TWM522700U

TWM522700U - Laser ranging perspective oblique angle measurement device

Info

Publication number: TWM522700U
Application number: TW105202948U
Authority: TW
Inventors: Huan-Wen Zhong; Yu-Jun Zeng; chao-yi Wang; yuan-rui Li; wei-xin Chen; zhi-yi Chen; Yi-Huan Hong; de-qing Chen
Original assignee: de-qing Chen
Priority date: 2016-03-03
Filing date: 2016-03-03
Publication date: 2016-06-01

Description

雷射測距斜視斜位角度量測裝置Laser ranging strabismus oblique angle measuring device

本創作係有關一種雷射測距斜視斜位角度量測裝置，尤指一種兼具多種感測可同步進行提高量測準確度、便於對語言表達不佳之患者進行斜視量測與便於對斜視患者進行術後視力訓練腦波融像量測之雷射測距斜視斜位角度量測裝置。The present invention relates to a laser ranging strabismus oblique angle measuring device, in particular to a patient who has multiple sensing and can simultaneously improve the measurement accuracy, facilitate strabismus measurement for patients with poor language expression and facilitate strabismus patients. A laser ranging strabismus oblique angle measuring device for post-operative vision training brain wave fusion measurement.

斜視為眼睛視線異常的其中一種狀況，可以眼球追蹤(Eye Tracking)量測斜視斜位角度變化。目前之裝置包括下列幾種：　　第一個類型為特殊隱形眼鏡與嵌入的鏡子或電磁感應器，測量其眼球運動的附件。其中與眼球貼合的隱形眼鏡提供了較為敏感的紀錄，是研究者研究學習動機和眼位運動模式的首選方法。鞏膜搜索線圈(Scleral Search Coil)即是一款利用電磁感應原理來測量眼位移動的眼球追蹤裝置。方法的優點是有很好的空間和時間(1毫秒)解析度，缺點是量測方式很容易受到受測者當時眼球狀況的影響，如眼球之分泌物等，且不適合長期配戴(通常不能長於 30分鐘)，又，軟式鏡片具有雙層架構，侵入性的方式可能會影響使用者的視力。　　第二種類型是使用一些非接觸式光學方法測量眼球運動，反映從眼睛到感應攝影機或其他特別設計的光學感應器，這種方式易受可見光影響，且每人眼球組織的折射率不同，反射出來的影像也會不同，會影響測量結果的準確性。　　第三種在眼睛周圍設置電磁測量電位，可在完全黑暗的場所中檢測，利用攝影機實際拍攝眼球的位置來測量眼球的運動。首先給受試者帶一個帽子，上面有兩個攝影機分別拍攝兩隻眼睛的位置，帽子上另有一攝影機對應螢幕上四個點來校正頭的位置。偵測眼睛的攝影機係測量瞳孔的移動來計算眼球的移動。缺點是戴久了(超過 1-2 小時)會不舒服。　　目前並沒有同時以多種感測器、非侵入性設備之雷射測距斜視斜位角度量測裝置。The oblique direction is regarded as one of the abnormalities of the eyesight of the eye, and the angle of the oblique position of the strabismus can be measured by Eye Tracking. Current devices include the following: The first type is a special contact lens with an embedded mirror or electromagnetic sensor that measures the attachment of the eye movement. The contact lens that fits the eyeball provides a more sensitive record and is the preferred method for researchers to study learning motivation and eye movement patterns. The Scleral Search Coil is an eye tracking device that uses the principle of electromagnetic induction to measure eye movement. The advantage of the method is that it has good space and time (1 millisecond) resolution. The disadvantage is that the measurement method is very susceptible to the eye condition of the subject at the time, such as the secretion of the eyeball, etc., and is not suitable for long-term wear (usually not More than 30 minutes), in addition, the soft lens has a two-layer structure, and the invasive way may affect the user's vision. The second type uses some non-contact optical methods to measure eye movements, reflecting from the eye to an inductive camera or other specially designed optical sensor, which is susceptible to visible light and has a different refractive index per person's eye tissue. The images that come out will also be different, which will affect the accuracy of the measurement results. The third type is to set the electromagnetic measurement potential around the eyes, which can be detected in a completely dark place, and the position of the eyeball is actually taken by the camera to measure the movement of the eyeball. First, the subject is given a hat with two cameras on which to take the positions of the two eyes. Another camera on the hat corresponds to four points on the screen to correct the position of the head. The camera that detects the eye measures the movement of the pupil to calculate the movement of the eye. The downside is that wearing it for a long time (more than 1-2 hours) will be uncomfortable. At present, there is no laser slanting slanting angle measuring device for a plurality of sensors and non-invasive devices.

