity detection. The data transmission port 5 is disposed on the body π! of the base 11, 8 201004606 and is electrically connected to an external device 300 (for example, "snow leg m, _ computer" is not shown in the figure) for data data transmission. And the data is electrically connected to the speed sensing component 3 and the force sensing component 2 to detect the velocity sensing component 3 and the force sensing component 2 The data is transmitted to the external device 300 for processing. Quad-frequency diagram 1, 2
不貫她例之作動方式如下：當該臨床人 員100需要牵拉該患者之下肢肌肉（例如小腿後侧之肌肉）以 測量其痙攣程度時，首先，是將該底座u之頂抵部112頂 抵於該患者之腳掌底部的突起部㈣㈣，再對該 施力座12進行施力，以使該施力座12是朝該底座u之本 體⑴以及該患者之腳掌200方向推擠，在施力的同時該 施力座12即會帶動該座體之本體lu與頂抵部ιΐ2朝該患 者之腳掌2GG處推去’而該患者之腳掌在接受到此—The insufficiency of her example is as follows: When the clinician 100 needs to pull the lower limb muscles of the patient (such as the muscles on the back side of the calf) to measure the degree of paralysis, firstly, the top of the base u is abutted to the top 112 Abutting the protrusion (4) (4) at the bottom of the sole of the patient, the force applying seat 12 is biased so that the force applying seat 12 is pushed toward the body (1) of the base u and the foot 200 of the patient, At the same time, the force applying seat 12 will drive the body lu and the abutting portion ι 2 of the seat body to push toward the foot 2GG of the patient', and the patient's foot receives the same -
牵拉時，其腳冑細特朝該臨床人貞100施力之相同方 向仰動’❿此仰動速度（牵拉速度）及關節角度變化（以患者 之腳踩為軸心）即會被該速度感測元件3所偵測及計算求得 該力感測元件2所偵測到之壓迫力，以及該速度感測 7L件3所偵測到之兩個方向的仰動速度即會藉由該資料傳 輸埠5傳送至該外界裝置3〇〇，而該外界裝置3〇〇即會利用 此資料進行牽拉速度及回饋阻力等量化數據的推算，進而 供臨床人員100判斷患者小腿後側之肌肉的痙攣程度。 此外’更可藉由該外界裝置300對該速度數據進行積 分即可得出位置，再把位置及回饋阻力之變化畫在—起， 9 201004606 即可以判斷出該關節（在本實施例中為患者之踩關節）可以牵 拉的範圍有多少。When pulling, the ankles are tilted in the same direction as the clinical person's 施100 force. 'The swaying speed (the pulling speed) and the joint angle change (with the patient's foot as the axis) will be The speed sensing component 3 detects and calculates the pressing force detected by the force sensing component 2, and the tilting speed of the two directions detected by the speed sensing 7L member 3 is borrowed. The data transmission 埠5 is transmitted to the external device 3〇〇, and the external device 3〇〇 uses the data to calculate the quantitative data such as the pulling speed and the feedback resistance, and then the clinical staff 100 determines the back side of the patient's lower leg. The degree of muscle sputum. In addition, the position can be obtained by integrating the speed data by the external device 300, and then the position and the feedback resistance change can be drawn, and the joint can be judged in 9 201004606 (in this embodiment, The extent to which a patient's foot joint can be pulled.