本創作之目的，在於提供一種雷射測距斜視斜位角度量測裝置，其兼具多種感測可同步進行提高量測準確度、便於對語言表達不佳之患者進行斜視量測與便於對斜視患者進行術後視力訓練腦波融像量測等優點。特別是，本創作所欲解決之問題係在於目前並沒有同時以多種感測器、非侵入性設備之雷射測距斜視斜位角度量測裝置等問題。解決上述問題之技術手段係提供一種雷射測距斜視斜位角度量測裝置，其包括：一視線導引部，係設於一虛擬兩眼視線交會點位，用以導引一待測者之視線；該待測者具有一頭部及兩眼，其中之一為正常眼；其中之另一為斜視眼，該斜視眼具有一眼虛擬點位；當該正常眼之視線朝向該虛擬兩眼視線交會點位，則該斜視眼因斜視而使視線偏向一虛擬斜視點位，並當該正常眼之視線被遮覆，則該斜視眼之視線自動轉向該虛擬兩眼視線交會點位；一斜視線矯正裝置，係可轉動的設於該斜視眼與該虛擬斜視點位之間，並具有一矯正虛擬點位，該斜視線矯正裝置係用以轉動反射而將該斜視眼之視線矯正至該虛擬兩視線交會點位；一腦波擷取部，係設於該待測者之該頭部，而擷取其腦波訊號，該腦波訊號係對應該待測者之兩眼視力，而具有一放鬆度訊號及一專注度訊號，當該正常眼之視線朝向該虛擬兩眼視線交會點位，且該斜視眼因斜視而使視線偏向該虛擬斜視點位，則該待測者之視力呈模糊，該放鬆度訊號與該專注度訊號不交會；反之，當該正常眼之視線朝向該虛擬兩眼視線交會點位，且該斜視眼之視線被矯正至該虛擬兩眼視線交會點位，則該待測者之視力呈清楚，該放鬆度訊號與該專注度訊號產生一交會點；用以確認該斜視眼位於一矯正後眼位角度；一雷射測距模組，係可於一第一測距位置、一第二測距位置、一第三測距位置之間變換；當位於該第一測距位置，係可量得該矯正虛擬點位與該眼虛擬點位之間的一第一邊長，當位於該第二測距位置，係可量得該虛擬兩眼視線交會點位與該矯正虛擬點位之間的一第二邊長，當位於該第三測距位置，係可量得該虛擬兩眼視線交會點位與該眼虛擬點位之間的一第三邊長，而可根據餘弦定理運算出一雷射測距角度，其應接近該矯正後眼位角度；一不可見光檢測模組，係包括一不可見發光裝置、一左側不可見光影像擷取裝置及一右側不可見光影像擷取裝置；該不可見光發光裝置係用以朝該兩眼發出一不可見光，而可於該斜視眼上產生不可見反射光點；當該斜視眼之視線從該虛擬斜視點位矯正至該虛擬兩眼視線交會點位時，該左側不可見光影像擷取裝置及該右側不可見光影像擷取裝置同時用以擷取該斜視眼之不可見反射光影像，而可得到一眼位追蹤角度，其係接近該矯正後眼位角度；一總控制部，係電性連結該視線導引部、該斜視線矯正裝置、該腦波擷取部、該雷射測距模組、該不可見光檢測模組其中至少一者，而用以控制其動作。本創作之上述目的與優點，不難從下述所選用實施例之詳細說明與附圖中，獲得深入瞭解。茲以下列實施例並配合圖式詳細說明本創作於後：The purpose of the present invention is to provide a laser ranging strabismus oblique angle measuring device, which has multiple sensing functions, can simultaneously improve the measurement accuracy, and is convenient for strabismus measurement and convenient strabismus for patients with poor language expression. The patient has the advantages of postoperative vision training brain wave fusion measurement. In particular, the problem to be solved by the present invention is that there is currently no problem of a slanting slanting angle measuring device for a plurality of sensors and non-invasive devices. The technical means for solving the above problem is to provide a laser ranging slanting oblique angle measuring device, comprising: a line of sight guiding portion, which is disposed at a virtual two-eye line of sight intersection point for guiding a person to be tested a line of sight; the subject has a head and two eyes, one of which is a normal eye; the other of which is a squint eye having a virtual point of sight; when the line of sight of the normal eye is toward the virtual eye When the line of sight meets, the squint eye is biased toward a virtual squint point due to squint, and when the line of sight of the normal eye is covered, the line of sight of the squint eye automatically turns to the virtual eye line intersection point; The squint line correction device is rotatably disposed between the squint eye and the virtual squint point, and has a corrected virtual point device for rotating the reflection to correct the line of sight of the squint eye to The virtual two-vision intersection point; a brain wave capturing part is disposed on the head of the subject to be tested, and extracts a brain wave signal, the brain wave signal is corresponding to the vision of the two eyes of the person to be tested, Have a relaxation signal and one The attention signal, when the line of sight of the normal eye is toward the intersection point of the virtual two-eye line of sight, and the squint eye is biased toward the virtual squint point due to squint, the visual acuity of the subject is blurred, and the relaxation signal is Contrary to the concentration signal; conversely, when the line of sight of the normal eye is toward the intersection point of the virtual two-eye line of sight, and the line of sight of the squint eye is corrected to the intersection point of the virtual two-eye line of sight, the person to be tested The visual acuity is clear, the relaxation signal and the concentration signal generate a meeting point; to confirm that the squint eye is located at a corrected eye position angle; a laser ranging module is at a first ranging position, a second ranging position and a third ranging position are transformed; when located at the first ranging position, a first side length between the corrected virtual point and the virtual point of the eye is quantifiable, When the second ranging position is located, a second side length between the virtual two-eye line of sight intersection point and the corrected virtual point is measured, and when located at the third ranging position, the quantity is determined Virtual two-eye line of sight intersection point and virtual point of the eye a third side length, and a laser ranging angle can be calculated according to the cosine theorem, which should be close to the corrected eye position angle; an invisible light detecting module includes an invisible light emitting device and a left invisible light An image capturing device and a right invisible image capturing device; the invisible light emitting device is configured to emit an invisible light to the two eyes, and generate an invisible reflected light spot on the squint eye; The left invisible image capturing device and the right invisible image capturing device simultaneously extract the invisible reflected light image of the squint eye when the line of sight is corrected from the virtual squint point to the virtual eye line intersection point. And obtaining an eye tracking angle, which is close to the corrected eye position angle; a total control unit electrically connecting the line of sight guiding portion, the squint line correcting device, the brain wave capturing portion, and the laser The at least one of the ranging module and the invisible light detecting module is configured to control the action thereof. The above objects and advantages of the present invention will be readily understood from the following detailed description of the embodiments and the accompanying drawings. The following examples are used in conjunction with the drawings to illustrate the creation in detail:

參閱第1及第2B圖，本創作係為一種雷射測距斜視斜位角度量測裝置，其包括：一視線導引部10，係設於一虛擬兩眼視線交會點位A，用以導引一待測者90之視線；該待測者90具有一頭部90A及兩眼，其中之一為正常眼91A(本案中係舉例右眼為正常眼)；其中之另一為斜視眼91B(本案中係舉例左眼為斜視眼)，該斜視眼91B具有一眼虛擬點位D；當該正常眼91A之視線朝向該虛擬兩眼視線交會點位A，則該斜視眼91B因斜視而使視線偏向一虛擬斜視點位B，並當該正常眼91A之視線被遮覆(如第2C圖所示)，則該斜視眼91B之視線自動轉向該虛擬兩眼視線交會點位A；一斜視線矯正裝置20，係可轉動的設於該斜視眼91B與該虛擬斜視點位B之間，並具有一矯正虛擬點位C，該斜視線矯正裝置20係用以轉動反射而將該斜視眼91B之視線矯正(矯正過程如第2C、第2D、第2E及第2F圖所示)至該虛擬兩視線交會點位A；一腦波(Electronecephalogram，簡稱EEG)擷取部30，係設於該待測者90之該頭部90A，而擷取其腦波訊號91，該腦波訊號91係對應該待測者90之兩眼視力，而具有一放鬆度訊號及一專注度訊號，當該正常眼91A之視線朝向該虛擬兩眼視線交會點位A，且該斜視眼91B因斜視而使視線偏向該虛擬斜視點位B，則該待測者90之視力呈模糊，該放鬆度訊號(如第6圖所示之放鬆曲線L1)與該專注度訊號(如第6圖所示之專注曲線L2)不交會；反之，當該正常眼91A之視線朝向該虛擬兩眼視線交會點位A，且該斜視眼91B之視線被矯正至該虛擬兩眼視線交會點位A，則該待測者90之視力呈清楚，該放鬆度訊號與該專注度訊號產生一交會點X；用以確認該斜視眼91B位於一矯正後眼位角度 (參閱第2C圖)；一雷射測距模組40，係可於一第一測距位置P1(參閱第4A圖，位於該矯正虛擬點位C)、一第二測距位置P2(參閱第4B圖，位於該虛擬兩眼視線交會點位A)、一第三測距位置P3(參閱第4C圖，鄰近該虛擬兩眼視線交會點位A，但角度與該第二測距位置P2不同)之間變換；當位於該第一測距位置P1，係可量得該矯正虛擬點位C與該眼虛擬點位D之間的一第一邊長，當位於該第二測距位置P2，係可量得該虛擬兩眼視線交會點位A與該矯正虛擬點位C之間的一第二邊長，當位於該第三測距位置P3，係可量得該虛擬兩眼視線交會點位A與該眼虛擬點位D之間的一第三邊長，而可根據餘弦定理運算出一雷射測距角度，其應接近該矯正後眼位角度；一不可見光檢測模組50，係包括一不可見發光裝置51、一左側不可見光影像擷取裝置52及一右側不可見光影像擷取裝置53；該不可見光發光裝置51係用以朝該兩眼發出一不可見光511，而可於該斜視眼91B上產生不可見反射光點 (如第3圖所示)；當該斜視眼91B之視線從該虛擬斜視點位B(如第2B圖所示的矯正前位置PA)矯正至該虛擬兩眼視線交會點位A(如第2F圖所示的矯正後位置PB)時，該左側不可見光影像擷取裝置52及該右側不可見光影像擷取裝置53同時用以擷取該斜視眼91A之不可見反射光影像50A，而可得到一眼位追蹤角度，其係接近該矯正後眼位角度；一總控制部60，係電性連結該視線導引部10、該斜視線矯正裝置20、該腦波擷取部30、該雷射測距模組40、該不可見光檢測模組50其中至少一者，而用以控制其動作。實務上，該視線導引部10可為視標、可見光裝置其中至少一者，用以導引該待測者90之視線。參閱第1圖，該腦波擷取部30又設有：一微處理器結構30A，係用以擷取特定頻段之該腦波訊號91，並儲存以供擷取，該微處理器結構30A可為型號“TGAMI”之訊號處理晶片；在此要特別說明的部分是，TGAM1訊號處理晶片之腳位包含了電源3.3V、接地(GND)、串列資料輸出(TX)、串列資料輸入(RX)、腦波訊號輸入(EEG)、腦波訊號接地(GND) 以及腦波訊號參考電位(REF)。 TGAM1訊號處理晶片同時保有腦波的擷取功能，其中包含了八個波段的腦波： [a] delta(0.5-2.75Hz)； [b] theta(3.5-6.75Hz)； [c] low-alpha(7.5-9.25Hz)； [d] high-alpha(10-11.75Hz)； [e] low-beta(13-16.75Hz)； [f] high-beta(18-29.75Hz)； [g] low-gamma(31-39.75Hz)； [h] high-gamma(41-49.75Hz)；其中，放鬆度訊號係取自low-beta(13-16.75Hz)及low-alpha(7.5-9.25Hz)兩個波段，這兩個值越大放鬆度越高。至於專注度訊號則取自low-gamma(31-39.75Hz)及high-gamma(41-49.75Hz)兩個波段，這兩個值越大專注度越高。本創作根據腦波國際定義及視力生理現象，將視力放鬆方程式定義如公式(1) ∙∙∙∙(1) 　　並將視力專注方程定義如公式(2) ∙(2) 　　該腦波訊號91係為該使用者90之大腦運轉所產生之電位差。一感測電極30B，係連結該微處理器結構30A，並用以貼設於該待測者90之頭部90A的一感測電極貼片位置Fp1上；一參考電極30C，係連結該微處理器結構30A，並用以貼設於該待測者90之頭部90A的一參考電極貼片位置A1上，而與該感測電極10B共同擷取該腦波訊號91，並傳送至該微處理器結構30A。參閱第5圖，該微處理器結構30A係包括：一放大器31、一類比/數位(A/D)轉換器32、一運算單元33、一帶通濾通器34及一快速傅立葉轉換單元(FFT)35；其中：該放大器31係用以接收該腦波訊號91，並進行訊號放大處理；該類比/數位(A/D)轉換器32，係用以讀取該放大器31進行訊號放大後之該腦波訊號91，並轉換出原始腦波資料(RAW EEG)，其概呈封包形式；該運算單元33，係用以讀取並分析該類比/數位(A/D)轉換器32處理後之該腦波訊號91之雜訊程度；該帶通濾波器34，係用以讀取該運算單元33分析後之該腦波訊號91，並進行濾波處理；該快速傅立葉轉換單元(FFT)35，係用以讀取濾波處理後之該腦波訊號91，並將腦波訊號91從時域訊號轉換為頻域訊號(公知技術，恕不贅述)，且區分出各頻段，例如：delta(0.5-2.75Hz)、theta(3.5-6.75Hz)、low-alpha (7.5-9.25Hz)、high-alpha(10-11.75Hz)、low-beta (13-16.75Hz)、high-beta(18-29.75Hz)、low-gamma (31-39.75Hz)，與high-gamma(41- 49.75Hz)；再將前述資料透過各頻段腦波數位資料(LONG EEG)封包處理，以供擷取。　　當將該腦波擷取部30 配戴於該待測者90之頭部90A，且該斜視眼91B從視線朝向該虛擬斜視點位B時，該待測者90之視力應呈現模糊，該放鬆度訊號(如第6圖所示之放鬆曲線L1)與該專注度訊號(如第6圖所示之專注曲線L2)不交會；反之，當該斜視眼91B之視線被矯正而朝向該虛擬兩眼視線交會點位A，則該待測者90之視力呈清楚，該放鬆度訊號與該專注度訊號產生一交會點X；此時可確認該斜視眼91B位於矯正後眼位角度 (參閱第2C圖)。該雷射測距模組40係將該第一邊長、該第二邊長及該第三邊長傳送至該總控制部60，供該總控制部60根據餘弦定理：進行運算；其中：；；；則可得到雷射測距角度，其應接近(最好狀態是等於)該矯正後眼位角度，而可輔助確認量測結果。在此要特別說明的部分是，參閱第2A圖，一般人之兩眼均為正常眼91A，兩眼之視線均朝向虛擬兩眼視線交會點位A。而如第2B圖所示，有的人其中一眼為斜視眼91B，其視線朝向一虛擬斜視點位B(具有一斜視眼位角度 )。斜視為一種潛在性眼位偏斜，但能在融合反射控制下保持雙眼單視，以強制兩眼球保持在正位而不顯出偏斜，一旦大腦融合作用遭到阻斷(如一眼被遮蓋時)或失去控制(如在過度使用目力或精神疲勞時)，眼位偏斜就會表現出來。本創作之斜視斜位角度矯正過程係如下所述：首先，先讓該待測者90之兩眼凝視遠方放鬆，待腦波呈現放鬆時，開始檢測，實驗測試時間共30秒鍾。 1.打開雙眼(如第2B圖所示)，右眼(即該正常眼91A)凝視該視線導引部10(位於該虛擬兩眼視線交會點位A上之遠方視標)，左眼(即該斜視眼91B)斜視另一視標(位於該虛擬斜視點位B上)，計時10秒。 2.遮蓋雙眼，計時10秒。 3.遮蓋右眼(如第2C圖所示)，則左眼(該斜視眼91B)之視線自動轉向該虛擬兩眼視線交會點位A(即該視線導引部10)； 4.移除右眼前方遮蓋板，旋轉平面鏡(即該斜視線矯正裝置20)，係可反射而將左眼(該斜視眼91B)之視線矯正(矯正過程如第2C、第2D、第2E及第2F圖所示)至該虛擬兩視線交會點A，使左、右眼同時正視該視線導引部10而產生融像(參閱第2F圖)。於前述斜視斜位角度矯正過程中，可進行下列三種量測模式： [a] 雷射測距量測模式：當該斜視眼91B位於該矯正後位置PB，將該雷射測距模組40分別移動至該第一測距位置P1(參閱第4A圖，位於該矯正虛擬點位C)、該第二測距位置P2(參閱第4B圖，該虛擬兩眼視線交會點位A)與該第三測距位置P3(參閱第4C圖，鄰近該虛擬兩眼視線交會點位A，但角度與該第三測距位置P3不同)；而分別量得該第一邊長、該第二邊長及該第三邊長，供該總控制部60根據餘弦定理運算而得到雷射測距角度，其應接近或是等於該矯正後眼位角度。 [b] 眼位追蹤量測模式：以該不可見光發光裝置51朝該兩眼發出不可見光511，而可於該斜視眼91B上產生不可見反射光點 (如第3圖所示)；當該斜視眼91B之視線從該虛擬斜視點位B(參閱第2B及第3圖，從矯正前位置PA及不可見反射光點，可測得一斜視眼位角度 )依序移動至一第一虛擬矯正點B1(如第2D及第3圖所示，此時從不可見反射光點測得一第一矯正眼位角度 )、一第二虛擬矯正點B2(如第2E及第3圖所示，從不可見反射光點可測得一第二矯正眼位角度 )移動到該虛擬兩眼視線交會點位A(參閱第2F及第3圖，從矯正後位置PB及不可見反射光點，可測得一眼位追蹤角度，其應等該矯正後眼位角度 )時，該左側不可見光影像擷取裝置52及該右側不可見光影像擷取裝置53同時用以擷取該斜視眼91A之不可見反射光影像50A，而可得到該眼位追蹤角度，可用以輔助確認該矯正後眼位角度。 [c] 腦波量測模式：當該斜視眼91B因斜視而使視線偏向該虛擬斜視點位B，則該待測者90之視力呈模糊，該放鬆度訊號(如第6圖所示之放鬆曲線L1)與該專注度訊號(如第6圖所示之專注曲線L2)不交會；反之，當該斜視眼91B之視線被矯正而朝向該虛擬兩眼視線交會點位A，則該待測者90之視力呈清楚，該放鬆度訊號與該專注度訊號產生一交會點X；用以確認該斜視眼91B位於矯正後眼位角度 (參閱第2C圖)。本創作進一步可再包括一斜視先行檢測裝置(設於該虛擬兩眼視線交會點位A上)，其具有一紅燈70A及一綠燈70B，正常而無斜視時，兩眼視線應朝向該斜視先行檢測裝置(如第2G圖所示)。而當其中之一眼為斜視時(假設右眼正常，左眼為斜視)，係先行檢測如下： 1.開啟該紅燈70A，其係發出一紅光701。此時該待測者90之右眼(即該正常眼91A)之視線會朝向該紅燈70A之光點，如第2H圖所示。同時，該待測者90之左眼(即斜視眼91B)應會偏斜，朝向該虛擬斜視點位B。 2.檢測人員詢問：請問看到什麼？該待測者90會回答：右眼看見紅光701。 3.遮蓋右眼(如第2I圖所示)，關閉紅燈70A並啟動綠燈70B，其係發出一綠光702。此時該待測者90之右眼(即該正常眼91A)被遮住，只能用左眼看。該待測者90之左眼(即斜視眼91B)則會偏斜回而注視此綠燈70B，即離開該虛擬斜視點位B之方向而回到正常之方向(該虛擬兩眼視線交會點位A)。 4.檢測人員詢問：請問看到什麼？由於此時之左眼(該斜視眼91B)之視線已轉向回該虛擬兩眼視線交會點位A處，該待測者90應是回答：看到綠光702。經上述過程即此可確認，該待測者90應適用本創作之測量。在此要額外說明的部分是，雙眼視覺(binocular vision)是指環境中物體的影像被聚焦且分別落在兩眼視網膜對應點上(主要指黃斑部)，因為落在視網膜上的光線會使視桿、視錐細胞產生動作電位，將所引起的電資訊沿視覺知覺系統傳入大腦，在大腦高級中樞把來自兩眼的視覺信號進行分析，綜合成一個完整的、具有立體感知的視覺印像過程。在雙眼視覺的產生過程中，感覺系統和運動系統是同時作用的。感覺系統是一個「看」的過程，眼睛將光線屈折聚集在視網膜上，視網膜將光的衝動傳遞到神經中樞，最後產生對物體形狀、顏色、運動和空間相對位置的認識，也就是將一眼的感覺資訊與另一眼的感覺資訊重合起來形成一單個像的能力，稱為「感覺融像」(sensory fusion)，為了使感覺融像出現，必須通過「運動融像」(moter fusion)使雙眼匹配一致，運動融像就是眼外肌為保持雙眼匹配而作出的反應。運動融像只有在感覺融像發生時才發生，運動融像是對感覺融像的反應；感覺融像只有當運動融像出現時才發生。而當雙眼產生融像(腦波融像)時，即為視力清晰的時候，此時該放鬆度訊號與該專注度訊號產生該交會點X。本創作之優點及功效係如下所述： [1] 多種感測可同步進行提高量測準確度。本創作同時設置雷射測距量測模式、眼位追蹤量測模式及腦波量測模式，可同時或分別進行量測斜視斜位角度，可將量得之角度重覆比對，提高量測準確度。故，多種感測可同步進行提高量測準確度。 [2] 便於對語言表達不佳之患者進行斜視量測。本創作係客觀量測斜視眼之角度變化，並不需要患者主觀表達視力之清晰度，對於語言障礙或語言表達能力比較差的斜視病患，完全不用考量其表達能力是否準確。故，便於對語言表達不佳之患者進行斜視量測。 [3] 便於對斜視患者進行術後視力訓練腦波融像量測。本創作不需要患者主觀表達視力之清晰度，對於術後患者，可直接進行術後視力訓練腦波融像量測。故，便於對斜視患者進行術後視力訓練腦波融像量測。以上僅是藉由較佳實施例詳細說明本創作，對於該實施例所做的任何簡單修改與變化，皆不脫離本創作之精神與範圍。 Referring to Figures 1 and 2B, the present invention is a laser ranging squint oblique angle measuring device, comprising: a line of sight guiding portion 10, which is disposed at a virtual two-eye line of sight intersection point A for Guiding a line of sight of the subject 90; the subject 90 has a head 90A and two eyes, one of which is a normal eye 91A (in this case, the right eye is a normal eye); the other is a squint eye 91B (in the present case, the left eye is a squint eye), the squint eye 91B has an eye virtual point D; when the line of sight of the normal eye 91A faces the virtual eye line intersection point A, the squint eye 91B is squint The line of sight is biased toward a virtual squint point B, and when the line of sight of the normal eye 91A is obscured (as shown in FIG. 2C), the line of sight of the squint eye 91B is automatically turned to the virtual two-eye line of sight intersection point A; The squint line correction device 20 is rotatably disposed between the squint eye 91B and the virtual squint point B, and has a corrected virtual point C for rotating the reflection to squint Eye line correction of eye 91B (correction process as shown in 2C, 2D, 2E, and 2F) to the virtual two The line of sight intersection point A; an electroencephalogram (EEG) extraction unit 30 is disposed on the head 90A of the subject 90, and captures the brain wave signal 91, the brain wave signal 91 is paired The subject's vision should be 90, and have a relaxation signal and a concentration signal, when the line of sight of the normal eye 91A faces the virtual eye line intersection point A, and the squint eye 91B makes the line of sight due to squint When the virtual squint point B is biased, the visual acuity of the test subject 90 is blurred, and the relaxation signal (such as the relaxation curve L1 shown in FIG. 6) and the concentration signal (such as the focus curve shown in FIG. 6) L2) does not meet; otherwise, when the line of sight of the normal eye 91A is toward the virtual two-eye line of sight intersection point A, and the line of sight of the squint eye 91B is corrected to the virtual two-eye line of sight intersection point A, the subject is tested The visual acuity of 90 is clear, and the relaxation signal generates an intersection point X with the concentration signal; to confirm that the squint eye 91B is located at a corrected eye position angle (Refer to FIG. 2C); a laser ranging module 40 is configurable at a first ranging position P1 (see FIG. 4A, located at the corrected virtual point C) and a second ranging position P2 (see Figure 4B is located at the virtual two-eye line of sight intersection point A) and a third ranging