藉由上述設計，本發明下胩B +奴a r腹肌肉痙攣測量裝置，誠然 具有下列優點： 1 _有效量化痙攣程度之測量： 本發明利用該座體單a 1搭載該力感測元件2 及速度感測元件3來_患者之反饋阻力、牵拉速With the above design, the lower jaw B + slave ar abdominal muscle spasm measuring device of the present invention has the following advantages: 1 _ Quantitative quantification of the degree of measurement: The present invention uses the body single a 1 to mount the force sensing element 2 and Speed sensing element 3 comes to the patient's feedback resistance, pull speed
度，及角度受限程度，能有效地將偵測方式量化， 使臨床人員100在判斷患者之座攀程度時能夠藉 由量化之數據來作為判斷之基礎，而不是如習知般 依據臨床人貝100之牵拉患者肢體所得知的阻力感 覺來進行判斷，進而有助於建立—套標準化的瘦擎 程度量化判斷標準。 2.臨床實用性佳·· 由於本發明是採用體積小、輕量化（整鱧裝置重 量小於100克）的設計方式，可供臨床人員手持 並輕易地對其進行操作，且不受限於使用場合，因 此無論是在實驗室、診間、病房、手術室等場合皆 可使用’使用靈活性及實用性佳，有效改善習知馬 達牽拉系統體積龐大，造價昂貴進而無法靈活應用 於臨床的缺點。 歸納上述，本發明之下肢肌肉痙攣測量裝置，使臨床 人員H)〇可施力推抵該施力S 12以使該底S u⑽於患者 下肢之欲測量部位，並藉由該力感測元件2測量形成於該 10 201004606 u &㈣座n之間㈣迫力以推算患者下肢對於 臨床人員100所施之力量的回饋阻力，再藉由該速度感測 元件3測量„亥底座1!受力後所產生的角速度進而提供阻 力、牽拉速度’及角度受限程度的量化數據，進而達到有 效量化痙攣程度之測量’且其手持式及輕量化之設計也可 令其具有極佳的臨床實用性，故確實能達到本發明之目的 〇 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疋一立體圖，說明本發明下肢肌肉痙攣測量裝置 之較佳實施例與一外界裝置的連接情形； 圖2疋一使用狀慂示意圖，說明該較佳實施例之使用 狀態； 圖3是一側視圖，說明該較佳實施例之一施力座位於 一自由位置的情形（省略臨床人員手部）；及 圖4疋一侧視圖，说明該施力座位於一壓迫位置的情 形（省略臨床人員手部）。 11 201004606 【主要元件符號說明】 1…… •…座體單元 3…… •…速度感測元件 11 ·.··. •…底座 4…… •…連接件 111… •…本體 5 ....... •…資料傳輸埠 112… 頂抵4 100… •…臨床人員 12··.·. —施力座 200… •…腳掌 121… •…凹陷部 300… •…外界裝置 2 ....... •…力感測元件Degree, and degree of angle limitation, can effectively quantify the detection method, so that the clinician 100 can use the quantified data as the basis for judgment when judging the degree of the patient's seat, instead of relying on the clinical person as is conventional. Bayer 100 pulls the resistance feelings of the limbs of the patient to judge, and thus helps to establish a standardized quantitative evaluation criteria. 2. Clinical applicability is good. · Because the invention adopts a design method that is small in size and light in weight (the weight of the whole device is less than 100 grams), it can be manually and easily operated by clinical personnel, and is not limited to use. Occasionally, it can be used in laboratories, clinics, wards, operating rooms, etc. 'Using flexibility and practicality, effectively improving the size of the conventional motor pulling system, making it expensive and inflexible for clinical use. Disadvantages. In summary, the lower limb muscle spasm measuring device of the present invention causes the clinical staff to apply a force to the force S 12 to make the bottom point S 10 (10) to the desired part of the patient's lower limb, and the force sensing element 2 The measurement is formed between the 10 201004606 u & (4) n (four) force to estimate the resistance of the patient's lower limbs to the force applied by the clinical staff 100, and then measured by the speed sensing component 3 „海底座1! After the force The resulting angular velocity in turn provides quantitative data on resistance, pulling speed' and angle-limited extent, which in turn enables effective quantification of the degree of measurement' and its hand-held and lightweight design also provides excellent clinical utility. Therefore, it is to be understood that the foregoing is only a preferred embodiment of the present invention, and is not intended to limit the scope of the invention, that is, the scope of the invention and the description of the invention The simple equivalent changes and modifications made are still within the scope of the present invention. [Simplified Schematic] FIG. 1 is a perspective view showing the lower extremity muscle spasm of the present invention. FIG. 2 is a side view showing the state of use of the preferred embodiment; FIG. 3 is a side view showing a preferred embodiment of the preferred embodiment; The situation in which the force seat is in a free position (the hand of the clinician is omitted); and the side view in Fig. 4 shows the case where the force application seat is in a pressing position (the hand of the clinician is omitted). 11 201004606 [Description of main component symbols] 1...... •...seat unit 3... •...speed sensing element 11 ····. •...base 4... •...connector 111... •...body 5 ....... •...data transfer埠112... The top reaches 4 100... •...clinical staff 12····. — force seat 200... •...foot 121...•...recessed 300... •...external device 2 ....... •...force Sensing element
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