position P3 (refer to Figure 4C, adjacent to the virtual two-eye line of sight intersection point A, but the angle and the second ranging position P2 Between the different distances; when located at the first ranging position P1, a first side length between the corrected virtual point C and the virtual point D of the eye is quantifiable When located at the second ranging position P2, a second side length between the virtual two-eye line of sight intersection point A and the corrected virtual point C can be measured. When located at the third ranging position P3, a third side length between the virtual two-eye line of sight intersection point A and the eye virtual point position D can be measured. And a laser ranging angle can be calculated according to the cosine theorem , which should be close to the corrected eye position angle An invisible light detecting device 50 includes an invisible light emitting device 51, a left invisible image capturing device 52, and a right invisible image capturing device 53; the invisible light emitting device 51 is used to face the two The eye emits an invisible light 511, and an invisible reflected light spot is generated on the squint eye 91B (as shown in Fig. 3); when the line of sight of the squint eye 91B is corrected from the virtual squint point B (such as the pre-correction position PA shown in Fig. 2B) to the virtual two-eye line of sight intersection point A (e.g. In the corrected position PB) shown in FIG. 2F, the left invisible image capturing device 52 and the right invisible image capturing device 53 are simultaneously used to capture the invisible reflected light image 50A of the squint 91A. Get a eye tracking angle , the system is close to the corrected eye position angle A total control unit 60 electrically connects the line of sight guiding unit 10, the squint line correcting device 20, the brain wave capturing unit 30, the laser ranging module 40, and the invisible light detecting module 50. At least one of them is used to control its actions. In practice, the line of sight guiding portion 10 can be at least one of an optotype and a visible light device for guiding the line of sight of the subject 90. Referring to FIG. 1 , the brain wave capturing unit 30 is further provided with: a microprocessor structure 30A for capturing the brain wave signal 91 of a specific frequency band and storing it for retrieval. The microprocessor structure 30A The chip can be processed by the signal of the model "TGAMI"; the part to be specially explained here is that the pin of the TGAM1 signal processing chip includes the power supply 3.3V, the ground (GND), the serial data output (TX), and the serial data input. (RX), brain wave signal input (EEG), brain wave signal ground (GND), and brain wave signal reference potential (REF). The TGAM1 signal processing chip also retains the brainwave capture function, which includes brain waves of eight bands: [a] delta (0.5-2.75Hz); [b] theta (3.5-6.75Hz); [c] low- Alpha (7.5-9.25 Hz); [d] high-alpha (10-11.75 Hz); [e] low-beta (13-16.75 Hz); [f] high-beta (18-29.75 Hz); [g] Low-gamma (31-39.75Hz); [h] high-gamma (41-49.75Hz); where the relaxation signal is taken from low-beta (13-16.75Hz) and low-alpha (7.5-9.25Hz) For both bands, the greater the two values, the higher the relaxation. As for the concentration signal, it is taken from the low-gamma (31-39.75Hz) and high-gamma (41-49.75Hz) bands. The higher the two values, the higher the concentration. This creation defines the vision relaxation equation as the formula (1) according to the international definition of brain waves and the physiological phenomenon of vision. ∙∙∙∙(1) and define the vision focusing equation as equation (2) ∙(2) The brain wave signal 91 is a potential difference generated by the operation of the brain of the user 90. A sensing electrode 30B is coupled to the microprocessor structure 30A and is attached to a sensing electrode patch position Fp1 of the head 90A of the subject 90; a reference electrode 30C is coupled to the microprocessor. The device structure 30A is disposed on a reference electrode patch position A1 of the head 90A of the test subject 90, and the brain wave signal 91 is captured together with the sensing electrode 10B and transmitted to the micro processing. Structure 30A. Referring to FIG. 5, the microprocessor structure 30A includes an amplifier 31, an analog/digital (A/D) converter 32, an arithmetic unit 33, a band pass filter 34, and a fast Fourier transform unit (FFT). 35; wherein: the amplifier 31 is configured to receive the brain wave signal 91 and perform signal amplification processing; the analog/digital (A/D) converter 32 is configured to read the amplifier 31 for signal amplification. The brain wave signal 91, and converts the original brain wave data (RAW EEG), which is in the form of a packet; the operation unit 33 is configured to read and analyze the analog/digital (A/D) converter 32 after processing. The noise level of the brain wave signal 91; the band pass filter 34 is configured to read the brain wave signal 91 analyzed by the operation unit 33, and perform filtering processing; the fast Fourier transform unit (FFT) 35 For reading the filtered brain wave signal 91, and converting the brain wave signal 91 from the time domain signal to the frequency domain signal (known in the art, not described), and distinguishing the frequency bands, for example: delta ( 0.5-2.75Hz), theta (3.5-6.75Hz), low-alpha (7.5-9.25Hz), high-alpha (10-11.75Hz), low-beta (13-16.75Hz), high-beta (18-29.75Hz), low-gamma (31-39.75Hz), and high-gamma (41-49.75Hz); then pass the above data through the brainwave digital data of each frequency band ( LONG EEG) Packet processing for capture. When the brain wave capturing portion 30 is worn on the head 90A of the subject 90, and the squint eye 91B is directed from the line of sight toward the virtual squint point B, the visual acuity of the subject 90 should be blurred. The relaxation signal (such as the relaxation curve L1 shown in FIG. 6) does not intersect with the concentration signal (such as the focus curve L2 shown in FIG. 6); conversely, when the line of sight of the squint 91B is corrected and faces the virtual When the two eyes are at the intersection point A, the visual acuity of the subject 90 is clear, and the relaxation signal generates an intersection point X with the concentration signal; at this time, it can be confirmed that the squint 91B is located at the corrected eye position angle. (See Figure 2C). The laser ranging module 40 is configured to have the first side length The second side length And the third side length Transfer to the overall control unit 60 for the general control unit 60 according to the cosine theorem: Perform an operation; where: ; ; ; then the laser ranging angle can be obtained , which should be close (the best state is equal to) the corrected eye position angle And can help confirm the measurement results. The part to be specifically described here is that, referring to Fig. 2A, the eyes of the average person are all normal eyes 91A, and the lines of sight of both eyes are toward the intersection point A of the virtual two-eye line of sight. As shown in FIG. 2B, one of the eyes is a squint eye 91B whose line of sight is toward a virtual squint point B (having a squint eye angle) ). Oblique is regarded as a potential eye position deflection, but can maintain binocular monocular under the control of fusion reflex, to force the two eyes to remain in the positive position without showing skew, once the brain fusion is blocked (such as one eye is When covering (or covering) or losing control (such as in excessive use of eyesight or mental fatigue), the eye position deflection will manifest. The strabismus oblique angle correction process of this creation is as follows: First, let the two eyes of the test subject gaze into the distance to relax, and when the brain wave is relaxed, the test is started, and the experimental test time is 30 seconds. 1. Open both eyes (as shown in Fig. 2B), and the right eye (i.e., the normal eye 91A) gaze at the line of sight guiding portion 10 (the far side object at the intersection point A of the virtual two eye line of sight), the left eye (ie, the squint eye 91B) squints another optotype (located on the virtual squint point B) for 10 seconds. 2. Cover your eyes and time 10 seconds. 3. Cover the right eye (as shown in Figure 2C), then the line of sight of the left eye (the squint eye 91B) automatically turns to the virtual two-eye line of sight intersection point A (ie, the line of sight guide 10); The right eye front cover and the rotating plane mirror (ie, the slant line correction device 20) are reflective and correct the line of sight of the left eye (the squint 91B) (correction process such as 2C, 2D, 2E, and 2F) The virtual two-line intersection point A is displayed so that the left and right eyes face the line-of-sight guiding unit 10 at the same time to generate a fusion image (see FIG. 2F). In the foregoing strabismus oblique angle correction process, the following three measurement modes can be performed: [a] Laser ranging measurement mode: When the squint eye 91B is located at the corrected position PB, the laser ranging module 40 is used. Moving to the first ranging position P1 (refer to FIG. 4A, located at the corrected virtual point C), the second ranging position P2 (refer to FIG. 4B, the virtual two-eye line of sight intersection point A) and the a third ranging position P3 (refer to FIG. 4C, adjacent to the virtual two-eye line of sight intersection point A, but the angle is different from the third ranging position P3); and the first side length is respectively measured The second side length And the third side length For the total control unit 60 to obtain the laser ranging angle according to the cosine theorem operation Should be close to or equal to the corrected eye position angle . [b] Eye position tracking measurement mode: the invisible light emitting device 51 emits invisible light 511 toward the two eyes, and an invisible reflected light spot can be generated on the squint eye 91B. (as shown in Fig. 3); when the line of sight of the squint eye 91B is from the virtual squint point B (see Figures 2B and 3, from the pre-correction position PA and the invisible reflected spot) Can measure a squint eye angle ) sequentially moves to a first virtual correction point B1 (as shown in Figures 2D and 3, at which point the reflected light spot is never visible) Measuring a first corrected eye position angle ), a second virtual correction point B2 (as shown in Figures 2E and 3, the reflected light spot is never visible) Measured a second corrected eye position angle Move to the virtual two-eye line of sight intersection point A (see 2F and 3, from the corrected position PB and the invisible reflected spot) , can measure the eye tracking angle , it should wait for the corrected eye position angle The left invisible image capturing device 52 and the right invisible image capturing device 53 are simultaneously used to capture the invisible reflected light image 50A of the squint eye 91A, and the eye tracking angle can be obtained. Can be used to assist in confirming the corrected eye position angle . [c] Brain wave measurement mode: When the squint eye 91B deflects the line of sight toward the virtual squint point B due to squint, the visual acuity of the subject 90 is blurred, and the relaxation signal (as shown in FIG. 6) The relaxation curve L1) does not intersect with the concentration signal (such as the focus curve L2 shown in FIG. 6); conversely, when the line of sight of the squint 91B is corrected and the point A of the virtual two-eye line of sight is reached, the waiting The visual acuity of the tester 90 is clear, and the relaxation signal generates an intersection point X with the concentration signal; to confirm that the squint eye 91B is located at the corrected eye position angle (See Figure 2C). The present invention may further include a squint-first detecting device (located on the virtual two-eye line of sight intersection point A) having a red light 70A and a green light 70B. When normal and without squint, the two eyes should be oriented toward the strabismus. The detection device is advanced (as shown in Figure 2G). When one of the eyes is strabismus (assuming the right eye is normal and the left eye is squint), the first detection is as follows: 1. The red light 70A is turned on, which emits a red light 701. At this time, the line of sight of the right eye of the subject 90 (ie, the normal eye 91A) will face the spot of the red light 70A, as shown in FIG. 2H. At the same time, the left eye of the subject 90 (ie, the squint eye 91B) should be skewed toward the virtual squint point B. 2. Inspectors ask: What do you see? The subject 90 will answer: the right eye sees the red light 701. 3. Cover the right eye (as shown in Figure 2I), turn off the red light 70A and activate the green light 70B, which emits a green light 702. At this time, the right eye of the subject 90 (ie, the normal eye 91A) is hidden and can only be seen with the left eye. The left eye of the test subject 90 (ie, the squint eye 91B) will be skewed back and look at the green light 70B, that is, away from the direction of the virtual squint point B and return to the normal direction (the virtual two-eye line of sight intersection point) A). 4. Inspectors ask: What do you see? Since the line of sight of the left eye (the squint eye 91B) has now turned back to the virtual two-eye line of sight intersection point A, the subject 90 should answer: see green light 702. It can be confirmed through the above process that the test subject 90 should apply the measurement of the present creation. What is additionally explained here is that binocular vision refers to the image of an object in the environment being focused and falling on the corresponding points of the retina of the two eyes (mainly the macula), because the light falling on the retina will The rods and cones generate action potentials, and the induced electrical information is transmitted to the brain along the visual perception system. The visual signals from both eyes are analyzed in the high-level center of the brain, and integrated into a complete stereoscopic perception. Printing process. In the process of generating binocular vision, the sensory system and the motion system act simultaneously. The sensory system is a process of "seeing". The eye gathers the light to the retina. The retina transmits the impulse of light to the nerve center, and finally produces an understanding of the shape, color, motion, and relative position of the object. The ability to combine information with the other's sensory information to form a single image, called sensory fusion, must be done by "moter fusion" in order for the sensory image to appear. The match is consistent, and the motion fusion is the response of the extraocular muscles to maintain the matching of the eyes. The motion fusion occurs only when the sensory fusion occurs, and the motion fusion is the reaction to the sensory fusion; the sensory fusion occurs only when the motion fusion image appears. When the eyes produce a fusion image (brain wave fusion), that is, when the vision is clear, the relaxation signal and the concentration signal generate the intersection point X. The advantages and functions of this creation are as follows: [1] Multiple sensing can be synchronized to improve measurement accuracy. The creation also sets the laser ranging measurement mode, the eye position tracking measurement mode and the brain wave measurement mode, and can measure the oblique angle of the oblique direction simultaneously or separately, and can repeatedly compare the measured angles and increase the amount. Measure accuracy. Therefore, multiple sensing can be synchronized to improve measurement accuracy. [2] Facilitate strabismus measurement in patients with poor language expression. This creation is an objective measure of the change in the angle of the strabismus. It does not require the patient to express the clarity of the subjective vision. For strabismus patients with poor language skills or poor verbal ability, it is not necessary to consider whether the expression ability is accurate. Therefore, it is convenient to perform strabismus measurement on patients with poor language expression. [3] It is convenient for postoperative vision training brain wave fusion measurement in patients with strabismus. This creation does not require the patient to express the clarity of the subjective vision. For postoperative patients, the brain wave fusion measurement of postoperative visual acuity training can be directly performed. Therefore, it is convenient for the strabismus patients to perform postoperative visual training brain wave fusion measurement. The above is only a detailed description of the present invention by way of a preferred embodiment, and any modifications and variations of the embodiments are possible without departing from the spirit and scope of the present invention.

10‧‧‧視線導引部
20‧‧‧斜視線矯正裝置
30‧‧‧腦波擷取部
30A‧‧‧微處理器結構
30B‧‧‧感測電極
30C‧‧‧參考電極
31‧‧‧放大器
32‧‧‧類比/數位轉換器
33‧‧‧運算單元
34‧‧‧帶通濾通器
35‧‧‧快速傅立葉轉換單元
40‧‧‧雷射測距模組
50‧‧‧不可見光檢測模組
50A‧‧‧不可見反射光影像
51‧‧‧不可見發光裝置
511‧‧‧不可見光
52‧‧‧左側不可見光影像擷取裝置
53‧‧‧右側不可見光影像擷取裝置
60‧‧‧總控制部
70A‧‧‧紅燈
70B‧‧‧綠燈
701‧‧‧紅光
702‧‧‧綠光
90‧‧‧待測者
90A‧‧‧頭部
91‧‧‧腦波訊號
91A‧‧‧正常眼
91B‧‧‧斜視眼
A‧‧‧虛擬兩眼視線交會點位
B‧‧‧虛擬斜視點位
B1‧‧‧第一虛擬矯正點
B2‧‧‧第二虛擬矯正點
C‧‧‧矯正虛擬點位
D‧‧‧眼虛擬點位
L1‧‧‧放鬆曲線
L2‧‧‧專注曲線
X‧‧‧交會點
‧‧‧斜視眼位角度
‧‧‧第一矯正眼位角度
‧‧‧第二矯正眼位角度
‧‧‧矯正後眼位角度
‧‧‧雷射測距角度
‧‧‧眼位追蹤角度
‧‧‧不可見反射光點
P1‧‧‧第一測距位置
P2‧‧‧第二測距位置
P3‧‧‧第三測距位置
‧‧‧第一邊長
‧‧‧第二邊長
‧‧‧第三邊長
Fp1‧‧‧感測電極貼片位置
A1‧‧‧參考電極貼片位置10‧‧‧Sight line guide
20‧‧‧ strabismus correction device
30‧‧‧ Brainwave Capture Department
30A‧‧‧Microprocessor structure
30B‧‧‧Sensor electrode
30C‧‧‧ reference electrode
31‧‧‧Amplifier
32‧‧‧ Analog/Digital Converter
33‧‧‧ arithmetic unit
34‧‧‧Bandpass filter
35‧‧‧Fast Fourier Transform Unit
40‧‧‧Laser ranging module
50‧‧‧Invisible light detection module
50A‧‧‧Invisible reflected light image
51‧‧‧Invisible lighting device
511‧‧‧Invisible light
52‧‧‧ Left invisible image capturing device
53‧‧‧ Right invisible image capturing device
60‧‧‧General Control Department
70A‧‧‧Red light
70B‧‧‧Green light
701‧‧‧Red light
702‧‧‧Green light
90‧‧‧Testees
90A‧‧‧ head
91‧‧‧ brain wave signal
91A‧‧‧ normal eyes
91B‧‧ squint eye
A‧‧‧Virtual two-eye line of sight
B‧‧‧Virtual squint point
B1‧‧‧First virtual correction point
B2‧‧‧second virtual correction point
C‧‧‧Correct virtual point
D‧‧‧ eye virtual point
L1‧‧‧ relaxation curve
L2‧‧‧ focus curve
X‧‧‧ meeting point
‧‧‧squint eye angle
‧‧‧First corrective eye angle
‧‧‧Second corrected eye position angle
‧‧‧corrected eye position angle
‧‧‧Laser ranging angle
‧‧‧ Eye tracking angle
‧‧‧Invisible reflected light spots
P1‧‧‧first ranging position
P2‧‧‧Second distance measurement position
P3‧‧‧ third ranging position
‧‧‧First side length
‧‧‧Second side length
‧‧‧third side length
Fp1‧‧‧ Sense electrode patch position
A1‧‧‧Reference electrode patch position

第1圖係本創作之示意圖第2A圖係正常視線之示意圖第2B圖係兩眼其中之一為斜視之示意圖第2C圖係正常眼遮住則斜視眼自動轉回正常視線之示意圖第2D圖係斜視眼矯正至第一矯正眼位角度之示意圖第2E圖係斜視眼矯正至第二矯正眼位角度之示意圖第2F圖係斜視眼矯正至矯正後眼位角度之示意圖第2G圖係本創作之眼球斜視反應裝置之示意圖第2H圖係第2G圖之使用過程之一之示意圖第2I圖係第2G圖之使用過程之二之示意圖第3圖係本創作之斜視眼之矯正眼位追縱之示意圖第4A、第4B及第4C圖係分別為本創作之雷射測距模組分別位於第一測距位置、第二測距位置與第三測距位置之示意圖第5圖係本創作之腦波擷取部之系統方塊圖第6圖係本創作之腦波訊號之曲線圖Fig. 1 is a schematic view of the present invention. Fig. 2A is a schematic view of a normal line of sight. Fig. 2B is a schematic view of one of the two eyes, which is a squint view. Fig. 2C is a schematic view of the normal eye, and the squint eye automatically returns to the normal line of sight. FIG. 2E is a schematic diagram of the squint eye corrected to the second corrected eye position angle. FIG. 2F is a schematic view of the squint eye corrected to the corrected eye position angle. FIG. 2G is a creation of the eye. Schematic diagram of the eye strabismus reaction device 2H is a schematic diagram of one of the processes of the 2G diagram, FIG. 2I is a schematic diagram of the second process of the 2G diagram, and FIG. 3 is a correction of the eye position of the squint eye of the present creation. The schematic diagrams of the 4A, 4B, and 4C diagrams of the laser ranging module of the present invention are respectively located at the first ranging position, the second ranging position, and the third ranging position. The system block diagram of the brain wave extraction section is shown in Fig. 6 is a graph of the brain wave signal of the present creation.

10‧‧‧視線導引部 10‧‧‧Sight line guide

20‧‧‧斜視線矯正裝置 20‧‧‧ strabismus correction device

30‧‧‧腦波擷取部 30‧‧‧ Brainwave Capture Department

30A‧‧‧微處理器結構 30A‧‧‧Microprocessor structure

30B‧‧‧感測電極 30B‧‧‧Sensor electrode

30C‧‧‧參考電極 30C‧‧‧ reference electrode

40‧‧‧雷射測距模組 40‧‧‧Laser ranging module

50‧‧‧不可見光檢測模組 50‧‧‧Invisible light detection module

51‧‧‧不可見發光裝置 51‧‧‧Invisible lighting device

52‧‧‧左側不可見光影像擷取裝置 52‧‧‧ Left invisible image capturing device

53‧‧‧右側不可見光影像擷取裝置 53‧‧‧ Right invisible image capturing device

60‧‧‧總控制部 60‧‧‧General Control Department

90‧‧‧待測者 90‧‧‧Testees

90A‧‧‧頭部 90A‧‧‧ head

91‧‧‧腦波訊號 91‧‧‧ brain wave signal

91A‧‧‧正常眼 91A‧‧‧ normal eyes

91B‧‧‧斜視眼 91B‧‧ squint eye

P2‧‧‧第二測距位置 P2‧‧‧Second distance measurement position

Fp1‧‧‧感測電極貼片位置 Fp1‧‧‧ Sense electrode patch position

A1‧‧‧參考電極貼片位置 A1‧‧‧Reference electrode patch position

Claims

一種雷射測距斜視斜位角度量測裝置，係包括：　一視線導引部，係設於一虛擬兩眼視線交會點位，用以導引一待測者之視線；該待測者具有一頭部及兩眼，其中之一為正常眼；其中之另一為斜視眼，該斜視眼具有一眼虛擬點位；當該正常眼之視線朝向該虛擬兩眼視線交會點位，則該斜視眼因斜視而使視線偏向一虛擬斜視點位，並當該正常眼之視線被遮覆，則該斜視眼之視線自動轉向該虛擬兩眼視線交會點位；　一斜視線矯正裝置，係可轉動的設於該斜視眼與該虛擬斜視點位之間，並具有一矯正虛擬點位，該斜視線矯正裝置係用以轉動反射而將該斜視眼之視線矯正至該虛擬兩視線交會點位；　一腦波擷取部，係設於該待測者之該頭部，而擷取其腦波訊號，該腦波訊號係對應該待測者之兩眼視力，而具有一放鬆度訊號及一專注度訊號，當該正常眼之視線朝向該虛擬兩眼視線交會點位，且該斜視眼因斜視而使視線偏向該虛擬斜視點位，則該待測者之視力呈模糊，該放鬆度訊號與該專注度訊號不交會；反之，當該正常眼之視線朝向該虛擬兩眼視線交會點位，且該斜視眼之視線被矯正至該虛擬兩眼視線交會點位，則該待測者之視力呈清楚，該放鬆度訊號與該專注度訊號產生一交會點；用以確認該斜視眼位於一矯正後眼位角度；　一雷射測距模組，係可於一第一測距位置、一第二測距位置、一第三測距位置之間變換；當位於該第一測距位置，係可量得該矯正虛擬點位與該眼虛擬點位之間的一第一邊長，當位於該第二測距位置，係可量得該虛擬兩眼視線交會點位與該矯正虛擬點位之間的一第二邊長，當位於該第三測距位置，係可量得該虛擬兩眼視線交會點位與該眼虛擬點位之間的一第三邊長，而可根據餘弦定理運算出一雷射測距角度，其應接近該矯正後眼位角度；　一不可見光檢測模組，係包括一不可見發光裝置、一左側不可見光影像擷取裝置及一右側不可見光影像擷取裝置；該不可見光發光裝置係用以朝該兩眼發出一不可見光，而可於該斜視眼上產生不可見反射光點；當該斜視眼之視線從該虛擬斜視點位矯正至該虛擬兩眼視線交會點位時，該左側不可見光影像擷取裝置及該右側不可見光影像擷取裝置同時用以擷取該斜視眼之不可見反射光影像，而可得到一眼位追蹤角度，其係接近該矯正後眼位角度；　一總控制部，係電性連結該視線導引部、該斜視線矯正裝置、該腦波擷取部、該雷射測距模組、該不可見光檢測模組其中至少一者，而用以控制其動作。A laser ranging strabismus oblique angle measuring device comprises: a line of sight guiding portion, which is disposed at a virtual two-eye line of sight intersection point for guiding a line of sight of a person to be tested; the subject to be tested has One head and two eyes, one of which is a normal eye; the other of which is a squint eye having a virtual point; when the line of sight of the normal eye is toward the point of intersection of the virtual two-eye line of sight, the strabismus The eye is biased toward a virtual squint point due to squint, and when the line of sight of the normal eye is covered, the line of sight of the squint eye automatically turns to the virtual eye line intersection point; a squint line correction device is rotatable Between the squint eye and the virtual squint point, and having a corrective virtual point, the squint straightening device is used for rotating the reflection to correct the line of sight of the squint eye to the virtual two-line intersection point; a brain wave capturing unit is disposed on the head of the subject to be tested, and extracts a brain wave signal, the brain wave signal is a pair of visual acuity of the person to be tested, and has a relaxation signal and a Focus signal, when the normal eye When the line of sight is toward the intersection point of the virtual two-eye line of sight, and the squint eye is biased toward the virtual squint point due to squint, the visual acuity of the subject is blurred, and the relaxation signal does not intersect with the concentration signal; When the line of sight of the normal eye faces the intersection point of the virtual two-eye line of sight, and the line of sight of the squint eye is corrected to the point of intersection of the virtual two-eye line of sight, the visual acuity of the subject is clear, and the relaxation signal is The focus signal generates a meeting point; the hole is determined to be at a corrected eye position angle; a laser ranging module is at a first ranging position, a second ranging position, and a first Transforming between three ranging positions; when located at the first ranging position, a first side length between the corrected virtual point and the virtual point of the eye may be measured, when located at the second ranging position, The second side length between the virtual two-eye line of sight intersection point and the corrected virtual point is measured, and when located in the third ranging position, the virtual two-eye line of sight intersection point and the a third side between the virtual points of the eye, but According to the cosine theorem, a laser ranging angle is calculated, which should be close to the corrected eye position angle; an invisible light detecting module includes an invisible light emitting device, a left invisible image capturing device and a right invisible light An image capturing device; the invisible light emitting device is configured to emit an invisible light to the two eyes, and an invisible reflected light spot is generated on the squint eye; and the line of sight of the squint eye is corrected from the virtual squint point to When the virtual two-eye line of sight intersects, the left invisible image capturing device and the right invisible image capturing device simultaneously capture the invisible reflected light image of the squint eye, and obtain an eye tracking angle. The system is close to the corrected eye position angle; a total control unit electrically connecting the line of sight guiding unit, the squint line correcting device, the brain wave capturing unit, the laser ranging module, and the invisible light detecting unit At least one of the modules is used to control its action.

如申請專利範圍第１項所述之雷射測距斜視斜位角度量測裝置，其中，該視線導引部係為視標、可見光裝置其中至少一者，用以導引該待測者之視線。The apparatus of claim 1 , wherein the line of sight guiding unit is at least one of an optotype and a visible light device for guiding the subject to be tested. Sight.

如申請專利範圍第１項所述之雷射測距斜視斜位角度量測裝置，其中：　該頭部係具有一感測電極貼片位置及一參考電極貼片位置；　該腦波擷取部又包括：　　一微處理器結構，係用以擷取特定頻段之該腦波訊號，並儲存以供擷取；　　一感測電極，係連結該微處理器結構，並用以貼設於該感測電極貼片位置上；　　一參考電極，係連結該微處理器結構，並用以貼設於該參考電極貼片位置上，而與該感測電極共同擷取該腦波訊號，並傳送至該微處理器結構。The laser ranging squint oblique angle measuring device according to claim 1, wherein: the head has a sensing electrode patch position and a reference electrode patch position; the brain wave capturing portion The method further includes: a microprocessor structure for capturing the brain wave signal of a specific frequency band and storing for capturing; a sensing electrode is coupled to the microprocessor structure and configured to be attached to the sensing a reference electrode is connected to the microprocessor structure and is attached to the reference electrode patch position, and the brain wave signal is taken together with the sensing electrode and transmitted to the micro Processor structure.

如申請專利範圍第３項所述之雷射測距斜視斜位角度量測裝置，其中，該微處理器結構係包括一放大器、一類比/數位轉換器、一運算單元、一帶通濾通器及一快速傅立葉轉換單元；其中：　該放大器係用以接收該腦波訊號，並進行訊號放大處理；　該類比/數位轉換器係用以讀取該放大器進行訊號放大後之該腦波訊號，並轉換出原始腦波資料；　該運算單元係用以讀取並分析該類比/數位轉換器處理後之該腦波訊號之雜訊程度；　該帶通濾波器係用以讀取該運算單元分析後之該腦波訊號，並進行濾波處理；　該快速傅立葉轉換單元，係用以讀取濾波處理後之該腦波訊號，並將腦波訊號從時域訊號轉換為頻域訊號；再將前述資料透過各頻段腦波數位資料封包處理，以供擷取。The laser ranging squint oblique angle measuring device according to claim 3, wherein the microprocessor structure comprises an amplifier, an analog/digital converter, an arithmetic unit, and a band pass filter. And a fast Fourier transform unit; wherein: the amplifier is configured to receive the brain wave signal and perform signal amplification processing; the analog/digital converter is configured to read the brain wave signal after the amplifier performs signal amplification, and Converting the original brain wave data; the computing unit is configured to read and analyze the noise level of the brain wave signal processed by the analog/digital converter; the band pass filter is used to read the operation unit after analysis The brain wave signal is filtered and processed; the fast Fourier transform unit is configured to read the filtered brain wave signal and convert the brain wave signal from the time domain signal to the frequency domain signal; It is processed through the brain wave digital data packet of each frequency band for extraction.